GB2553260A - A ready-to-use, hydrophilic, self-dispersive, fragmentable and biodegradable porous sponge matrix and a method of manufacturing thereof - Google Patents
A ready-to-use, hydrophilic, self-dispersive, fragmentable and biodegradable porous sponge matrix and a method of manufacturing thereof Download PDFInfo
- Publication number
- GB2553260A GB2553260A GB1608671.2A GB201608671A GB2553260A GB 2553260 A GB2553260 A GB 2553260A GB 201608671 A GB201608671 A GB 201608671A GB 2553260 A GB2553260 A GB 2553260A
- Authority
- GB
- United Kingdom
- Prior art keywords
- sponge
- polymers
- solution
- matrix
- water
- 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.)
- Granted
Links
- 239000011159 matrix material Substances 0.000 title claims abstract description 51
- 238000004519 manufacturing process Methods 0.000 title claims abstract description 12
- 229920000642 polymer Polymers 0.000 claims abstract description 72
- 238000000034 method Methods 0.000 claims abstract description 49
- 239000003814 drug Substances 0.000 claims abstract description 37
- 239000000203 mixture Substances 0.000 claims abstract description 34
- 239000007787 solid Substances 0.000 claims abstract description 21
- 229920000159 gelatin Polymers 0.000 claims abstract description 19
- 235000019322 gelatine Nutrition 0.000 claims abstract description 19
- 229920001661 Chitosan Polymers 0.000 claims abstract description 18
- 108010010803 Gelatin Proteins 0.000 claims abstract description 18
- 239000008273 gelatin Substances 0.000 claims abstract description 18
- 235000011852 gelatine desserts Nutrition 0.000 claims abstract description 18
- 238000002156 mixing Methods 0.000 claims abstract description 18
- 239000002250 absorbent Substances 0.000 claims abstract description 17
- 230000002745 absorbent Effects 0.000 claims abstract description 17
- 229920001282 polysaccharide Polymers 0.000 claims abstract description 12
- 239000005017 polysaccharide Substances 0.000 claims abstract description 12
- 229920002451 polyvinyl alcohol Polymers 0.000 claims abstract description 9
- 241000196324 Embryophyta Species 0.000 claims abstract description 8
- 239000002202 Polyethylene glycol Substances 0.000 claims abstract description 8
- 235000010443 alginic acid Nutrition 0.000 claims abstract description 8
- 229920000615 alginic acid Polymers 0.000 claims abstract description 8
- 229920001223 polyethylene glycol Polymers 0.000 claims abstract description 8
- FHVDTGUDJYJELY-UHFFFAOYSA-N 6-{[2-carboxy-4,5-dihydroxy-6-(phosphanyloxy)oxan-3-yl]oxy}-4,5-dihydroxy-3-phosphanyloxane-2-carboxylic acid Chemical compound O1C(C(O)=O)C(P)C(O)C(O)C1OC1C(C(O)=O)OC(OP)C(O)C1O FHVDTGUDJYJELY-UHFFFAOYSA-N 0.000 claims abstract description 7
- 239000004372 Polyvinyl alcohol Substances 0.000 claims abstract description 7
- 229940072056 alginate Drugs 0.000 claims abstract description 7
- 229940124597 therapeutic agent Drugs 0.000 claims abstract description 7
- 229920000915 polyvinyl chloride Polymers 0.000 claims abstract description 6
- 239000004800 polyvinyl chloride Substances 0.000 claims abstract description 6
- UBLAMKHIFZBBSS-UHFFFAOYSA-N 3-Methylbutyl pentanoate Chemical compound CCCCC(=O)OCCC(C)C UBLAMKHIFZBBSS-UHFFFAOYSA-N 0.000 claims abstract description 4
- 244000208874 Althaea officinalis Species 0.000 claims abstract description 4
- 235000006576 Althaea officinalis Nutrition 0.000 claims abstract description 4
- 241000206575 Chondrus crispus Species 0.000 claims abstract description 4
- 244000134552 Plantago ovata Species 0.000 claims abstract description 4
- 235000003421 Plantago ovata Nutrition 0.000 claims abstract description 4
- 239000009223 Psyllium Substances 0.000 claims abstract description 4
- 235000004426 flaxseed Nutrition 0.000 claims abstract description 4
- 239000010903 husk Substances 0.000 claims abstract description 4
- 235000001035 marshmallow Nutrition 0.000 claims abstract description 4
- 229940070687 psyllium Drugs 0.000 claims abstract description 4
- 229940126585 therapeutic drug Drugs 0.000 claims abstract description 4
- 239000001917 trigonella foenum graecum l. absolute Substances 0.000 claims abstract description 4
- 150000004676 glycans Chemical class 0.000 claims abstract 5
- 239000000243 solution Substances 0.000 claims description 40
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 claims description 21
- 239000000126 substance Substances 0.000 claims description 17
- QTBSBXVTEAMEQO-UHFFFAOYSA-N Acetic acid Chemical compound CC(O)=O QTBSBXVTEAMEQO-UHFFFAOYSA-N 0.000 claims description 16
- QGZKDVFQNNGYKY-UHFFFAOYSA-N Ammonia Chemical compound N QGZKDVFQNNGYKY-UHFFFAOYSA-N 0.000 claims description 8
- KIUKXJAPPMFGSW-DNGZLQJQSA-N (2S,3S,4S,5R,6R)-6-[(2S,3R,4R,5S,6R)-3-Acetamido-2-[(2S,3S,4R,5R,6R)-6-[(2R,3R,4R,5S,6R)-3-acetamido-2,5-dihydroxy-6-(hydroxymethyl)oxan-4-yl]oxy-2-carboxy-4,5-dihydroxyoxan-3-yl]oxy-5-hydroxy-6-(hydroxymethyl)oxan-4-yl]oxy-3,4,5-trihydroxyoxane-2-carboxylic acid Chemical compound CC(=O)N[C@H]1[C@H](O)O[C@H](CO)[C@@H](O)[C@@H]1O[C@H]1[C@H](O)[C@@H](O)[C@H](O[C@H]2[C@@H]([C@@H](O[C@H]3[C@@H]([C@@H](O)[C@H](O)[C@H](O3)C(O)=O)O)[C@H](O)[C@@H](CO)O2)NC(C)=O)[C@@H](C(O)=O)O1 KIUKXJAPPMFGSW-DNGZLQJQSA-N 0.000 claims description 7
- 102000008186 Collagen Human genes 0.000 claims description 7
- 108010035532 Collagen Proteins 0.000 claims description 7
- 229920001436 collagen Polymers 0.000 claims description 7
- 229920002674 hyaluronan Polymers 0.000 claims description 7
- 229960003160 hyaluronic acid Drugs 0.000 claims description 7
- 108010009736 Protein Hydrolysates Proteins 0.000 claims description 6
- 229960000583 acetic acid Drugs 0.000 claims description 6
- 235000010948 carboxy methyl cellulose Nutrition 0.000 claims description 5
- 230000035876 healing Effects 0.000 claims description 5
- 239000007788 liquid Substances 0.000 claims description 5
- 239000000843 powder Substances 0.000 claims description 5
- IXPNQXFRVYWDDI-UHFFFAOYSA-N 1-methyl-2,4-dioxo-1,3-diazinane-5-carboximidamide Chemical compound CN1CC(C(N)=N)C(=O)NC1=O IXPNQXFRVYWDDI-UHFFFAOYSA-N 0.000 claims description 4
- 229910021529 ammonia Inorganic materials 0.000 claims description 4
- 239000001768 carboxy methyl cellulose Substances 0.000 claims description 4
- 239000008112 carboxymethyl-cellulose Substances 0.000 claims description 4
- 238000004090 dissolution Methods 0.000 claims description 4
- 238000001035 drying Methods 0.000 claims description 4
- 239000000284 extract Substances 0.000 claims description 4
- 238000001914 filtration Methods 0.000 claims description 4
- -1 poly(vinyl pyrrolidone) Polymers 0.000 claims description 4
- 229920002635 polyurethane Polymers 0.000 claims description 4
- 239000004814 polyurethane Substances 0.000 claims description 4
- 239000000661 sodium alginate Substances 0.000 claims description 4
- 235000010413 sodium alginate Nutrition 0.000 claims description 4
- 229940005550 sodium alginate Drugs 0.000 claims description 4
- 229920002134 Carboxymethyl cellulose Polymers 0.000 claims description 3
- 108010076876 Keratins Proteins 0.000 claims description 3
- 102000011782 Keratins Human genes 0.000 claims description 3
- 229920000604 Polyethylene Glycol 200 Polymers 0.000 claims description 3
- 239000002253 acid Substances 0.000 claims description 3
- 238000007865 diluting Methods 0.000 claims description 3
- 238000003756 stirring Methods 0.000 claims description 3
- SXRSQZLOMIGNAQ-UHFFFAOYSA-N Glutaraldehyde Chemical compound O=CCCCC=O SXRSQZLOMIGNAQ-UHFFFAOYSA-N 0.000 claims description 2
- 239000012362 glacial acetic acid Substances 0.000 claims description 2
- WSFSSNUMVMOOMR-NJFSPNSNSA-N methanone Chemical compound O=[14CH2] WSFSSNUMVMOOMR-NJFSPNSNSA-N 0.000 claims description 2
- 229940113115 polyethylene glycol 200 Drugs 0.000 claims description 2
- 229920002959 polymer blend Polymers 0.000 claims description 2
- 229920001451 polypropylene glycol Polymers 0.000 claims description 2
- 230000005855 radiation Effects 0.000 claims description 2
- 238000007669 thermal treatment Methods 0.000 claims description 2
- 238000011037 discontinuous sequential dilution Methods 0.000 claims 1
- 230000000087 stabilizing effect Effects 0.000 claims 1
- 238000012856 packing Methods 0.000 abstract description 34
- 238000001356 surgical procedure Methods 0.000 abstract description 21
- 208000032843 Hemorrhage Diseases 0.000 abstract description 14
- 230000000740 bleeding effect Effects 0.000 abstract description 10
- 208000001780 epistaxis Diseases 0.000 abstract description 9
- 208000031737 Tissue Adhesions Diseases 0.000 abstract description 7
- 230000017423 tissue regeneration Effects 0.000 abstract description 7
- 239000000463 material Substances 0.000 description 27
- 239000006260 foam Substances 0.000 description 26
- 208000027418 Wounds and injury Diseases 0.000 description 20
- 229940079593 drug Drugs 0.000 description 18
- 206010052428 Wound Diseases 0.000 description 17
- 229940014259 gelatin Drugs 0.000 description 12
- 230000008569 process Effects 0.000 description 12
- 239000000047 product Substances 0.000 description 12
- 210000004027 cell Anatomy 0.000 description 11
- 210000001519 tissue Anatomy 0.000 description 11
- 230000001276 controlling effect Effects 0.000 description 10
- 239000002904 solvent Substances 0.000 description 10
- 241001465754 Metazoa Species 0.000 description 8
- 239000013543 active substance Substances 0.000 description 8
- 238000009472 formulation Methods 0.000 description 8
- 230000029663 wound healing Effects 0.000 description 8
- 239000012867 bioactive agent Substances 0.000 description 7
- 239000008280 blood Substances 0.000 description 7
- 210000004369 blood Anatomy 0.000 description 7
- 239000003795 chemical substances by application Substances 0.000 description 7
- 239000002131 composite material Substances 0.000 description 7
- 150000004804 polysaccharides Chemical class 0.000 description 7
- 238000012377 drug delivery Methods 0.000 description 6
- 238000013129 endoscopic sinus surgery Methods 0.000 description 6
- 230000002439 hemostatic effect Effects 0.000 description 6
- 239000011148 porous material Substances 0.000 description 6
- 238000002360 preparation method Methods 0.000 description 6
- 230000001225 therapeutic effect Effects 0.000 description 6
- 238000010521 absorption reaction Methods 0.000 description 5
- 150000001875 compounds Chemical class 0.000 description 5
- 230000000694 effects Effects 0.000 description 5
- 239000002245 particle Substances 0.000 description 5
- 235000019422 polyvinyl alcohol Nutrition 0.000 description 5
- 108090000190 Thrombin Proteins 0.000 description 4
- 238000007906 compression Methods 0.000 description 4
- 230000006835 compression Effects 0.000 description 4
- 230000006378 damage Effects 0.000 description 4
- 239000012530 fluid Substances 0.000 description 4
- 239000000017 hydrogel Substances 0.000 description 4
- 208000014674 injury Diseases 0.000 description 4
- 230000003993 interaction Effects 0.000 description 4
- 210000003928 nasal cavity Anatomy 0.000 description 4
- 229920000867 polyelectrolyte Polymers 0.000 description 4
- 229960004072 thrombin Drugs 0.000 description 4
- 229920000954 Polyglycolide Polymers 0.000 description 3
- 108010063195 Surgiflo Proteins 0.000 description 3
- 239000012062 aqueous buffer Substances 0.000 description 3
- 230000000975 bioactive effect Effects 0.000 description 3
- 239000013060 biological fluid Substances 0.000 description 3
- 239000012620 biological material Substances 0.000 description 3
- 230000036760 body temperature Effects 0.000 description 3
- 229940105329 carboxymethylcellulose Drugs 0.000 description 3
- 238000006243 chemical reaction Methods 0.000 description 3
- 230000001010 compromised effect Effects 0.000 description 3
- 238000004132 cross linking Methods 0.000 description 3
- 208000037265 diseases, disorders, signs and symptoms Diseases 0.000 description 3
- 208000035475 disorder Diseases 0.000 description 3
- 239000003937 drug carrier Substances 0.000 description 3
- 125000000524 functional group Chemical group 0.000 description 3
- 239000000499 gel Substances 0.000 description 3
- 239000003102 growth factor Substances 0.000 description 3
- 230000023597 hemostasis Effects 0.000 description 3
- 239000004633 polyglycolic acid Substances 0.000 description 3
- 229950008885 polyglycolic acid Drugs 0.000 description 3
- 201000009890 sinusitis Diseases 0.000 description 3
- 230000006641 stabilisation Effects 0.000 description 3
- 238000011105 stabilization Methods 0.000 description 3
- 210000000130 stem cell Anatomy 0.000 description 3
- 229920001059 synthetic polymer Polymers 0.000 description 3
- 238000012876 topography Methods 0.000 description 3
- GYDJEQRTZSCIOI-LJGSYFOKSA-N tranexamic acid Chemical compound NC[C@H]1CC[C@H](C(O)=O)CC1 GYDJEQRTZSCIOI-LJGSYFOKSA-N 0.000 description 3
- 229960000401 tranexamic acid Drugs 0.000 description 3
- SLXKOJJOQWFEFD-UHFFFAOYSA-N 6-aminohexanoic acid Chemical compound NCCCCCC(O)=O SLXKOJJOQWFEFD-UHFFFAOYSA-N 0.000 description 2
- 108010039209 Blood Coagulation Factors Proteins 0.000 description 2
- 102000015081 Blood Coagulation Factors Human genes 0.000 description 2
- UXVMQQNJUSDDNG-UHFFFAOYSA-L Calcium chloride Chemical compound [Cl-].[Cl-].[Ca+2] UXVMQQNJUSDDNG-UHFFFAOYSA-L 0.000 description 2
- 108010080379 Fibrin Tissue Adhesive Proteins 0.000 description 2
- 208000005422 Foreign-Body reaction Diseases 0.000 description 2
- FQISKWAFAHGMGT-SGJOWKDISA-M Methylprednisolone sodium succinate Chemical compound [Na+].C([C@@]12C)=CC(=O)C=C1[C@@H](C)C[C@@H]1[C@@H]2[C@@H](O)C[C@]2(C)[C@@](O)(C(=O)COC(=O)CCC([O-])=O)CC[C@H]21 FQISKWAFAHGMGT-SGJOWKDISA-M 0.000 description 2
- XGMPVBXKDAHORN-RBWIMXSLSA-N Triamcinolone diacetate Chemical compound C1CC2=CC(=O)C=C[C@]2(C)[C@]2(F)[C@@H]1[C@@H]1C[C@@H](OC(C)=O)[C@@](C(=O)COC(=O)C)(O)[C@@]1(C)C[C@@H]2O XGMPVBXKDAHORN-RBWIMXSLSA-N 0.000 description 2
- TZIZWYVVGLXXFV-FLRHRWPCSA-N Triamcinolone hexacetonide Chemical compound C1CC2=CC(=O)C=C[C@]2(C)[C@]2(F)[C@@H]1[C@@H]1C[C@H]3OC(C)(C)O[C@@]3(C(=O)COC(=O)CC(C)(C)C)[C@@]1(C)C[C@@H]2O TZIZWYVVGLXXFV-FLRHRWPCSA-N 0.000 description 2
- 239000003242 anti bacterial agent Substances 0.000 description 2
- 229940088710 antibiotic agent Drugs 0.000 description 2
- 239000003963 antioxidant agent Substances 0.000 description 2
- 235000006708 antioxidants Nutrition 0.000 description 2
- 230000004888 barrier function Effects 0.000 description 2
- 230000008901 benefit Effects 0.000 description 2
- 230000015572 biosynthetic process Effects 0.000 description 2
- 230000023555 blood coagulation Effects 0.000 description 2
- 239000003114 blood coagulation factor Substances 0.000 description 2
- 210000001124 body fluid Anatomy 0.000 description 2
- 239000010839 body fluid Substances 0.000 description 2
- 239000001110 calcium chloride Substances 0.000 description 2
- 229910001628 calcium chloride Inorganic materials 0.000 description 2
- 239000001913 cellulose Substances 0.000 description 2
- 229920002678 cellulose Polymers 0.000 description 2
- 229960003957 dexamethasone Drugs 0.000 description 2
- UREBDLICKHMUKA-CXSFZGCWSA-N dexamethasone Chemical compound C1CC2=CC(=O)C=C[C@]2(C)[C@]2(F)[C@@H]1[C@@H]1C[C@@H](C)[C@@](C(=O)CO)(O)[C@@]1(C)C[C@@H]2O UREBDLICKHMUKA-CXSFZGCWSA-N 0.000 description 2
- 238000005516 engineering process Methods 0.000 description 2
- 230000002708 enhancing effect Effects 0.000 description 2
- HIDUXZXZQUHSBT-UHFFFAOYSA-N ethenol;formaldehyde Chemical compound O=C.OC=C HIDUXZXZQUHSBT-UHFFFAOYSA-N 0.000 description 2
- 238000007710 freezing Methods 0.000 description 2
- 230000008014 freezing Effects 0.000 description 2
- 210000001214 frontal sinus Anatomy 0.000 description 2
- RWSXRVCMGQZWBV-WDSKDSINSA-N glutathione Chemical compound OC(=O)[C@@H](N)CCC(=O)N[C@@H](CS)C(=O)NCC(O)=O RWSXRVCMGQZWBV-WDSKDSINSA-N 0.000 description 2
- 238000000265 homogenisation Methods 0.000 description 2
- 238000003780 insertion Methods 0.000 description 2
- 230000037431 insertion Effects 0.000 description 2
- 239000004973 liquid crystal related substance Substances 0.000 description 2
- 230000007246 mechanism Effects 0.000 description 2
- 210000004379 membrane Anatomy 0.000 description 2
- 239000012528 membrane Substances 0.000 description 2
- 229960004584 methylprednisolone Drugs 0.000 description 2
- 210000002850 nasal mucosa Anatomy 0.000 description 2
- 229920005615 natural polymer Polymers 0.000 description 2
- 125000000963 oxybis(methylene) group Chemical group [H]C([H])(*)OC([H])([H])* 0.000 description 2
- 210000003695 paranasal sinus Anatomy 0.000 description 2
- 235000018102 proteins Nutrition 0.000 description 2
- 102000004169 proteins and genes Human genes 0.000 description 2
- 108090000623 proteins and genes Proteins 0.000 description 2
- 239000007858 starting material Substances 0.000 description 2
- 150000003431 steroids Chemical group 0.000 description 2
- 230000002459 sustained effect Effects 0.000 description 2
- 238000013268 sustained release Methods 0.000 description 2
- 239000012730 sustained-release form Substances 0.000 description 2
- 229960005294 triamcinolone Drugs 0.000 description 2
- GFNANZIMVAIWHM-OBYCQNJPSA-N triamcinolone Chemical compound O=C1C=C[C@]2(C)[C@@]3(F)[C@@H](O)C[C@](C)([C@@]([C@H](O)C4)(O)C(=O)CO)[C@@H]4[C@@H]3CCC2=C1 GFNANZIMVAIWHM-OBYCQNJPSA-N 0.000 description 2
- 229960002117 triamcinolone acetonide Drugs 0.000 description 2
- YNDXUCZADRHECN-JNQJZLCISA-N triamcinolone acetonide Chemical compound C1CC2=CC(=O)C=C[C@]2(C)[C@]2(F)[C@@H]1[C@@H]1C[C@H]3OC(C)(C)O[C@@]3(C(=O)CO)[C@@]1(C)C[C@@H]2O YNDXUCZADRHECN-JNQJZLCISA-N 0.000 description 2
- 229960004320 triamcinolone diacetate Drugs 0.000 description 2
- 229960004221 triamcinolone hexacetonide Drugs 0.000 description 2
- 239000003981 vehicle Substances 0.000 description 2
- 238000009736 wetting Methods 0.000 description 2
- PFTAWBLQPZVEMU-DZGCQCFKSA-N (+)-catechin Chemical compound C1([C@H]2OC3=CC(O)=CC(O)=C3C[C@@H]2O)=CC=C(O)C(O)=C1 PFTAWBLQPZVEMU-DZGCQCFKSA-N 0.000 description 1
- IZFHEQBZOYJLPK-SSDOTTSWSA-N (R)-dihydrolipoic acid Chemical compound OC(=O)CCCC[C@@H](S)CCS IZFHEQBZOYJLPK-SSDOTTSWSA-N 0.000 description 1
- TUSDEZXZIZRFGC-UHFFFAOYSA-N 1-O-galloyl-3,6-(R)-HHDP-beta-D-glucose Natural products OC1C(O2)COC(=O)C3=CC(O)=C(O)C(O)=C3C3=C(O)C(O)=C(O)C=C3C(=O)OC1C(O)C2OC(=O)C1=CC(O)=C(O)C(O)=C1 TUSDEZXZIZRFGC-UHFFFAOYSA-N 0.000 description 1
- MSWZFWKMSRAUBD-IVMDWMLBSA-N 2-amino-2-deoxy-D-glucopyranose Chemical compound N[C@H]1C(O)O[C@H](CO)[C@@H](O)[C@@H]1O MSWZFWKMSRAUBD-IVMDWMLBSA-N 0.000 description 1
- NLXLAEXVIDQMFP-UHFFFAOYSA-N Ammonium chloride Substances [NH4+].[Cl-] NLXLAEXVIDQMFP-UHFFFAOYSA-N 0.000 description 1
- VHUUQVKOLVNVRT-UHFFFAOYSA-N Ammonium hydroxide Chemical compound [NH4+].[OH-] VHUUQVKOLVNVRT-UHFFFAOYSA-N 0.000 description 1
- 229920002101 Chitin Polymers 0.000 description 1
- 206010053567 Coagulopathies Diseases 0.000 description 1
- 229920000742 Cotton Polymers 0.000 description 1
- 239000004971 Cross linker Substances 0.000 description 1
- 208000008960 Diabetic foot Diseases 0.000 description 1
- BWGNESOTFCXPMA-UHFFFAOYSA-N Dihydrogen disulfide Chemical compound SS BWGNESOTFCXPMA-UHFFFAOYSA-N 0.000 description 1
- 239000001263 FEMA 3042 Substances 0.000 description 1
- BWGVNKXGVNDBDI-UHFFFAOYSA-N Fibrin monomer Chemical group CNC(=O)CNC(=O)CN BWGVNKXGVNDBDI-UHFFFAOYSA-N 0.000 description 1
- 108010049003 Fibrinogen Proteins 0.000 description 1
- 102000008946 Fibrinogen Human genes 0.000 description 1
- 208000003899 Foreign-Body Granuloma Diseases 0.000 description 1
- 239000001828 Gelatine Substances 0.000 description 1
- 108010024636 Glutathione Proteins 0.000 description 1
- XUJNEKJLAYXESH-REOHCLBHSA-N L-Cysteine Chemical compound SC[C@H](N)C(O)=O XUJNEKJLAYXESH-REOHCLBHSA-N 0.000 description 1
- PWKSKIMOESPYIA-BYPYZUCNSA-N L-N-acetyl-Cysteine Chemical compound CC(=O)N[C@@H](CS)C(O)=O PWKSKIMOESPYIA-BYPYZUCNSA-N 0.000 description 1
- 229920000715 Mucilage Polymers 0.000 description 1
- 206010028748 Nasal obstruction Diseases 0.000 description 1
- 208000025690 Otorhinolaryngologic disease Diseases 0.000 description 1
- 241001494479 Pecora Species 0.000 description 1
- LRBQNJMCXXYXIU-PPKXGCFTSA-N Penta-digallate-beta-D-glucose Natural products OC1=C(O)C(O)=CC(C(=O)OC=2C(=C(O)C=C(C=2)C(=O)OC[C@@H]2[C@H]([C@H](OC(=O)C=3C=C(OC(=O)C=4C=C(O)C(O)=C(O)C=4)C(O)=C(O)C=3)[C@@H](OC(=O)C=3C=C(OC(=O)C=4C=C(O)C(O)=C(O)C=4)C(O)=C(O)C=3)[C@H](OC(=O)C=3C=C(OC(=O)C=4C=C(O)C(O)=C(O)C=4)C(O)=C(O)C=3)O2)OC(=O)C=2C=C(OC(=O)C=3C=C(O)C(O)=C(O)C=3)C(O)=C(O)C=2)O)=C1 LRBQNJMCXXYXIU-PPKXGCFTSA-N 0.000 description 1
- 239000004264 Petrolatum Substances 0.000 description 1
- 108010039918 Polylysine Proteins 0.000 description 1
- 206010040070 Septic Shock Diseases 0.000 description 1
- 239000004809 Teflon Substances 0.000 description 1
- 229920006362 Teflon® Polymers 0.000 description 1
- 206010044248 Toxic shock syndrome Diseases 0.000 description 1
- 231100000650 Toxic shock syndrome Toxicity 0.000 description 1
- GYDJEQRTZSCIOI-UHFFFAOYSA-N Tranexamic acid Chemical compound NCC1CCC(C(O)=O)CC1 GYDJEQRTZSCIOI-UHFFFAOYSA-N 0.000 description 1
- 208000000558 Varicose Ulcer Diseases 0.000 description 1
- 229960004308 acetylcysteine Drugs 0.000 description 1
- 239000000853 adhesive Substances 0.000 description 1
- 150000001299 aldehydes Chemical class 0.000 description 1
- 239000000783 alginic acid Substances 0.000 description 1
- 229960001126 alginic acid Drugs 0.000 description 1
- 239000003513 alkali Substances 0.000 description 1
- 229940100095 amicar Drugs 0.000 description 1
- 229960002684 aminocaproic acid Drugs 0.000 description 1
- 235000011114 ammonium hydroxide Nutrition 0.000 description 1
- 229940035676 analgesics Drugs 0.000 description 1
- 239000000730 antalgic agent Substances 0.000 description 1
- 230000003266 anti-allergic effect Effects 0.000 description 1
- 230000001567 anti-fibrinolytic effect Effects 0.000 description 1
- 230000002924 anti-infective effect Effects 0.000 description 1
- 230000001028 anti-proliverative effect Effects 0.000 description 1
- 239000000504 antifibrinolytic agent Substances 0.000 description 1
- 229940082620 antifibrinolytics Drugs 0.000 description 1
- 229940030225 antihemorrhagics Drugs 0.000 description 1
- 239000004599 antimicrobial Substances 0.000 description 1
- 239000007864 aqueous solution Substances 0.000 description 1
- MSWZFWKMSRAUBD-UHFFFAOYSA-N beta-D-galactosamine Natural products NC1C(O)OC(CO)C(O)C1O MSWZFWKMSRAUBD-UHFFFAOYSA-N 0.000 description 1
- 229920002988 biodegradable polymer Polymers 0.000 description 1
- 239000004621 biodegradable polymer Substances 0.000 description 1
- 229920001222 biopolymer Polymers 0.000 description 1
- 208000034158 bleeding Diseases 0.000 description 1
- 230000017531 blood circulation Effects 0.000 description 1
- 210000000988 bone and bone Anatomy 0.000 description 1
- 229960002713 calcium chloride Drugs 0.000 description 1
- ADRVNXBAWSRFAJ-UHFFFAOYSA-N catechin Natural products OC1Cc2cc(O)cc(O)c2OC1c3ccc(O)c(O)c3 ADRVNXBAWSRFAJ-UHFFFAOYSA-N 0.000 description 1
- 235000005487 catechin Nutrition 0.000 description 1
- 230000010261 cell growth Effects 0.000 description 1
- 230000001413 cellular effect Effects 0.000 description 1
- 235000019365 chlortetracycline Nutrition 0.000 description 1
- 229950001002 cianidanol Drugs 0.000 description 1
- 230000035602 clotting Effects 0.000 description 1
- 239000000470 constituent Substances 0.000 description 1
- 239000003246 corticosteroid Substances 0.000 description 1
- 238000005520 cutting process Methods 0.000 description 1
- 229940099355 cyklokapron Drugs 0.000 description 1
- XUJNEKJLAYXESH-UHFFFAOYSA-N cysteine Natural products SCC(N)C(O)=O XUJNEKJLAYXESH-UHFFFAOYSA-N 0.000 description 1
- 235000018417 cysteine Nutrition 0.000 description 1
- 230000034994 death Effects 0.000 description 1
- 230000006735 deficit Effects 0.000 description 1
- 238000011161 development Methods 0.000 description 1
- 230000018109 developmental process Effects 0.000 description 1
- 238000009792 diffusion process Methods 0.000 description 1
- 238000010790 dilution Methods 0.000 description 1
- 239000012895 dilution Substances 0.000 description 1
- ORXJMBXYSGGCHG-UHFFFAOYSA-N dimethyl 2-methoxypropanedioate Chemical compound COC(=O)C(OC)C(=O)OC ORXJMBXYSGGCHG-UHFFFAOYSA-N 0.000 description 1
- 238000001125 extrusion Methods 0.000 description 1
- 210000000416 exudates and transudate Anatomy 0.000 description 1
- 239000000835 fiber Substances 0.000 description 1
- 229940012952 fibrinogen Drugs 0.000 description 1
- 229960002442 glucosamine Drugs 0.000 description 1
- 229960003180 glutathione Drugs 0.000 description 1
- 230000000025 haemostatic effect Effects 0.000 description 1
- 239000012456 homogeneous solution Substances 0.000 description 1
- 230000007062 hydrolysis Effects 0.000 description 1
- 238000006460 hydrolysis reaction Methods 0.000 description 1
- 239000007943 implant Substances 0.000 description 1
- 238000002513 implantation Methods 0.000 description 1
- 238000005470 impregnation Methods 0.000 description 1
- 208000015181 infectious disease Diseases 0.000 description 1
- 239000004615 ingredient Substances 0.000 description 1
- 210000005007 innate immune system Anatomy 0.000 description 1
- 230000002452 interceptive effect Effects 0.000 description 1
- 238000012423 maintenance Methods 0.000 description 1
- 239000012229 microporous material Substances 0.000 description 1
- 230000000116 mitigating effect Effects 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 230000004001 molecular interaction Effects 0.000 description 1
- 230000000921 morphogenic effect Effects 0.000 description 1
- 230000000420 mucociliary effect Effects 0.000 description 1
- 208000024628 myospherulosis Diseases 0.000 description 1
- 239000002105 nanoparticle Substances 0.000 description 1
- 230000017074 necrotic cell death Effects 0.000 description 1
- 210000001331 nose Anatomy 0.000 description 1
- 208000001797 obstructive sleep apnea Diseases 0.000 description 1
- 230000002688 persistence Effects 0.000 description 1
- 229940066842 petrolatum Drugs 0.000 description 1
- 235000019271 petrolatum Nutrition 0.000 description 1
- 239000000546 pharmaceutical excipient Substances 0.000 description 1
- 235000017807 phytochemicals Nutrition 0.000 description 1
- 239000000419 plant extract Substances 0.000 description 1
- 229930000223 plant secondary metabolite Natural products 0.000 description 1
- 229920000656 polylysine Polymers 0.000 description 1
- 238000006116 polymerization reaction Methods 0.000 description 1
- 150000008442 polyphenolic compounds Chemical class 0.000 description 1
- 235000013824 polyphenols Nutrition 0.000 description 1
- 229920002689 polyvinyl acetate Polymers 0.000 description 1
- 239000011118 polyvinyl acetate Substances 0.000 description 1
- 229920000036 polyvinylpyrrolidone Polymers 0.000 description 1
- 239000001267 polyvinylpyrrolidone Substances 0.000 description 1
- 235000013855 polyvinylpyrrolidone Nutrition 0.000 description 1
- 230000008092 positive effect Effects 0.000 description 1
- 239000002243 precursor Substances 0.000 description 1
- 230000002035 prolonged effect Effects 0.000 description 1
- 239000011541 reaction mixture Substances 0.000 description 1
- 238000011084 recovery Methods 0.000 description 1
- 230000001105 regulatory effect Effects 0.000 description 1
- 208000037803 restenosis Diseases 0.000 description 1
- 238000002435 rhinoplasty Methods 0.000 description 1
- 150000003839 salts Chemical class 0.000 description 1
- 238000001878 scanning electron micrograph Methods 0.000 description 1
- 230000037390 scarring Effects 0.000 description 1
- 238000007789 sealing Methods 0.000 description 1
- 238000001338 self-assembly Methods 0.000 description 1
- XMUHNMQFDVIWGU-UHFFFAOYSA-M sodium;2,3-bis(sulfanyl)propane-1-sulfonate;hydrate Chemical compound O.[Na+].[O-]S(=O)(=O)CC(S)CS XMUHNMQFDVIWGU-UHFFFAOYSA-M 0.000 description 1
- 125000006850 spacer group Chemical group 0.000 description 1
- 239000003381 stabilizer Substances 0.000 description 1
- 238000006467 substitution reaction Methods 0.000 description 1
- 230000002194 synthesizing effect Effects 0.000 description 1
- 229920002994 synthetic fiber Polymers 0.000 description 1
- 229920002258 tannic acid Polymers 0.000 description 1
- LRBQNJMCXXYXIU-NRMVVENXSA-N tannic acid Chemical compound OC1=C(O)C(O)=CC(C(=O)OC=2C(=C(O)C=C(C=2)C(=O)OC[C@@H]2[C@H]([C@H](OC(=O)C=3C=C(OC(=O)C=4C=C(O)C(O)=C(O)C=4)C(O)=C(O)C=3)[C@@H](OC(=O)C=3C=C(OC(=O)C=4C=C(O)C(O)=C(O)C=4)C(O)=C(O)C=3)[C@@H](OC(=O)C=3C=C(OC(=O)C=4C=C(O)C(O)=C(O)C=4)C(O)=C(O)C=3)O2)OC(=O)C=2C=C(OC(=O)C=3C=C(O)C(O)=C(O)C=3)C(O)=C(O)C=2)O)=C1 LRBQNJMCXXYXIU-NRMVVENXSA-N 0.000 description 1
- 229940033123 tannic acid Drugs 0.000 description 1
- 235000015523 tannic acid Nutrition 0.000 description 1
- 239000004753 textile Substances 0.000 description 1
- 230000000699 topical effect Effects 0.000 description 1
- QQJLHRRUATVHED-UHFFFAOYSA-N tramazoline Chemical compound N1CCN=C1NC1=CC=CC2=C1CCCC2 QQJLHRRUATVHED-UHFFFAOYSA-N 0.000 description 1
- 229960001262 tramazoline Drugs 0.000 description 1
- 230000001052 transient effect Effects 0.000 description 1
- 230000007704 transition Effects 0.000 description 1
- 230000008733 trauma Effects 0.000 description 1
- 210000001944 turbinate Anatomy 0.000 description 1
- 229910021642 ultra pure water Inorganic materials 0.000 description 1
- 239000012498 ultrapure water Substances 0.000 description 1
- 230000002792 vascular Effects 0.000 description 1
- 125000000391 vinyl group Chemical group [H]C([*])=C([H])[H] 0.000 description 1
- 229920002554 vinyl polymer Polymers 0.000 description 1
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
- A61L15/00—Chemical aspects of, or use of materials for, bandages, dressings or absorbent pads
- A61L15/16—Bandages, dressings or absorbent pads for physiological fluids such as urine or blood, e.g. sanitary towels, tampons
- A61L15/42—Use of materials characterised by their function or physical properties
- A61L15/425—Porous materials, e.g. foams or sponges
-
- 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
- A61L24/00—Surgical adhesives or cements; Adhesives for colostomy devices
- A61L24/04—Surgical adhesives or cements; Adhesives for colostomy devices containing macromolecular materials
- A61L24/043—Mixtures of macromolecular materials
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F13/00—Bandages or dressings; Absorbent pads
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F13/00—Bandages or dressings; Absorbent pads
- A61F13/00987—Apparatus or processes for manufacturing non-adhesive dressings or bandages
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F13/00—Bandages or dressings; Absorbent pads
- A61F13/01—Non-adhesive bandages or dressings
- A61F13/01008—Non-adhesive bandages or dressings characterised by the material
- A61F13/01012—Non-adhesive bandages or dressings characterised by the material being made of natural material, e.g. cellulose-, protein-, collagen-based
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F13/00—Bandages or dressings; Absorbent pads
- A61F13/01—Non-adhesive bandages or dressings
- A61F13/01034—Non-adhesive bandages or dressings characterised by a property
- A61F13/01042—Absorbency
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F13/00—Bandages or dressings; Absorbent pads
- A61F13/12—Bandages or dressings; Absorbent pads specially adapted for the head or neck
- A61F13/122—Bandages or dressings; Absorbent pads specially adapted for the head or neck specially adapted for the face
- A61F13/126—Bandages or dressings; Absorbent pads specially adapted for the head or neck specially adapted for the face specially adapted for the nose
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F13/00—Bandages or dressings; Absorbent pads
- A61F13/15—Absorbent pads, e.g. sanitary towels, swabs or tampons for external or internal application to the body; Supporting or fastening means therefor; Tampon applicators
- A61F13/20—Tampons, e.g. catamenial tampons; Accessories therefor
- A61F13/2002—Tampons, e.g. catamenial tampons; Accessories therefor characterised by the use
- A61F13/2005—Tampons, e.g. catamenial tampons; Accessories therefor characterised by the use specially adapted for the nose cavity
-
- 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
- A61L15/00—Chemical aspects of, or use of materials for, bandages, dressings or absorbent pads
- A61L15/16—Bandages, dressings or absorbent pads for physiological fluids such as urine or blood, e.g. sanitary towels, tampons
- A61L15/22—Bandages, dressings or absorbent pads for physiological fluids such as urine or blood, e.g. sanitary towels, tampons containing 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
- A61L15/00—Chemical aspects of, or use of materials for, bandages, dressings or absorbent pads
- A61L15/16—Bandages, dressings or absorbent pads for physiological fluids such as urine or blood, e.g. sanitary towels, tampons
- A61L15/22—Bandages, dressings or absorbent pads for physiological fluids such as urine or blood, e.g. sanitary towels, tampons containing macromolecular materials
- A61L15/225—Mixtures of macromolecular compounds
-
- 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
- A61L15/00—Chemical aspects of, or use of materials for, bandages, dressings or absorbent pads
- A61L15/16—Bandages, dressings or absorbent pads for physiological fluids such as urine or blood, e.g. sanitary towels, tampons
- A61L15/42—Use of materials characterised by their function or physical properties
- A61L15/44—Medicaments
-
- 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
- A61L15/00—Chemical aspects of, or use of materials for, bandages, dressings or absorbent pads
- A61L15/16—Bandages, dressings or absorbent pads for physiological fluids such as urine or blood, e.g. sanitary towels, tampons
- A61L15/42—Use of materials characterised by their function or physical properties
- A61L15/64—Use of materials characterised by their function or physical properties specially adapted to be resorbable inside the body
-
- 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
- A61L24/00—Surgical adhesives or cements; Adhesives for colostomy devices
- A61L24/001—Use of materials characterised by their function or physical properties
- A61L24/0015—Medicaments; Biocides
-
- 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
- A61L24/00—Surgical adhesives or cements; Adhesives for colostomy devices
- A61L24/001—Use of materials characterised by their function or physical properties
- A61L24/0036—Porous materials, e.g. foams or sponges
-
- 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
- A61L24/00—Surgical adhesives or cements; Adhesives for colostomy devices
- A61L24/001—Use of materials characterised by their function or physical properties
- A61L24/0042—Materials resorbable by the body
-
- 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
- A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
-
- 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
- A61L2400/04—Materials for stopping bleeding
Landscapes
- Health & Medical Sciences (AREA)
- General Health & Medical Sciences (AREA)
- Engineering & Computer Science (AREA)
- Veterinary Medicine (AREA)
- Public Health (AREA)
- Life Sciences & Earth Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- Chemical & Material Sciences (AREA)
- Epidemiology (AREA)
- Materials Engineering (AREA)
- Biomedical Technology (AREA)
- Vascular Medicine (AREA)
- Heart & Thoracic Surgery (AREA)
- Hematology (AREA)
- Surgery (AREA)
- Otolaryngology (AREA)
- Dispersion Chemistry (AREA)
- Pulmonology (AREA)
- Manufacturing & Machinery (AREA)
- Materials For Medical Uses (AREA)
Abstract
A ready-to-use, hydrophilic, self-dispersive, fragmentable and biodegradable porous sponge matrix with high flexibility and absorbent capacity, wherein said sponge is porous by having interconnected vesicular micro-voids for holding or encapsulating therapeutic agents/drugs/cells inside, and wherein said sponge is obtained by lyophilizing a blend of polymers. Preferably, at least one of the polymers is in powdered form. The polymers may be selected from gelatin, chitosan, alginate, polyvinyl alcohol, polyvinyl chloride, polyethylene glycol and/or synthetic or naturally derived molecules including mucilaginous polysaccharides. The mucilaginous polysaccharides may be obtained from plant sources, for example Irish moss, marshmallow roots, fenugreek seed, flax seeds or psyllium husk seed. The sponge matrix is preferably in the form of a plug, tampon or sheet. Also disclosed is a method of making the porous sponge matrix, the method comprising sequentially blending the polymers together, blending at least one of the polymers in powdered solid form and then lyophilizing the blend of polymers. The porous sponge matrix may be used for controlling bleeding, wound closure, prevent tissue adhesion and/or support tissue regeneration. In particular, for nasal packing following surgery and for treating epistaxis.
Description
(54) Title of the Invention: A ready-to-use, hydrophilic, self-dispersive, fragmentable and biodegradable porous sponge matrix and a method of manufacturing thereof
Abstract Title: A ready-to-use, hydrophilic, self-dispersive, fragmentable and biodegradable porous sponge matrix and a method of manufacturing thereof (57) A ready-to-use, hydrophilic, self-dispersive, fragmentable and biodegradable porous sponge matrix with high flexibility and absorbent capacity, wherein said sponge is porous by having interconnected vesicular micro-voids for holding or encapsulating therapeutic agents/drugs/cells inside, and wherein said sponge is obtained by lyophilizing a blend of polymers. Preferably, at least one of the polymers is in powdered form. The polymers may be selected from gelatin, chitosan, alginate, polyvinyl alcohol, polyvinyl chloride, polyethylene glycol and/or synthetic or naturally derived molecules including mucilaginous polysaccharides. The mucilaginous polysaccharides may be obtained from plant sources, for example Irish moss, marshmallow roots, fenugreek seed, flax seeds or psyllium husk seed. The sponge matrix is preferably in the form of a plug, tampon or sheet. Also disclosed is a method of making the porous sponge matrix, the method comprising sequentially blending the polymers together, blending at least one of the polymers in powdered solid form and then lyophilizing the blend of polymers. The porous sponge matrix may be used for controlling bleeding, wound closure, prevent tissue adhesion and/or support tissue regeneration. In particular, for nasal packing following surgery and for treating epistaxis.
At least one drawing originally filed was informal and the print reproduced here is taken from a later filed formal copy.
Application No. GB1608671.2
RTM
Date :9 November 2016
Intellectual
Property
Office
The following terms are registered trade marks and should be read as such wherever they occur in this document:
Merocel
Surgiflo
Quixil
Flo seal
Nasopore
Intellectual Property Office is an operating name of the Patent Office www.gov.uk/ipo
A readv-to-use, hydrophilic, self-dispersive, fraqmentable and biodegradable porous sponge matrix and a method of manufacturing thereof
Field of the invention:
The present invention relates to the field of Medical Biosciences. The present invention provides, generally, porous absorbent materials which are suitable for packing antrum or cavities of the human or animal body.
Particularly, the present invention provides a ready-to-use, self-dispersive, biodegradable and biocompatible device. More particularly, the invention relates to medical nonwoven porous textiles. Even more particularly, the invention relates to a device to be used as nasal packing in the form of a plug, sheet or tampon, for instance for controlling bleeding, endoscopic sinus surgery, in most common procedures of ear dressing, wound closure, prevent tissue adhesion and/or support tissue regeneration, wound healing process, epistaxis purposes.
The present invention also provides a porous scaffold intended for use as a therapeutic agent carrier. The present invention provides a sterile product to carry the therapeutic agent and/or bioactive molecules, biological or chemicals. The present invention provides an art with preference to upregulate and downregulate the process of self-dispersive nature of the porous matrix. The present invention also relates to a method of preparing such a device for biomedical field.
The terms sponge/matrix/scaffold/device have been used interchangeably throughout the specification and, unless the context dictates otherwise, they all refer to the same product, as discussed and covered in the scope of this specification.
Background of the invention:
Nasal packs are indispensable in ENT practice where the pack is applied to the nasal cavities, The most common purpose of nasal packing is to control bleeding following surgery to the septum or nasal reconstruction, to prevent adhesion or restenosis and to treat epistaxis, Further, the packing can be also used to provide support to the septum after surgery.
The range of materials used for this purpose is wide, including both removable and absorbable materials. In cases of septoplasty and rhinoplasty surgery, conventional non-biodegradable packings are frequently removed within 24-48 hours following surgery. In the case of epistaxis, packing is left in for extended periods of time to promote healing and to prevent the patient from touching and accidentally interfering with the recovery of the wound. The packing may be left in the nose for as long as 7-10 days. If the wound is high up in the nasal cavity, packings treated with petrolatum and/or antibiotics are sometimes used. In the art, biodurabie wound dressings are used for nasal packing. These biodurabie packs have to be removed after several days as described above.
Numerous materials have been proposed in the prior art for use as foams for absorbing or removing body fluids. Conventional packs consisting of gauze or cotton have several disadvantages: the fluid absorption capacity of the material is relatively low, the structure is relatively fragile and individual threads or fibers may break off, erroneous failure to remove the material from the body after internal surgery may lead to serious complications and the material is relatively expensive. Certain hydrophilic synthetic materials intended for biomedical applications have improved properties when compared to conventional materials when it comes to absorption capacities and physico-mechanical properties. Examples of such material are the cross-linked polyurethane -based hydrogels as disclosed in e.g. US 3,903,232, US 3,961,629, US 4,550,126 and EP-A-0 335 669. However, these materials are biodurabie and not biodegradable.
The ideal packing would be that which, besides controlling hemorrhage and acting as a barrier to adhesion formation, is easily adaptable and reasonably well tolerated by the patient. Numerous packing agents are available, including vaseline-soaked ribbon gauze; fingerstall packs, polyvinyl acetate sponge (Merocel); various balloon tamponade devices. Even if most of them are very effective as regards hemostasis, these agents sometimes cause considerable discomfort for patients, both in terms of pain and bleeding on removal (von Schoenberg M, et.al, Nasal packing after routine nasal surgery -which is not justified. J Laryngol Otol, 1993; 107:902-5; Samad I. et.al, The efficacy of nasal septal surgery. J Otolaryngol, 1992; 21:88-91 ;Pomerantz 3. et.al, Platelet gel for endoscopic sinus surgery. Ann Otoi Rhino! Laryngol, 2005; 114:699-704; Vaiman M. et.al, The use of fibrin glue as hemostatic in endonasal operations: a prospective, randomized study. Rhinology, 2002; 40:185-8).
Other complications are associated with removable nasal packing (Weber R. et al., Packing in endonasal surgery, Am J Otolaryngol, 2001; 22:306-20; Weber R. et.al, Packing and stents in endonasal surgery, Rhinology, 2000; 38:49-62), such as: septal perforation (due to pressure necrosis); pack dislodgement; aspiration; toxic shock syndrome; foreign body granuloma; myospherulosis; obstructive sleep apnea secondary to nasal obstruction and death.
One of the most important disadvantages of removable nasal packing could be considered its impact on nasal mucosa, and especially on the ciliated mucosal surface area. Animal studies investigating the mucosal trauma caused by removable nasal packing have shown a 50% to 70% loss of the ciliated mucosal surface area in the region of the pack (Shaw C.L. et ah, Effect of packing on nasal mucosa of sheep, J Laryngol Otoi, 2000; 114:506-9). Therefore, a transient impairment of the patient's innate immune system, the mucociliary clearance, may be associated with the use of removable nasal packing (Chandra R.K. et.al, The effect of FioSeal on mucosal healing after endoscopic sinus surgery: a comparison with thrombinsoaked gelatin foam. Am 3 Rhinol, 2003; 17:51-5). The impact on patients' qualify of life and also the possible complications of removable nasal packing have led to the ongoing development and application of absorbable biomaterials that do not require subsequent removal and still achieve positive effects on hemostasis, promote wound healing, and provide middle turbinate support.
This lack of biodegradability makes such materials less suitable for use in body cavities during surgery, since there is always a possibility that the foam is left accidentally in the body. Furthermore, removing non-biodegradable foams after application in a natural body orifice may be very uncomfortable fora patient and may open up the wound and/or lead to additional scarring of the tissue. In order to prevent these undesired effects, biodegradable sponges or absorbing foams comprising materials of a natural source such as gelatine, proteins, collagen, chitin, chitosan, cellulose or polysaccharides have been suggested,
A wide range of absorbable materials for use in nasal surgery have been developed , including absorbable porcine gelatin (Surgiflo, Ethicon Inc) and thrombin combination; carboxy-methyl-cellulose (CMC, AthroCare); chitosan gel (Department of Chemistry, University of Otago, Dunedin, New Zealand); Fibrin glue (Quixil, Omrix Co.); FloSeal (Baxter International Inc); hyaluronic acid (MeroGel, Medtronic);microporous polysaccharide hemispheres (MPH, Medafor Inc); Platelet gel (PPAI Medical); Surgiflo hemostatic matrix combined with thrombin; topical antifibrinolytics such as epsilon-aminocaproic acid (Amicar, Lederle Parenterals Inc) and tranexamic acid (Cyklokapron, Pfizer). NasoPore, Polyganics B.V., Groningen, the Netherlands.
However, all of these materials tend to lack the required mechanical strength and have undesirable effects on hemostatic, adhesion and healing features. For example, the haemostatic sponge of denaturated gelatin of WO 90/13320 does not have sufficient mechanical strength to stop a severe nose-bleed, because the compression strength of the material in the wet condition is too low and the sponge liquefies too fast after being applied in the nasal cavity.
US 3,902,497 and US 3,875,937 disclose surgical dressings of bio-absorbable polymers of poly glycolic acid (PGA), Such materials are, although useful in other applications, not useful in applications where sufficient counter pressure from the foam is required, such as in nose-bleeding, because the material is quite hard and brittle and is not resilient. Moreover, the PGA material is not sufficiently hydrophilic to absorb the blood during severe bleeding, Some hydrophilic synthetic polymers based on poiyurethene (WO 2004062704 Al) are used for nasal plug (e.g nasopore, polyganic) but applicability covering ail features is not clear, No published literature has investigated the hemostatic or wound-healing properties of polyethylene glycol (NasoPore, Polyganics B.V., Groningen, the Netherlands) after ESS. Further, the mechanical properties are compromised to make it highly fragmentable.
Because of lack of standardization in this matter, still the choice is in the surgeon's hand, according to his abilities, beliefs, or technical possibilities. Now there is no generally recognized standard for which types of materials should be used, how long packs should remain placed, or when placement is indicated. This invention addresses current indications and effectiveness of nasal packs and stents and overcoming or at least mitigating the risks associated therewith. However, the need for absorbable sponges or absorbent foams that can be left in the wound is now generally well recognized.
Nasal packs should generally have smooth surfaces to minimize mucosal damage, improve wound healing and increase patient comfort. Functional endoscopic endonasal sinus surgery allows the use of modern nasal packs, since pressure is no longer required. So called hemostatic/resorbable materials are a first step in this direction. However, they may lead to adhesions and foreign body reactions in mucosal membranes. Simple occlusion is an effective method for creating a moist milieu for improved wound healing and avoiding dryness. Stenting of the frontal sinus is recommended if surgery fails to produce a wide, physiologically shaped drainage path that is sufficiently covered by intact tissue.
Requirements of such foams include: a high and rapid absorption capacity, particularly for blood; strength, to be readily handled in surgical procedures; conformability, so as to fit into any topography; and the ability to maintain mechanical properties of bodily tissues, for a specific period of time during or after surgery or after application of the matrix, soft so as to avoid injury to such sensitive tissues. In some instances, the softness of the foam may be increased by wetting of the foam. Therefore, the absorbing foam should also have enough mechanical strength and elasticity in the wet condition and can also be cleared off via natural process to reduce doctors' dependency,
Reference is made to United States Patent Number 9,039,657, entitled Implantable devices and methods for delivering drugs and other substances to treat sinusitis and other disorders dated 26.05.2015. That invention relates to implantable devices and methods for delivering drugs and other substances to locations within the body of a human or animal subject, to treat or diagnose sinusitis and a variety of other disorders. The invention includes implantable substance delivery devices that comprise reservoirs and barriers that control the rate at which substances pass out of the reservoirs. The delivery devices may be advanced into the body using guidewires, catheters, ports, introducers and other access apparatus. In some embodiments the delivery devices may be loaded with one or more desired substance before their introduction into the body. In other embodiments the delivery devices are loaded and/or reloaded with a desired substance after the delivery device has been introduced into the body. The present invention relates generally to medical devices and methods and more particularly to substance delivering implants and methods for treating a broad range of disorders including but not limited to sinusitis and other ear, nose and throat disorders.
Further reference is made to United States Patent Application Publication 2004/0116958A1, (now US Patent Number 8,740,929) entitled Spacing device for releasing active substances in the paranasal sinus by Gopferich et al, dated 03.06.2014. That invention relates to a tubular sheath or spacer” formed of biodegradable or non-biodegradable polymer that, prior to insertion in the patient's body, is loaded with a controlled amount of an active substance, such as a corticosteroid or anti-proliferative agent. Surgery is performed to create a fenestration in a frontal sinus and the sheath is inserted into such fenestration. Thereafter, the sheath which has been preloaded with the active substance is inserted into the surgically created fenestration where it a) deters closure of the surgically created fenestration, b) serves as a conduit to facilitate drainage from the sinus and
d) delivers the active substance. The sheath of the invention of US patent number 8,740,929 remains substantially in a single configuration (i.e., it does not transition between a collapsed configuration and an expanded configuration) although it may be coated with a material that swells when in contact with mucous or body fluid. In some embodiments, the sheath is formed of multiple layers of polymeric material, one or more of which is/are loaded with the active substance and one or more of which is/are free of the active substance. In other embodiments, the sheath has a hollow body which forms a reservoir system wherein the active substance is contained and a membrane which controls the release of the active substance from the reservoir. In some embodiments, the sheath may be anchored by causing the end of the sheath that extends into the sinus to swell or otherwise enlarge.
Another reference is made to US Patent Number 3,948,254 entitled Novel drug delivery device by Zaffaroni dated 06.04.1976. That invention relates to implantable drug delivery devices comprising a drug reservoir surrounded by a micro-porous wall. The reservoir may be formed of a solid drug carrier that is permeable to passage of the drug. The rate of passage of the drug through the wall may be slower than the rate at which the drug passes through the solid drug carrier that forms the reservoir. The patent describes a number of applications for the implantable drug delivery devices including placement in a nasal passage. Specifically, the invention claimed is a nasal delivery device for dispensing a drug within a nasal passage at a controlled rate wherein the nasal device is comprised of (a) a wall defining the device dimensioned for insertion and placement within a nasal passage, with the wall formed of a nasal acceptable micro-porous material, (b) a reservoir surrounded by the wall and comprised of a solid carrier permeable to drug and containing drug in an amount sufficient for the device to meter it at a continuous and controlled rate for a prolonged period of time from the device, (c) a liquid medium permeable to the passage of drug by diffusion charged in the micro-pores, and (d) wherein the device releases drug when in a nasal environment by passage of drug from the carrier and through the liquid to the exterior of the device to produce a useful result.
There are also several examples in the patent literature where various sustained release mechanisms have generally been proposed using systems with preincorporated drugs into matrices or polymers. These include U.S. Pat. No. 3,948,254 (Zafferoni), US 2003/0185872A2 (now U.S. Pat. No. 7,074,426) (Kochinke), WO 92/15286 (Shikani), and U.S. Pat. No. 5,512,055 (Domb, et al.). In general, these references discuss various materials and structures that may be used to construct sustained drug delivery vehicles and provide a good overview of the state of sustained drug delivery art. These are helpful in laying out certain materials and schemes for creating sustained release systems for drugs.
Further reference is made to United States Patent number 8,784,893, entitled Polymer formulations for delivery of bioactive agents dated 22.07.2014. That invention provides compositions comprising a bioresorbable polymer matrix and a bio active agent, wherein the bioactive agent is dispersed within polymer matrix as a solid. Also provided therein are methods for preparing a bioactive agent formulation, wherein the agent is present in a solid form and, wherein the agent is occluded into a polymeric matrix by polymerization of polymer matrix precursors or by selfassembly of the polymer. The invention provides a hydrogel composition formed by combining an aqueous buffer, a thiol-functionalized hyaluronic acid and a crosslinking accelerant in the presence of a gel-persistence-enhancing compound selected from the group consisting of N-acetyl cysteine, glutathione, 2,3-dimercapto-lpropanesulfonic acid, 2,3-dimercapto-l-propanesulfonic acid sodium salt monohydrate, cysteine, dihydrolipoic acid, and pharmaceutically acceptable salts thereof, wherein the hydrogel comprises disulfide crosslinks. This composition also comprises an excipient and is having a pH of between 5 and 8 when in aqueous solution. The composition further comprises a bioactive agent as solid particles. The bioactive agent is a steroid, selected from the group consisting of triamcinolone, triamcinolone diacetate, triamcinolone acetonide, triamcinolone hexacetonide, methylprednisolone and dexamethasone. The solid particles have a particle size between about 0.1 micron and 2 mm. The bioactive agent is not covalently bound to the thiol-functionalized hyaluronic acid. The composition forms in about 1 second to 30 minutes after combining the thiol-functionalized hyaluronic acid, the gel8 persistence enhancing compound, and the cross-linking accelerant in aqueous buffer. There is also provided a kit for providing a hydrogel composition, the kit comprising container with a thiol-functionalized hyaluronic acid, a gel-persistence enhancing compound, and a cross-linking accelerant and an aqueous buffer. The kit may also comprise another container with a steroid selected from the group consisting of triamcinolone, triamcinolone diacetate, triamcinolone hexacetonide, triamcinolone acetonide, methylprednisolone and dexamethasone.
Another reference is made to United States Patent 8,535,709 entitled Agents for controlling biological fluids and methods of use thereof by Kennedy, et al. This patent discloses therapeutic formulations adapted for positive-pressure application for controlling biological fluid at a desired site in a subject, absorbent articles comprising therapeutic formulations, and anti-infective devices coated with therapeutic formulations, said formulations comprising about 25% to about 99% by weight liquidcrystal forming compound and 0% to about 75% by weight solvent. In addition, methods of using said formulations including methods for controlling biological fluid at a desired site in a subject, methods for controlling blood loss, and methods for facilitating effective closure of a vascular wound or incision site at a desired site in a subject are disclosed, the methods comprising administering particular formulations comprising liquid-crystal forming compounds and solvents that are described herein.
Reference is made to United States Patent 8,475,824 entitled Resorbable matrix having elongated particles by McKay dated 02.07.2013. The invention relates to Compression resistant matrices and methods having elongated particles embedded therein. The compression resistant matrices provide improved stability and mechanical strength and resists shifting, extrusion and rotation after implantation. In some embodiments, the matrices provided reduce or prevent surface compression of the implantable matrix which will cause unwanted increased amounts of growth factor (e.g., bone morphogenic protein) to leak from the matrix.
It is an objective of the present invention to overcome or at least mitigate the drawbacks and problems associated with the sponges and absorbent foams of the prior art and to provide a biocompatibie porous material that is controlled and tunable,, self-dispersive, biodegradable, that is able to absorb fluids and that has improved and tunable mechanical properties, such as a high elasticity, even when wet.
The present invention therefore provides a self-dispersive, fragmentable and biodegradable porous sponge matrix, made up of a lyophilized blend of different polymers, synthetic and natural, with high flexibility and absorbent capacity, to be used for various biomedical applications. The said matrix is prepared using sequential mixing of pre-made solution of polymers, one of them as powdered solid form. The sponge mentioned is soft, highly flexible, porous and hydrophilic in nature. The same is tunably self-dispersive, fragmentable and bioabsorbable at body temperature and pH.
Objects of the invention:
A main objective of the invention is to provide a porous sponge matrix and a method of manufacturing thereof. Another objective of the invention is to provide a readyto-use, hydrophilic, self-dispersive, fragmentable and biodegradable sponge. A further objective of the invention is to provide a sponge device for porous absorbent materials which are suitable for packing antrum or cavities of the human or animal body. Another objective of the invention is to provide a method of preparation of such sponge/device.
A further objective of the invention is to provide a porous scaffold meant as therapeutic carrier, more specific as a Hemostasis and packing product.
A further objective of the invention is to provide a device to be used as nasal packing in the form of a plug, sheet or tampon, for instance for controlling bleeding, endoscopic sinus surgery, in most common procedures of ear dressing, wound closure, prevent tissue adhesion and/or support tissue regeneration, wound healing process, epistaxis purposes.
Another objective of the invention is to provide a sterile wound dressing product to carry the therapeutic and/or bioactive molecules, biological or chemicals.
Another objective of the invention is to provide an art with preference to upregulate and downregulate the process of self-dispersiveness and bioaborbability of the porous matrix.
Summary of the invention:
The present invention provides a ready-to-use, hydrophilic, self-dispersive, fragmentable and bioabsorbable porous composite biocompatible device and a method of preparation thereof, comprising a scaffold composed of polymeric composites and polyelectrolyte complex (PEC) comprising of composite of polymers.
Preferred polymers comprise functional groups: -C(O)-O-; NH2/3+; -OH;
-CH2OCH2C(O)O' groups as functional or -CH-O- (e.g. C2H4O; C6H10O5; CeHsOe); -CHN-O- (e.g. C8H13NO5); O-C-C- (e.g. O-CH2-CH2); -C(O)N- groups in the backbone of the polymers.
The porous matrix is suitable for packing antrum or other cavities of the body and as carrier of plurality of therapeutics to be used as nasal packing in the form of a plug, sheet or tampon, for instance for controlling bleeding, endoscopic sinus surgery, in most common procedures of ear dressing, wound closure, prevent tissue adhesion and/or support tissue regeneration, wound healing process, epistaxis purposes.
Brief description of the drawings:
Figure 1 represents an SEM image of a scaffold in accordance with an embodiment of the present invention: A) in sectional view; B) in sectional view at higher magnification; and C) on a surface view.
Statement of the invention:
Accordingly, the present invention provides a ready-to-use, hydrophilic, selfdispersive, fragmentable and biodegradable porous sponge matrix with high flexibility and absorbent capacity and a method of manufacturing thereof, wherein said sponge is porous having interconnected vesicular micro-voids for holding or encapsulating therapeutic agents/drugs/cells inside, with large surface area and micro-areas for reactions to occur, and wherein said sponge is obtained using a lyophilized blend of polymers, preferably sequential mixing of two or more polymers followed by homogenization with specific aspect ratio of shaft, impeller and vessel of the system for mixing, for a definite period of time, such that the resulting matrix sponge performs at significant level for using in various biomedical applications.
Detailed description of the invention:
It should be noted that the particular description and embodiments set forth in the specification below are merely exemplary of the wide variety and arrangement of instructions which can be employed with the present invention. The present invention may be embodied in other specific forms without departing from the spirit or essential characteristics thereof. All the features disclosed in this specification may be replaced by similar other or alternative features performing similar or same or equivalent purposes. Thus, unless expressly stated otherwise, they all are within the scope of present invention. Various modifications or substitutions are also possible without departing from the scope or spirit of the present invention. Therefore, it is to be understood that this specification has been described by way of the most preferred embodiments and for the purposes of illustration and not limitation.
The present invention provides generally porous absorbent materials which are suitable for packing antrum or cavities of the human or animal body and method of preparation thereof. The device of present invention is a porous scaffold to be used as nasal packing in the form of a plug, sheet or tampon, for instance for controlling bleeding, for example following endoscopic sinus surgery, in most common procedures of ear dressing, wound closure, prevent tissue adhesion and/or support tissue regeneration, wound healing process, epistaxis purposes.
The present invention basically relates to the efficient deployment of a biodegradable, biocompatible medical aid through a highly porous scaffold that can be deployed at the point of proposed use. The scaffold under the present invention allows the medical aid suitable for packing antrum or cavities of the human or animal body with an ability to stop bleeding and also reduce dependency on medical staff, preserve tissue after injury and facilitate surgical speed.
The present invention is a hydrophilic self-dispersive, fragmentable and bioabsorbable porous composite foam/sponge, suitable for packing antrum or other cavities of the body. The sponge preferably comprises polymers having functional groups -C(O)-O-; -NH2/3+; -OH; -CH2OCH2C(O)O' groups as functional or -CH-O(e.g. C2H4O; CeHioOs; CeHsOe); -CH-N-O- (e.g. CsHisNOs); O-C-C- (e.g. O-CH2-CH2); -C(O)N- groups in the backbone of the polymers.
The said spongy patch under the present invention consists of synthetic and natural polymers to name a few polyvinylalcohol, alginic acid salt, modified cellulose, gelatin, chitosan and other having the groups mentioned before. The said sponge can be impregnated with therapeutics such as growth factors, anti-oxidants, clotting agents for instance, including but not limited to thrombin, calcium chloride (CaCb), polyphenol, and tranexamic acid. The same can also be impregnated with biological materials such as cells e.g. primary cells and stem cells. These constituents are held in the vesicular voids of the matrix, on the internal surface of the sponge which are able to act rapidly when blood flows into the dressing. Once the scaffold under the present invention is in contact with blood, the dressing enables sealing and stabilization of wound surfaces.
The said sponge/foam is a porous scaffold characterized in that the structure is reticulate and has an inner surface considerably larger than its outer surface, that it contains hollow spaces, pores within the reticulate structure and that it can absorb many times its own weight in liquids in a short period of time. On the other hand, it may be used for wound closure, e.g. to prevent infection and/or tissue adhesion, or for tissue regeneration purpose (cell in-growth into pores).
Such sponge/foams are the subject of the present invention and are also referred to as absorbent foams/ sponges. The said sponge/foam are biodegradable as the ability of a polymer to be acted upon biochemically in general by living cells or organisms or part of these systems, including hydrolysis, and to degrade and disintegrate into chemical or biochemical products. Further, the invention is bioresorbable, i.e. it comprises an ability of being completely metabolized by the human or animal body making this packing suitable for internal body application.
The novel scaffold under the present invention provides a highly soft, smooth and exudates absorbency property to the scaffold. The presence of hydrophilic group in the matrix of the polymer from which the foam of the invention is comprised further provides said foam with required characteristics such as the capacity to absorb aqueous liquids and being readily biodegradable, bioresorbable and self-dispersive to get naturally clean off from the cavity/antrum such as nasal sinuses.
The polymer ofthe present invention may be produced in bulk, or, more preferably, it may be produced in a solvent. A very suitable such solvent is water or acidified water. The advantage of producing a polymer ofthe present invention in said solvent is that a very advantageous starting material is thus provided for the preparation of sponge of the invention, This starting material is already present in the form of a solution, and no time consuming dissolution of polymers in solvents needs to be accomplished. Most preferred is the use of the solvent acidified water. The one of the polymers used must be added as solid powdered form.
The present invention aims to overcome the problems in the existing prior arts and provides the novel and unique features in the scaffold by providing on-demand services for nasal packing sponge with high porosity and regulated pores on the same platform of a matrix. The technologies involved are the timed patterned physico14 chemical treatment of the two or more polymers used stated above using a very simplified process to obtain tunable self-dispersive interaction and orientation between the molecules out of all at least one of the preferred polymers, which are used in form of powder solid. The used technology provides the proper interaction and orientation between the functional and backbone groups of the polymers used, resulted into a typical polyelectrolyte complex (PEC) and polymer sandwich.
The present invention provides the requirements of such sponge with a high and rapid absorption capacity, particularly for blood, strength to be readily handled in surgical procedures, conformable so as to fit into any topography, maintenance of tissues' mechanical properties, for a specific period of time during or after surgery or after application of the matrix, soft so as to avoid injury to sensitive tissues. In some instances, the softness of the foam may be increased by wetting of the foam. Therefore, the absorbing foam should also have enough mechanical strength and elasticity in the wet condition and can also be cleared off via natural process to reduce doctors' dependency.
Further, the present invention is to overcome the drawbacks and the problems associated with the sponges and absorbent foams of the prior art and to provide a biocompatible porous material that is controlled and tunable self-dispersive, biodegradable, that is able to absorb fluids and that has improved and tunable mechanical properties, such as a high elasticity, even when wet.
A ready-to-use, hydrophilic, self-dispersive, fragmentable and biodegradable porous sponge with high flexibility and absorbent capacity, made up of lyophilized blend of different polymers, to be used for various biomedical application. The said matrix is prepared using sequential mixing of pre-made solution of polymers and one of them as powdered solid form. The sponge mentioned is soft, highly flexible, porous and hydrophilic in nature. The resulting product is tunable self-dispersive, fragmentable and bioresorbable at body temperature and pH. Further, the interconnected vesicular micro-voids hold the drug/cells inside and as a result the encapsulated therapeutics of the matrix perform at significant level. Further the highly porous structure of the present invention results into interconnected small voids, provide a large surface area and micro-areas for reactions to occur and thus exert a pseudo-catalytic effect on blood clotting. The PEC containing micro-mesh and body's fibrinogen converted into fibrin forms an efficacious plug and prevents the loss of blood and stops the loss of clotting factor. The novel device of the present invention makes the product light weighted, to be more physical and also altering the blood clotting mechanism. The scaffold of the present invention can be removed easily usually without causing additional/secondary hemorrhage from the application site.
The novel porous scaffold ofthe present invention is also capable of being used as a carrier for other therapeutics/ bioactive molecules/ cell (primary or stem cell) towards tissue engineering and other biomaterial applications. Moreover, the scaffold of the present invention is also capable of being used as a cover for the compromised tissues either as acellular or cellular product.
The utilization of more than one type of polymer & their properties for multitherapeutics loaded preparation and impregnation of the same with PEC scaffold, a system for more than one types of the pharmaceuticals (like clotting factors, cofactors, clot stabilizers, antibiotics, analgesics, anti-allergic, antioxidants, growth factors, etc.) to get delivered in phase-wise and controlled manner for extended period of time.
The novel aspect ofthe present invention is the sequential timed patterned physicochemical treatment of the synthetic and natural polymers by using a very simplified process to obtain a highly flexible stabilized tunable self-dispersive porous scaffold, which can be further tuned using any cross-linker, if required. Further, the invention comprises the preparation of said PEC containing sponge, which is achieved using a specific aspect ratio of shaft, impeller and vessel of the system for mixing. One of the ingredient polymers is added in powder form and rest are in solution from using the water or acidified water as solvent.
The present invention comprises polyelectrolyte complex such as of gelatin and alginate in porous sponge. The present invention provides, a method for preparing a biodegradable absorbent sponge/foam suitable for as hemostatic sponge, wound dressing material, packing antrum or other cavities of the human or animal body, including dental packs, or as a drug delivery vehicle, comprises preparing a polymer according to the invention in acidified water or water, diluting the polymer solution during interaction of the functional and backbone group of the polymers with the solvent and the polymer solution, freezing the reaction mixture, and subliming the solvent, under vacuum at low temperature.
The invention also provides a process for preparing said sponge scaffold, which is provided below in detail:
In a preferred embodiment, said polymers are preferably selected from but not limited to gelatin, chitosan, collagen, alginate, polyethylene glycol, polyvinyl Pyrrolidone, polyvinyl alcohol, polyurethane, keratin, Carboxy-methyl cellulose, gelatin hydrolysate, chitosan hydrolysate, partially denatured collagen and/or synthetic or naturally derived molecules such as phytochemicals.
In another embodiment, said therapeutic agents and pharmaceuticals are selected from but not limited to Tannic acid, Catechin family, tranexamic acid, calcium chloride, thrombin and/or glucosamine, Polylysine.
In a preferred embodiment, said sponge/scaffold is produced by the steps:
a) preparing a homogeneous solution of the individual polymers with different ratio in water or in water and acetic acid and subjecting for hot air treatment to obtain polymer solution at 50-90 degree C;
b) mixing of polymer solution obtained in step (a) at controlled parameters (18°25°C and 55±5% R.H) and sequential manner to obtain polymer composite solution (illustrated in Example 1);
c) mixing, as solid powder form, one of polymers to obtain final polymer composite solution obtained in step (b) containing PEC followed by freezing and drying at low temperature under vacuum, respectively at -80°C and -5°C for 4000 min;
d) Cutting the above obtained porous scaffold/sponge/foam obtained at the end of step (c) as per requirement at 18°-25°C and 55±5% R.H.
e) Optionally, the obtained scaffolds in steps (c) & (d) are subjected for stabilization either by ammonia vapor or ammonia solution or alkali solution following aldehyde vapor or EDC as per requirement for 10-12 hrs at 18°-25°C and 55±5% R.H.
f) Subsequent treatment of the obtained scaffold in step (d) & (e) is under vacuum at 25-40 degree C overnight (10-12 hrs); and
g) Followed by gamma irradiation of the scaffold obtained in steps (d) &(f) to obtain the final ready to use product.
h) Optionally, the scaffold may be loaded with the required pharmaceutical/ therapeutic solution containing different ratio of drugs as per the requirement into the obtained scaffold in step (f) followed by step (g) to obtain the final ready to use product at 18°-25°C and 55±5% R.H.
i) Optionally, the scaffold may be loaded with the required cells (primary/stem cells) as per the requirement into the obtained scaffold in step (g) under aseptic condition to obtain the final ready to use product at 18°-25°C and 55±5% R.H.
In another embodiment, said method involves physico-chemical treatment of said polymers using a very simplified process in order to obtain a stable molecular interaction and orientation between the molecules of the said polymers, causing an interaction and orientation between the functional groups of the polymers used, resulting in a typical polyelectrolyte complex (PEC), so as to obtain a highly porous matrix.
Accordingly, the present invention provides a ready-to-use, hydrophilic, selfdispersive, fragmentable and biodegradable porous sponge matrix and a method of manufacturing thereof, said sponge is porous having interconnected vesicular microvoids for holding or encapsulating the therapeutics/drugs/cells inside, with large surface area and micro-areas for reactions to occur, said sponge is obtained using a lyophilized blend and sequential mixing of two or more biopolymers with high flexibility and absorbent capacity, followed by homogenization with specific aspect ratio of shaft, impeller and vessel of the system for mixing, for a definite period of time, such that the resulting matrix sponge performs at significant level for using in various biomedical applications.
In an embodiment, said sponge is prepared using sequential mixing of pre-made solution of polymers with one of them as powdered solid form to get differential solubility of polymer complex and tunable self-dispersiveness, fragmentability and bioabsorbability and thus obtained homogenized composite mixture is cast immediately within a time limit.
In another embodiment, said sponge is soft, highly flexible, porous, hydrophilic, selfdispersive, fragmentable in nature and is bioabsorbable at body temperature and pH.
In another embodiment, said polymers used for synthesizing said sponge are preferably selected from but not limited to gelatin, chitosan, collagen, alginate, polyvinyl alcohol, poly(vinyl pyyrolidone), polyurethane, polyethylene glycol, polypropylene glycol keratin, hyaluronic acid, carboxymethyl cellulose, gelatin hydrolysate, chitosan hydrolysate, partially denatured collagen and/or synthetic or naturally derived molecules such as mucilaginous polysaccharides.
In yet another embodiment, said sponge is obtained by mixing different polymer solutions preferably polyvinyl chloride (5%-15%), Gelatin (2%-7%), Sodium Alginate (0.5%-2%) polyethylene glycol-200 (lml-5ml), and chitosan (0.5%-l%).
In another embodiment, the sequential timed patterned physico-chemical treatment of polymers is preferably dissolution of polymers to form the solution with concentration mentioned above at a temperature between 40-70°C, whilst preferably:
• Stirring of the polymer blend temp 18-25° C, 55±5% R.H for 20-30min using a stirrer with aspect ratio of the diameter of container and impeller ranging between 1.17 to 1.57 for 20 mins at the 1000-3600 rpm.
• Adding of acid, preferably glacial acetic acid (0.5-2.5%), at rate of lml/min and at temp 18-25° C, 55±5% R.H for 5-10min.
• adding of solid powder preferably of chitosan, 0.5% - 1.2% final concentration at the rate of lmg/ml at temp 18-25° C, 55±5% R.H for 30-40min.
In another embodiment, said mucilaginous polysaccharides are obtained from various plants sources like Irish moss, Marshmallow roots, Fenugreek seed, Flax seeds, Psyllium husk seed and any other equivalent.
In another embodiment, said mucilaginous plant extract mentioned is obtained using a sequential method of dilution, filtration and by drying the plant source and then dissolving in ultrapure water to prepare a solution of concentration 0.2%-l% followed by thermal treatment; diluting the solution thus obtained 2-3 times and homogenizing to form a homogenized solution for 23-30 min at 18-25° C, 55±5% R.H; filtering the homogenized solution and subjecting to 55°C under hot air for 1215 hr; using the dried extract ranging from 0.5% to 2% to obtain the desired sponge.
In another embodiment, said sponge is prepared in the same manner using the mucilaginous polysaccharide extract solution of concentration ranging from 0.4% to 1.5%.
In yet another embodiment, said sponge is stabilized and tuned using different chemicals and radiation or a combination of both, wherein said chemicals are preferably selected from but not limited to glutaraldehyde, formaldehyde, EDC, ammonia, and using solution or vapor to form a stable cross linked matrix following treatment with ammonia vapor and preferably followed by Gamma irradiation.
In another embodiment, said sponge can degrade thermally and can be easily removed from the site of application in the body cavity.
In another embodiment, said sponge comprises interconnected small voids, providing a large surface area and micro-areas which is hydrophilic in nature and retains water, resulting in formation of soft flexible dressing which provides support for the healing tissue in nasal cavity and external auditory meatus.
In another embodiment, said sponge is used for various applications like dressing for nasal interventions, ear and other body cavities, absorbent foam dressing for exudating wounds, diabetic foot ulcers, venous ulcers, as a drug and cell carrier and cell growth matrix, as carrier for various therapeutic and antimicrobial agents, nanoparticles, etc., as a cover for the compromised tissues, as a dressing for body cavity where it is difficult to cover the wound using traditional dressing methods.
In an embodiment, said sponge is preferably prepared in the form of a plug, tampon or sheet.
Advantages of the invention:
» Product has a high and rapid absorption capacity for fluids, particularly for blood ® Good strength to be readily handled in surgical procedures ® Conformable so as to fit into any topography « Good mechanical strength and elasticity in the wet condition ® Easy to clear-off via natural process to reduce doctors' dependency • Light weight in nature • Easy to remove without causing additional/secondary hemorrhage from the application site
The following example is for the purposes of illustration only and therefore should not be construed to limit the scope of the present invention:
Example 1:
Mix 30 ml of 7.5 % PVA solution using a mixer having an aspect ratio of the diameter of container and impeller of 1.37 at 3300 RPM, 22 degree C and add 15 ml of 10% Gelatin solution to it to get mixture B. Add 15 ml of 1% Alginate solution to mixture B to get mixture C at 2800 RPM, 22 degree C. Add 3 ml of PEG-200 to mixture C to get mixture D at 3000 RPM, 22 degree C. Following this add 30 ml of mucilage (1%) to the solution mixture D, stir using homogenizer for 20 min at 2300 RPM, 22 degree C and then add 0.75 ml of Acetic acid and homogenize for 1 min to get mixture E. Add 0.75 gm of chitosan to mixture E and homogenize for 30 min at 1800 RPM, 22 degree C. Cast the samples in Teflon tray followed by drying at low temperature under vacuum. Cut the sample into the desirable size and shape followed by stabilization and gamma irradiation.
Claims (19)
1. A ready-to-use, hydrophilic, self-dispersive, fragmentable and biodegradable porous sponge matrix with high flexibility and absorbent capacity, wherein said sponge is porous by having interconnected vesicular micro-voids for holding or encapsulating therapeutic agents/drugs/cells inside, and wherein said sponge is obtained by lyophilizing a blend of polymers.
2. A sponge matrix as claimed in claim 1, wherein said sponge is prepared using sequential mixing of polymers, with at least one of the polymers in powdered solid form.
3. A sponge matrix as claimed in claim 1 or 2, wherein said polymers are selected from gelatin, chitosan, collagen, alginate, polyvinyl alcohol, poly(vinyl pyrrolidone), polyurethane, polyethylene glycol, polypropylene glycol keratin, hyaluronic acid, carboxymethyl cellulose, gelatin hydrolysate, chitosan hydrolysate, partially denatured collagen and/or synthetic or naturally derived molecules including mucilaginous polysaccharides.
4. A sponge matrix as claimed in claim 3, wherein said mucilaginous polysaccharides are obtained from plant sources.
5. A sponge matrix as claimed in claim 4, wherein said plant sources comprise one or more of Irish moss, Marshmallow roots, Fenugreek seed, Flax seeds, Psyllium husk seed.
6. A sponge matrix as claimed in any preceding claim, wherein said sponge is prepared in the form of a plug, tampon or sheet.
7. A soft flexible dressing comprising a sponge matrix as claimed in any preceding claim, wherein said sponge comprises interconnected voids, is hydrophilic in nature, retains water, and provides support for the healing tissues in body cavities and external auditory meatus.
8. A method of making a sponge matrix as claimed in claim 1, comprising the steps of:
a. sequential blending polymers together;
b. blending at least one of the polymers in powdered solid form; and
c. lyophilizing the blend of polymers.
9. A method as claimed in claim 8, wherein said polymers are selected from solutions comprising polyvinyl chloride (5%-15%), gelatin (2%-7%), sodium alginate (0.5%-2%), polyethylene glycol-200 (lml-5ml), and chitosan (0.5%-l%).
10. A method as claimed in claim 8 or 9, comprising of dissolution of the polymers to form a solution at a temperature 40-70°C with following steps:
a. stirring of the polymer blend at a temperature 18-25° C, 55±5% R.H for 20-30min using a stirrer with aspect ratio of the diameter of container and impeller ranging between 1.17 to 1.57 for 15-30, preferably 20 mins, at the 1000-3600 rpm.
b. adding an acid, preferably glacial acetic acid (0.5-2.5%), at rate of lml/min and at temp 18-25° C, 55±5% R.H for 5-10min.
c. adding of solid powder polymer, preferably chitosan, to a 0.5%-1.2% final concentration, at a rate of lmg/min at temp 18-25° C, 55±5% R.H for 30-40min.
11. A method as claimed in claim 8, 9 or 10 of making a sponge matrix as claimed in claim 3 or 4, comprising sequential dilution, filtration and drying of the plant source and then dissolving in water to prepare a solution of concentration 0.2%1%.
12.A method as claimed in claim 11, wherein said dissolution in water is followed by thermal treatment.
13. A method as claimed in claim 11 or 12, further comprising diluting the solution thus obtained 2-3 times and homogenizing for 23-30 min at 18-25° C, 55±5% R.H to form a homogenized solution; filtering the homogenized solution and subjecting to 55°C under hot air for 12-15 hr; and using the dried extract ranging from 0.5% to 2% to obtain the desired sponge.
14. A method as claimed in claim 13, wherein said plant source comprises mucilaginous polysaccharide extract solution of concentration ranging from 0.4% to 1.5%.
15. A method as claimed in any of claims 8 to 14, comprising stabilizing and tuning the sponge and using chemicals and radiation or a combination of both.
16. A method as claimed in claim 13, wherein said chemicals are selected from glutaraldehyde, formaldehyde, EDC, ammonia in liquid or vapour to form a stable cross-linked matrix.
17. A method as claimed in any of claims 8 to 14, comprising the following components:
Component
Relative proportion
Concentration
1.
polyvinyl
chloride
20-40% by volume
5%-15% by weight in solution
with water
2.
gelatin
12.5-20% by volume
2%-7% by weight in solution
with water
3.
sodium
alginate
12.5-20% by volume
0.5%-2% by weight in solution
with water
4.
polyethylene
glycol
2-4% by volume
average molecular weight
between 100 and 300
5.
acetic acid
0.5 and 2% by volume
0.5-2.5% by weight in solution
with water
6.
chitosan
0.5 to 1.5 gm per 100ml
of components 1. to 5.
Solid
18.A method as claimed in claim 18, comprising the following components:
Component
Relative proportion
Concentration
1.
polyvinyl
chloride
30-35% by volume
7%-12% by weight in solution
with water
2.
gelatin
14-18% by volume
3%-6% by weight in solution
with water
3.
sodium
alginate
14-18% by volume
0.75%-1.5% by weight in
solution with water
4.
polyethylene
glycol
3.0-3.5% by volume
average molecular weight
between 150 and 250
5.
acetic acid
0.5 and 1% by volume
0.75-1.5% by weight in solution
with water
6.
chitosan
0.5 to 1.0 gm per 100ml
of components 1. to 5.
Solid
19.The ready-to-use, self-dispersive, fragmentable and biodegradable porous sponge and method of manufacturing thereof, substantially as hereinbefore claimed and/or described in any of the preceding claims, description and drawings.
Intellectual
Property
Office
Application No: GB1608671.2 Examiner: Dr Kerri Stenning
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
GB1608671.2A GB2553260B (en) | 2016-05-17 | 2016-05-17 | A ready-to-use, hydrophilic, self-dispersive, fragmentable and biodegradable porous sponge matrix and a method of manufacturing thereof |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
GB1608671.2A GB2553260B (en) | 2016-05-17 | 2016-05-17 | A ready-to-use, hydrophilic, self-dispersive, fragmentable and biodegradable porous sponge matrix and a method of manufacturing thereof |
Publications (3)
Publication Number | Publication Date |
---|---|
GB201608671D0 GB201608671D0 (en) | 2016-06-29 |
GB2553260A true GB2553260A (en) | 2018-03-07 |
GB2553260B GB2553260B (en) | 2021-06-16 |
Family
ID=56320546
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
GB1608671.2A Active GB2553260B (en) | 2016-05-17 | 2016-05-17 | A ready-to-use, hydrophilic, self-dispersive, fragmentable and biodegradable porous sponge matrix and a method of manufacturing thereof |
Country Status (1)
Country | Link |
---|---|
GB (1) | GB2553260B (en) |
Families Citing this family (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
CN114681656B (en) * | 2020-12-31 | 2023-07-07 | 苏州博创同康生物工程有限公司 | Antibacterial repair absorbable composite polysaccharide biological material and preparation method and application thereof |
Citations (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2004082594A2 (en) * | 2003-03-18 | 2004-09-30 | Sk Chemicals Co. Ltd. | Alginate sponge and preparation method thereof |
WO2009131434A1 (en) * | 2008-04-24 | 2009-10-29 | Universiti Malaya | Extracellular scaffolds comprising blends of polyvinyl alcohol and carboxymethyl chitosan |
US20100318048A1 (en) * | 2009-06-16 | 2010-12-16 | Baxter International Inc. | Hemostatic sponge |
WO2014035245A1 (en) * | 2012-08-31 | 2014-03-06 | Polyganics B.V. | Hemostatic foam |
KR20150058606A (en) * | 2013-11-18 | 2015-05-29 | 한국원자력연구원 | Preparation methods of porous foam composed chitosan-gelatin-algin using ultrasonication and radiation |
WO2015145457A1 (en) * | 2014-03-24 | 2015-10-01 | Datt Mediproducts Limited | A ready to use biodegradable and biocompatible device and a method of preparation thereof |
-
2016
- 2016-05-17 GB GB1608671.2A patent/GB2553260B/en active Active
Patent Citations (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2004082594A2 (en) * | 2003-03-18 | 2004-09-30 | Sk Chemicals Co. Ltd. | Alginate sponge and preparation method thereof |
WO2009131434A1 (en) * | 2008-04-24 | 2009-10-29 | Universiti Malaya | Extracellular scaffolds comprising blends of polyvinyl alcohol and carboxymethyl chitosan |
US20100318048A1 (en) * | 2009-06-16 | 2010-12-16 | Baxter International Inc. | Hemostatic sponge |
WO2014035245A1 (en) * | 2012-08-31 | 2014-03-06 | Polyganics B.V. | Hemostatic foam |
KR20150058606A (en) * | 2013-11-18 | 2015-05-29 | 한국원자력연구원 | Preparation methods of porous foam composed chitosan-gelatin-algin using ultrasonication and radiation |
WO2015145457A1 (en) * | 2014-03-24 | 2015-10-01 | Datt Mediproducts Limited | A ready to use biodegradable and biocompatible device and a method of preparation thereof |
Also Published As
Publication number | Publication date |
---|---|
GB2553260B (en) | 2021-06-16 |
GB201608671D0 (en) | 2016-06-29 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US10293075B2 (en) | Ready-to-use, hydrophilic, self-dispersive, fragmentable and biodegradable porous sponge matrix and a method of manufacturing thereof | |
US10076590B2 (en) | Modified starch material of biocompatible hemostasis | |
EP2203053B1 (en) | Modified starch material of biocompatible hemostasis | |
CA2656523C (en) | Flexible bioresorbable hemostatic packing and stent | |
EP2233157A1 (en) | A biocompatible denatured starch sponge material | |
KR101468287B1 (en) | Macromolecular composition, and method for preparing elastic wound dressing using thereof | |
US20160346239A1 (en) | Hemostatic composition and device | |
US20110070285A1 (en) | Method of making flexible bioresorbable hemostatic packing and stent having a preselectable in-vivo residence time | |
EP2879620B1 (en) | Compositions and methods for the treatment of bone voids and open fractures | |
CN111954545A (en) | Method for preparing hemostatic composition | |
ES2323126T3 (en) | HEMOSTATIC AGENT CONTAINING POLYVINYL ALCOHOL AND ITS AVAILABLE FOR MEDICINE. | |
EP4327840A2 (en) | Compositions comprising oxidized cellulose | |
GB2553260A (en) | A ready-to-use, hydrophilic, self-dispersive, fragmentable and biodegradable porous sponge matrix and a method of manufacturing thereof | |
CN109568635B (en) | In-situ expansion high-water-absorption hemostatic material and preparation method thereof | |
WO2016022708A1 (en) | Method of causing delayed hemostasis | |
Ghanim et al. | Insight into Topical Preparations for Wound Healing: Traditional and Modern Dressings | |
KR20220079325A (en) | Expandable wound dressing and process for preparing the same |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
732E | Amendments to the register in respect of changes of name or changes affecting rights (sect. 32/1977) |
Free format text: REGISTERED BETWEEN 20230615 AND 20230621 |