WO2012137158A1 - Composição de vidros bioactivos, sua utilização e respectivo método de obtenção - Google Patents
Composição de vidros bioactivos, sua utilização e respectivo método de obtenção Download PDFInfo
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- WO2012137158A1 WO2012137158A1 PCT/IB2012/051681 IB2012051681W WO2012137158A1 WO 2012137158 A1 WO2012137158 A1 WO 2012137158A1 IB 2012051681 W IB2012051681 W IB 2012051681W WO 2012137158 A1 WO2012137158 A1 WO 2012137158A1
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
- A61K33/00—Medicinal preparations containing inorganic active ingredients
- A61K33/06—Aluminium, calcium or magnesium; Compounds thereof, e.g. clay
- A61K33/08—Oxides; Hydroxides
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
- A61K33/00—Medicinal preparations containing inorganic active ingredients
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
- A61K33/00—Medicinal preparations containing inorganic active ingredients
- A61K33/16—Fluorine compounds
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
- A61K33/00—Medicinal preparations containing inorganic active ingredients
- A61K33/42—Phosphorus; Compounds thereof
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
- A61K9/00—Medicinal preparations characterised by special physical form
- A61K9/0012—Galenical forms characterised by the site of application
- A61K9/0019—Injectable compositions; Intramuscular, intravenous, arterial, subcutaneous administration; Compositions to be administered through the skin in an invasive manner
- A61K9/0024—Solid, semi-solid or solidifying implants, which are implanted or injected in body tissue
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/02—Inorganic materials
- A61L27/10—Ceramics or glasses
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/28—Materials for coating prostheses
- A61L27/30—Inorganic materials
- A61L27/306—Other specific inorganic materials not covered by A61L27/303 - A61L27/32
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/28—Materials for coating prostheses
- A61L27/30—Inorganic materials
- A61L27/32—Phosphorus-containing materials, e.g. apatite
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/50—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
- A61L27/58—Materials at least partially resorbable by the body
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- C—CHEMISTRY; METALLURGY
- C03—GLASS; MINERAL OR SLAG WOOL
- C03C—CHEMICAL COMPOSITION OF GLASSES, GLAZES OR VITREOUS ENAMELS; SURFACE TREATMENT OF GLASS; SURFACE TREATMENT OF FIBRES OR FILAMENTS MADE FROM GLASS, MINERALS OR SLAGS; JOINING GLASS TO GLASS OR OTHER MATERIALS
- C03C10/00—Devitrified glass ceramics, i.e. glass ceramics having a crystalline phase dispersed in a glassy phase and constituting at least 50% by weight of the total composition
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- C—CHEMISTRY; METALLURGY
- C03—GLASS; MINERAL OR SLAG WOOL
- C03C—CHEMICAL COMPOSITION OF GLASSES, GLAZES OR VITREOUS ENAMELS; SURFACE TREATMENT OF GLASS; SURFACE TREATMENT OF FIBRES OR FILAMENTS MADE FROM GLASS, MINERALS OR SLAGS; JOINING GLASS TO GLASS OR OTHER MATERIALS
- C03C3/00—Glass compositions
- C03C3/04—Glass compositions containing silica
- C03C3/062—Glass compositions containing silica with less than 40% silica by weight
- C03C3/064—Glass compositions containing silica with less than 40% silica by weight containing boron
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- C—CHEMISTRY; METALLURGY
- C03—GLASS; MINERAL OR SLAG WOOL
- C03C—CHEMICAL COMPOSITION OF GLASSES, GLAZES OR VITREOUS ENAMELS; SURFACE TREATMENT OF GLASS; SURFACE TREATMENT OF FIBRES OR FILAMENTS MADE FROM GLASS, MINERALS OR SLAGS; JOINING GLASS TO GLASS OR OTHER MATERIALS
- C03C3/00—Glass compositions
- C03C3/04—Glass compositions containing silica
- C03C3/076—Glass compositions containing silica with 40% to 90% silica, by weight
- C03C3/11—Glass compositions containing silica with 40% to 90% silica, by weight containing halogen or nitrogen
- C03C3/112—Glass compositions containing silica with 40% to 90% silica, by weight containing halogen or nitrogen containing fluorine
-
- C—CHEMISTRY; METALLURGY
- C03—GLASS; MINERAL OR SLAG WOOL
- C03C—CHEMICAL COMPOSITION OF GLASSES, GLAZES OR VITREOUS ENAMELS; SURFACE TREATMENT OF GLASS; SURFACE TREATMENT OF FIBRES OR FILAMENTS MADE FROM GLASS, MINERALS OR SLAGS; JOINING GLASS TO GLASS OR OTHER MATERIALS
- C03C3/00—Glass compositions
- C03C3/04—Glass compositions containing silica
- C03C3/076—Glass compositions containing silica with 40% to 90% silica, by weight
- C03C3/11—Glass compositions containing silica with 40% to 90% silica, by weight containing halogen or nitrogen
- C03C3/112—Glass compositions containing silica with 40% to 90% silica, by weight containing halogen or nitrogen containing fluorine
- C03C3/115—Glass compositions containing silica with 40% to 90% silica, by weight containing halogen or nitrogen containing fluorine containing boron
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- C—CHEMISTRY; METALLURGY
- C03—GLASS; MINERAL OR SLAG WOOL
- C03C—CHEMICAL COMPOSITION OF GLASSES, GLAZES OR VITREOUS ENAMELS; SURFACE TREATMENT OF GLASS; SURFACE TREATMENT OF FIBRES OR FILAMENTS MADE FROM GLASS, MINERALS OR SLAGS; JOINING GLASS TO GLASS OR OTHER MATERIALS
- C03C4/00—Compositions for glass with special properties
- C03C4/0007—Compositions for glass with special properties for biologically-compatible glass
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- 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
- A61L2400/06—Flowable or injectable implant compositions
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L2430/00—Materials or treatment for tissue regeneration
- A61L2430/02—Materials or treatment for tissue regeneration for reconstruction of bones; weight-bearing implants
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L2430/00—Materials or treatment for tissue regeneration
- A61L2430/12—Materials or treatment for tissue regeneration for dental implants or prostheses
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L2430/00—Materials or treatment for tissue regeneration
- A61L2430/38—Materials or treatment for tissue regeneration for reconstruction of the spine, vertebrae or intervertebral discs
Definitions
- the present invention relates to a set of high in vitro biomineralization bioglass compositions, expressed by rapidly depositing on their surface an x-ray diffraction-detectable carbonated hydroxyapatite layer after one hour of immersion in simulated physiological fluid (SBF) and controlled biodegradation rates, translated as weight losses of less than 2% when immersed for 5 days in a Tris HCl solution (pH: 7,25) according to ISO 10993 - "Biological Evaluation of Medical Devices" Part 14 - "Identification and quantification of ceramic degradation products” and their compositions may be designed to exhibit antibacterial activity, which are essential conditions for rapid reconstruction of damaged hard tissues and to prevent postoperative infections due to possible contamination. .
- SBF simulated physiological fluid
- Bioactive materials are thus designated to induce a specific biological activity; in most cases the desired biological activity is to establish a strong connection with bone or even soft tissue [Rawlings, Clin. Mater. 14 (1993) 155-179].
- Bioactive glass and vitroceramics are a class of biomaterials, ie materials that develop a special response on their surface when in contact with biological fluids, leading to the formation of a strong bond with living tissues.
- bioactivity is defined as the ability of material to bind to bone tissue via the formation of a surface layer of hydroxyapatite similar to that in bone.
- silicate glasses comprising sodium, calcium, phosphorus and silicon dioxide salts.
- the compositions of these glasses included (mol% ranges) SiO 2 (40-52%), CaO (10-50%), Na 2 O (10-35%), P 2 O 5 (2-8%), CaF 2 (0-25%) and B 2 0 3 (0-10%).
- a particular example is the 45S5 Bioglass® bioglass of the SiO 2 -P 2 C> 5-CaO-Na 20 system patented by Hench et al in US Patent Document no. 4234972.
- Hench et al. also prepared alkali-free bioglass compositions via sol-gel processes in the SiO 2 -CaO-P 20 O 5 system as indicated in US Patent Document no. No. 5074916, as well as fluorine-containing bio-glasses in which a CaO portion of the 45S5 Bioglass ® composition has been replaced by CaF 2 as indicated in US Patent Document no. 4775646.
- the bioactivity of the resulting glasses was lower compared to that of the 45S5 Bioglass ® bioglass.
- US2007162151A1 and WO2006118554A1 report a method of preparing bioactive glass macroporous graft materials having compositions based on the "45S5 Bioglass ® " by Hench et al described in US Patent Document no. 4234972, but enriched with CaO and P 2 O 5 , and with small additions of MgO and CaF 2 : 34-50% CaO, 20-50% SiO 2 , 0- 25% Na 2 0, 5-17% P 2 O 5, 0-5% MgO, 0-1% CaF 2.
- biodegradation rates after 5 days of immersion in SBF are very high, ranging from 2-30%.
- the method of preparing macroporous graft materials is complicated, involving large particle size frits ranging in the range of 40-300 micrometers; and organic inclusions such as pore-forming, with particle sizes ranging from 50-600 micrometres, whose weight fractions may range from 20-70%.
- the addition of 1-5% polyvinyl alcohol as an organic binder allows the consolidation of compacts by dry pressing.
- the method known as gelcasting involving the in situ polymerization of monomers and dimers by the addition of catalysts and reaction initiators has also been used as an alternative consolidation method. Regardless of the process adopted for obtaining the compacts, they were then sintered at temperatures of 750-900 ° C for 1-5 h to obtain the final product.
- JP2000271205A reports a series of bioactive glass compositions comprising the following limits for the contents of the various components: 30-70% CaO, 30-70% Si0 2 , 0-40% P 2 0 5 , 0-20% MgO, 0-5% CaF 2 , also assuming some narrower ranges: 40-50% CaO, 30-40% Si0 2 , 10-20% P 2 0 5 , 0, 5-10% MgO, 0-2% CaF 2 and in particular the following specific composition: 45% CaO, 34% SI0 2, 16% P 2 0 5 4 5% MgO, 0.5% CaF 2 as well as the use of such bioactive glass as a filler material in polymethyl methacrylate (PMMA) bone cements.
- PMMA polymethyl methacrylate
- US5527836A also reports the use of bioactive glass compositions as fillers in polymethyl methacrylate (PMMA) bone cements.
- PMMA polymethyl methacrylate
- the contents of the various components in the bioactive glass compositions generally varied within the following limits: 40-50% CaO, 30-40% Si0 2 , 10-20% P 2 0 5 , 0-10% MgO, 0-2% CaF 2 , although some oxides have been excluded from some formulations, while alkaline oxides have been introduced into other compositions.
- compositions were tested: (1) 47.7% CaO, 34% SiO 2 , 16.2% P 2 0 5 , 4.6% MgO, 0.5% CaF 2 ; (2) 46.5% CaO, 36% SiO 2 , 17% P 2 0 5 , 0.5% CaF 2 ; (3) 5.0% Na 2 O, 0.5% K 2 O, 34.0% CaO, 46% Si O 2 , 11.5% P 2 O 5 , 3.0% MgO, 0.5% CaF 2 .
- These compositions do not differ much from those proposed in the previous document and therefore have the same problems of liquid phase separation and high biodegradation rates.
- the authors also used crystallized powders by heat treatment at 1050 ° C. From the comparative studies, the authors concluded for the best performance of alkaline metal free glassy or vitroceramic powders, especially if combined with hydrophilic polymer chains.
- apatite-volastonite-based vitroceramic (CERABONE ® AW) designed along the 3CaO-P 2 0 5 - CaO-Si0 2 - MgO ⁇ CaO ⁇ 2Si0 2 pseudo-ternary system, the composition of which was described in the document.
- Patent Application No. 03-131263 has been the most successful bioactive vitroceramic material as a bone substitute in human medicine.
- the vitroceramic composition comprises MgO, CaO, SiO 2 , P 2 O 5 and CaF 2 in which the weight ratios between the components are 4.6: 44.7: 34.0: 16.2: 0.5.
- the vitroceramic has good bioactivity, good mechanical strength (flexural: 178 MPa and under compression: 1080 MPa) and can be machined in various forms. Since 1983, this vitroceramic has been successfully used in spinal and hip surgeries in patients with extensive lesions and defects [T. Yamamuro, A / W glass ceramic: Clinical applications, in An Introduction to Bioceramics. Edited by LL Hench, J. Wilson World Scientific, Singapore, 1993]. However, although CERABONE® AW material has the highest mechanical strength of all bioceramics developed to To date, glass-ceramic porous supports derived from this composition cannot be used in load-bearing applications [Kokubo et al. J. Mater. Know. Mater. Med. 15 (2004) 99-107].
- US patent document no. No. 4,778,329 describes a biocompatible, alkali-free vitroceramic material in which a mixture of crystalline phases of apatite, volastonite and diopsite is formed, the composition of which comprises (wt.%): 7.2-14% MgO, 25-38% CaO, 4.5- 50% Si0 2 , 8.2-25% P 2 0 5 , 0-4% B 2 0 3 , 0-3% F 2 and 0-6% A1 2 0 3 . Also, in US patent document no. No.
- 4,560,666 discloses a biocompatible vitroceramic material belonging to the MgO-CaO-SiO 2 -P 2 Os system based on apatite and alkaline earth silicate crystals (diopsite / akermanite / forsterite).
- the sol-gel process is an alternative route for preparing bioactive glasses.
- the reagents alkoxides, metal salts, etc.
- a suitable medium to form a homogeneous atomic scale solution.
- hydrolysis and polycondensation reactions whereby small molecules give rise to the formation of polymeric structures.
- This method involves the formation of a colloidal suspension (sol), followed by its gradual polymerization, which leads to the production of inorganic materials dispersed in a solvent through the growth of oxo-metallic polymers forming a three-dimensional porous structure whose viscosity increases. with aging, turning into a hard gel.
- the gel is then heat treated to promote dehydration and chemical stabilization of the powders or to densify the compacts [Hench & West, The Sol-Gel Process, 90 Chem. Rev. 33 (1990)].
- the sol-gel process is an alternative route for preparing bioactive glasses at much lower temperatures compared to those used in the melting process, even of more refractory compositions free of alkali metals or other flux-function compounds.
- US patent document no. US5074916 reports the preparation of alkaline-free bioglass formulations based only on Si02 (44-86%), CaO (4-46%), and P205 (3-15%) (weight percentages).
- EP20050823528 reports the use of silver salt solutions to impregnate biocompatible vitreous or vitroceramic coatings having the following molar composition: 57% Si0 2 - 34% CaO - 6% Na 2 0 - 3% A1 2 0 3 applied over impants to give them bactericidal properties.
- This property allows the formation of a strongly adherent carbonated hydroxyapatite layer, unlike Bioglass ® , and other bio-glasses inspired by it, in which the continued dissolution of the substrate eventually releases the carbonated hydroxyapatite layer and, in vivo, leads to disruption of the connection between the implant and bone tissue.
- the low solubility also allows bioglass frits to be easily processed in an aqueous medium without the risk of suspension coagulation (a commonly observed phenomenon with prior art bioglass frits) and the size of their particles can be sufficiently reduced. for optimizing the rheological properties of suspensions and for impregnating polymeric sponges for the preparation of porous supports for bone regeneration or tissue engineering.
- the low content or absence of alkali metals in the bio-glasses of the present invention makes the pH variations when in contact with physiological fluids much lower than those experienced by 45S5 Bioglass ® , and other bio-glasses inspired by it.
- bioactive glasses of the present invention have a much lower degradation rate (less than half) of Bioglass ®, and other bioactive glasses it inspired.
- the extremely high degree of bioactivity of the bioglass of the present invention allows it to be somewhat sacrificed by a partial devitrification of about 30% which doubles the mechanical flexural strength and thus achieves a better balance between these two properties. relevant.
- the solvel-prepared bio-glasses of the present invention can be further used as coatings of other biomaterials, including porous grafts, in order to stimulate the cascade of biological processes that occurs after in vivo implantation due to their higher reactivity and better suitability.
- of the composition for its intended purpose including the prevention of bacteriological contamination, and may further accumulate other functionalities such as storage and controlled release of drugs in situ.
- bioactive glass compositions comprising the following elements:
- magnesium oxide between 0-30%
- compositions further comprise alkali metals in a concentration of less than 5%.
- compositions do not contain alkali metals.
- compositions have phosphorus pentoxide or silica forming the vitreous network.
- compositions comprise the following elements:
- compositions have a source of calcium selected from at least one of the following: calcium oxide, calcium hydroxide, calcium carbonate, calcium nitrate, calcium sulfate, calcium silicates.
- compositions have a source of magnesium selected from at least one of the following: magnesium oxide, magnesium hydroxide, magnesium carbonate, magnesium nitrate, magnesium sulfate, magnesium silicates.
- compositions have a phosphorus source selected from at least one of the following: phosphorus pentoxide, ammonium dihydrogen phosphate, trimethylphosphate, triethylphosphate, phosphoric acid, phosphorus pentoxide source.
- a phosphorus source selected from at least one of the following: phosphorus pentoxide, ammonium dihydrogen phosphate, trimethylphosphate, triethylphosphate, phosphoric acid, phosphorus pentoxide source.
- compositions have a fluorine / fluoride source selected from at least one of the following: calcium fluoride, magnesium fluoride, trifluoroacetic acid, hexafluorophosphate acid, ammonium hexafluorophosphate.
- a fluorine / fluoride source selected from at least one of the following: calcium fluoride, magnesium fluoride, trifluoroacetic acid, hexafluorophosphate acid, ammonium hexafluorophosphate.
- compositions are doped with at least one oxide of the following elements: Na, K, Li, Ru, Cs, Fr, Sr, Bi, Zn, Ag, B, Cu, Mn, Fe, Ti in Molar percentages range from 0-10%.
- compositions have molar percentages of oxides ranging from 0-5%.
- the compositions comprise the following elements: - oxides, such as Na 2 O, K 2 O, SiO 2 , CaO, MgO, P 2 O 5 , Na 2 O, K 2 O, Ru 2 O, Cs 2 O, Fr 2 O, SrO, Bi 2 O 3 , ZnO, Ag 2 O, B 2 O 3 , Cu 2 O, MnO 2 , Fe 2 O 3 , TiO 2 ;
- - oxides such as Na 2 O, K 2 O, SiO 2 , CaO, MgO, P 2 O 5 , Na 2 O, K 2 O, Ru 2 O, Cs 2 O, Fr 2 O, SrO, Bi 2 O 3 , ZnO, Ag 2 O, B 2 O 3 , Cu 2 O, MnO 2 , Fe 2 O 3 , TiO 2 ;
- alkoxides such as tetraethylortosilicate, Si (OC 2 H 5 ) 4 (TEOS) or tetramethylortosilicate, Si (OCH 3 ) 4 , (TMOS), titanium isopropoxide, C 2 H 2 S 0 4 Ti];
- carbonate hydroxides such as NaOH, Ca (OH) 2 , Mg (OH) 2 , Fe (OH) 3 ;
- carbonates such as Na 2 CO 3 , K 2 CO 3 , CaCO 3 , MgCO 3 , SrCO 3 ;
- nitrates such as NaN0 3, Ag (N0 3), Mg (N0 3) 2, Ca (N0 3) 2, Ca (N0 3) 2 .4H 2 0, Ag 2 (N0 3) 2, Fe (N0 3) 3 , Fe (NO 3 ) 3 ⁇ 9H 20 ;
- sulfates such as Na 2 SO 4 , K 2 SO 4 , CaSO 4 ;
- phosphates or phosphorus precursors such as ammonium dihydrogen phosphate (NH 4 H 2 P0 4), trimethylphosphate, (CH 3 0) 3 PO (TMP), triethyl phosphate (C 2 H 5 0) 3 PO (PTE), phosphoric acid, disodium phosphate, Na 2 HP0 4 , monosodium phosphate, NaH 2 P0 4 sodium tri triphosphate, Na 5 OioP 3 , sodium hexametaphosphate, (NaP0 3 ) 6 ;
- fluorides or fluorine precursors such as calcium fluoride, CaF 2 , magnesium fluoride (MgF 2 ), trifluoroacetic acid, CF 3 COOH (TFA), hexafluorophosphate acid (HPF6), ammonium hexafluorophosphate (NH 4 PFg);
- chlorides such as CaCl 2 , MgCl 2 , FeCl 3 ;
- borates such as sodium tetraborate, Na 2 B 4 0 7 ⁇ 10H 2 O.
- compositions further comprise polymeric resins.
- compositions are in powder form. In yet another preferred embodiment, the compositions have a particle size of less than 500 ⁇ m.
- compositions further comprise injectable calcium phosphate or polymethyl methacrylate based cements.
- compositions are used in medicine.
- bioactive glass compositions are used as prostheses, implants, toothpastes, dental cements and bone fillers.
- bioactive glass compositions are used in in vitro synthesis of bone tissue.
- bioactive glass compositions are used as an implant coating, particularly orthopedic and dental prostheses.
- bioactive glass compositions wherein the prostheses are made of cobalt chromium alloys, stainless steel, or polymeric materials, or Ti6A14V, or ceramic materials or mixtures thereof. It is a further object of the present invention to describe frits comprising the aforementioned glass compositions.
- fillers composed of mixtures of oxides, preferably carbonates, nitrates, sulphates, fluorides, at temperatures in the range 1050-1600 ° C and time intervals of 1 - 2 h;
- the method further comprises an annealing step at temperatures between 400-700 ° C, preferably between 500-600 ° C.
- the method for obtaining bioactive glasses comprises the following steps:
- - dissolving compounds including: alkoxides, phosphates, fluorides, nitrates, chlorides, sulfates, oxides, acids in absolute ethanol;
- the method utilizes liquid or steamed water.
- the method for obtaining bioactive glasses has a catalyst which is an acid or a base.
- the method for obtaining the bioactive glasses presents Si02 sources which are alkoxides, such as tetraethylorthosilicate and / or tetramethylortosilicate.
- the present invention relates to a set of bioactive glass / glass ceramics compositions, commonly referred to as bio glass / bio glass ceramics, ie materials that develop a special response on their surface when in contact with biological fluids, leading to the formation of a strong bond with living tissues through an interfacial layer of carbonated hydroxyapatite, some of them capable of being easily sintered.
- bio glass / bio glass ceramics ie materials that develop a special response on their surface when in contact with biological fluids, leading to the formation of a strong bond with living tissues through an interfacial layer of carbonated hydroxyapatite, some of them capable of being easily sintered.
- the bio-glass compositions of the present invention generally have high in vitro biomineralization rates, which translates into making it possible after a immersion time in simulated physiological fluid (SBF) detects the surface layer of x-ray diffraction-carbonated hydroxyapatite and controlled biodegradation rates, translated into weight losses of less than 2% when immersed for 5 days in a Tris HC1 solution (pH : 7.25) according to ISO 10993 - "Biological Evaluation of Medical Devices", Part 14 - "Identification and Quantification of Ceramic Degradation Products", essential conditions for the rapid reconstruction of damaged hard tissues.
- SBF simulated physiological fluid
- powders derived from molten and water-cooled glasses may be completely densified in the temperature range 800-900 ° C without crystallization occurring, or resulting in a dense amorphous glassy mass with some fine diopsite crystals (CaMgSi 2 0 6 ), and / or wollastonite (CaSi0 3 ) and / or fluorapatite [Ca 5 (P0 4 ) 3 F] with various proportions between amorphous and crystal clear.
- the glassware / glass ceramics object of the present invention can be used in different applications in regenerative medicine and tissue engineering.
- Fig. 1 TCP-40 bioactive glass x-ray diffraction spectrum after immersion 0.1 g of glass powder in 50 ml of SBF solution for one hour. It was found that by the end of this short period of time a layer of HCA had already formed on the surface of the glass particles, confirmed by the respective peak on the diffractogram, showing a high capacity for biomineralization.
- Fig. 2 X-ray diffraction spectrum of TCP-20 bioactive glass after soaking 0.1 g of glass powder in 50 ml of SBF solution for twelve hours. It was found that at the end of this time a well crystallized HCA layer was formed on the surface of the glass particles, confirmed by the intense diffractogram peak, showing a high biomineralization capacity.
- Fig. 3 Comparison between differential thermal analysis (DTA) and heating microscopy (HSM) curves presented for bioactive glass TCP-20. Maximum shrinkage is found to occur prior to the start of crystallization thus allowing completely dense bodies to be obtained from glass powder compacts by heat treatment at temperatures in the range 800-850 ° C for 1 h.
- DTA differential thermal analysis
- HSM heating microscopy
- Fig. 4 X-ray diffraction spectrum of a TCP-20 bioactive glass powder compact sintered at 800 ° C for one hour, confirming that the material is in an amorphous but well-densified state, as can be deduced from high mechanical flexural strength (85 MPa).
- Fig. 5 X-ray diffraction spectrum of a FA-20 bioactive glass powder compact sintered at 850 ° C for one hour, giving rise to the formation of a about 30 wt vitro-ceramic. % of crystalline phases. Diopsite is the phase crystalline form, with fluorapatite being present as a secondary crystalline phase.
- the present invention relates to a set of high bioactivity bioglass compositions, some of them capable of being sintered.
- the bioglass compositions of the present invention exhibit high rates of in vitro biomineralization, expressed as the ability to deposit a surface layer of hydroxyapatite within one hour of SBF immersion, and controlled biodegradation rates, essential conditions for rapid reconstruction. damaged hard tissues.
- the powders derived from the melt and water-cooled (frit) glass can be completely densified in the temperature range 800-900 ° C without crystallization occurring, or resulting in a dense, amorphous glass mass with some fine diopsite crystals.
- CaMgSi 2 0 6 and / or volastonite (CaSi0 3 ) and / or fluorapatite [Ca 5 (PC> 4) 3F] with various proportions between amorphous and crystalline fractions.
- the glassware and glass ceramics object of the present invention may be used in different applications in regenerative medicine and tissue engineering.
- the bio-glasses of the present invention may be prepared by melting fillers composed of mixtures of oxides, carbonates, nitrates, sulfates, fluorides, etc., in platinum crucibles or other suitable material at temperatures in the range 1500-1600 ° C, and time intervals of 1 - 2 h, followed by casting in metal or graphite molds or other suitable materials to obtain glass bodies, or pouring into water to obtain frits for processing materials via powder compaction and sintering.
- the bio-glasses object of the present invention may be prepared by sol-gel from solutions of alkoxides, phosphates, fluorides, nitrates, chlorides, sulfates, oxides, acids etc.
- Reagents are usually dissolved in absolute ethanol and the reactions of Hydrolysis is induced by controlled additions of liquid or vapor water and catalysts (acidic or basic).
- This method involves the formation of a colloidal suspension (sol), followed by its gradual polymerization, which leads to the production of inorganic materials dispersed in a solvent through the growth of oxo-metallic polymers forming a three-dimensional porous structure whose viscosity increases. with aging, turning into a hard gel. The gel is then heat treated to promote dehydration and chemical stabilization of the powders or to densify the compacts.
- Silica (SiO 2 ) and phosphorus pentoxide (P 2 O5) are the two major oxides of the vitreous network, and their networks have limited miscibility. Thus, one of these forming oxides should play a predominant role in a given composition. Otherwise, liquid phase separation will occur during melting and cooling, whereby the glass obtained is not homogeneous and easily degrades when immersed in physiological fluid, SBF or even pure water.
- Silica is the most typically used forming oxide and is also the most relevant component in the formation of bioactive glasses.
- the molar percentage of S1O 2 in the melt-prepared glasses affects the glazing behavior, molecular structure as well as sintering and crystallization behaviors.
- the molecular structure of a glass plays a crucial role in determining its bioactivity.
- High bioactivity derives from a glass structure dominated by metasilicate Q 2 chains, which are occasionally linked to Q 3 units, while Q 1 species terminate chains, where the distribution of Q n species provides a measure of the degree of interconnection of glass lattice and the index n refers to the number of bridging oxygen (BOs) connecting a forming ion to the glass lattice.
- the highest solubility of silica much bioactive vitreous compositions is related to a significant fraction of Q 1 groups (Si) as vitreous structures in which Q 3 predominantly (Si) groups have a moderate bioactivity [Tilocca, Proc. R. Soc. 465 (2009) 1003-1027].
- Silica leaching when bioglass is brought into contact with simulated physiological fluid (SBF) also indirectly increases bioactivity through the surface Si-OH silanol groups generated during the hydrolysis of Si-O-Si bonds, a process which in turn In turn, it contributes to the decrease in interfacial energy between apatite and glass.
- Soluble silica species also function as nucleation centers for calcium phosphate precipitation; New applications of bioactive glasses as supporting structures in tissue engineering require the direct action of silica and calcium leached species to activate the genes that induce osteoblast proliferation [Tilocca et al. Faraday Discuss. 136 (2007) 45-55].
- the molar percentage of SiO 2 in the glasses is preferably from 29 - 60%. If the molar percentage of S1O 2 is less than 29%, the glass becomes prone to extensive crystallization immediately after casting of the melt. Thus, the minimum content of S1O 2 is 29% or even preferably 29,5% or more. Similarly, SiO 2 contents greater than 60% reduce the glazing capacity and lead to extensive melt crystallization. Thus, the maximum content of SiO 2 is 60%, or preferably 50%. In the case of glasses prepared by sol gel, the silica content may be as high as 90%.
- the sources of SiO 2 may be alkoxides such as tetraethylortosilicate, Si (OC 2 H 5 ) 4 (TEOS) tetramethylortosilicate, Si (OCH 3 ) 4 , (TMOS).
- TEOS tetraethylortosilicate
- Si (OCH 3 ) 4 TMOS
- the molar percentage of SiO 2 may be about 10% or even less.
- the bioactive glasses of the present invention comprise a source of calcium including but not limited to calcium oxide (CaO), calcium hydroxide, calcium carbonate (CaCC> 3), calcium nitrate (Ca (NO3) 2), calcium sulfate. (CaSC), calcium silicates or another source of calcium.
- the source of calcium oxide includes any decomposition compound that forms calcium oxide.
- the release of Ca 2+ ions from the bioglass surface contributes to the formation of a calcium phosphate rich layer.
- the molar percentage of CaO in glasses may range from 20-60%.
- the molar percentage of CaO in the glasses may be 20-55%, or more preferably 25-53%.
- Bioactive glasses of the present invention preferably comprise a magnesium source including but not limited to magnesium oxide (MgO), magnesium hydroxide, magnesium carbonate (MgCOs), magnesium nitrate (Mg (N0 3) 2), magnesium sulfate (MgSO 4 ), magnesium silicates or another source of magnesium oxide.
- the source of magnesium oxide includes any compound which upon decomposition forms magnesium oxide. Recent data indicate that magnesium may act as intermediate oxide and partially as a network modifier [Watts et al. J. Non-Cryst. Solids 356 (2010) 517-524].
- Magnesium ions reduce the size of the formed carbonated hydroxyapatite (HCA) crystals and lower the coefficient of thermal expansion of the glass, this lowering being an advantage when bioglass is intended for the coating of metal prostheses including, but not limited to metal alloys such as as the T6A14V.
- HCA carbonated hydroxyapatite
- metal prostheses including, but not limited to metal alloys such as as the T6A14V.
- magnesium ions preferentially associate with phosphorus ions on the glass surface, causing a decrease in the concentration of calcium phosphate-like surface domains that act as apatite nucleation centers, thus suppressing the crystallization of apatite and favoring the formation of amorphous calcium phosphate [Pérez-Pariente et al. Chem. Mater. 12 (2000) 750-755; Jallot, Appl. Surf Know. 211 (2003) 89-95].
- the molar percentage of magnesium oxide (MgO) in the glasses should be between 0-30%.
- the molar percentage of MgO in the glasses should be between 0 - 25%, or preferably between 2 - 24%.
- Bioactive glasses of the present invention preferably comprise a source of P 2 O 5 including but not limited to phosphorus pentoxide (P 2 O 5), ammonium dihydrogen phosphate (NH 4 H 2 P0 4), trimethylphosphate, (CH 3 0 ) 3 PO (TMP), triethyl phosphate, (C 2 H 5 0) 3 PO (TEP), phosphoric acid, or another source of phosphorus pentoxide.
- the source of phosphorus pentoxide includes any compound which upon decomposition forms phosphorus pentoxide.
- the structural arrangement of phosphate groups in bioactive glasses largely determines their degree of bioactivity.
- the phosphate group in the bioactive glass structure should preferably exist in an orthophosphate (Q °) environment.
- Q ° orthophosphate
- the release of phosphate ions from the bioglass surface contributes to the formation of HCA.
- HCA formation on the surface of the bioglass is possible even when the bioglass does not provide phosphate ions since the physiologist fluid contains phosphate ions [De Aza et al. J. Biomed. Mater. Res. B: Appl. Biomater. 73B (2005) 54-60].
- the supply of phosphate ions by bioglass increases the rate of formation of HCA and the ability to bind to bone tissues [Tilocca, Proc. R. Soc. A 465 (2009) 1003- 1027].
- P 2 O 5 has a beneficial effect on the way the viscosity of glass is temperature dependent, increasing the working temperature range and is therefore an advantage for glass making and forming.
- the addition of P 2 O 5 also lowers the thermal expansion coefficient of the glass due to the re-polymerization of the silicate mesh, [Kansal et al. Acta Biomater. 6 (2010) 4380-4388]. This is an advantage when bioglass is intended for coating of metal prostheses including but not limited to metal alloys such as Ti6A14V.
- P 2 O 5 acts as a sintering additive, thereby improving the sinterability of glass powders.
- the molar percentage of P 2 O 5 in the present invention is thus limited to 0-10% in glasses where silica is the predominant forming oxide.
- the molar percentage of P 2 O 5 in these bio glasses should be between 0 - 8%.
- the molar percentage of P 2 O 5 in the bioglass should be between 1.7 - 8%.
- its molar percentage of P 2 O 5 must be between 30 - 50%.
- the molar percentage of P 2 O 5 in these bio-glasses should be between 33-40%.
- the bioactive glasses of the present invention preferably comprise a source of fluorine.
- Fluorine is preferably supplied in the form of fluorides such as calcium fluoride (CaF 2 ), or magnesium fluoride
- MgF 2 trifluoroacetic acid, CF 3 COOH (TFA), hexafluorophosphate (HPFg), ammonium hexafluorophosphate
- Fluoride stimulates osteoblasts, controls the dissolution of glass and increases bone density, so implants with the ability to release fluoride are of great interest to osteoporotic patients.
- Fluoride further promotes the formation of apatitic structures that resemble natural biological forms by substituting hydroxyl ions in the apatite network. This mixed apatitis is thermodynamically more stable and therefore less soluble and less resorbable.
- fluorine is a well-known anticancer agent. Fluoride released from dental restorative materials prevents demineralization and remineralization of hard tooth tissues
- the molar percentage of fluorine (preferably provided by CaF 2 for melt-prepared glasses or hexafluorophosphate (HPF6) for sol-gel glass) is restricted to a range of 0- 5%
- the molar percentage of CaF 2 in the bioglass should be between 0 - 3%.
- the molar percentage of CaF 2 and P 2 Os in the bioglass should be between 0.5 2%. Note that very small amounts of fluorine, approximately 0.03-0.08 ppm, in in vitro solutions are sufficient to change the balance from a demineralization situation to a remineralization situation [Wiegand et al. Dental Mater. 23 (2007) 343-362]. Increasing the fluorine concentration in the glass can degrade its bioactivity as this element is known to inhibit glass dissolution [Lusvardi et al. Acta Biomater. 5 (2009) 3548-3562].
- bioactive glass compositions contain sodium oxide (Na 2 ⁇ 0) and may also contain potassium oxide (K 2 O).
- Na 2 ⁇ 0 sodium oxide
- K 2 O potassium oxide
- incorporation of these compounds into bioactive glasses is advantageous from the point of view of glass production, as melting temperatures are lowered, the presence of these alkali, sodium and potassium metals in glasses may diminish their usefulness in vivo.
- high alkaline metal bioactive glasses are capable of absorbing water by osmosis, which in turn may cause swelling and fracture of polymeric matrices in which they are embedded in composites and may, in the case of the polymeric matrices are degradable, leading to high levels of degradation.
- These bioactive glasses may also be unsuitable as metal prosthetic coating materials due to their high coefficient of thermal expansion conferred by alkali metals.
- the total molar percentage of alkali oxides in the bioactive glasses of the present invention should not exceed 10%, preferably below 5%, or preferably still free of alkali metals.
- boron oxide (B 2 O 3 ) in the bioglass formulation is based on recent evidence about its beneficial effect on bone remodeling and repair [A. Gorustovich, JM Porto Lopez, MB Guglielmotti, RL Cabrini, Biomed. Mater. 2006, 1,100]; [THE. Gorustovich, T. Steimetz, FH Nielsen, MB Guglielmotti, Arch. Oral Biol. 2008, 53, 677], and a bactericidal action against Staphylococcus aureus [E. Munukka, O, Lepp ⁇ ranta, M. Korkeamáki, M., Vaahtio, T. Peltola, D. Zhang, L. Hupa, H.
- boron oxide exerts a melting action by lowering melt viscosity and temperature dependence, and extending the working temperature range and can facilitate fabrication and formation. of the glass.
- the molar percentage of boron oxide should not exceed 8% and should preferably be below 5%.
- doping oxides such as strontium oxide, bismuth oxide and zinc oxide
- the incorporation of doping oxides is justified by the beneficial effects derived from the gradual leaching of the respective ions in the physiological fluid, stimulating enzymatic and cellular activity.
- the molar percentage of each of these oxides may range from 0-10%, preferably from 2 to 6%.
- the bioactive glasses of the present invention are preferably aluminum-free as described in US Patent Document no. 2009/0208428 Al.
- the bioactive glasses of the present invention may be in particulate or monolithic forms such as discs or other regular or non-regular geometric shapes.
- the glasses may be supplied in any desired form, for example as pellets, sheets, discs, fibers, etc.
- the preferred size depends on the application of the bioactive glass concerned; however, the preferred range of particle sizes is less than 500 ⁇ m.
- the bioactive glass composition of the present invention is chosen to give the glass an enlarged processing window, resulting in a marked difference between glass transition (T g ) and onset crystallization (T c ) temperatures.
- Such glasses are particularly suitable for fiber fabrication and sintering of powder compacts since the enlarged processing window allows for fiber stretching without crystallization occurring.
- Castings cast in cooled molds of good thermally conductive materials eg bronze, graphite, etc.
- retain their glassy structure thus making them suitable for the manufacture of air stretch fibers, which involves even more cooling. roughness due to the small diameter of the fibers (in the order of tens of micrometers) than in the case of casting in molds, thus ensuring the maintenance of the glassy phase in the fibers, which can in turn be woven according to varying architectures.
- Another relevant feature of the invention relates to the ability to process completely amorphous materials or containing fine diopsite (CaMgSi206) and / or volastonite (CaSiOs) crystals, and may also contain fluorapatite [Ca 5 (P0 4 ) 3F] crystals from biomass glass powders consolidated by various techniques used in the processing of ceramic and sintered materials.
- Processing techniques may include dry pressing, and colloidal processing from aqueous or non-aqueous suspensions such as slip fill, belt processing, injection molding, and direct consolidation techniques that do not involve the removal of liquid used in dispersion such as: casting followed by in situ polymerization, consolidation based on starch gelation, casting followed by suspension coagulation, casting followed by rapid freezing, consolidation induced by temperature variations, gelation induced by temperature variations, etc.
- the sintered glass compacts disclosed in this invention are prepared from the above disclosed compositions for bioactive glasses which have a good ability to be densified by heat treatment.
- sintered bodies have high mechanical strength and controlled biodegradability.
- the glass ceramics disclosed in this invention are prepared by sintering bioglass powders with average particle sizes between 1 - 20 pm, followed by crystallization.
- the frits are sintered at a temperature range of 800-900 ° C for periods of time between 30 min - 60 min to obtain glass ceramic with different proportions between the amorphous and crystalline fractions, which in turn allow obtaining glass ceramics with varying degrees of bioactivity and mechanical strength.
- the molar percentage of S1O 2 in the bioglass is preferably between 34-50%. If the molar percentage of S1O 2 is less than 34%, crystallization precedes sintering, resulting in a weakly sintered and fragile glass ceramic material. Therefore, the minimum content of S1O 2 is 34%, or preferably 34.1% or more. Likewise, S1O 2 contents greater than 50% decrease sinterability and favor extensive melt crystallization, thus converting the glass ceramic to a bioinert material. Therefore, the maximum S1O 2 content is 50%, or preferably 46.4%.
- a third relevant feature of the present invention relates to the potential uses of bioactive glasses described above in regenerative medicine, preferably in applications related to the prevention and / or treatment of damaged tissues.
- the tissues may be bone tissues, cartilage, soft tissues including ligaments, and dental tissues including calcified dental tissues such as enamel and dentin.
- Damaged or bio-treated tissue disclosed in the invention may be animal tissue, preferably from mammalian or human tissue.
- Bioactive glasses are preferably intended for regenerative medicine applications in humans or animals such as dogs, cats, horses, sheep and goats, swine, cattle, etc.
- the bioactive glasses disclosed in the present invention are for the prevention and treatment of tissues.
- tissue damage may result from accidents, or from diseases such as arthrosis, periodontal lesions, filling in bone defects resulting from the removal of tumors such as osteosarcoma, etc.
- bioactive glasses disclosed in the present invention enables the repair and reconstruction of damaged tissues.
- immersion of bioactive glass in physiological fluid has been found to result in the formation of an HCA layer at the required site and activation of tissue regeneration mechanisms in vivo.
- bioactive glass to bone defects stimulates the deposition of HCA on the bioglass surface and surrounding tissues.
- the bioactive glasses disclosed in the present invention have the ability to repair damaged tissues by promoting HCA deposition and thus stimulating regeneration of damaged tissues.
- Bioactive glasses disclosed within the scope of the present invention have a particular feature that they can be used in vertebroplasty and percutaneous kyphoplasty, two minimally invasive intervention techniques used to treat painful vertebral compressive fractures.
- Bioactive glasses can be incorporated into polymeric cements, usually based on polymethyl methacrylate, or calcium phosphate based cements, and injected into the vertebral spaces to prevent the effects of osteoporosis, restore vertebra height and prevent spinal curvature vertebral.
- Bioactive glasses disclosed within the scope of the present invention may also be used in the treatment of damaged dental cavity tissues, preferably in the treatment of periodontal diseases. Bioactive glasses are particularly used to promote rapid deposition of HCA and the formation of new bone at sites where periodontal disease has resulted in the destruction of the bone supporting the tooth. In addition, the same bioactive glasses may be used in the treatment of dental caries. This particular application will benefit from the high levels of fluoride in saliva given the known effectiveness of this element in preventing / treating caries. Bioactive glasses disclosed within the scope of the present invention may further be used as cariostatic agents and inhibitors of tooth demineralization.
- Fluoride released from the bioactive glasses disclosed within the scope of the present invention may precipitate on the tooth surface and form a calcium fluoride-like layer which serves as a fluorine reservoir when pH is low.
- This calcium fluoride-type material called soluble KOH-fluoride, facilitates the precipitation of minerals by forming fluoroapatite or fluorohydroxyapatite, thereby preventing loss of mineral ions.
- Such bioactive glasses may, for example, be incorporated into toothpaste, chewing gum, toothpaste or oral care products.
- bioactive glasses disclosed within the scope of the present invention results in a local increase in pH due to physicochemical reactions taking place on the surface of the glasses. Bacteria found on the surface of human skin that multiply under acidic conditions are inhibited by the alkaline conditions produced by the bioglass. Thus, bioactive glasses disclosed within the scope of the present invention contribute to the prevention and / or treatment of bacteriological infections associated with damaged tissues.
- the fourth relevant feature of the present invention is to provide implant coating materials comprising the bioactive glasses described above.
- the coatings can be used to coat metal components to be implanted into the body, thus combining the excellent mechanical strength of implant materials, namely metals and alloys such as Ti6A14V and cobalt chromium alloys, polymers and ceramics, and the biocompatibility of the materials.
- bioactive glasses can be applied to metal implants by various methods including but not limited to: glazing, flame thermal spraying, plasma thermal spraying, rapid immersion in molten glass, immersion in a suspension of glass particles dispersed in a solvent with a polymeric binder, or electrophoretic deposition.
- Bioactive coatings allow the formation of an HCA layer on the surface of the prosthesis that supports bone growth and osteointegration. This allows the formation of an interfacial layer between the implant surface and the surrounding tissue.
- the prosthesis provides a preferred means of replacing a bone or articulated joint such as for example in the shoulder, elbow, hip, knee, or jaw.
- the prosthesis referred to in the present invention may be used in replacement surgeries of the respective damaged joints in order to restore lost functionality.
- Bioactive glasses disclosed within the scope of the present invention may also be used to coat orthopedic devices such as femoral components of total hip arthroplasties, bone fracture fixation screws or pins.
- a particularly relevant feature of the present invention is that it provides porous and bioactive carrier materials comprising the bioactive glasses described above.
- Porous and bioactive support materials are preferably used in tissue engineering. They can be used in in vitro synthesis of bone tissue when in the presence of a cell-inoculated culture medium.
- the bioactivity of porous supports allows the formation of a strong interface between bone tissue and the porous support, and induces osteoblast proliferation.
- bone tissue formed on the bioactive porous supports may be inserted into areas that present a higher risk of fracture, and the potential for decreased or null bone tissue formation.
- the formed bone tissue may be used to replace damaged or diseased bone tissue.
- the coefficient of thermal expansion (CTE) of the glasses was obtained by dilatometry using prismatic samples with a cross section of 45 mm (Bahr Thermo Analyze DIL 801 L, Hullhorst, Germany; heating rate 5 K min -1 ).
- the sintering behavior of glasses was studied by heating microscopy (HSM) using powders with particle sizes between 5-20 pm.
- HSM heating microscopy
- the image analyzer takes into account the thermal expansion of the alumina substrate while measuring the sample height during heating, taking the base as a reference.
- HSM software calculates the percentage change in height, width and sample area from images. The measurements were made in air atmosphere at a heating speed of 5 K min -1 . Cylindrical samples with a height and diameter of approximately 3 mm were prepared by dry pressing of the starting powders.
- the cylindrical samples were placed on an alumina support (> 99.5 wt.% AI 2 O 3 ) with dimensions of 10 ⁇ 15 ⁇ 1 mm.
- the temperature was measured with a Pt / Rh (6/30) thermocouple in contact with the alumina support.
- the in vitro bioactivity of the glasses reflected in their ability to induce the formation of an HCA layer on their surfaces, was investigated by immersing the glass powders in a 37 ° C SBF solution.
- the SBF solution was prepared with the following ionic concentrations (Na + 142.0, K + 5.0, Ca 2+ 2.5, Mg 2+ 1.5, Cl ⁇ 125.0, HPO 4 ⁇ 1.0 , HCC> 3 27.0 ⁇ 2, S0 4 2 1 _1 ⁇ 0.5 mmol) approximately equivalent to human plasma as reported by Tas [Biomaterials 21 (2000) 1429-1438].
- a glass designated as y TCP-40 'having the composition 45.08 CaO - 14.72 MgO - 10.12 P 2 0 5 - 29, 45 Si0 2 - 0.63 CaF 2 (mol.%) was prepared by melting. mixing of the raw materials, in particular of high purity Si0 2 , CaCC> 3, MgCC> 3, NH 4 H 2 P0 4 and CaF 2 powders. The raw material mixture was homogenized by dry milling, calcined at 900 ° C for 1h, and then melted in platinum crucible at 1590 ° C for 1h. The fried glass was obtained by rapidly cooling the melt in cold water. The frit was then ground in a planetary agate vat mill, resulting in a fine glass powder with particle sizes between 5-20 ⁇ . The amorphous nature of the glass was confirmed by XRD analysis.
- the glasses of the compositions shown in Table 2 were melted, fried and ground to particle sizes between 5-20 ⁇ as described in Examples 1 and 2.
- the amorphous nature of the glass was confirmed by XRD analysis.
- the sintered glass ceramic bodies have been shown to have good in vitro biomineralization capacity after 3 days of immersion in SBF solution by forming a layer of HCA on its surface.
- Example 4 Glasses containing B 2 0 3 and Na 2 0
- the glasses of the compositions shown in Table 2 were melted, fried and ground to particle sizes between 5-20 ⁇ as described in Examples 1 to 3.
- the amorphous nature of the glass was confirmed by XRD analysis.
- both glasses showed evidence of the deposition of a layer of HCA on the surface of the particles after 24 hours of immersion in SBF solution, whose intensities of characteristic peaks gradually increased with the time of immersion.
- Example 5 Sol-gel glasses with bactericidal activity
- SG-BG and SG-AgBG bio-glasses were prepared by sol-gel (SG) and aimed to evaluate the bactericidal properties of the composition SG-AgBG containing silver oxide. All precursors were supplied by Aldrich. TEOS was prehydrolyzed for 1 h in a 0.1 M nitric acid solution. To this solution was then successively added triethylphosphate (TEP), calcium nitrate, and silver nitrate, with a 45 min interval between each addition to promote complete hydrolysis. SG-AgBG samples were handled and kept in the dark to preserve the oxidation state +1 of the silver ion. The silver-free bio-glass SG-BG was prepared identically.
- SG-P35 and SG-P36 bio glasses were prepared by sol-gel (SG).
- TEOS was prehydrolyzed for 1 h in a 0.1 M solution of nitric acid.
- Calcium nitrate Ca (N03) 2 ⁇ 4H 2 0 was also dissolved in this solution.
- a solution of diammonium phosphate, (NH 4 ) 2 HPO 4 prepared in distilled water was then added together with nitric acid to adjust the pH between 3-4.
- the obtained sun was aged and dried following a procedure similar to that reported in example 5. The dried powders were then calcined at 800 ° C resulting in amorphous material and tricalcium beta-phosphate.
Abstract
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BR112013025742A2 (pt) | 2017-06-20 |
US9238044B2 (en) | 2016-01-19 |
BR112013025742A8 (pt) | 2019-01-22 |
JP2014512325A (ja) | 2014-05-22 |
US20140193499A1 (en) | 2014-07-10 |
CA2832418A1 (en) | 2012-10-11 |
PT2695623T (pt) | 2020-06-26 |
PT105617A (pt) | 2012-10-08 |
EP2695623A1 (en) | 2014-02-12 |
EP2695623B1 (en) | 2020-05-06 |
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