Hydrophilic non-woven nanofiber membrane to promote bone regeneration (Machine-translation by Google

专利摘要:
Hydrophilic nonwoven nanofiber membrane to promote bone regeneration. The invention refers to a hydrophilic nonwoven nanofiber membrane based on acrylate and methacrylate copolymers and its preparation process. Furthermore, the invention refers to its hydrolyzed form, additionally functionalized with a divalent cation selected from Zn+2, Cat+2 Mg+2 and Sr+2, an antibacterial agent, and any combination thereof. Furthermore, the invention refers to a non-resorbable membrane to promote bone regeneration and a non-resorbable periodontal membrane comprising said hydrophilic non-woven nanofiber membrane, its hydrolyzed form or its hydrolyzed form additionally functionalized with a divalent cation selected from Zn+2, Ca+2, Mg+2 and Sr+2, an antibacterial agent and any of the combinations thereof. (Machine-translation by Google Translate, not legally binding)
公开号:ES2791771A1
申请号:ES201930393
申请日:2019-05-03
公开日:2020-11-05
发明作者:Pérez Manuel Toledano；Ruiz Raquel Osorio；Castillo Antonio Luis Medina
申请人:Nanomateriales Y Polimeros S L；Universidad de Granada；
IPC主号:

专利说明:

[0002] Hydrophilic non-woven nanofiber membrane to promote bone regeneration
[0004] The invention refers to a hydrophilic nonwoven nanofiber membrane based on acrylate and methacrylate copolymers and its preparation process. Furthermore, the invention refers to its hydrolyzed form, additionally functionalized with a divalent cation selected from Zn + 2, Ca + 2, Mg + 2 and Sr + 2, an antibacterial agent and any of the combinations thereof. Furthermore, the invention refers to a non-resorbable membrane to promote bone regeneration and a non-resorbable periodontal membrane comprising said hydrophilic non-woven nanofiber membrane, its hydrolyzed form or its hydrolyzed form additionally functionalized with a divalent cation selected from Zn + 2, Ca + 2, Mg + 2, and Sr + 2, an antibacterial agent, and any combination thereof.
[0006] State of the art
[0008] The use of dental implants has become a very widespread and predictable treatment modality for the restoration of teeth that have been lost and for various cases of edentulism. It is evident that the use of a regenerative technique with the placement of a dental implant is an important step that helps in the process of bone regeneration. Because the clinical success of implant therapy is based on osseointegration, defined as the direct anchoring of the implant in bone tissue without the interposition of fibrous tissue, considerable research has been done to promote bone growth.
[0010] The basic principle of Guided Bone Regeneration (ROG) involves the placement of mechanical barriers to protect blood clots and to isolate the bone defect from the surrounding connective tissue, thereby providing bone-forming cells with access to an isolated space for bone regeneration. ROG has, in many cases, an unpredictable clinical outcome and remains challenging. Successful bone regeneration requires: I) primary wound closure to promote undisturbed and uninterrupted healing, II) angiogenesis to provide the necessary supply of blood and undifferentiated mesenchymal cells, III) space creation and maintenance to facilitate space for the growing bone and IV) wound stability to induce blood clot formation and allow for uneventful healing. It is usually obtained through the use of barrier membranes that are placed after surgery. There are two types of membranes based on their reabsorption characteristics.
[0012] The use of resorbable tissue engineering matrices to induce bone formation, when additional support is needed, is not always successful. An important limitation of resorbable materials is the inability to exert spatio-temporal control over the wound healing process. Most of the absorbable membranes used (eg, collagen, polylactic-co-glycolic, polycaprolactone) and bone graft substitutes (eg, hydroxyapatite-HAp and other calcium phosphates) show a relatively rapid rate of biodegradation. It should be taken into account that the healing period of the alveolar bone, after periodontal regeneration or after extraction, usually takes 6 to 12 months. Currently, the absorbable materials used have several disadvantages, since their dissolution behavior is not as durable as required. Furthermore, some degradation products of these resorbable materials have a low pH, may not be cytocompatible and could also alter the remineralization processes [Ivanovski S, Vaquette C, Gronthos S, Hutmacher DW, Bartold PM (2014) Multiphasic Scaffolds for Periodontal Tissue Engineering. J Dent Res 93 (12): 1212-1221] [Shimauchi H, Nemoto E, Ishihata H, Shimomura M (2013) Possible functional scaffolds for periodontal regeneration. Japan Dent Sci Rev 49: 118-130].
[0014] Although much research is being done on resorbable periodontal membranes, synthetic non-resorbable polytetrafluoroethylene (PTFE) membranes still represent the gold standard for clinicians, due to the greater predictability of their effects compared to resorbable membranes. However, PTFE has significant disadvantages: I) low adhesion to cells, II) total absence of the ability to connect to bone tissue and provide osseointegration, without the formation of an intermediate layer of connective tissue; a second surgery is necessary to remove the non-integrated membrane, and finally III) lack of antibacterial properties, with frequent infections [Sam G, Pillai BRM (2014) Evolution of Barrier Membranes in Periodontal Regeneration-Are the third Generation Membranes J of Clin Diagn Res 8: 14-17], Therefore the ideal membrane for ROG should resemble the morphology of natural bone. Natural bone is a hybrid of inorganic-organic tissue composed of hydroxyapatite nanocrystals and collagen fibers (with diameters that range from 50 to 500 nm) assembled in a porous mesh, with interconnected pores. Bone is nanostructured, so nanomaterials should be the best choice for bone substitutes.
[0016] For the reasons stated above, the development of new membranes suitable for bone regeneration is necessary.
[0018] Description of the invention
[0020] A first aspect of the present invention refers to a hydrophilic nonwoven nanofiber membrane (herein "the membrane of the invention") characterized in that it comprises a mixture of:
[0021] ^or a first copolymer of (MA) ³ -co- (HEA ^{) 2} with statistical topology in a percentage by weight between 35% and 65%; Y
[0022] ^or a second copolymer of (MMA) ¹ -co- (HEMA ^{) 1} in a percentage by weight between 35% and 65%.
[0024] The term "hydrophilic non-woven nanofiber membrane" refers to a membrane made up of long fibers that have a diameter between 150 nm and 400 nm. Said membranes are non-woven, this means that they are like a felt, that they are not woven or knitted: they are made from long fibers (continuous length), joined together by chemical, mechanical, thermal or solvent treatment, and are hydrophilic.
[0026] Ideally, each needle produces a single fiber that is wound on the drum from the beginning to the end of the electrospinning process (kilometer). The reality is that fibers are cut intermittently throughout the electrospinning process.
[0028] The term "copolymer with statistical topology" refers to statistical copolymers, that is, a copolymer in which the distribution of the monomers in the chain is random since all the monomers present in the solution have the same affinity / probability of reacting both with monomers of the same chemical nature (with themselves) and with monomers of a different chemical nature.
[0030] In a preferred embodiment of the membrane of the invention, it comprises a mixture of:
[0031] ^or a first copolymer of (MA) 3-co- (HEA) 2 with statistical topology at 50% by weight; Y
[0032] ^or a second copolymer of (MMA) i-co- (HEMA) i in 50% by weight.
[0033] Said membrane shows resistance to abrasion, flexibility, elasticity, resistance to mechanical stress, and therefore can be easily manipulated; it can be cut, bent and twisted.
[0034] One of the most important parameters in the electrospinning process is the molecular weight of the polymer. Generally, a higher molecular weight is preferred as it promotes entanglement between larger chains by facilitating fiber formation during spinning. In contrast, a lower molecular weight can lead to bead-forming droplets or beads combined with short fibers, resulting in heterogeneous materials with unwanted physical properties: uneven surface, low specific surface, low resistance to abrasion and stress. mechanical, loss of elasticity.
[0035] In another preferred embodiment of the membrane of the invention, the first copolymer of (MA) ³ -co- (HEA ^{) 2} has a molecular weight above 50,000 Da and 3-106 Da. More preferably, the first copolymer of (MA) ³ -co- (HEA ^{) 2} has a molecular weight between 1-106 Da and 3-106 Da. In another preferred embodiment of the membrane of the invention, the second copolymer of (MMA) ¹ -co- (HEMA ^{) 1} has a molecular weight between 50,000 Da and 1-106 Da.
[0036] In another preferred embodiment of the membrane of the invention, the membrane further comprises SiO ² nanoparticles (NPs-SiC ² ), and said SiO ² nanoparticles are:
[0037] • homogeneously dispersed in the membrane, that is, homogeneously trapped in the complete volume of fibers forming a solid solution (composite material) and / or
[0038] • physically adsorbed on the membrane surface,
[0039] in a percentage by weight between 0.1% and 60% with respect to the final weight of the membrane.
[0040] In the present invention the term "SiO ² nanoparticles" refers to particles of sizes between 1 nm and> 100 nm, preferably sizes between 1 nm and 100 nm, more preferably between 1 nm and 30 nm.
[0041] Silicon dioxide (SiO ² ) can improve not only the bioactivity of materials, but also adhesion and cell proliferation in artificial tissues, facilitating the differentiation of osteogenic cells. SiO ² is considered to be osteoinductive and a catalyst for bone formation. Therefore, to improve the bioactivity of the membranes, they were doped with SiO ² nanoparticles.
[0042] The SiO ² nanoparticles (NPs-SiO ² ) can be introduced into the membranes in two ways: 1) by suspending them in the electrospinning solution, and then carrying out the electrospinning process. In this case, the NPs-SiO ² are trapped homogeneously in the entire volume of fibers, forming a solid solution (composite material):
[0043] 2) by physical adsorption on the surface of the fibers once the membrane has been manufactured: the membrane is impregnated with a suspension of NPs-SiO ² , and then the water is evaporated.
[0044] Option (1) is preferred because NPs-SiO ² are retained in the fibers more efficiently and their leaching is minimized; with option (1) the NPs-SiO ² can remain on the membrane for longer than with (2).
[0045] A second aspect of the present invention refers to a process for preparing the membrane of the present invention (herein "the process of the invention") that includes the preparation of the copolymers that are subjected to electrospun to produce said membrane. The copolymers of the present invention can be prepared by conventional radical polymerization or by metal catalyzed living radical polymerization (MC-LRP) such as: normal atom transfer radical polymerization (normal ATRP), reverse atom transfer radical polymerization (ATRP) reverse) and atom transfer radical polymerization generated by electron transfer (AGET ATRP).
[0046] In a preferred embodiment of the process of the invention, the process is characterized in that it comprises the following steps:
[0047] a) synthesis of the first copolymer of (MA) ³ -co- (HEA ^{) 2} with statistical topology by metal-catalyzed living radical polymerization, using a metallic catalytic system;
[0048] b) synthesis of the second copolymer of (MMA) i-co- (HEMA) i by radical polymerization by reverse atom transfer using a metal catalyst system;
[0049] c) preparation by electrospinning of a nanofiber membrane comprising a mixture, wherein said mixture comprises the first copolymer obtained in step (a) and the second copolymer obtained in step (b), and
[0050] d) heat treatment of the nanofiber membrane obtained in step (c), where the heat treatment is applied in the form of hot water in a temperature range between 30 ° C and 80 ° C, for example for at least 4 hours , and wherein the nanofiber membrane in step (c) is kept tensioned by a mount.
[0052] Step (a) of the process of the invention refers herein to the synthesis of the first copolymer of (MA) ³ -co- (HEA ^{) 2} by metal-catalyzed living radical polymerization, using a metal catalytic system and the step (b) refers to the synthesis of the second copolymer of (MMA) i-co- (HEMA) i by radical polymerization by reverse atom transfer, using a metallic catalytic system.
[0054] The term "metal catalyzed living radical polymerization" refers to polymerization methods based on establishing a rapid dynamic equilibrium between a minimal amount of growing radicals and a large majority of latent species, in which a metal complex in a low oxidation state acts as the catalyst.
[0056] The term "radical reverse atom transfer polymerization" refers to polymerization methods based on establishing a rapid dynamic equilibrium between a minimal amount of growing radicals and a large majority of latent species, in which a metal complex in the state of Low oxidation acts as a catalyst, where the latent species are alkyl halides, and the reaction is initiated by a conventional radical initiator and a Cu2 + complex.
[0058] In the present invention the term "metal catalyst system" refers to the catalyst used in the metal catalyzed living radical polymerization of step (a) and to the catalyst used in the reverse atom transfer radical polymerization of step (b). Said metallic catalytic system comprises a metal, a ligand and an initiator and uses a particular solvent. Preferably, the metal catalyst system of step (a) and step (b) is an amino complex of copper.
[0060] Preferably, the metal of the metal catalyst system of step (a) and / or step (b) comprises a transition metal or a mixture of transition metals in different oxidation states. More preferably, the metal of the metal catalyst system of step (a) and the Step (b) is independently selected from the list consisting of Cu, Fe, Co, Ni, Ru, Pl, Rh, Re, Cr, and Mo.
[0061] Preferably, said metal of the metal catalytic system of stage (a) and / or stage (b) has a percentage by weight comprised between 0.00001% and 0.1%.
[0062] Preferably, the ligand of the metal catalyst system of step (a) and / or step (b) is a multidentate aliphatic amine that can be linear or branched. More preferably, the metal catalyst system ligand of step (a) and step (b) is independently selected from the list consisting of N, N, N ', N ", N" -pentamethyldiethylenetriamine (PMDETA) tris (2 -pyridylmethyl) amine, tris [2- (dimethylamino) ethyl] amine, 2,2'-bipyridyl, N, N, N ', N'-tetrakis (2-pyridylmethyl) ethylenediamine and 1,1,4,7,10 , 10-hexamethyltriethylenetetramine.
[0063] Preferably, said ligand has a percentage by weight between 0.0001% and 0.2%.
[0064] It should be mentioned that the initiator of step (a) and step (b) are preferably different.
[0065] Preferably, the initiator of the metal catalyst system of step (a) is independently selected from the list consisting of dodecyl 2-bromoisobutyrate, ethyl α-bromoisobutyrate, ethyl α-bromoisobutyrate, octadecyl 2-bromoisobutyrate, α-bromoisobutyrate methyl, methyl 3-bromopropionate, tert-butyl 3-bromopropionate, ethyl 2-bromopropionate.
[0066] Preferably, the initiator of step (b) is independently selected from the list consisting of 1,1'azo-bs (cyclohexanecarbonitrile) (ACHN), 2,2'-2,2'-azo-bis dihydrochloride (2-methylpropionamidine) (AAPH), 4,4'-azo-bis (4-cyanovaleric acid) (ACVA), tert-butyl hydroperoxide, cumene hydroperoxide, 2,5-di (tert-butyl peroxide) -2, 5-dimethyl-3-hexene, dicumyl peroxide, and 2,5-bis (tert-butylperoxide) -2,5-dimethylhexane.
[0067] The percentage by weight of the initiator in stage (a) and stage (b) is between 0.00001% and 0.2%.
[0068] Preferably, the solvent used with the metal catalyst system of step (a) and step (b) is independently selected from the list consisting of acetone, dimethylformamide, poly (ethylene glycol), dimethylsulfoxide, 1-4 dioxane, ethanol, propanol , hexane, water, carbon dioxide, ionic liquid, and a combination thereof.
[0069] The percentage by weight of the solvent in stage (a) and stage (b) is below 90%; preferably the weight percent of the solvent in step (a) and step (b) is between 40% and 60%.
[0070] In another preferred embodiment of the present invention, the metal catalyst system of step (a) and step (b) does not use any solvent. In other words, step (a) and step (b) are carried out without solvent since the monomers are liquid and miscible with each other.
[0071] In a preferred embodiment of the process of the present invention, the metal catalyst system of step (a) uses Cu ° / Cu2 + as the transition metal, tris (2-dimethylaminoethyl) amine as the ligand, methyl 2-bromopropionate as the initiator, and dimethylsulfoxide as a solvent.
[0072] Stage (c) of the process of the invention refers to the preparation by electrospinning of a nanofiber membrane comprising a mixture, where said mixture comprises the first copolymer obtained in stage (a) and the second copolymer obtained in stage ( b). Preferably, step (c) is carried out in the presence of an additive capable of increasing the conductivity of the mixed / solvent solution. More preferably, in the presence of hydrochloric acid (HCl), where the weight percent of HCl in step (c) is between 0.0001% and 0.2%.
[0074] The solvent of step (c) is selected from the list consisting of acetone, dimethylformamide, poly (ethylene glycol), dimethylsulfoxide, 1-4 dioxane, ethanol, propanol, hexane, water, carbon dioxide, ionic liquid, and a combination thereof. More preferably, the solvent in step (c) is dimethylsulfoxide.
[0076] Preferably, the percentage by weight of the solvent used in step (c) is in a range between 20% and 98%.
[0078] Stage (d) refers to a heat treatment of the nanofiber membrane obtained in stage (c), where the heat treatment is applied in the form of hot water in a temperature range between 30 ° C and 80 ° C and wherein the nanofiber membrane obtained in step (c) is kept under tension by means of a mount. The purpose of this step (d) is to convert the nanofiber membrane obtained in step (c) from hydrophobic to hydrophilic; A visual transformation of the membrane is observed when the wet heat treatment of step (d) is performed for at least 4 hours. Please note that the membrane remains hydrophilic for days, and even years.
[0080] A third aspect of the invention refers to a process for preparing the hydrophilic membrane of nonwoven nanofibers that comprises SiO ² nanoparticles, wherein said SiO ² nanoparticles are homogeneously dispersed in the membrane, characterized in that it comprises all the stages of invention process:
[0081] a) synthesis of the first copolymer of (MA) ³ -co- (HEA ^{) 2} by metal-catalyzed living radical polymerization, using a metal catalyst system;
[0082] b) synthesis of the second copolymer of (MMA) i-co- (HEMA) i by radical polymerization by reverse atom transfer using a metal catalyst system;
[0083] c) preparation by electrospinning of a nanofiber membrane comprising a mixture, wherein said mixture comprises the first copolymer obtained in step (a) and the second copolymer obtained in step (b), and
[0084] d) heat treatment of the nanofiber membrane obtained in step (c), where the heat treatment is applied in the form of hot water in a temperature range between 30 ° C and 80 ° C, for example for at least 4 hours , and wherein the nanofiber membrane in step (c) is kept tensioned by a mount.
[0086] and wherein the mixture of step (c) comprises SiO ² nanoparticles.
[0088] Another aspect of the invention refers to a process for preparing the hydrophilic nonwoven nanofiber membrane comprising SiO ² nanoparticles, wherein said SiO ² nanoparticles are physically adsorbed, characterized in that it comprises all the stages of the process of the invention :
[0089] a) synthesis of the first copolymer of (MA) ³ -co- (HEA ^{) 2} by metal-catalyzed living radical polymerization, using a metal catalyst system;
[0090] b) synthesis of the second copolymer of (MMA) i-co- (HEMA) i by radical polymerization by reverse atom transfer using a metal catalyst system;
[0091] c) preparation by electrospinning of a nanofiber membrane comprising a mixture, where said mixture comprises the first copolymer obtained in step (a) and the second copolymer obtained in step (b) and optionally comprises SiO ² nanoparticles, and
[0092] d) heat treatment of the nanofiber membrane obtained in step (c), where the heat treatment is applied in the form of hot water in a temperature range between 30 ° C and 80 ° C, for example for at least 4 hours , and wherein the nanofiber membrane in step (c) is kept tensioned by a mount.
[0094] and a further step (e) of impregnating the membrane obtained in step (d) in a suspension of NPs-SiO ² and evaporating the solvent.
[0096] Another aspect of the invention refers to a hydrophilic nonwoven nanofiber membrane hydrolyzed (in the present specification, the hydrolyzed membrane of the present invention), characterized in that it comprises the hydrophilic nonwoven nanofiber membrane comprising carboxyl groups, wherein the The concentration of carboxyl groups in the membrane is in a range between 20 pmol / g of the membrane and 3000 pmol / g of the membrane.
[0097] The term "hydrolyzed nonwoven nanofiber hydrophilic membrane" refers herein to the aforementioned hydrophilic nonwoven nanofiber membrane which has been partially hydrolyzed and now comprises carboxyl groups (COOH) and then partially dried at room temperature (18- 28 ° C). The number of accessible COOH groups in the membrane is in a range between 20 pmol / g of the membrane and 3000 pmol / g of the membrane. It was observed that a hydrolysis time greater than 1 hour, produced a high rigidity in the membranes, making them brittle and brittle.
[0099] In a preferred embodiment of the hydrolyzed membrane of the present invention, said membrane is functionalized with a divalent cation selected from Zn + 2, Ca + 2, Mg + 2 and Sr + 2, an antibacterial agent and / or any of the combinations of the same. More preferably, the hydrophilic nonwoven nanofiber membrane is functionalized with Zn + 2, Ca + 2, and doxycycline.
[0101] The functionalization of the hydrolyzed membrane of the present invention with a divalent cation selected from Zn + 2, Ca + 2, Mg + 2 and Sr + 2 comprises a step of impregnating the hydrolyzate with a solution of a divalent cation selected from Zn + 2 , Ca + 2, Mg + 2 and Sr + 2, and a drying step at room temperature (18-28 ° C).
[0103] The functionalization of the hydrolyzed membrane of the present invention with a bacterial agent, more preferably doxycycline, comprises a step of impregnating the hydrolyzate with a solution of an antibacterial agent and a step of drying at room temperature (18-28 ° C).
[0105] According to the accessible COOH groups in the hydrolyzed nonwoven nanofiber hydrophilic membrane, the concentration of Ca2 + and Zn2 + charged on the membrane as (COO ') ² is in a range between 0.0125 pmol / g membrane and 1500 pmol / g of the membrane. A concentration of calcium and zinc higher than 1500 pmol / g of the membrane can be loaded onto the hydrophilic hydrolyzed nonwoven nanofiber membrane, when all accessible COOH groups are coordinated. The excess of Zn2 + or Ca2 is physically adsorbed on the membrane surface in the form of their respective salts (ZnCL and CaCL) during the drying of the membrane.
[0106] Doxycycline (DOX) was non-covalently bound to the membrane by acid-base interactions between the amino groups of DOX and the carboxyl groups of the membrane, as well as by hydrogen bonding between the hydroxyl groups of the membrane. When all available carboxyl and hydroxyl groups on the membrane are bound to doxycycline, the excess DOX is physically adsorbed on the membrane surface during drying. The DOX concentration is in a range between 0.01 mg / mg of the membrane and 1 mg / mg of the membrane.
[0108] Another aspect of the invention refers to a non-resorbable membrane to promote bone regeneration, characterized in that it comprises the hydrophilic non-woven nanofiber membrane mentioned above.
[0110] Another aspect of the invention refers to a non-resorbable periodontal membrane characterized in that it comprises the hydrophilic non-woven nanofiber membrane mentioned above.
[0112] Resorbable and non-resorbable barrier membranes are commercially available, with the non-resorbable PFTE membranes being the gold standard in guided bone regeneration. The main disadvantage of resorbable membranes is the unpredictable resorption time and the toxic substances released during degradation, which affect bone formation. Among many others, the main disadvantage of non-resorbable barrier membranes is that they do not achieve osseointegration. Furthermore, in the case of the latter membranes, a second surgical intervention is necessary to remove them after regeneration, which can result in injury to the regenerated tissue. Its low efficacy results in a high degree of relapse.
[0114] In the present invention, the non-resorbable membrane of the invention is an innovative bioactive membrane that allows:
[0115] • Complete osseointegration, avoiding the need for a second surgery.
[0117] • Rapid bone regeneration, improving the precipitation of natural minerals and the activation of bone-forming cells. No need to fill with bone precursors.
[0119] • Reduce the proliferation of periodontal bacteria when it contains an antibacterial agent
[0121] The last aspect of the invention refers to a coating for an implant characterized in that it comprises the hydrophilic non-woven nanofiber membrane above that can provide an advantage for its osseointegration. Osseointegration involves direct contact between, for example, a titanium implant and bone. Most of the transcutaneous metal implants have not been successful, mainly due to infections. Transcutaneous titanium alloy implants produce corrosion particles and generally fail due to mechanisms related to surface interaction in the bone, causing inflammation, along with fibrous aseptic loosening or infection that may require removal of the implant. In addition, low oxygen concentrations from poor vascularization at a surface interface with a foreign metal, promotes an increase in host cell-related electrons as in the case of free radicals and protons that can promote infection and inflammation that greatly influence in implant failure. Covering the implant with the hydrophilic non-woven nanofiber membrane mentioned above is an effective way to avoid the risks mentioned.
[0122] Unless defined otherwise, all technical and scientific terms used herein have the same meaning as is commonly understood by one of ordinary skill in the art to which this invention belongs. Methods and materials similar or equivalent to those described herein may be used in the practice of the present invention. Throughout the description and claims, the term "comprise" and its variations are not intended to exclude other technical features, additives, components, or steps. Additional objects, advantages, and features of the present invention will become apparent to those skilled in the art upon analysis of the description, or may be learned by practice of the invention. The following examples and drawings are provided by way of illustration and are not intended to limit the present invention.
[0123] Brief description of the drawings
[0124] FIG. 1. Theoretical modeling of the copolymerization of MA and HEA, Fa vs the conversion of (A) and Fa vs fa (B).
[0125] FIG. 2. Chromatographic profile of HEA / MA-10/90 (A), HEA / MA-15/85 (B), HEA / MA-25/75 (C), HEA / MA-35/65 (D), HEA / MA-45/55 (E).
[0126] FIG. 3. H1RMN spectra of HEA / MA-10/90 (A), HEA / MA-15/85 (B), HEA / MA-25/75 (C), HEA / MA-35/75 (D).
[0127] FIG. 4. Theoretical modeling of the copolymerization of MMA and HEMA, Fa vs conversion (A) and Fa vs fa (B).
[0128] FIG. 5. Chromatographic profile of MMA-co-HEMA (A), and H1RMN spectra of MMA-co-HEMA (B).
[0129] FIG. 6. Schematic of the electrospinning system: injection pump (1), injection needle (2), collecting drum (3), high voltage sources (4), Taylor cone (5) and mechanical axis with transverse displacement (6 ).
[0130] FIG. 7. Non-woven membrane produced with the blends: (A) / (B) 0: 100 (A), 100: 0 (B), 25:75 (C), 50:50 (D), 75:25 (E ).
[0131] FIG. 8. Non-woven membrane produced with mixture (A) / (B) 75:25 (A), and with mixture (A) / (B) 50:50 (B).
[0132] FIG. 9. Tiss-OH before (A) and after heating (B).
[0133] FIG. 10. Connective collagen network (A), and nanofiber non-woven membrane (Tiss-OH) (B). FIG. 11. FESEM micrographs of membranes after 7 days immersion in SBFS; TissHYD (A), Tiss-Ca2 + (B), Tiss-Zn2 + (C).
[0134] FIG. 12. Bone histomorphometry obtained after using Tiss-Zn2 +, by silver nitrate staining (von Kossa stain) to visualize mineralized bone, at six weeks of follow-up: histology section including the bone defect and the region of interest (ROI ) showing a large dense bone formation (A). Total area (TS) in ROIs; the asterisks (*) show the presence of medullary and adipose tissue (B); they look themselves Bone Junction Imaging (BB). Bone perimeter (BPm) in the ROI (C). Bone thickness (BTh) with measurements plotted in ROIs (D). Osteoid surface (OS), in yellow, in the ROI (E).
[0136] FIG. 13. Bone histomorphometry obtained by silver nitrate staining (von Kossa stain) to visualize mineralized bone, at six weeks of follow-up, after not using any membrane-control (A) and Tiss-Ca2 + (B). Trabecular bone formation was observed along the margin of the calvaric defect (arrow), and within the defect. Mbr: membrane, NB: new bone and OB: old bone (pointers show scattered islands of bone, corresponding to new bone).
[0138] FIG. 14. Bone histology obtained after using Tiss-Zn2 + (A) and Tiss-Ca2 + (B) membranes by staining with toluidine blue to visualize mineralized bone, at six weeks of healing time. Individual arrows indicate the presence of osteoblasts; double arrows indicate the presence of osteocytes; facing arrows refer to blood vessels; pointers indicate fibrous connective tissue. NB: new bone, Os: osteoid tissue.
[0140] FIG. 15. Field emission scanning electron microscope (FE-SEM) image of F. nucleatum, S. oralis, A. naeslundii, V. parvula, A. actinomycetemcomitans and P. gingivalis grown in vitro as a multi-species biofilm At 12 hours of incubation in PTFE (control) (A), hydroxyapatite (HAp) TissHYD (C), Tiss-Ca2 + (D), Tiss-Zn2 + (E) and Tiss-DOX (F) discs.
[0142] FIG. 16. Number of bacteria [Log CFU / mean biofilm (standard deviation)] of F. nucleatum, S. oralis, A. naeslundii, V. parvula, A. actinomycetemcomitans and P. gingivalis grown in vitro as a multi-species biofilm a 72 hours of incubation, measured by quantitative real-time polymerase chain reaction (qPCR) (N = 3 for each incubation time) on Hydroxyapatite (HAp) (A), PTFE (control) (B) discs, T-COOH (C), Tiss-Ca2 + (D), Tiss-Zn2 + (E) and Tiss-DOX (F).
[0144] Fig. 17. FESEM tissue micrographs after doping with silicon dioxide and immersion in SBFS for 7 days: Tiss-SiO ² -COOH (A), Tiss-SiO ² -Ca2 + (B), Tiss- SiO ² -Zn2 + ( C) and Tiss-SiO2-DOX (D).
[0146] Examples
[0148] 1. Synthesis of copolymers
[0150] 1.1 Preparation of copolymers of ( MA-co-HEA)
[0152] In the present invention, a variant of metal-catalyzed living radical polymerization (MC-LRP) has been optimized: copper-mediated living radical polymerization (Cu ° -MC-LRP) has been optimized to obtain a linear hydrophilic acrylate copolymer ( MA-co-HEA) with statistical topology and with a high molecular weight (above 1x106 Da).
[0154] The Cu ° -LRP system used was: methyl 2-bromopropionate as initiator, tris (2-dimethylaminoethyl) amine as ligand, Copper / Copper (ll) as transition metal: MBP / M6-TREN / Cu ° / BrCu ² , and dimethyl sulfoxide (DMSO) was used as the solvent. The selected monomers were: methyl acrylate (MA), and hydroxyethyl acrylate (HEA).
[0155] First, a theoretical analysis of the copolymerization of MA and HEA was performed using the terminal model [Mayo, FR; Lewis, FMJ Am. Chem Soc. 66, ( 1944), 1594-1601]. The terminal model assumes that radical reactivity only depends on the terminal unit of the growing chain, such that the mole fraction of monomer-a in the copolymer (Fa) depends only on the mole fractions of the monomer ( f ^a and f ^b1 with f ^a + f ^b1 = 1) and the monomer reactivity ratios:
[0160] where r ^a and r ^b are the copolymerization reactivity ratios r ^a = kp ^aa / kp ^ab , r ^b = kp ^bt / kp ^ba, kp ^¡j is the coefficient of the propagation rate for the addition of monomer j to radical i . The copolymerization reactivity ratios for MA and HEA used are r ^a = 0.94 and r ^b = 0.90 respectively.
[0162] Fig. 1 shows the theoretical modeling of the copolymerization of MA and HEA: F ^a vs the conversion (F ^a is the mole fraction of MA in the copolymer throughout the polymerization) for different initial molar fractions of MA in the feed ( f ^oa ), and F ^a vs f ^a ( f ^a is the mole fraction of MA in the feed throughout the polymerization).
[0164] Theoretical modeling of the copolymerization of MA and HEA shows that F ^a is practically equal to the initial mole fraction of the feed (Fig. 1A) for any initial mole fraction of MA (Fig. 1B). The system undergoes near azeotropic copolymerization at any initial mole fraction of the feed. Therefore, the theoretical copolymerization of MA and HAE provides a copolymer with statistical topology (MA-HEA-MA-HEA-MA-HEA ................).
[0165] Cu ° -LRP is very sensitive to any trace of impurities: mainly the inhibitor that contains both monomers, and the di-acrylates that are formed in the HEA monomer by condensation of the HEA molecules. Thus, in Cu ° -LRP impurities at a very low concentration provide low yields, low molecular weights and a cross-linked polymer, and therefore it is strictly necessary to properly purify the monomers.
[0166] HEA purification protocol:
[0167] 1. First, HEA was purified on a basic alumina column.
[0169] 2. 70 ml of HEA previously purified on a basic alumina column were dissolved in 210 ml of distilled water, and then traces of ethylene glycol diacrylate were removed by 11 liquid-liquid extractions with 210 ml of hexane.
[0171] 3. Then 58 g of NaCl were dissolved in the aqueous HEA solution, and the HEA monomer was extracted by 5 liquid-liquid extractions with 200 ml of diethyl ether.
[0173] 4. The solution of HEA with diethyl ether was dried with 300 g of anhydrous sodium sulfate: the solution was stirred for a few minutes and then filtered to remove the sodium sulfate. 5
[0175] 5. The diethyl ether was then completely evaporated on a rotary evaporator, and the purified HEA was stored at -20 ° C.
[0176] MA purification protocol:
[0177] 1. The required volume of MA was passed through a column of basic alumina.
[0178] Once the monomers were purified, six copolymers of ( MA-co-HEA) _ with different mole% of HEA and MA in the feed were synthesized by Cu ° -LRP. The six different values of mole% of HEA / MA were: a) HEA / MA 10/90 b) HEA / MA 15/85, c) HEA / MA 25/75, d) HEA / MA 34/66, e) HEA / MA 45/55, f) HEA / MA 55/45. Table 1 shows the% by weight of each component in the final polymerization mixture for each mole% HEA / MA.
[0180] Table 1. % by weight of each component in the mixture for each molar% of HEA and MA.
[0182]
[0185] The total mass of monomers (MA HEA) 59.2700 g was added in Schlenk flasks, and then: 59.2700 g of DMSO, 0.0020 g of Cu °, 0.0160 g of tris [2- ( dimethylamino) ethyl] amine (M6-TREN), 0.0012 g of CuBr ² , and 0.0060 g of methyl 2-bromopropionate (MBP). The flasks were closed with a septum stopper, the oxygen was removed by bubbling nitrogen for a few minutes, and then four freeze-vacuum-thaw cycles were performed (after the last freeze-vacuum-thaw cycle the flasks were filled with nitrogen). The sealed flask was then placed in a thermostatic oil bath at 25 ° C for 24h. The copolymers were then purified by dissolving them in acetone and precipitating them in distilled water (twice). After purification the copolymers were dried under vacuum at 80 ° C to constant weight. The copolymers a), b), c), d) had a white color and a rubbery texture, and the final conversion was between 90-95% by weight in all cases. The copolymerization of e) and f) (Table 1) did not take place properly: the yield was below 40%, and the copolymer did not have a rubbery texture. Therefore the optimum mole% range of HEA in the feed was between 10% and 34%.
[0187] The (MA-co-HEA) copolymers were characterized by GPC (Viscotek 270max from Malvern) and H1RMN (Bruker Avance 400 MHz spectrometer). Samples for GPC were prepared by dissolving 1 mg of each copolymer in 10 ml of 1-methyl-2-pyrrolidinone (NMP) and analyzed in triplicate.
[0189] Fig. 2 shows a chromatographic profile of each copolymer, and Table 2 shows the molecular weight (Mw and Mn) and Mw / Mn. Fig. 3 shows the H1RMN spectra of said copolymers.
[0191] Table 2. Molecular weights of each synthesized copolymer.
[0192]
[0194] Table 3 shows the actual mole% HEA in each copolymer: it was calculated by the ratio of the intensity between the signals a (CH ³ of MA) and b (CH ² -CH ² of HEA) of the H ¹ NMR spectra.
[0195] Table 3. Actual mole% HEA in each synthesized copolymer.
[0196]
[0197] H1RMN analysis shows that the HEA concentrations in the copolymers are practically the same as the feed concentrations.
[0199] The solubility of the synthesized acrylate copolymers was tested in acetone, dimethylformamide (DMF), dimethylsulfoxide (DMSO), 1-4 dioxane, and NMP. The copolymers were fully soluble in all the solvents tested up to 6% by weight: above 6%, the viscosity of the solutions was extremely high. The lower viscosity 6% by weight solution was the solution made in DMF, indicating that the DMF solvent is the best solvent for these copolymers.
[0201] To have the maximum concentration of functional groups (OH groups) in the nanofiber nonwoven membrane, the acrylate copolymer selected for the blend formulations was (MA) ³ -co- (HEA) ² (Table 2).
[0203] 1.2 Preparation of MMA-co-HEMA copolymers
[0205] The theoretical modeling of the copolymerization of MMA and HEMA with statistical topology (MMA-HEMA-MMA-HEMA-MMA-HEMA ................) is shown in Fig. 4: Fa vs conversion where Fa is the mole fraction of MMA in the copolymer throughout polymerization, for different initial mole fractions of MMA ( f ^oa ) in the feed, and F ^a vs f ^a where f ^a is the fraction molar MMA in the feed throughout the polymerization.
[0207] The Cu ° -LRP technique used to synthesize the MA-co-HEA copolymers did not work well in the copolymerization of the methacrylic monomers (MMA and HEMA): very low yields and molecular weights were obtained, and also the concentration of HEMA in the copolymers was much lower than the feed concentrations.
[0209] Therefore, to synthesize a chemically miscible methacrylate copolymer with (MA) ³ -co- (HEA) ² , the copolymerization of MMA and HEMA was carried out by another variant of MC-LRP such as radical transfer polymerization of reverse atom (reverse ATRP) [Chem. Rev. 101, ( 2001) , 2921-2990.]: A molecular weight as high as Cu ° -LRP cannot be obtained by reverse ATRP, but reverse ATRP is much less sensitive to impurities, and therefore easier to use. carry out.
[0211] The reverse ATRP system used was: 2,2'-azo-bis (2-methylpropionitrile) (AIBN) as initiator, N, N, N ', N ", N" -pentamethyldiethylenetriamine (PMDETA) as ligand, copper (ll ) as the transition metal, and a dimethylsulfoxide (DMSO) / xylene mixture was used as the solvent. The selected monomers were methyl methacrylate (MMA), and 2-hydroxyethylmethacrylate (HEMA).
[0213] MMA v HEMA purification protocol:
[0215] 1. The required volume of MMA and HEMA was passed through a basic alumina column.
[0217] In a two-neck flask equipped with a magnetic stirrer and reflux, the following were added: 95.00 ml of DMSO, 0.14 g of CuBr ² , 0.24 g of N, N, N ', N ", N" - pentamethyldiethylenetriamine (PMDETA), 90.08 g of MMA and 40.12 g of previously purified HEMA, 0.23 g of 2,2'-azobis (2-methylpropionitrile) (AIBN) dissolved in 60.02 g of xylene. The mixture was stirred at 250 rpm, when all components were completely dissolved the reaction mixture was cooled to 0 ° C and purged with high purity nitrogen for 20 min. Then the reaction at 80 ° C in an oil bath for 6 hours. After polymerization, the copolymer was purified by dissolving it in acetone and precipitating it in distilled water three times. Then, the solid copolymer was washed with distilled water 3 times, and dried under vacuum at 80 ° C to constant weight. The methacrylate copolymer had a white color and a hard, brittle texture. The conversion was 70%.
[0219] % by weight of each component in the polymerization mixture: 33,200% DMSO, 0.050% CuBr ² , 0.083% PMDETA, 14.030% HEMA, 31.500% MMA, 0.080% AIBN and 21.000% xylene.
[0221] The MMA-co-HEMA copolymer was characterized by GPC (Viscotek 270 max from Malvern) and by H1RMN (Bruker Avance 400 MHz spectrometer). Samples for GPC were prepared by dissolving 1 mg of copolymers in 10 ml 1-Methyl-2-pyrrolidinone (NMP) and analyzed in triplicate. Fig. 5 shows the chromatographic profile and H1RMN spectrum of the MMA-co-HEMA copolymer.
[0223] Table 4 shows the molecular weights: Mw and Mn and Mw / Mn calculated by GPC.
[0225] Table 4. Molecular weights of MMA-co-HEMA copolymers.
[0227]
[0230] Furthermore, Table 5 shows the actual mole% of HEMA in the copolymer calculated by the intensity of the a (CH ³ of MMA) and b (CH ² -CH ² of HEMA) signals from the 1H-NMR spectra.
[0232] Table 5. Actual mole% of HEMA in the copolymers.
[0234]
[0237] He was tested solubility (MMA) ¹ -CO- ^{(HEMA) 1} in acetone, dimethylformamide (DMF), dimethylsulfoxide (DMSO), 1-4 dioxane and NMP, and the copolymer was completely soluble up to a percentage of 38% in weigh; above 38% the viscosity of the solutions was extremely high. For (MMA) r co- (HEMA ^{) 1} the lower viscosity 38% by weight solution was also the one prepared in DMF solvent, indicating that DMF is also the best solvent for this copolymer.
[0239] 2. Preparation of a nonwoven membrane by electrospinning
[0241] The solubility between the copolymers (MMA) ¹ -co- (HEMA) ¹ ; (A) and (MA) 3-co- (HEA) 2; (B) Tested in acetone, dimethylformamide (DMF), dimethylsulfoxide (DMSO), 1-4 Dioxane, and NMP. The (A) / (B) mass / mass ratios tested were: 10/90, 25/75, 50/50, 75/25 and 90/10, and the ratio ((A) + (B)) / solvent, mass / mass was 3/97 in all cases. Both copolymers were completely soluble, at all ratios. The lower viscosity solutions were the DMF solutions, and therefore DMF was selected as the solvent to optimize the electrospinning process.
[0243] To study and modulate the mechanical properties of nonwoven membranes, the selected (A) / (B) mass / mass mixtures to be processed by electrospinning were: 0/100, 25:75, 50:50, 75:25 and 100 / 0, and the mixture / solvent, mass / mass was 3/97. When the copolymers were completely dissolved, the solutions were loaded into 20 cm3 Teflon syringes (Becton & Dickinson) and extruded through a stainless steel capillary, with external and internal diameters of 1.5 mm and 1.1 mm. , respectively. The injection system was coupled to a mechanical system with axial movement, flow rates and tensions were selected to allow collection of dry fibers from non-woven membranes, and the fibers were collected on a rotating drum collector. Fig. 6 shows a schematic of the electrospinning process system; and Table 6 shows the parameters used in the processing.
[0245] Table 6. Electrospinning process parameters.
[0247]
[0250] Fig. 7 shows an analysis by SEM microscopy of the nonwoven nanofiber membranes obtained with the mixtures (A) / (B) 0: 100 (A), 100: 0 (B), 25:75 (C), 50 : 50 (D), 75:25 (E).
[0252] The pure copolymer (B) provides elastic rubbery materials, in which the fibers are 100% fused together, forming a film (Fig. 7A).
[0254] The nonwoven membranes obtained with pure copolymer (A) did not have any melting point between the fibers, they were completely loose (Fig. 7B), and this provided materials with zero resistance to abrasion; materials that are difficult to handle.
[0255] In the non-woven membranes obtained with the mixture (A) / (B) 25:75 (Fig. 7C), the fusion between the fibers was no longer 100% as in the case of the pure copolymer (B) (Fig. 7A ). but there were still many melting points between the fibers (black circles in Fig. 7C), and for both non-woven membranes with a very low specific surface area and a very high elasticity were obtained.
[0256] Blend (A) / (B) 75:25 (Fig. 7E) gave compact nonwoven membranes with better abrasion resistance than that obtained with neat copolymer (A) (Fig. 7B), but the membranes were not still flexible and exhibited very low tensile strength.
[0257] The (A) / (B) 50:50 mass / mass mixture (named Tiss-OH; Fig. 7D) provided compact non-woven membranes with excellent mechanical properties: very high abrasion resistance, high flexibility, high elasticity, high strength to mechanical stress, and therefore easy to manipulate: it can be cut, bent, twisted, ... etc.
[0258] The low abrasion resistance of the nonwoven membrane produced with the 75:25 blend (A) / (B), compared to the nonwoven membrane produced with the 50:50 blend (A) / (B) is shown in Fig. 8.
[0259] Tiss-OH Electrospinning Scaling Process
[0260] To increase the production of Tiss-OH, the mass / mass mixture / solvent (DMF) ratio was studied. The optimal mix / DMF ratio in% mass / mass was 13.50 / 86.50: above this value the viscosity was too high to be processed by electrospinning.
[0261] To keep the electrospinning process stable over time, it was necessary to increase the conductivity of the mixed / solvent solution by adding 0.048 g of hydrochloric acid (HCl).
[0262] The optimal solution mixture / solvent% mass / mass for the scaling of the electrospinning process was prepared as follows: 5,000 g of (MA) ³ -co- (HEA ^{) 2} (6.246% by weight) and 5,000 g of (MMA) ¹ -co- (HEMA ^{) 1} (6.246% by weight), in 70,000g of DMF (87.4479% by weight), when the copolymers were completely dissolved, 0.048 g of hydrochloric acid (HCI) (0.059 % by weight) to the solution.
[0263] The electrospinning system was the same as that shown in Fig. 6, but to increase production, the single needle injection system of Fig. 6 was replaced by a ten needle head.
[0264] Electrospinning process parameters optimized for a ten needle head are shown in Table 7.
[0265] Table 7. Electrospinning scaling process parameters.
[0267]
[0268]
[0270] The thickness of Tiss-OH was easily controlled from a few microns to hundreds of microns, controlling the processing time (2h processing * 45 pm thickness).
[0271] 2.1. Conversion of Tiss-OH from hydrophobic to hydrophilic
[0272] Tiss-OH is initially hydrophobic; converting it to a hydrophilic material requires additional heat treatment. The heat treatment was carried out by introducing Tiss-OH in a hot water bath (40 ° C) for 5 hours. To avoid shrinkage of the materials during heat treatment, they were kept tensioned using frames.
[0273] The heat treatment produces an irreversible reorientation of the hydrophobic and hydrophilic domains present on the surface of the fibers, which causes the material to go from being completely hydrophobic to being highly hydrophilic: the OH groups of the fibers are rearranged to interact through bonds of hydrogen with the water molecules, while the hydrophobic groups are hidden from the water.
[0274] After heat treatment, the water adsorption capacity (Q) of Tiss-OH was calculated, taking into account the expression:
[0275] Q = (mass of water absorbed) / (mass of dry non-woven membrane)
[0276] Six samples of nonwoven membranes were dried in a vacuum oven at 50 ° C for 2h. They were then immersed in distilled water for 3h at room temperature; water retained on the surface of the samples was removed using cellulose paper. Subsequently, the samples were weighed and the calculated Q was 2.06 ± 0.15.
[0277] Furthermore, to roughly calculate the pore size distribution of Tiss-OH, a vacuum filtration test has been performed using a series of aqueous suspensions of monodisperse hydrophilic nano and microparticles with sizes between 150 nm and 5000 nm in diameter. The Tiss-OH allowed the passage of particles from 800 nm to 3000 nm in diameter.
[0278] The thermal resistance of Tiss-OH was studied by immersing it in water at 100 ° C for 24h. The internal structure, mechanical properties and mass of the Tiss-OH were exactly the same before and after heating (Fig. 9).
[0279] 2.2. Hydrolysis of Tiss-OH to obtain Tiss-HYD
[0280] The natural collagen mesh that forms the connective tissue of bones is composed of nanofibrils of approximately 50 nm that group together to form fibers of approximately 500 nm with morphology, mechanical and physicochemical properties similar to those of Tiss-OH.
[0281] Fig. 10 are SEM images of a connective collagen (A) and Tiss-OH (B) network, showing a very similar morphological structure.
[0283] To introduce carboxyl groups (COOH) on the surface of the fibers, a partial hydrolysis of the ester groups: R-COOCH ³ and RCOOCH ² CH ² OH of the 45 micron thick Tiss-OH membrane was performed (Fig. 7DJ, to obtain TissHYD. The hydrolysis solution was sodium carbonate (333 mM), pH = 12.50. It was observed that a hydrolysis time greater than 1 hour, produced a high rigidity in the membranes, making them brittle and brittle. both the time selected for hydrolysis was 30 min. Therefore, the hydrolysis was carried out by introducing Tiss-OH in a sodium carbonate solution (333 mM), pH = 12.50 for 30 min. Next, the membranes (TissHYD ) were washed 3 times with distilled water and dried at room temperature The number of COOH groups calculated by the toluidine blue O adsorption test (TBO method) according to Biomaterials.14, ( 1993), 817- 822. The assay includes incubation of carboxylated matrices with toluidine blue O in an alkaline buffer with subsequent washing, followed by elution and quantification of eluded TBO by UV-Vis spectrometry. The number of accessible carboxyl groups was 560 ± 50 qmol / g of the membrane. After hydrolysis the calculated Q was 3.06 ± 0.20.
[0285] 2.2. Functionalization of TissHYD with Zn * 2 ( Tiss-Zn2 *) and Ca2 * ( Tiss-Ca2 *)
[0287] TissHYD was functionalized with Zn + 2 (Tiss-Zn2 +) and Ca2 + (Tiss-Ca2 +). The ability of carboxyl groups to complex with divalent cations was used to functionalize TissHYD (Tiss membranes) with Zn + 2 and Ca2 +. TissHYD was impregnated with a solution of Zn2 + and Ca2 +, and then the water was evaporated in vacuo at constant temperature: in this way TissHYD was loaded with 1.1 qg / mg, of Ca2 + and Zn2 +.
[0289] 2.3. Functionalization of TissHYD with doxycycline ( Tiss-DOX)
[0291] Doxycycline (DOX) was non-covalently bound to TissHYD by acid-base interactions between the amino groups of DOX and the carboxyl groups of TissHYD. The TissHYD was impregnated with a DOX solution of twice its mass, of 40 mg / ml, and then the water was evaporated in vacuo at constant temperature: in this way the TissHYD was loaded with 0.8 mg of DOX / mg Tiss .
[0293] 3. CELLULAR STATIC IN VITRO BIOACTIVITY TEST OF TissHYD, Tiss-Zn2 * Tiss-Ca2 *
[0295] The membranes should enhance bone formation through bioactivity, therefore for this application, the analysis proposed by Kokubo (ISO 23317: 2012. Implants for surgery. In vitro evaluation for apatite-forming ability of implant materials) was performed.
[0297] The membranes were soaked in 20 ml of simulated body fluid solution (SBFS ) [H 7.45] in sterile flasks for 7 days. The reagents per 1000 ml of SBFS were: 8.035 g of NaCl, 0.355 g of NaHCO ³ , 0.225 g of KCl, 0.231 g of K ² HPO ⁴ - ³ H ² O, 0.311 g of MgCl ² - ⁶ H ² O, 39 g of 1M HCl, 0.292 g of CaCL, 0.072 g of Na ² SO ⁴ , 118 g of Tris, 0 to 5 ml of 1M HCl for final pH adjustment.
[0299] After drying, the surfaces were analyzed by FESEM at 2.5 Kv, at a working distance of 3.5 mm and elemental analysis was carried out by means of an EDX coupled to the FESEM, at a working distance of 15 mm. The results of the FESEM images of TissHYD, Tiss-Ca2 + and Tiss-Zn2 + after 7 days of immersion in SBFS are presented in Fig. 11.
[0300] After the dive, the differences between the groups were evidenced:
[0302] In TissHYD (Fig. 11 A) some rounded deposits were rarely observed in the samples. Traces of calcium were observed in the EDX spectra.
[0304] In Tiss-Ca2 + (Fig. 11B), an increase in the diameter of the nanofibers was observed, and the nanofibers lost their smooth appearance. A few spots of calcium deposits were evenly distributed over the surface of the nanofibers.
[0306] In Tiss-Zn2 + (Fig. 11C), the diameter of the nanofibers was greatly increased (from 300 to about 500 nm), and the mineral deposits (100 nm) were randomly distributed on the surfaces of the nanofibers.
[0308] Calcium and phosphorus were found in the EDX spectra on the surfaces of the nanofibers. Numerous agglomerations of spherical nanocrystals were identified on the surface of Tiss-Zn2 +. SBFS are fluids with ion concentrations practically equal to those of human blood plasma and are used to evaluate the bioactivity of biomaterials for hard tissue repair. Zinc promoted the biomimetic precipitation of the Ca / P deposits and the formation of Hydroxyapatite nanocrystals (HAp, Ca ¹⁰ (PO ⁴ ) ⁶ (OH) ² ) during its immersion in SBFS. The formation of zincen complexes in the tissues facilitated the binding of phosphate groups. These phosphate groups, on the surface, have infracoordinated oxygens, which leads to the creation of reactive surfaces that will attract calcium ions from SBFS. This biomimetic deposition of Ca / P is considered as a coating method inspired by the natural process of biomineralization. Furthermore, it must be considered that crystalline HAp is very slow to reabsorb, and most HAp-based bone substitutes are either not reabsorbed or are extremely slowly reabsorbed. However, if HAp or nano-HAp precipitates on the surfaces, it is not reabsorbed, facilitating the regeneration of hard tissues. Biomimetic remineralization of the tissues tested will facilitate bone regeneration. HAp facilitates the formation of other materials similar to this bone apatite, such as carbonate-HAp, and is capable of stimulating cells, leading to bone formation. Furthermore, HAp promotes osteoconductivity. Osteoblasts stimulated with extracellular Ca2 + and PO ⁴ 2- increased mRNA expression of bone morphogenetic protein 2. Fibroblast growth factor-2 (FGF-2) and protein expression levels also increased due to Ca2 + concentration. extracellular.
[0310] 4. BONE FORMATION IN DEFAULT MODEL IN RABBIT SHELL
[0312] Three types of membranes were tested, Tiss-Zn2 + (loaded with 1.1 pg (Zn2 +) / mg Tiss), Tiss-Ca2 + (loaded with 1.1 pg (Ca2 +) / mg Tiss) and TissHYD. Naked defects without any type of membrane were used as a control. Six New Zealand breed rabbits with identical characteristics (age: 6 months; weight: 3.5-4 kg) were selected for the study, and were fed daily with the Harlan-Teckland Lab Animal Diets (2030) diet. Surgical interventions were performed at the Jesús Usón minimally invasive surgery center (CCMI, Cáceres, Spain). The experiment was developed in accordance with the guidelines of the US National Institute of Health (NHI) and the European directive 86/609 / EEC regarding the care and use of animals for experimentation. The study also complied with the European directive 2010/63 / EU on the protection of animals used for scientific purposes and with all laws and regulations. The researchers obtained the approval of the Institution's Ethics Committee. As required by the legislative framework, the minimum number of animals per ethical reasons. Models have been published referring to histological and animal experimentation methods.
[0314] Before starting the surgical procedure, vital signs were taken and then the rabbits were immobilized. Midazolam (0.25 mg / kg) and propofol (5 mg / kg) were administered intravenously as anesthesia for induction, and an inspired 2.8% sevoflurane gas inhalation was also used. Ketorolac (1.5 mg / kg) and tramadol (3 mg / kg) analgesia was provided. Once the animals were selected and prepared, incisions with a # 15 scalpel were made between the aces of their ears and between their eyes. A triangular surgical area was made after connecting the two incisions with another in the central line of the skull. The epithelial, connective, and muscular tissues were separated with a Prichard periosteal from the operative area and the surface of the skull was washed with a sterile saline solution. Six non-critical bone defects (diameter: 6 mm; depth: 3 mm) were created in the parietal bone, on each side of the central line of the skull, 3 mm apart, using a trephine (Helmut-Zepf Medical Gmbh, Seitingen, Germany ) mounted on an implant micromotor that operates at 2000 rpm under saline irrigation. The trephine had an external diameter of 6mm, a length of 30mm, and teeth of 2.35mm. Piezoelectric surgery was used to remove the internal table and medullary bone in each defect. The depth was controlled with a periodontal probe. A randomly assigned membrane was used to cover each bone defect, leaving a bare defect in each animal. The randomization sequence was generated using specific software (Research Randomizer, V. 4.0, Urbaniak GC & Plous S, 2013). The membranes were fixed with Tissucol fibrin tissue adhesive (Baxter, Hyland SA Immuno, Rochester, MI, USA), which was placed on the edges of the bone adjacent to the defects. Adequate adhesion and limited mobility of the membranes were confirmed when the fins were moved back to their initial position. Sutures were made in the following planes using resorbable material: periosteal (4/0), sub-epidermal (4/0) and cutaneous (2/0). Simple points were used as close to the edge as possible. The wound was carefully cleaned with a sterile saline solution. Anti-inflammatory analgesia was administered (buprenorphine 0.05 mg / kg and carprofen 1 ml / 12.5 kg). Animals were sacrificed six weeks after surgery using an intravenous overdose of a potassium chloride solution. Skull samples were obtained from each specimen by cutting them in a sagittal anatomical plane. After the mass was removed from the brain and the skull was washed with sterile saline, the tissue samples were individually cut and marked. Cranial block specimens were recovered and stored in 5% formaldehyde solution (pH 7) and blocks were recovered from the regenerated bone defect using an oscillating autopsy saw (Exakt, Kulzer, Wehrheim, Germany). The dissected specimens were immediately immersed in a solution of 4% formaldehyde and 1% calcium and processed for sectioning and ground sectioning following the method of Donath and Bruener. For histological staining and rapid tissue contrast analysis (Merck-Merck Toluidine Blue, Darmstadt, Germany), a metachromatic stain was used to assess the percentage of new bone formation. To visualize mineralized bone, the von Kossa (VK) staining technique with silver nitrate (Sigma-Aldrich Chemical Co., Poole, United Kingdom) was used, using Image J software. The following data were compiled: bone surface (BS), osteoid surface (OS), percentage of osteoid surface (OS / TS), bone perimeter (BPm) and bone thickness (BTh). A 1% toluidine blue (TB) solution with a pH of 3.6 was chosen which was adjusted with 1N HCl. The samples were exposed to staining for 10 minutes at room temperature, rinsed with distilled water, and they were air dried. Osteocytes, osteoblasts and blood vessels were analyzed in sections stained with TB.
[0316] Means and standard deviations (SD) in pixels were calculated and then converted to mm or mm2. A one-way ANOVA and paired samples t-test were applied, with a significance level of p <0.05.
[0317] The implanted membranes were well tolerated by the surrounding soft tissues, without any evidence of necrosis, allergy symptoms, immune reactions, or incompatibility. No specimen showed any sign of inflammation or infection induced by the use of the biomaterials.
[0318] The von Kossa staining technique (VK) made it possible to observe that all bone defects treated with membranes showed greater bone surface area (BS) and bone thickness (BTh) than the control group (Tables 9 and 10). Fig. 12 shows a bone defect with an implanted Tiss-Zn2 + membrane stained with silver nitrate (von Kossa stain) to visualize mineralized bone, at six weeks of follow-up.
[0319] Fig. 12 is a histological section including the bone defect and the region of interest (ROI), showing a large dense bone formation.
[0320] Fig. 12B is the total area (TS) in the ROI; asterisks (*) show the presence of marrow and adipose tissue. Images of the bone junction (BB) are seen.
[0321] In Fig. 12C, the perimeter of the bone (BPm) is observed in the ROI, and in Fig. 12D. bone thickness (BTh) is measured with the measurements plotted on the ROI.
[0322] In Fig. 12E, an osteoid surface (OS) is depicted. It can be seen how the membranes have a higher BTh than the control (Ctr), and therefore produced more osteoid surface (OS), compared to the control group (see the OS / TS ratio in Tables 9 and 10).
[0323] Table 9. Histomorphometric data obtained within the new bone formed in the region of interest (ROI) (Mean ± SD).
[0325]
[0327] Abbreviations: BS: Bone surface, OS: Osteoid surface, TS: Total surface, BPm: Bone perimeter, BTh: bone thickness, Ctr: control.
[0328] Tiss-Zn2 + achieved a greater bone perimeter (BPm) than that produced by TissHYD (Table 10). Table 10. Statistical results of the P values after data analysis. Bold letters indicate significance at P <0.05.
[0329]
[0332] Abbreviations: BS: Bone surface, OS: Osteoid surface, TS: Total surface, BPm: Bone perimeter, BTh: bone thickness, Ctr: control.
[0334] For comparison, Fig. 13 shows bone sections stained by the von Kossa silver nitrate technique at six weeks of follow-up, without any membrane -control (Fig. 13A) - and Tiss-Ca2 + membrane (Fig. 13B ). Trabecular bone formation was observed along the margin of the calvaric defect (arrowhead), and within the defect. The pointers in Fig. 13 (Mbr: membrane, NB: new bone and OB: old bone) show scattered islands of bone, corresponding to the new bone. It was observed that the bone defect in the control group was filled with connective tissue and a few immature bone trabeculae (Fig. 13A). Areas of trabecular bone formation could also be identified in defects treated with any of the membrane types (Figs. 12B, 13B).
[0336] Table 11. Bone cells and blood vessels detected within the newly formed bone in the region of interest (ROI) (Medial Standard Deviation (SD)).
[0338]
[0341] Abbreviations: Ctr: control.
[0343] Table 12. Statistical results of the P values after data analysis with toroidal tests. Letters in bold indicate a si nificance at P <0.05.
[0345]
[0347] Abbreviations: Ctr: control.
[0348] Both Tiss-Zn2 + and Tiss-Ca2 + promoted a higher number of osteoblasts than the control group. The number of osteoblasts was higher in subjects treated with Tiss-Zn2 + membranes than with unloaded membranes (Table 12). In some areas of all samples, osteoblasts were observed in the process of facing the bone directly on the surface of the membrane (Figs. 14A and 14B). Tiss-Ca2 + did not produce a greater quantity of osteoblasts than the rest of the membranes, but it did originate a greater quantity of blood vessels than the control group (Table 12). Tiss-Ca2 + showed dense and clear collagen fibers that run parallel to the bone defect and the membrane. The control group promoted fewer blood vessels than Tiss-Ca2 +. Many large vessels could be detected in the samples treated with the Tiss-Zn2 + membrane (Fig. 14A). Small blood vessels were shown in close proximity to the new bone and the Tiss-Ca2 + biomaterial.
[0350] The images obtained with TB also made it possible to observe that the Tiss-Zn ² + and Tiss-Ca2 + membranes promoted the formation of the bone matrix (Fig. 14) on the membrane, outside the surgical defect. There were no inflammatory cells or multinuclear giant cells present at the bone interface in the Tiss-Zn2 + treated animals (Fig. 14A).
[0352] In this experimental study, bone regeneration was observed represented in all groups. At the end of the study, the size of the defects was smaller than their original size. All bone defects showed mineralized bone surface within the region of interest (Fig.
[0353] 12A), but Tiss-Zn2 +, Tiss-Ca2 + and TissHYD achieved significantly higher newly formed bone (BS) compared to controls (Tables 9 and 10). The tissue pattern appeared to be composed of membranes in intimate contact with the newly formed bone and with the osteoid tissue. The significant increase in bone surface (BS), that is, mineralized bone matrix excluding osteoid, and bone thickness (BTh) were associated with a generalized increase in osteoblasts promoted by all membranes, compared to the group of control, especially when Tiss-Zn2 + membranes were used (Tables 9 and 10).
[0354] New bone was observed directly in contact with the surfaces of the Tiss-Zn2 + membrane in the regions that showed successful bone conduction (Fig. 14A). The newly formed bone was continuous from the margin of the defect without any soft tissue invasion. Continuously regenerated bone adhered to the Tiss-Zn2 + membrane forms images of bone junction (Fig. 14B). Multiple interconnected ossified trabeculae were observed in the region of interest (Fig. 12A).
[0356] The application of Tiss-Zn2 +, Tiss-Ca2 + and TissHYD membranes induced significant changes in bone remodeling and structural indices. This increase in remodeling could result in the replacement of over-mature and old bone with younger, more resilient bone (Rubin et al., 2018). The osteoid or bone matrix that will be, but not yet, mineralized showed a greater surface area than in the control group when common membranes from young bones were used (La Monaca et al., 2018).
[0358] Not only was osteogenesis observed, but also an increased biological activity after determining the amount of osteoblasts when the Tiss-Zn2 + and Tiss-Ca2 + membranes were used (Table 10). Tiss-Zn2 + has shown an increase in the cell proliferation / scar tissue ratio (Augustine et al., 2014). The formation of new bone indicates that the membranes can induce the proliferation of osteoblasts to fill, or partially fill, intracortical pores by nucleating aggregates that induce their subsequent fusion to form amorphous calcium phosphate and finally apatite crystals, thus reactivating the conversion of mesenchymal cells to bone-forming osteoblasts (Vrahnas et al., 2018). It has been shown that the previous formation of zinc complexes in tissues facilitates the binding of the phosphate group with the biomimetic precipitation of Ca / P deposits and the formation of hydroxyapatite nanocrystals. These phosphate groups, on the surface, present undercoordinated oxygens, leading to reactive surfaces that will attract calcium ions from the media. This biomimetic deposition of Ca / P is considered a coating method inspired by the biomineralization process. In addition to that, phosphoproteins are believed to supply phosphate for mineralization, being capable of modulating nucleation and crystal growth, as well as binding to the collagen network. Greater solubility of ZnO when in contact with acidic substrates, such as some non-collagenous acidic proteins, could also explain the effective release of zinc ions, which stimulates protein phosphorylation, increases calcium deposition and facilitates crystal precipitation. . Osteoblasts stimulated with Ca2 +, and extracellular PO ⁴ 2- increased mRNA expression of bone morphogenetic protein 2 (Shimauchi et al., 2013; Tada et al., 2010).
[0360] Moreover, the connectivity of the pores described in these membranes could influence the possibility that a greater number of osteoblasts can penetrate the porous structure (Guarnieri et al., 2018). In addition, microvessel growth was observed near the membrane (Fig. 14A) when Tiss-Zn2 + membranes were used, which contributes to the integration of the biomaterial in the tissue (Turri and Dahlin, 2015).
[0362] The current findings provide additional evidence that these membranes act as a bioactive modulator of signaling to the underlying defects. These results provide evidence that the membranes are useful and advantageous for the regeneration of bone tissue.
[0364] 5. ANTIBACTERIAL EFFECTS OF TissHYD, Tiss-Zrí2 *, Tiss-Ca2 + AND Tiss-DOX.
[0366] Hydroxyapatite (HAp) discs with a diameter of 7 mm and a thickness of 1.8 mm (Clarkson Chromatography Products, Williamsport, PA, USA) were attached to four types of membranes: TissHYD, Tiss-Ca2 + (loaded with 1.1 pg (Ca2 +) / mg Tiss), Tiss-Zn2 + (loaded with 1.1 pg (Zn2 +) / mg Tiss), and Tiss-DOX (loaded with 0.8 mg (DOX) / mg Tiss. Naked HAp discs and HAp discs coated with a PTFE membrane as control. All specimens were used to develop an oral multi-species biofilm. Reference strains Streptococcus oralis CECT 907T, Veillonella parvula NCTC 11810, Actinomyces naeslundii ATCC were used 19039, Fusobacterium nucleatum DMSZ 20482, Aggregatibacter actinomycetemcomitans DSMZ 8324, and Porphyromonas gingivalis ATCC 33277. Briefly, pure anaerobic cultures of each bacterium were grown in protein-rich medium containing brain-heart infusion broth. Control HAp discs and coated with the different memb Frogs were then placed in the wells of a 24-well tissue culture plate. Each well was then inoculated with 1.5 ml of a suspension of a mixture of bacteria prepared and incubated under anaerobic conditions (10% H ^2, 10% CO ² , and N ² balance) at 37 ° C for 12 , 24, 48 and 72 h. To control the sterility of the system, plates containing only culture medium were used.
[0368] Biofilms were observed from 12 to 72 hours of evolution by Scanning Electron Microscopy (SEM, for its acronym in English). For this analysis, the specimens were fixed in a solution of 4% paraformaldehyde and 2.5% glutaraldehyde for 4h at 4 ° C. After that, the specimens were critically desiccated, sputter-coated with gold, and analyzed.
[0370] For a quantitative evaluation of bacterial growth, DNA was isolated from the biofilm after 12, 24, 48 and 72 hours of incubation using a commercial kit (MolYsis Complete5; Molzym GmgH & CoKG, Bremen, Germany), following the manufacturer's instructions ( The protocol for the extraction of bacterial DNA from stage 6 was followed, avoiding the preliminary stages). The 5 'nuclease hydrolysis probe PCR assay method was used to detect and quantify bacterial DNA.
[0372] Primers and probes were obtained from Life Technologies Invitrogen (Carlsbad, CA, USA), Applied Biosystems (Carlsbad, CA, USA), and Roche (Roche Diagnostic GmbH; Mannheim, Germany) and targeted against the 16S rRNA gene. Quantitative polymerase chain reaction (qPCR) amplification was performed in a total volume of the reaction mixture of 10 pL. Analyzes were performed with a LightCycler® 480 II thermal cycler (Roche). The plates used in the study were FramStar 480 with a clear frame and white wells (4titude; The North Barn; Damphurst Lañe, UK), sealed with QPCR Adhesive Clear Sea (4titude). Each DNA sample was analyzed in duplicate. The quantification cycle (Cq) was determined using the provided software package (LC 480 Software 1.5; Roche). Cell quantification by qPCR was based on standard curves. The correlation between the Cq and CFU ml-1 values was generated automatically by the software (LC 480 Software 1.5; Roche).
[0374] Shapiro-Wilk goodness-of-fit tests and data distribution were used to assess normality. The data were expressed as means and standard deviation (SD). To compare the effects of the material surface at different exposure times in CFU ml-1, analysis of variance and post-hoc tests with Dunett's T3 correction were used. The results were considered statistically significant with p <0.05.
[0376] FESEM images of different biofilm formation are shown in Fig. 15. After 24 h, high amounts of bacteria were observed in all discs forming a thick layer of bacteria, with initial characteristics of a structured biofilm. Except in the case of Tiss-DOX discs that showed absence or few isolated bacteria on the surfaces. Microbial communities interspersed with channels could be observed, suggesting that the bacteria may have reached the exponential phase of growth. No significant differences were observed between the specimen discs in relation to the biofilm structure, except for the biofilms in the Tiss-DOX discs, which lacked an organized structure.
[0378] Bacterial counts (CFU mL-1) for all six species at 72 h incubation time in the tested specimens are shown in Fig. 16. Over time, the dynamics of bacterial growth were similar regardless of the specimen. The biofilms in the HAp discs coated with Tiss-DOX reached the lowest amount of bacteria, compared to the rest of the groups (p <0.01).
[0380] 6. DOPING OF TissHYD WITH SIO NANOPARTICLES2 ( NPS-SIO2 )
[0382] Silicon dioxide (SiO ² ) is able to improve not only the bioactivity of materials but also adhesion and proliferation in artificial tissues, which facilitates the differentiation of osteogenic cells. SiO ² is considered to be an osteoinductive and a catalyst for bone formation. Therefore, to improve the bioactivity of the membranes, they were doped with SiO ² nanoparticles (NPs-SiO ² ) in two different ways:
[0384] 1) 1g of NPs-SiO ² was added to the optimal solution for scaling electrospinning (see section 6), and the solution was prepared as follows: 1,000g of NPs-SiO ² (1,219% by weight) was dispersed in 70,000 g of DMF (85.316% by weight) by means of 20 min of sonication, then 5,000 g of (MA) ⁵ -co- (HEA) ⁵ (6.094% by weight) were dissolved, and 6,000 g of ( MMA) ³ -co- (HEMA) ² (7.313% by weight) in the suspension of NPs-SiO ² DMF. When the copolymers completely dissolved, 0.048 g of hydrochloric acid (HCl) (0.058% by weight) was added to the solution. Then, using the parameters of Table 7, the solution was processed by electrospinning, and a non-woven membrane of nanofibers doped with NPs-SiO ² (TissSi-OH) was obtained: The mechanical properties of the membranes were not affected by the incorporation of NPs-SiO ² . Next, to introduce carboxyl groups (COO ^h ) on the surface of the fibers, a partial hydrolysis of the ester groups: R-COCH ³ and RCOCH ² CH ² OH of TissSi- OH was performed to obtain TissHYDSi. The hydrolysis was carried out by introducing both membranes in a sodium carbonate solution (333 mM) pH = 12.50 for 30 min. The membranes were then washed 3 times with distilled water and dried at room temperature. The number of accessible COOH groups calculated by the TBO method was 660 ± 50 pmol / g.
[0386] 2) TissHYD was impregnated with a 10-20 nm suspension of SiO ² nanoparticles (SiO ² -NPS) and then the water was evaporated under vacuum at a constant temperature: in this way the membrane was loaded with 0.06 mg of SiO ² -NPS / mgTiss.
[0388] Subsequently, the membranes doped with SiO ² -NPs using procedure 1) and 2) (TissHYDSi) were functionalized with zinc, calcium and DOX through the following protocols:
[0390] 6.1. Functionalization of TissHYDSi with Zn + 2 ( TissSi-Zn2 +) and Ca2 + ( TissSi-Ca2 +).
[0392] The ability of carboxyl groups to complex with divalent cations was used to functionalize TissHYDSi with Zn + 2 and Ca2 +. The TissHYDSi was impregnated with a solution of Zn2 + and Ca2 +, and then the water was evaporated under vacuum at a constant temperature: in this way the TissHYDSi was loaded with 1.1 pg / mg, Ca2 + and Zn2 +.
[0394] 6.2. TissHYDSi functionalization with doxycycline ( TissSi-DOX).
[0396] Doxycycline (DOX) was attached to the TissHYDSi membrane non-covalently by acid-base interactions between the amino groups of DOX and the carboxyl groups of TissHYDSi, as well as by hydrogen bonds between the hydroxyl groups of the membrane and the DOX amino groups. The TissHYDSi was impregnated with a DOX solution, and then the water was evaporated in vacuo at a constant temperature: in this way the TissHYDSi was loaded with 0.8 mg DOX / mg Tiss.
[0398] 7. IN VITRO CELLULAR STATIC TEST FOR TissHYDSi, TissSi-Zn2 + TissSbCa2 + AND TissSi-DOX.
[0400] To investigate the effect of the inclusion of silicon dioxide on the bioactivity of the membranes, the analysis proposed by Kokubo (ISO 23317: 2012. Implants for surgery In vitro evaluation for apatite-forming ability of implant materials) was performed, as has detailed previously in section 3.1.
[0402] The results of the FESEM images of TÍSS-SiO ² -COOH, Tiss-SiO ² -Ca2 +, Tiss- SiO ² -Zn2 + and Tiss-SiO ² -DOX performed by procedure 1) after 7 days of immersion are presented in the Fig. 17. Tissue bioactivity was demonstrated in all cases. The inclusion of silicon dioxide in the sample tissues has dramatically increased the occurrence of mineral deposits on all surfaces tested (Fig. 11: without SiO ² and 17: with SiO ² ).
[0403] The rounded deposits were abundant and uniformly distributed on the nanofibers in all cases: similar results were obtained with the materials doped with SiO ² by method 2).
[0405] SiO ² doped membranes have been shown to increase bioactivity through increased mineralization.

权利要求:
Claims (26)
[1]
1. A hydrophilic nonwoven nanofiber membrane, characterized in that it comprises a mixture of
^or a first copolymer of (MA) 3-co- (HEA) 2 with statistical topology in a percentage by weight between 35% and 65%; Y
^or a second copolymer of (MMA) ¹ -co- (HEMA ^{) 1} in a percentage by weight between 35% and 65%.
[2]
2. The hydrophilic non-woven nanofiber membrane according to claim 1, characterized in that it comprises a mixture of
^or a first copolymer of (MA) ³ -co- (HEA ^{) 2} with a statistical topology of 50% by weight; Y
^or a second copolymer of (MMA) ¹ -co- (HEMA ^{) 1} at 50% by weight.
[3]
The hydrophilic non-woven nanofiber membrane according to any of claims 1 or 2, characterized in that the first copolymer of (MA) ³ -co- (HEA ^{) 2} has a molecular weight above 80,000 Da, between 50,000 Da and 3-106 Da.
[4]
The hydrophilic nonwoven nanofiber membrane according to claim 3, characterized in that the first copolymer of (MA) ³ -co- (HEA ^{) 2} has a molecular weight between 1-106 Da and 3-106 Da.
[5]
The hydrophilic non-woven nanofiber membrane according to any of claims 1 to 4, characterized in that the second copolymer of (MMA) r co- (HEMA ^{) 1} has a molecular weight between 50,000 Da and 1-106 Da.
[6]
6. The hydrophilic nonwoven nanofiber membrane according to any of claims 1 to 5, characterized in that it also comprises SiO ² nanoparticles, wherein said SiO ² nanoparticles are homogeneously dispersed in the membrane and / or are physically adsorbed on the surface of the membrane, in a percentage by weight of between 0.1% and 60% with respect to the final weight of the membrane.
[7]
7. A process for preparing the hydrophilic nonwoven nanofiber membrane according to any of claims 1 to 5, characterized in that it comprises the following steps:
a) synthesis of the first copolymer of (MA) ³ -co- (HEA ^{) 2} by metal catalyzed living radical polymerization using a metal catalyst system;
b) synthesis of the second copolymer of (MMA) ¹ -co- (HEMA ^{) 1} by radical polymerization by reverse atom transfer using a metal catalyst system;
c) preparation by electrospinning of a nanofiber membrane comprising a mixture, wherein said mixture comprises the first copolymer obtained in step (a) and the second copolymer obtained in step (b), and
d) heat treatment of the nanofiber membrane obtained in step (c), where the heat treatment is applied in the form of hot water in a temperature range between 30 ° C and 80 ° C and where the nanofiber membrane obtained in step (c) it is kept tensioned by a saddle.
[8]
8. The process according to claim 7, wherein the catalyst system of step (a) and step (b) is an amino complex of copper.
[9]
9. The process according to claim 7, wherein the metal of the metal catalyst system of step (a) and / or step (b) comprises a transition metal or a mixture of transition metals in different oxidation states.
[10]
The process according to claim 9, wherein the metal of the metal catalyst system of step (a) and step (b) is independently selected from the list consisting of Cu, Fe, Co, Ni, Ru, Pl, Rh, Re, Cr and Mo.
[11]
The process according to any of claims 7, 9 or 10, wherein the ligand of the metal catalyst system of step (a) and / or step (b) is a multidentate aliphatic amine.
[12]
12. The process according to any of claims 7, 9 to 11, wherein the metal catalyst system ligand of step (a) and step (b) is independently selected from the list consisting of N, N, N ' , N ", N ', - pentamethyldiethylenetriamine (PMDETA), tris (2-pyridylmethyl) amine, tris [2- (dimethylamino) ethyl] amine, 2,2'-Bipyridyl, N, N, N', N'-tetrakis (2-pyridylmethyl) ethylenediamine and 1,1,4,7,10,10-hexamethyltriethylenetetramine.
[13]
The process according to any one of claims 7 to 12, wherein the initiator of the metal catalyst system of step (a) is independently selected from the list consisting of dodecyl 2-bromoisobutyrate, ethyl α-bromoisobutyrate, α-bromoisobutyrate ethyl, octadecyl 2-bromoisobutyrate, methyl α-bromoisobutyrate, methyl 3-bromopropionate, tert-butyl 3-bromopropionate, ethyl 2-bromopropionate.
[14]
The process according to any one of claims 7 to 12, wherein the initiator of the metal catalyst system of step (b) is independently selected from the list consisting of 1,1'azo-bis (cyclohexanecarbonitrile) (ACHN), 2,2'-azo-bis (2-methylpropionamidine) 2,2-dihydrochloride (AAPH), 4,4'-azo-bis (4-cyanovaleric acid) (ACVA), tert-butyl hydroperoxide, cumene hydroperoxide , 2,5-di (tert-butylperoxide) -2,5-dimethyl-3-hexane, dicumyl peroxide and 2,5-bis (tert-butylperoxide) -2,5-dimethylhexane.
[15]
The process according to any one of claims 6 to 14, wherein the solvent used with the metal catalyst system of step (a) and step (b) is independently selected from the list consisting of acetone, dimethylformamide, poly ( ethylene glycol), dimethylsulfoxide, 1,4-dioxane, ethanol, propanol, hexane, water, carbon dioxide, ionic liquid, and a combination thereof.
[16]
16. The process according to any of claims 6 to 14, wherein the metal catalyst system of step (a) and step (b) does not use a solvent.
[17]
The process according to any one of claims 6 to 16, wherein the solvent used in step (c) is dimethylformamide.
[18]
18. The process according to any of claims 6 to 17, wherein the percentage by weight of the solvent used in step (c) is in a range between 20% and 98%.
[19]
19. A process for the preparation of the hydrophilic nonwoven nanofiber membrane according to claim 6, wherein said SiO ² nanoparticles are homogeneously dispersed in the membrane, characterized in that it comprises all the steps of the process according to any of claims 7 to 18 and wherein the mixture of step (c) comprises SiO ² nanoparticles.
[20]
20. A process for preparing the hydrophilic nonwoven nanofiber membrane according to claim 6, wherein said SiO ² nanoparticles are physically adsorbed on the surface of the membrane characterized in that it comprises all the steps of the process according to any of claims 7 to 19 and an additional step (e) of impregnating the membrane obtained in step (d) in a suspension of SiO ² nanoparticles and evaporating the solvent.
[21]
21. A hydrophilic nonwoven nanofiber hydrolyzed membrane characterized in that it comprises the hydrophilic nonwoven nanofiber membrane according to any of claims 1 to 6, comprising carboxyl groups, wherein the concentration of carboxyl groups in the membrane is in a range between 20 pmol / g of the membrane and 3000 pmol / g of the membrane.
[22]
22. The hydrophilic hydrolyzed nonwoven nanofiber membrane according to claim 21, characterized in that it is functionalized with a divalent cation selected from among Zn + 2, Ca + 2, Mg + 2 and Sr + 2, an antibacterial agent and / or any of their combinations.
[23]
23. The hydrophilic nonwoven nanofiber hydrolyzed membrane according to claim 21, characterized in that the hydrophilic nonwoven nanofiber membrane is functionalized with Zn + 2, Ca + 2 and doxycycline.
[24]
24. A non-resorbable membrane for promoting bone regeneration characterized in that it comprises the hydrophilic nonwoven nanofiber membrane according to any of claims 1 to 6 or the hydrophilic nonwoven nanofiber hydrolyzed membrane according to claims 21 to 23.
[25]
25. A non-resorbable periodontal membrane characterized in that it comprises the hydrophilic non-woven nanofiber membrane according to any of claims 1 to 6 or the hydrolyzed non-woven nanofiber hydrophilic membrane according to claims 21 to 23.
[26]
26. A coating for an implant characterized in that it comprises the hydrophilic nonwoven nanofiber membrane according to any of claims 1 to 6 or the hydrolyzed nonwoven nanofiber hydrophilic membrane according to claims 21 to 23.

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公开号 | 公开日

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ES2791771B2|2021-05-11|

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WO2020224960A1|2020-11-12|

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