PROCESS FOR THE PRODUCTION OF CHITOSAN-BASED HYDROGEL AND NEGATIVELY LOADED POLYELECTROLYTES AND POR

专利摘要:
The subject of the present invention is a method for manufacturing a hydrogel comprising the following successive steps: a first step of supplying at least one powder of an anionic polymer (A) and at least one chitosan powder ( B) comprising amine functions (-NH2); a second step of dry blending at least the powders (A) and (B) of the first step to form a mixture of powders; a third step of suspending the mixture of powders obtained at the end of the second step in an aqueous medium having a pH making it possible to solubilize the anionic polymer (A) without solubilizing the chitosan (B); - A fourth step of adding an acid to the suspension obtained at the end of the third step so as to form the hydrogel.
公开号:FR3038318A1
申请号:FR1556283
申请日:2015-07-02
公开日:2017-01-06
发明作者:Nicolas Blanchemain；Bernard Martel；Claudia Flores；Frederic Cazaux；Feng Chai；Nicolas Tabary
申请人:De Lille 1 Sciences Et Tech, University of；Universite Lille 1 Sciences et Technologies；
IPC主号:

专利说明:

The present invention relates to the technical field of hydrogel production processes, in particular implantable, as well as the technical field of manufacturing processes for cellular materials obtained via said hydrogels, in particular concerning the technical field of manufacturing processes for physical hydrogels. .
The present invention also relates to the technical field of hydrogels, cellular materials (including sponges) derived from said hydrogels, and medical devices comprising such hydrogels or cellular materials.
Background of the invention
The hydrogels or macromolecular gels comprising, for the most part, water, are matrices of polymer (s) swollen with a large quantity of water. The macromolecules are interconnected together, forming a scaffold network that gives the gel the properties of a material with viscoelastic properties.
The bonds between polymer chains can be of two forms: permanent or reversible. When they are permanent, we observe the presence of covalent bonds, we speak then of chemical hydrogels. When the bonds between the chains are reversible, the macromolecules interact via non-covalent bonds of hydrogen, ionic or hydrophobic types, dipole-dipole are then called physical hydrogels.
The hydrogels can be used as biomaterials, that is to say as medical devices, in particular implantable. Such hydrogels may comprise a polymer network based on natural polysaccharides (for example: starch, cellulose, carrageenans, alginates, etc.), proteins (gelatin), or based on synthetic polymers such as polyacrylamides. polyacrylates ("carbomers") forming three-dimensional macromolecular networks entangled and stabilized by covalent bonds (irreversible or permanent chemical gels) or by hydrogen, hydrophobic, dipolar (dipole-dipole) or electrostatic bonds (reversible physical gels) .
Chitosan (CHT), belonging to the family of naturally available polysaccharides, is the only cationic polymer of natural origin known to date (positively charged polyelectrolyte, referred to as PE +), it is produced by deacetylation of chitin, or extracted directly from mushrooms. Chitosan is a copolymer composed of the random distribution of β-1,4-linked D-glucosamine and N-acetyl-D-glucosamine. A chitosan is characterized by its degree of deacetylation, which represents the percentage of glucosamine repeating units on its macromolecular chain.
Chitin is the component of the exoskeleton of arthropods (crustaceans) or the endoskeleton of cephalopods. Chitosan is characterized by its high content of amine functions (of the order of 5 millimoles (mmol) per gram, depending on its degree of deacetylation (commonly between 60% and 90%) CHT is widely used in biomedical applications for its biocompatibility, bio-resorbability, haemocompatibility and healing properties, and for its action against the development of bacterial strains.
Chitosan is a polymer available in powder form, or flakes with a greater or lesser grain size. It is the only natural amine polymer to be in the form of a powder, insoluble in pure water, but soluble from the acidification of water by at least 1% (vol / vol) acetic acid (preferably ) concentrated. Other polyamines bearing primary amine functions (-NH 2) exist, such as polyvinylamine, polyallylamine and polyethyleneimine, but they are only available in the form of concentrated aqueous solutions, or solid in the form of a gum (because very hygroscopic) and do not constitute powders with fluidity or free flow.
The crosslinking of the CHT ionically to obtain a hydrogel is a gentle and simple way to achieve because it occurs spontaneously, without heating or catalyst. Anionic crosslinking agents are thus used with sulfates, citrates, phosphates or polyphosphates, polyoxyanions, or calcium salts. The method consists in allowing the "object" to be soaked in CHT (film, monolyth, etc.) in an aqueous solution containing the crosslinking agent that diffuses inside the "object" at the same time as the water that causes it. swelling and the formation of a gel. The alternative methods consist in adding the crosslinking agent in the aqueous solution of chitosan previously dissolved in a dilute solution of acetic acid (often at least 0.5% acetic acid for example), or conversely, the solution of CHT is added dropwise into the crosslinking agent solution, by means of a syringe for example (J. Berger et al., European Journal of Pharmaceutics and Biopharmaceutics 57 (2004) 19-34).
Cyclodextrins, also belonging to the family of polysaccharides, are cage molecules capable of forming reversible inclusion complexes with many active principles, in particular lipophilic. Cyclodextrins are cyclic polysaccharides resulting from enzymatic degradation of starch. They consist of a sequence of six to eight gluco-pyranose units, linked together by α- (1,4) bonds forming a macrocycle whose periphery is rich in hydroxyl functions which bring solubility in water, while that the interior forms an apolar and hydrophobic cavity giving the cyclodextrins complexing properties with lipophilic active principles. Chemical (non-reversible) gels based on cyclodextrins obtained by crosslinking a cyclodextrin with epichlorohydrin, a diepoxide, a diisocyanate, pyromellitic dianhydride, sodium trimetaphosphate or EDTA used as agents of the invention are known. crosslinking. These cross-linked or "hyperbranched" cyclodextrin polymers form either insoluble macroscopic gels, or soluble nanogels which exhibit entrapment and vectorization properties of organic molecules, including therapeutic agents (Progress in Polymer Science, Volume 38, Issue 2, February 2013, Pages 344-368, Advanced Drug Delivery Review 65 (2013) 1188-1203, Belstein Journal of Organic Chemistry, 2014, 10, 2586-2593).
Previous work combining cyclodextrin and chitosan has been published. However, this work did not consist in obtaining a macroscopic physical gel from the mixture of a cyclodextrin polymer and chitosan. For example, Auzely (CR Chimie 14 (2011) 167-177) performed a covalent grafting of cyclodextrin (CD) on chitosan (= CHT-CD), on the one hand, and the adamantane (ada) grafting on chitosan (= CHT-ada) on the other hand. These two polymers when mixed in solution form a supramolecular macroscopic gel by forming a network formed of these two types of polymers, caused by the spontaneous formation of inclusion complexes between cyclodextrins and adamantane, forming a hydrogel stabilized by supramolecular interactions between the interpenetrating CHT-ada and CHT-CD networks. Moreover, the very high stability of the CD-ada complex does not allow in the mixtures the inclusion of a third molecule, such as a therapeutic agent in the cavities of the cyclodextrins if the stoichiometry (or the molar ratio) CD / ada is less than 1, all the cavities being irreversibly complexed by an adamantane group.
Most gels marketed as medical devices are ready to use, that is to say already hydrated, and containing a mineral filler, for example calcium phosphate or calcium beta triphosphate, or an active therapeutic molecule . In'oss ™, which is an injectable gel based on HPMC (hydroxypropylmethylcellulose) containing hydroxyapatite for bone filling, may be mentioned; Periochip® or Atridox® based on gelatin and PLA polymer (polylactic acid) respectively containing an active ingredient for application in periodontology. There are also gels for filling wrinkles based on hyaluronic acid or collagen, or gel coatings on a textile panel based on CMC (carboxymethylcellulose), optionally loaded with an active ingredient, used in the manufacture of dressings whose function is to maintain the hydration of the wound or to release an active ingredient. Biom'Up sells a bone filling material (Matribone ®) in the form of a collagen-based sponge including a load of calcium betatriphosphate powder.
There are also physical hydrogels formed by an ionic complex resulting from the interactions between a negative polyelectrolyte and a positive polyelectrolyte. The publication from the "International Journal of Biological Macromolecules" and entitled "Recent development of chitosan-based polyelectrolyte complexes with natural polysaccharides for drug delivery" authored by Yangchao Luo and Qin Wang, 64 (2014) 353-367, lists the various work that has been done with chitosan over the last decade to form such ionic complexes. The polyanions mixed with chitosan are hyaluronic acid (HA), pectin, carrageenan, xanthan gum, gellan gum, cashew gum, gum arabic, carboxymethylcellulose, glucomannan, and gum kondagogu.
Hydrogels formed from such polyelectrolyte complexes also acquire their hydrogel form through lower energy physical interactions such as dipole-dipole association, Van der Waals bonds, and hydrogens. Compared with hydrogels obtained by chemical crosslinking, hydrogels formed from ionic complexes have the advantage of not being toxic, well tolerated by living organisms and biocompatible. Indeed, chemical crosslinkers can induce some toxicity from the reactive functional groups they support. In order to remove their traces in the gel from the purification steps of implantable or medical gels in general, washing with water or with solvents is therefore necessary for the chemically crosslinked hydrogels. These steps can degrade the structure of these hydrogels. In addition, when these chemically cross-linked hydrogels comprise an active ingredient, these purification steps of the hydrogels formed can cause the loss of the active ingredient by diffusion in the medium which served to extract traces of crosslinking agent.
Physical (reversible) gels can be destroyed by increasing temperature, increasing ionic strength, changing solvent polarity or pH, while chemical gels are permanently stabilized through covalent bonds.
The publication entitled "Chitosan / cyclodextrin nanoparticles as macromolecular drug delivery system", by AHKrauland and MJ.AIonso, International Journal of Pharmaceutics 340 (2007) 134-142 describes the synthesis of nanoparticles presented as nanogels based on chitosan and a carboxymethylated β-cyclodextrin monomer allowing the slow release of encapsulated molecules. In this case nanogels were obtained, and not gels in the macroscopic state. A nano gel can be defined as a "object" of highly hydrated globular form, often between 20 and several hundred nm in size.
The publication entitled "Chemically cross-linked and grafted cyclodextrin hydrogels: from nanostructures to drug-eluting medical devices", by A.Concheiro, C.Alvarez-Lorenzo, Advanced Drug Reviews 65 (2013) 1188-1203, describes the manufacture of hydrogels based on cyclodextrins which are chemically grafted onto preformed macromolecules (often of the poly (acrylic) type), obtained by polymerization of monomers carrying cyclodextrin, or crosslinked by crosslinking agents such as a diepoxide, a diisocyanate, the dianhydride pyromellitic, sodium trimetaphosphate or EDTA.
The publication "Chitosan derivatives bearing cyclodextrin cavities as novel adsorb matrices", from M.Prabaharan and JFMano, Carbohydrate Polymers 63 (2006) 153-156 describes the synthesis of macromolecules of chitosan on which cyclodextrins are grafted via amide bond.
The active agents incorporated in the physical hydrogels are high molecular weight molecules (proteins, peptides, DNA, etc.) whose controlled delivery is made possible by their slow diffusion through the macromolecule networks of the polyelectrolyte complexes. The delivery of these active agents is also directly related to the rate of erosion or bioresorption of the matrix of the hydrogel.
In contrast, low molecular weight molecules rapidly diffuse through the polymer network of the gel. Indeed, if the bioactive molecules do not exhibit particular interactions with the polymer (s) forming the architecture of the gel, their small steric hindrance allows them to diffuse freely through the meshes of these very open macromolecular networks. (A hydrogel is mainly composed of water), so the kinetics of release of these small molecules will not be controlled by the diffusion rate or the erosion rate of the hydrogel and it will be very fast.
The known physical hydrogels, as well as their corresponding cellular materials, disintegrate in the short term (after a few hours) or spontaneously when immersed in water, especially when it is loaded with salts; which is the case of all physiological fluids. This last characteristic is important in the case of hydrogels intended to be implanted in the body so that they retain their structures for a determined period of time so as not only to ensure their filling and / or reinforcement function and to allow controlled release. and targeted one or more active principle (s)
Finally, there is no hydrogel to date capable of sequestering or containing a mineral charge on an implantation site (for example a bone defect), this is due to the too rapid degradation of the structure of the hydrogel which causes the short-term release of the mineral filler from the hydrogel matrix. The mineral filler is chosen from the materials used for bone filling containing calcium phosphates in various forms (powders, monolytes, granules, etc.), hydroxyapatite or calcium phosphate of a constitution similar to the main mineral component of the bone. Indeed, the incorporation of a sufficient quantity of mineral filler in a hydrogel and its maintenance on the implantation site long enough are necessary in many applications in the field of dental surgery, maxillofacial or the field of orthopedic surgery. However, the incorporation of a large amount of mineral filler in a cross-linked hydrogel physically destabilizes, and facilitates the disintegration of the latter.
The present invention thus seeks to provide a hydrogel, in particular physically crosslinked, resulting from a complex of at least one negative polyelectrolyte and at least one positive polyelectrolyte allowing the complexation of therapeutic molecules of low molecular weight (less than or equal to about 250 g / mol), then ensure their prolonged release.
The present invention also seeks to provide a hydrogel for encapsulating and controlling the release of one or more component (s) of high molecular weight, especially greater than about 250 g / mol.
The present invention also seeks to provide a compact hydrogel, moldable, homogeneous and thixotropic (so that the latter is injectable).
The present invention further seeks to provide a hydrogel and a cellular material from said hydrogel which are stable and do not disintegrate spontaneously when immersed in water or in a physiological medium, and even though they include a significant amount a mineral charge.
The present invention seeks to provide a hydrogel and a cellular material derived from said hydrogel which are able to understand a significant amount of mineral filler, in particular which represents up to 90% of the weight of the device, while maintaining an excellent consistency, good malleability and excellent absorption properties of biological fluids (blood) that can trigger the biological process of cell differentiation leading to the genesis of osteoblastic cells.
Object and summary of the invention
The present invention overcomes the aforementioned problems in that it has as its object, according to a first aspect, a method of manufacturing a hydrogel advantageously comprising the following successive steps: a first step of supplying at least one powder of an anionic polymer (A) and at least one chitosan powder (B) comprising amine functions (-NH 2); a second step of dry blending at least the powders (A) and (B) of the first step to form a mixture of powders; a third step of suspending the mixture of powders obtained at the end of the second stage in an aqueous medium, in particular with stirring, having a pH making it possible to solubilize the anionic polymer (A) without solubilizing the chitosan, preferably a pH greater than or equal to 4, more preferably at a pH greater than or equal to 4.5, particularly greater than or equal to 5, preferably the aqueous medium is water (for example distilled water or water ultra pure) or an aqueous suspension of at least one living cell, such as human or animal cells, in particular stem cells, whose pH is about 7 (+/- 0.5), corresponding to the pH of a culture medium or physiological fluid; - A fourth step of adding an acid to the suspension obtained at the end of the third step so as to form the hydrogel.
The inventors have discovered that the gelling process is strictly related to the chemical nature of the two polymers (A) and (B), and to the particular way of implementing them.
The chitosan powder is insoluble in an aqueous medium having a pH greater than or equal to 4, preferably greater than or equal to 4.5, particularly greater than or equal to 5. In contrast, the chitosan solubilizes in an aqueous medium if it contains a dilute acid such as hydrochloric acid or acetic acid. In an aqueous solution that is sufficiently acidic, the amine-NH 2 functions of chitosan are protonated to ammonium -NH 3 + functions, because of this property, chitosan is considered in the context of the present invention as a polycation (polyelectrolyte: PE +).
The publication "Chitin and Chitosan: Properties and Applications", Mme.Rinaudo, Prog.Polym.Sci.31 (2006) 603-632, describes the solubilization of chitosan, which depends in particular on its degree of deacetylation, its molar mass and the pH of the aqueous medium in which the chitosan is solubilized.
It should be noted that at a pH less than or equal to 5 and greater than or equal to 4, amine functions of chitosan (B) will be partially protonated but in an insufficient quantity to obtain the solubilization of chitosan (B). Rinaudo reports that the solubilization of chitosan usually occurs for a degree of ionization of glucosamine units greater than 0.5 (or 50%).
The proportion of ionized glucosamine units (corresponding to the degree of ionization of chitosan) can be evaluated by a standard acid-base assay well known to those skilled in the art.
The suspension of the mixture of powders comprising the powders (A) and (B) in an aqueous medium causes a decrease in the pH of this medium when the polyanion (A) comprises acid functions (for example carboxylic -COOH), then the pH goes up and stabilizes. Nevertheless, it has been observed that when the pH of the aqueous medium, before addition of the powder mixture, is greater than or equal to 4, preferably greater than or equal to 4.5, still preferably greater than or equal to 5, the possible drop in pH further the addition of the powder mixture is not sufficient to cause the solubilization of chitosan. Only the addition of the acid in the fourth stage leads to a drop in pH sufficient to solubilize the chitosan.
The anionic polymer according to the invention, or polyanion, is soluble at pH greater than or equal to 4, in particular greater than or equal to 4.5, in particular notammen greater than or equal to 5, and carries functional functions, in particular of sulphate acid functional groups (-0 -S (= O) 2-OH or -SO 4 H) and / or their salts, or sulphonic acid functions (-S (= O) 2 -OH or -SO 3 H) and / or their salts, and / or phosphoric acid functions (-O-P (= O) 2 -OH or -PO 4 H) and / or their salts, and / or carboxylic acid functions (-COOH) and / or their salts, capable of forming anionic functions in an aqueous medium, in particular by releasing an H + proton with regard to the sulphonic acid, acid sulphate, phosphoric acid or carboxylic acid functions, for the formation of carboxylate (-COO) and / or sulphate -SO4 'and / or sulphonate functions -SO3 'and / or phosphonates -PO4'.
The macromolecules carrying the acid functions defined above, and amine functions are ionizable and are called polyelectrolytes. High polyelectrolytes are distinguished from weak polyelectrolytes as a function of the propensity these functions have to ionize in aqueous solution, which depends on the pKa of each polyelectrolyte. The equilibrium constant Ka is of the type (AH) -> <- (A) + (H +), (arrows with opposite directions), such that Ka = ([A] x [H +]) / [H +]; thus we define the pKa = -log (Ka) which makes it possible to evaluate the ionization of an acid as a function of the pH of the medium. Thus the "Polymer Handbook", 2 volumes Set, 4th Edition, classifies polyelectrolytes into strong and weak polyelectrolytes, according to the pKa of the ionizable functions that they carry. Acid sulfates, sulfonic acids and phosphoric acid groups are strong polyelectrolytes, that is to say, ionized at low pH (less than 2), while polyelectrolytes carrying carboxylic groups are polyanions classified as weak polyelectrolytes (ionised car). at pH often greater than 4). Polyelectrolytes carrying secondary and tertiary primary amines are polycations classified as polyelectrolytes said to be weak because they are ionized at a pH of less than 5 (approximately).
The formation of a polyelectrolyte complex occurs through electrostatic interactions between acidic and basic ionic functions. Thus, the most favorable pH conditions for the formation of a polyeletrolyte complex are those when the pH of the solution is greater than the pKa of the polyanion, and lower than the pKa of the functions of the polycation.
For the purposes of the present invention, the term "anionic polymer or polyanion" is understood to mean any polymer comprising, in powder form, anionic functions or capable of forming anionic functions once solubilized in an aqueous medium, in particular at a pH greater than or equal to 4 , more particularly at a pH greater than or equal to 4.5, especially at a pH greater than or equal to 5.
In the second step, the powders of chitosan (B) (PE +) and the anionic polymer (PE) (A) are intimately mixed. Thus, the particles of PE + are combined by electrostatic interactions with the particles of PE '. These electrostatic interactions are explained by the fact that chitosan and the anionic polymer have zeta potentials of opposite signs.
Preferably, the zeta potential of chitosan is of the order of +20 mV to +50 mV, and the zeta potential of the preferred cyclodextrin (Al) polymer according to the invention, described below, is of the order of -30 mV.
Advantageously, during the third step, the chitosan, not being solubilized, remains in suspension in the aqueous medium thanks to the presence of the very hydrophilic PE which remains adsorbed on its surface by electrostatic interactions, forming a hydrophilic layer which allows maintain a homogeneous suspension.
The term "homogeneous suspension" means a suspension that does not sediment rapidly when slowing down or stopping the stirring.
"Powder" means any solid substance reduced to small grains at room temperature.
The term "ambient temperature" means a temperature of between 10 ° C. and 35 ° C., in particular between 15 ° C. and 25 ° C.
The pH values given in this text are measured using a pH meter at room temperature.
For the purposes of the present invention, the term "polymer" is intended to mean, in particular to designate the anionic polymer and the cationic polymer according to the invention (chitosan (B)), an oligomer or a polymer which may be a homopolymer or a copolymer (e.g. that is to say comprising at least two different repetition units).
The term "without solubilizing chitosan" means that no amine function of chitosan or an insufficient number of amine functions of chitosan are protonated in the aqueous medium to cause dissolution of the chitosan powder. Preferably, the solubilization of chitosan (B) is obtained for an alpha degree of ionization of at least 0.5, that is to say at least 50% in number of the amine glucose units of chitosan (B) relative to the number Total amine glucose units of chitosan (B) are ionized in glucosammonium units.
Preferably, the degree of deacetylation of the chitosan (B) according to the invention is greater than or equal to 60%, more preferably greater than or equal to 75%, particularly less than or equal to 95%, more particularly less than or equal to 90% , in particular less than or equal to 85%. The acid added during the fourth step of the process according to the invention is different from the polyanion.
When the acid is added, the pH of the suspension decreases, particularly at a pH of less than or equal to 5, more particularly less than or equal to 4.5, in particular less than or equal to 4, which causes the solubilization of chitosan by protonation of its amines (-NH2) in ammonium functions (-NH3 +), with the acetate as the counterion (CH3COO), or chloride (CI) if the added acid is respectively acetic acid and hydrochloric acid. The macromolecules of chitosan are deployed under the effect of intra-molecular electrostatic repulsions between the ammonium groups formed (the electrostatic charges of the same sign repelling each other), and reach a so-called "pelota" conformation which then occupy the entire volume of the aqueous medium. Simultaneously ionic bonds are formed between the ammonium groups of the chitosan (-NH3 +) anionic functions (COO) of the anionic polymer.
Then, once the amine functions are protonated, the pH of the hydrogel rises to stabilize, preferably at a pH greater than or equal to 4, more preferably at a pH greater than or equal to 4.5, in particular at a higher pH or equal to 5.
Said anionic polymer is thus dispersed in the chitosan network. These ionic interactions cause the physical crosslinking of the gel, and the setting in mass of the aqueous dispersion. The hydrogel according to the invention is therefore reversible.
Advantageously, the hydrogel according to the invention is a macroscopic gel which has the characteristics of a viscoelactic material having a specific shape.
For the purposes of the present invention, the term "hydrogel" is preferably used to mean a solid viscoelastic material having a shape that is to say that it retains the dimensions and the shape of the container in which it has been formed when removed from this container.
Preferably, the first step and / or the second step and / or the third step and / or the fourth step according to the invention is / are carried out at ambient temperature.
It has been observed that the addition of the acid after suspension in the third stage is very important because this way of proceeding makes it possible to obtain a very firm, stable hydrogel, and able to remain on a determined zone without any problems. flow for several hours at room temperature or at about 37 ° C, especially for at least 48 hours.
In addition, the hydrogel according to the invention retains its shape and its integrity in an aqueous medium, in particular at room temperature or at about 37 ° C. for several hours, at least for 24 hours, preferably at least for 48 hours.
In the state of the art, the physical hydrogels based on chitosan are made by mixing the aqueous acidic solution of chitosan with the aqueous solution of the polyanion or by sprinkling the polyanion, for example carboxymethylcellulose, on the acidic aqueous solution of chitosan ( pH of the order of 2-3). In both routes, the hydrogels obtained are not as firm and stable as the hydrogel according to the invention.
The role of the chitosan in the hydrogel according to the invention is to ensure the architecture of the gel, and to give it its required rheological properties.
Preferably, the ratio of the total mass of water (g) in the hydrogel to the total mass of the hydrogel is greater than or equal to 50%, more preferably greater than or equal to 60%, more preferably greater than or equal to equal to 70%, especially greater than or equal to 80%, even more particularly greater than or equal to 85%, especially greater than or equal to 90%.
Advantageously, the hydrogel according to the invention is capable of satisfying one or more properties, including the following: to be biocompatible, to be injectable by means of a syringe, to be capable of maintaining a certain shape obtained by molding for at least a few hours and / or not to flow in order to remain in place on the zone to which it has been applied, and to be able to release one or more active substance (s). The hydrogel according to the invention is advantageously thixotropic which allows it to be injectable. The hydrogel thus has a rheofluidifying behavior: the polymer fluidifies when it is exposed to a mechanical shear stress, and recovers its gel state at rest free of any stress. When the hydrogel is disposed in the body of the syringe, it becomes fluid under the effect of the shear stress applied through the piston to flow through the outlet port of the syringe, and then into the needle and eventually in the catheter, and finally recovers its firm hydrogel form once free of stress on the area to which it was applied. For example, a standard needle in fluid connection with the outlet of a syringe has a diameter of between 0.1 mm and 0.5 mm.
The hydrogels according to the invention can be used in numerous medical applications, and especially as a filling material in restorative surgery, aesthetics, urology, dental surgery, ophthalmology, orthopedics, maxillofacial surgery in order to preventing tissue adhesions and / or promoting the generation of various bone or soft tissues and / or releasing one or more active substances to the area to which they are applied.
When the hydrogels according to the invention comprise at least one functional agent and / or living cells, they contribute, for example, to scarring, to the treatment of a disease (cancer), to reducing the pain (anesthetic effect), to reducing the inflammation, or to prevent or fight an infection.
According to one embodiment, the suspension of the mixture of powders obtained at the end of the third step is cast or injected into a mold and the acid is then added so as to correlatively mold and form the hydrogel.
According to one embodiment, the second step of mixing the powders (A) and (B) is carried out using a powder mixing device, in particular a planetary stirrer, in particular without grinding (i.e. say without significant reduction of the size of the solid particles constituting the powder).
In a variant, the powder (A) and / or the powder (B) in the first stage and / or the mixture of the powders comprising at least the powders (A) and (B) in the second stage is / are sieved (s) ) on a sieve having mesh sizes less than or equal to 500 μm, preferably less than or equal to 300 μm, still preferably less than or equal to 200 μm, in particular less than or equal to 150 μm, more particularly lower or equal to 125 pm.
Preferably, the particle size distribution of the powder (A) and / or the powder (B) or the mixture of the powders (A) and (B) was measured with a Mastersizer S (Malvern Instruments, Orsay, France) using a 300 mm lens. The sample was dispersed in the dry state with compressed air at 4 bar.
Preferably, the powder (A) and / or the powder (B) and / or the mixture of the powders (A) and (B), optionally in combination with at least one powder other than the powders (A) and (B), as at least one inorganic filler, is / are screened on the sieving device having the following reference: a sieve -Plastic, nylon DIN 41p5, Nr: 948414 W: 0.125pm, marketed by BIOBLOCK SCIENTIFIC.
The respect of a given size for the polycation and polyanion particles is important because it allows the formation of a homogeneous gel, that is to say without the presence of lumps, and having the viscoelastic properties expected.
The powder (A) and the powder (B) can also be sieved using a vibration sieve, for example those sold by Fristch.
Preferably, during the first step, the powder (A) and / or the powder (B) is / are ground separately prior to their passage over a sieve, preferably using a Pulverisette device 14 ® marketed by the company Fritsch and equipped with a grid of 200pm.
In a variant, the mixture of the second stage is carried out by dry co-grinding at least of the powders (A) and (B).
Preferably, the powders (A) and (B) are co-crushed dry in a mortar manually.
The powders (A) and (B) can also be coiled on a ball mill, in particular a planetary micro-grinder spray such as those marketed by the company Fritsch.
Grinding allows the reduction of the size of the solid particles into smaller fragments. The term co-grinding refers to the simultaneous grinding of at least two different powders (A) and (B).
In the above variants, it has been observed that co-grinding and / or grinding followed by mixing advantageously make it possible to reduce the size of the solid particles of the powders but also to ensure an intimate mixture between the powders (A ) and (B) and thus a better contact area between the anionic polymer and chitosan. This arrangement promotes the homogeneity of the aqueous dispersion comprising these powders in the third step. The reproducibility in the formation of the hydrogel is thus also increased, as is the reactivity between the anionic polymer and chitosan, in particular for the setting of the hydrogel.
In one variant, the anionic polymer comprises acid sulphate functional groups (-O-S (= O) 2 -OH or -SO 4 H) and / or salts known as acid sulphate functional groups, and / or sulphonic acid functional groups (-S (= 0) 2-OH or -SO 3 H) and / or salts called sulfonic acid functional groups, and / or phosphoric acid functions (-O-P (= O) 2 -OH or -PO 4 H) and / or salts of said acid functional groups phosphoric and / or carboxylic acid functional groups (-COOH) and / or carboxylic acid functional salt salts, preferably phosphoric acid functional groups and / or salts of said phosphoric acid functional groups; and / or carboxylic acid functions (-COOH) and / or salts of said carboxylic acid functions, preferably carboxylic acid functions (-COOH) and / or salts of said carboxylic acid functions, particularly carboxylic acid functions (-COOH). ).
The salts of sulphonic acids (sulphonate salts -SO3X), acid sulphates (sulphate salts -SO4X), phosphoric acids (phosphonate salts -PO4X) and carboxylic acids (carboxylate salts -COOX) are monovalent, said salts thus comprise at least at least one -OX group (replacing the OH group present in the acids) in which X is preferably selected from sodium, potassium, lithium, silver, more preferably it is potassium or sodium.
In one variant, the anionic polymer is chosen from the list comprising: a cyclodextrin polymer, hyaluronic acid, carboxymethylcellulose, heparin, a heparinate salt, especially sodium heparinate, polyacrylic acid, sodium polyacrylate, a polyacrylic acid salt, pectin, alginic acid, sodium alginate, carrageenan, xanthan gum, gellan gum (carboxylic acid salt), glucomannan, gum of kondagogu, gum arabic, gum of cash, still preferably in the list consisting of a cyclodextrin polymer, hyaluronic acid, carboxymethylcellulose, heparin, pectin, alginic acid, sodium alginate , acrylic acid and a salt of acrylic acid, more preferably a cyclodextrin polymer, acrylic acid, pectin and sodium alginate. Heparin, a heparinate salt, carrageenan include acid sulfate functions or salts of basic sulphate functions. Hyaluronic acid, pectin, acrylic acid polymer or its salt, carboxymethylcellulose, alginic acid, xanthan gum, gellan gum, glucomannan, kondagogu gum, gum arabic, gum of cash and the cyclodextrin polymer (according to its synthetic route) comprise carboxylic acid functions (-COOH) or salts of said carboxylic acid functions (which salts have already been defined in the present text in the above paragraph with reference to the polymer anionic).
In one variant, the anionic polymer (A) is a cyclodextrin polymer obtained by the polymerization reaction of a mixture comprising at least one cyclodextrin and / or at least one cyclodextrin derivative and / or at least one cyclodextrin and / or at least one inclusion complex derived from cyclodextrin, with at least one (poly) carboxylic acid and / or its corresponding (poly) carboxylic acid anhydride (Al-list); or - at least one pyrophosphate (A2 list); or at least epichlorohydrin, the polymer obtained undergoing a carboxyalkylation step, in particular carboxymethylation, in order to graft carboxylic acid functions (-COOH) (list A3).
Advantageously, the hydrophilic network of the cyclodextrin polymer increases the biocompatibility and ensures the cohesion of the hydrogel which can not dissolve spontaneously in the physiological medium and migrate. The hydrophilic network also provides a stabilization of the inclusion complex between the guest and the cavity of the cyclodextrin. Cyclodextrin also contributes to the stability of the gel by improving its adsorption properties (known as reservoir properties) regulated by the guest host affinity, and causing the more or less slow release of the latter. The hydrogel may comprise a soluble cyclodextrin polymer or an insoluble cyclodextrin polymer or a mixture thereof, preferably a soluble cyclodextrin polymer, still more particularly belonging to the (Al) family.
The anionic cyclodextrin polymer ensures both the crosslinking of chitosan by ionic interactions, and at the same time allows the complexation of therapeutic molecules of low molecular weight (less than about 250 g / mol), by formation of inclusion complexes, and then to ensure their prolonged release.
The cyclodextrin polymer according to the invention, in particular crosslinked or hyperbranched, in particular from the (Al) list, may exist in soluble or insoluble form. The soluble polymer consists of nanoscale size gels (i.e., less than or equal to about 100 nm in size) (see Green Chemistry Publication, 2015, 17, 2444-2454 for photos of nanoparticle based nanogels). a cyclodextrin polymer), which form clear solutions in water. The insoluble polymer corresponds to micrometric particles (that is to say whose dimensions are greater than 1 μm), millimetric and beyond, which form biphasic systems in water, the solutions are therefore cloudy and not limpid .
Preferably, the cyclodextrin polymer is that belonging to the (Al) list. This family of polymers (Al) has the advantage of being easier to suspend in an aqueous medium, because these polymers are very hydrophilic. This arrangement thus facilitates the formation of a homogeneous and firm hydrogel.
Advantageously, the cyclodextrin polymer, in particular those belonging to the list (Al), retains its function of retention and controlled release of molecules, especially small sizes, which is not possible with chitosan. Chitosan is complementary since large molecules can be retained inside its three-dimensional macromolecular network, then released more or less prolonged. Other polymers of cyclodextrins exist than those of list (Al) defined above, however the latter are very specific because their very high levels of carboxylate functions (at least 3 mmol of COOH groups per gram, in particular about at least 3- 5 mmol of COOH groups per gram) are not attainable by the other polymerization or chemical modification pathways of cyclodextrin polymers. The family of polymers of the list (Al) defined above thus makes it possible to obtain hydrogels having their own shape, ie able to be molded, cut, having a firm, homogeneous and durable texture.
Preferably, the cyclodextrin polymer, in particular belonging to the list (Al), is obtained from a base mixture in which the ratio of weight (g) to cyclodextrin (s) and / or derivative (s) of cyclodextrin and / or inclusion complex (s) (derivative (s)) of cyclodextrin relative to the total weight (g) of said base mixture is greater than or equal to 40%, preferably less than or equal to 65%.
By "cyclodextrin" is meant any native cyclodextrin, in particular Γα-cyclodextrin or β-cyclodextrin or gamma-cyclodextrin.
The term "cyclodextrin derivative" is intended to mean any native cyclodextrin, in particular Γα-cyclodextrin or β-cyclodextrin or gamma-cyclodextrin, in which at least one hydroxyl group, preferably at least half of the hydroxyl groups, is / are substituted. (s), in particular amine (s), in particular by an amine (-NH2), esterified, etherified, alkylated, hydroxyalkylated, carboxyalkyl (s), in particular carboxymethyl ( s), sulfoalkylated (s), in particular sulfobutylated (s), and mixtures thereof.
Said at least one hydroxyl group of the cyclodextrin may be substituted by a linear, and / or branched, unsaturated or unsaturated or unsubstituted, substituted or unsubstituted alkyl chain comprising from 1 to 10 carbon atoms, preferably from 1 to 6 carbon atoms, still more preferably from 1 to 4 carbon atoms, especially a methyl group, an ethyl group, an n-propyl group, an isopropryl group, an n-butyl group, an iso-butyl group, a sec-butyl group, a group tert-butyl, each of said groups being optionally, and independently of each other, substituted by one or more hydroxyl groups (-OH); and / or substituted by one or more carboxylic acid groups (-COOH); and / or substituted by one or more sulfonic acid groups and / or one or more salts of said sulfonic acid functional groups. Said at least one hydroxyl group of the cyclodextrin can thus be substituted with a hydroxypropyl group or with a carboxymethyl group.
The term "cyclodextrin inclusion complex" or "cyclodextrin-derived inclusion complex" means any cyclodextrin or cyclodextrin derivative within the meaning of the present invention complexing a functional agent as defined in the present text, or complexing a cell. living as defined in this text. The person skilled in the art selects one or more cyclodextrin (s) and / or one or more cyclodextrin derivative (s) and / or one or more cyclodextrin inclusion (derivative) complex (s) capable of reacting with the crosslinking agent. In particular, with regard to the Al-list of cyclodextrin polymers, if one or more cyclodextrin derivatives are used, they must have sufficient hydroxyl groups (-OH) to be present. capable of carrying out a polycondensation reaction with the (poly) carboxylic acids and / or their corresponding anhydrides. EP 1 165 621 B1 describes the synthesis of cyclodextrin polymers obtained by polycondensation reactions between (poly) carboxylic acids and the native cyclodextrins (alpha, beta, gamma) or derivatives (methyl, hydroxypropyl cyclodextrins) which are perfectly suitable for the implementation of the invention. The polymer obtained is either soluble in water or insoluble according to the progress of the polycondensation reaction. It is characterized by a high content of cyclodextrin, between 40% and 65% by weight and by its richness in carboxylic acid functions, of the order of 3-5 mmol per gram of cyclodextrin polymer.
For the purposes of the present invention, the term "carboxylic acid" means an acid comprising a function -COOH.
Within the meaning of the present invention, the term "polycarboxylic acid" is understood to mean an acid comprising at least two -COOH functions, and by its "corresponding anhydride", an acid comprising at least one -CO-O-CO-function.
The term "pyrophosphate" means any compound comprising a P-O-P bond, in particular comprising the following function -O-PO (OH) -O-PO (OH) -O-.
According to one embodiment, the cyclodextrin polymer obtained by reaction with epichlorohydrin does not comprise carboxylic acid functions so that it undergoes a carboxyalkylation reaction, in particular carboxymethylation with the aid of chloroacetic acid so that graft -CH2COOH groups on said polymer.
The carboxyalkylation is preferably carried out with a (poly) carboxylic acid substituted with at least one chlorine, bromine or iodine atom on its alkyl chain. Preferably, the alkyl chain is linear and / or branched, unsaturated or unsaturated, substituted or unsubstituted, comprising from 1 to 10 carbon atoms, preferably from 1 to 6 carbon atoms, more preferably from 1 to 4 carbon atoms. , especially a methyl group, an ethyl group, an n-propyl group, an isopropryl group, an n-butyl group, an iso-butyl group, a sec-butyl group, a tert-butyl group.
In a variant, the pyrophosphate (A2) is sodium metatriphosphate.
In a variant, the (poly) carboxylic acid or its corresponding acid anhydride is chosen from the list comprising: saturated or unsaturated or aromatic, linear or branched or cyclic (poly) carboxylic acids and hydroxypoly (carboxylic) acids, preferably in the list comprising: citric acid, polyacrylic acid, poly (methacrylic acid), 1,2,3,4-butanetetracarboxylic acid (BTCA), maleic acid, citraconic acid , itaconic acid, 1,2,3-propanetricaboxylic acid, trans-aconitic acid, all-cis-1,2,3,4-cydopentanetetracarboxylic acid, melititic acid, pyromellitic acid , editic acid (ethylene diamine tetraacetic acid or EDTA), oxydisuccinic acid, thiodisuccinic acid or among the acid anhydrides of said (poly) carboxylic acids, such as pyromellitic dianhydride, and mixtures thereof, preferably citric acid and BTCA.
Preferably, the (poly) carboxylic acid is chosen from acyclic acids, more preferably not comprising amine functions (-NH 2), more particularly from nitrogen-free acids. The cyclodextrin polymers obtained with these acids are more hydrophilic than those obtained with cyclic acids and can be synthesized by an aqueous route, unlike, for example, the polymers obtained with pyrommelitic dianhydride, the synthesis of which must be carried out in DMF (dimethylformamide).
In one variant, the acid added to the suspension during the fourth step of the process according to the invention is chosen from the list comprising: acetic acid, in particular glacial acetic acid, formic acid, acid tartaric acid, salicylic acid, glutamic acid, propanoic acid, hydrochloric acid and mixtures thereof; preferably acetic acid and hydrochloric acid, and their mixture, more preferably acetic acid.
Preferably, said acetic acid is concentrated to at least 50%, more preferably at least 80%, more preferably at least 95%, especially at least 99%.
In a variant, the anionic cyclodextrin polymer (A) comprises at least 2 mmol / g of carboxylic acid functions (-COOH), preferably at least 3 mmol / g of carboxylic acid functions (-COOH), more preferably at least 3.5 mmol / g of carboxylic acid functions (-COOH).
The amount of carboxylic functions per g of cyclodextrin polymer can be measured by acid-base titration in the presence of colored indicators.
The measurement method consists in dissolving a determined quantity of a cyclodextrin polymer in a given volume of water in the presence of a colored indicator, for example phenolphthalein (a few drops), and then gradually adding (to the droplet) by drop), in particular using a graduated burette, a 0.1 mol / l sodium hydroxide solution to said solution with stirring (using a magnetized bar, for example) until a change is obtained. color of the solution containing the colored indicator. The number of moles of sodium hydroxide added corresponding to the number of moles of carboxylic acid functions (-COOH) neutralized.
In a variant, the ratio of the mass (g) of said at least one chitosan powder (B), relative to the total mass (g) of the hydrogel at the end of the fourth step is greater than or equal to 1%, preferably less than or equal to 8%, more preferably less than or equal to 5%, more preferably less than or equal to 4%.
In a variant, the ratio of the mass (g) of said at least one powder of the anionic polymer (A) to the total mass (g) of the hydrogel at the end of the fourth step is greater than or equal to 1%, preferably less than or equal to 20%, still preferably less than or equal to 15%, more preferably less than or equal to 10%, particularly less than or equal to 6%.
In a variant, the ratio of the mass (g) of the chitosan powder (B) to the mass (g) of the polyanion powder (A) is between 0.6 and 1.4, more preferably between 0.8 and 1.2, more preferably between 0.9 and 1.1.
In one variant, the method for manufacturing a hydrogel according to the invention comprises the addition of at least one mineral filler in powder form to the powder mixture produced during the second step, preferably the ratio of the mass ( g) mineral load relative to the total mass (g) of the powder mixture is greater than or equal to 30%.
Said at least one mineral filler is therefore intimately mixed with the powders (A) and (B). Preferably, said inorganic filler is sieved and / or (co) milled according to the embodiments defined above with respect to the powders (A) and (B), in particular as regards the size of the sieved particles.
In a variant, said at least one inorganic filler is chosen from the list comprising: bioceramics, in particular calcium phosphates, such as hydroxyapatite and calcium betatriphosphate, calcium carbonate, alumina (Al 2 O 3), zirconia (ZrO 2), glasses, ionomer glasses, titanium dioxide and a mixture of these (for bone reconstruction).
The subject of the present invention is also, according to a second aspect, a method of manufacturing a cellular material, such as a sponge, comprising a method of manufacturing a hydrogel described according to any one of the preceding embodiments with reference to a first aspect of the invention, wherein a blowing agent is added in powder form to the powder mixture in the second step.
Such a pore-forming agent may be any agent capable of being transformed into a gas under acidic conditions, with a pH of less than or equal to 5, the pores of which are formed by the molecules of carbon dioxides escaping from the hydrogel. Such blowing agents may be ammonium carbonate, ammonium bicarbonate, sodium carbonate, sodium bicarbonate, calcium carbonate, and mixtures thereof. The proportion by weight of blowing agent is between 1% and 15% relative to the total weight of the powder mixture in the second step. These compounds are available from Sigma-Aldrich.
In the state of the art, the cellular material is referred to as "porous scaffold".
The concentration of pore-forming agent affects the pore size in the cellular material. The average pore size in the cellular material is preferably greater than or equal to 1 μm and less than or equal to 1000 μm, more preferably between 100-500 μm. The pore density is between 4% and 75%.
The subject of the present invention is, according to a third aspect, a process for producing a porous cellular material, such as a sponge, comprising the implementation of the method for manufacturing a hydrogel described according to any one of the variants. previous embodiment with reference to a first aspect of the invention for obtaining a hydrogel. Said method further comprises a lyophilization step (in particular a sublimation desiccation step of the ice under a reduced atmosphere) carried out on the hydrogel obtained at the end of the fourth step for the formation of a cellular material.
Preferably, the porous cellular material is flexible and elastic, that is to say it can be compressed or stretched manually in all directions without being damaged, then resumes its initial dimensions (or close to its original dimensions) after loosening compression or stretching.
Preferably, the cellular material comprises closed pores.
This freeze-drying step can be carried out with any apparatus of the state of the art. The lyophilization is carried out for a sufficient time to remove at least 98% water, at least 99% water, more preferably at least 99.5% water.
Advantageously, this lyophilization step is carried out by arranging the hydrogel in a specific form, for example in a mold.
In a variant, the process for manufacturing a cellular material according to a second or third aspect of the invention comprises a step of heat treatment of said cellular material at a temperature greater than or equal to 100 ° C., for at least 5 minutes, in particular for at least 60 minutes, preferably at a temperature greater than or equal to 120 ° C for at least 5 minutes, in particular for at least 30 minutes, more preferably at a temperature greater than or equal to 140 ° C for at least 5 minutes .
This arrangement significantly improves the mechanical properties of the cellular material.
Advantageously, it has been observed that the compressive strength is also improved. The cellular material is compressed under the effect of a compression stress exerted manually but returns to its original shape quickly once released from this constraint. Such quality has been observed on the dry cellular material, but also after impregnation of said cellular material in water.
According to a fourth aspect, the subject of the present invention is a method for manufacturing a hydrogel according to any one of the variant embodiments described with reference to the first aspect of the invention or a process for manufacturing a cellular material, according to any of the embodiments described with reference to the second or third aspect according to the invention, comprising a step of impregnating the hydrogel or the cellular material in a solution comprising at least one functional agent and / or at least one a living cell.
Advantageously, said functional agent is selected from a first list (I) comprising anticoagulants, anti-thrombogenic agents, antimitotic agents, anti-proliferation agents, anti-adhesion agents, anti-migration agents, adhesion promoters. cells, growth factors, antiparasitic agents, anti-inflammatory agents, angiogenesis, vitamins, hormones, proteins, antifungals, antimicrobial molecules, antiseptics, antibiotics (including ciprofloxacin and chlorhexidine), nicotine, one or more essential oils, and the mixture thereof; and said at least one living cell is selected from a second list (II) comprising animal and / or human and / or plant cells.
Preferably, living cells include prokaryotic cells, eukaryotic cells, bacteria, insect cells, yeast cells, plant cells, mammalian cells, such as endothelial cells, nerve cells, lymphoblasts, fibroblasts, osteoblates, hepatocytes, stem cells, embryonic cells, adipocytes, ...; and cells designed to express a particular molecule.
The subject of the present invention is, according to a fifth aspect, a device for absorbing and draining and / or releasing a functional agent and / or supporting at least one living cell comprising: the hydrogel obtained by the implementation of the process described according to any one of the variant embodiments with reference to the first or fourth aspect according to the invention; or - comprising the cellular material obtained by the implementation of the process described according to any one of the alternative embodiments with reference to the second or third or fourth aspect according to the invention.
Advantageously, said device is chosen from: a syringe comprising at least one reservoir receiving a determined volume of hydrogel to be injected; a dressing capable of delivering at least one functional agent and / or capable of draining the skin, and a patch capable of delivering at least one functional agent, such as nicotine.
The subject of the present invention is, according to a sixth aspect, a hydrogel obtainable by implementing the manufacturing method according to any one of the variant embodiments with reference to the first or fourth aspect according to the invention, comprising advantageously: a cyclodextrin polymer (A) obtained by the polymerization reaction of a mixture comprising at least one cyclodextrin and / or at least one cyclodextrin derivative and / or at least one cyclodextrin inclusion complex and / or at least one inclusion complex derived from cyclodextrin, with at least one (poly) carboxylic acid and / or its corresponding (poly) carboxylic acid anhydride (Al); or - at least one pyrophosphate (A2), or - at least epichlorohydrin, the polymer obtained undergoing a carboxymethylation step in order to graft carboxylic acid functions (-COOH) (A3), and - chitosan (B) comprising amine functions (NH2).
Preferably, the cyclodextrin polymer belongs to the (Al) family.
In one variant, the anionic polymer (A) comprises carboxylic acid functions (-COOH).
In a variant, the anionic polymer (A) comprises at least 3 mmol / g of carboxylic acid functional groups (COOH).
Preferably, the embodiments and definitions described above with reference to any of the one to five aspects characterizing the hydrogel apply independently to the hydrogel according to a sixth aspect of the invention.
DETAILED DESCRIPTION OF THE DRAWINGS FIGS. 1A and 1B show a hydrogel which has been obtained by a process different from the method for manufacturing a hydrogel according to the invention; - Figures 2A and 2B show a hydrogel obtained by the implementation of the manufacturing process; FIG. 3 represents the curves of the elastic modules G 'of cellular materials according to the invention. FIG. 4 is a histogram representing on the ordinate the amount of ciprofloxacin (CFX) absorbed in mg per g of different cellular materials; FIG. 5 is a graph showing the ciprofloxacin release curves as a function of time of different cellular materials corresponding to those referenced in FIG. 4; FIG. 6 represents the graphs of the evolutions of the elastic and viscous modules G 'and G "of an exemplary hydrogel according to the invention as a function of time (minutes) and of two alternately applied stresses A and B; Figures 7 and 8 are photographs showing hydrogels according to the invention respectively 1 hour and 24 hours after their formation.
Detailed description of the invention
The present invention will be better understood on reading the exemplary embodiments described below and cited by way of non-limiting example.
The compounds used are the following: chitosan powder (CHT1): "Chitosan - Medium molecular weight" (Medium Mw: 431,000 g / mol) sold by Sigma Aldrich, case number: 9012-76-4, in the form of powder, the viscosity is 563.00 cps at a concentration of 1% in 1% acetic acid, the degree of deacetylation is greater than or equal to 75%. chitosan powder (CHT2): "Chitosan - Low molecular weight" (LowMw: 39,000 g / mol) sold by Sigma Aldrich, case no .: 9012-76-4, in the form of a powder and / or granules, the viscosity is 96 cps at a concentration of 1% in 1% acetic acid, the degree of deacetylation is greater than or equal to 75%. -Chitosan powder (CHT3): "Chitosan - High molecular weight" (HighMw: 1,250,000 g / mol) sold by BioResources, Case No .: 9012-76-4, in the form of powder and / or granules, the degree of deacetylation is greater than or equal to 75%. cyclodextrin polymer: the polymer is synthesized as follows: 400 g of β-cyclodextrin (Kleptose®, Roquette Frères, Lestrem, France), 400 g of citric acid CAS 77-92-9, Sigma Aldrich, Saint Quentin Fallavier , France), and 120 g of sodium hypophosphite (Sigma Aldrich, Saint Quentin Fallavier, France) are dissolved in 2 liters of an aqueous solution (distilled water). The water of this aqueous solution is then evaporated to dryness under vacuum at 60 ° C. under 58 mm of mercury in a rotary evaporator for a time sufficient to obtain a solid mixture. The solid residue of evaporation is then heated under vacuum at 140 ° C. for 120 minutes. Then, the solid mixture is suspended in 2 liters of distilled water. This suspension is filtered on sintered glass. The insoluble polymer is recovered in the filter, which is washed thoroughly with water and then dried at room temperature for one week (it could also be dried for example in a ventilated oven at 60 ° C. for 24 hours). The filtrate comprising the soluble polymer is dialyzed on a 6000-8000 dalton membrane for 5 days, and then the dialyzed solution is concentrated using a rotary evaporator. The purified filtrate is frozen and then freeze-dried, using a Christ model alpha 1-2 / LD freeze-dryer at a temperature of -63 ° C., under vacuum at 0.06 mbar, for a sufficient time to obtain a solid in powder form. The purified filtrate can be, alternatively to lyophilization, also atomized, for example using the Buchi B-290 atomizer.
71 g of soluble cyclodextrin polymer (CDsl) and 320 g of insoluble cyclodextrin polymer (Cdil) are thus obtained. Polyacrylic Acid (PAA): Product Code (323667-250G)
Mw = 1,800 and Mw = 450,000 provided by Sigma Aldrich® - Sodium alginate: product code (180947-500G), Lot (09611 DD), Sigma Aldrich® - Apple-pectin pectin (Poly-D-galacturonic acid methyl ester): Product code (75282-500G), Lot (BCBG 4396V), Sigma Aldrich® I- Description of the procedure for the determination of the IEC ("Ionic Echanae Capacity") of the cyclodextrin polymer fCdsl or Cdilj. that is to say, the number of carboxylic acid functional groups f-COOH in mmoles per gram of cyclodextrin polymer: 100 mg of polymer (CDsl or Cdil) are dissolved in 100 ml of 0.1M NaCl solution and are then assayed by standard 0.1 M sodium hydroxide in the presence of phenolphthalein as a colored indicator The current IEC is approximately 4 mmol per gram of polymer (CDsl or Cdil), which is quite similar to that of chitosan which has about 5 mmol of functions amines per gram (for a degree of deacetylation of about 80%). related to the IEC proximity of chitosan and cyclodextrin polymer (according to the Al family), and is related to the proportions of chitosan and cyclodextrin polymer brought together for gel formation. II-Examples of Preparation of Hydroel According to the Invention and Comparative
The proportions indicated in w / w represent the ratio between the mass of the added component and the total mass of the hydrogel, therefore at the end of the fourth step of the process according to the invention.
Example 1: 0.04g of chitosan (CHT1) (2% w / w) and 0.05g (2.5% w / w) of the cyclodextrin polymer (CDsl) were co-milled in a mortar for 1 minute. The powder obtained was suspended in 1.89 g of ultrapure water and then vortexed for 15 seconds (the instantaneous pH of the solution is 3.5, which goes back to 4.1). 0.02 g of a solution of glacial acetic acid was then added to the suspension (the pH drops during the addition of acid to 3.2 and then rises above 5) which will be mixed with vortex for 20 seconds. A compact gel is obtained from the first seconds during stirring. The hydrogel obtained comprises 89% water.
Example 2: 0.04 g (2% w / w) of chitosan (CHT1) and 0.06 g (3% w / w) of the cyclodextrin polymer (CDsl) were co-milled in a mortar for 1 minute. The resulting powder was suspended in 1.88 g of ultrapure water and then mixed with a vortex for 15 seconds. 0.02 g of a solution of glacial acetic acid was then added to the suspension which will be vortexed for 20 seconds. A compact gel is obtained from the first seconds during stirring. The hydrogel obtained comprises 72% water.
Example 3: 0.04 g (2% w / w) of chitosan (CHT1) and 0.20 g (10% w / w) of the cyclodextrin polymer (CDsl) were co-milled in a mortar for 1 minute. The resulting powder was suspended in 1.74 g of ultrapure water and then vortexed for 15 seconds. 0.02 g of a solution of glacial acetic acid was then added to the suspension which will be vortexed for 20 seconds. A compact gel is obtained from the first seconds during stirring. The hydrogel obtained comprises 60% water.
Example 4: 0.05 g (2.5% w / w) of chitosan (CHT1) and 0.06 g (3% w / w) of the cyclodextrin polymer (CDsl) were co-milled in a mortar for 1 minute. The resulting powder was suspended in 1.87 g of ultrapure water and then vortexed for 15 seconds. 0.02 g of a solution of glacial acetic acid was then added to the suspension which will be vortexed for 20 seconds. A compact gel is obtained from the first seconds during stirring. The hydrogel obtained comprises 93% water.
Example 5: 0.02 g (1% W / W) of chitosan (CHT1) and 0.04 g (2% w / w) of the cyclodextrin polymer (CDsl) were co-milled in a mortar for 1 minute. The resulting powder was suspended in 1.92 g of ultrapure water and then vortexed for 15 seconds. 0.02 g of a 1% acetic acid solution was then added to the suspension which would be vortexed for 20 seconds. The gel obtained is not compact and tends to flow slowly.
Example 6: 0.06 g (3% w / w) of chitosan (CHT1) and 0.04 g (2% w / w) of the cyclodextrin copolymer (CDsl) were co-milled in a mortar for 1 minute. The resulting powder was suspended in 1.88 g of ultrapure water and then mixed with a vortex for 15 seconds. 0.02 g of a 1% acetic acid solution was then added to the suspension which would be vortexed for 20 seconds. The gel obtained from the first seconds during stirring is very compact, does not flow, and is moldable.
Example 7: 0.04 g (2% w / w) of chitosan (CHT1) and 0.02 g (1% W / W) of the cyclodextrin polymer (CDsl) were co-milled in a mortar for 1 minute. The powder obtained was suspended in 1.92 g of ultrapure water and then vortexed for 15 seconds. 0.02 g of a 1% acetic acid solution was then added to the suspension which would be vortexed for 20 seconds. The gel obtained tends to flow.
Example 8: 0.06g of chitosan (CHT1) (3% w / w) and 0.06g (3% w / w) of the cyclodextrin polymer (CDsl) were co-milled in a mortar for 1 minute. The resulting powder was suspended in 1.86 g of ultrapure water and then vortexed for 15 seconds. 0.02 g of a solution of glacial acetic acid was then added to the suspension which will be vortexed for 20 seconds. A compact gel is formed from the first seconds during agitation, homogeneous, and not flowing by gravity is obtained.
Example 9: 0.06g of chitosan (CHT1) (3% w / w) and 0.1g (5% w / w) of the cyclodextrin polymer (CDsl) were co-milled in a mortar for 1 minute. The resulting powder was suspended in 1.82 g of ultrapure water and then vortexed for 15 seconds. 0.02 g of a solution of glacial acetic acid was then added to the suspension which will be vortexed for 20 seconds. A compact gel is formed from the first seconds during agitation, homogeneous, and not flowing by gravity is obtained.
Example 10: identical to Example 8 except that the chitosan is that of the reference CHT2.
Example 11: identical to Example 8 except that the chitosan is that of the reference CHT3.
For Examples 10 and 11, the resulting hydrogel is firm, compact, and homogeneous. It does not flow if we return the container.
Example 12: identical to Example 8 except that the amount of chitosan is 3% w / w and the amount of the cyclodextrin polymer (CDsl) is 10% w / w The hydrogel obtained is firm and compact but more viscous, thick than the other hydrogels exemplified according to the invention. Comparative Example 13: Same as Example 8 except that the cyclodextrin polymer (CDsl) is replaced by a commercial carboxymethylcyclodextrin sodium salt monomer (Aldrich, reference 21906). The hydrogel obtained flows if the container is returned and is not firm.
Example 14: identical to Example 8 except that the cyclodextrin polymer (CDsl) is replaced by a polyacrylic acid polymer of Mw 1800 (referenced above).
Example 14A: identical to Example 8 except that the cyclodextrin polymer (CDsl) is replaced by pectin (referenced above).
Example 14B: identical to Example 8 except that the cyclodextrin polymer (CDsl) is replaced by sodium alginate (referenced above).
Figure 7 shows the hydrogels of Examples 8, 14, 14A and 14B, one hour after their formation. Figure 8 shows the hydrogels of Examples 8, 14, 14A and 14B after 24 hours. It is observed that the hydrogels formed from these polyanions are firm and do not flow even 24 hours after their formation.
Example 15: identical to Example 8 except that the chitosan polymer is replaced by a polyacrylic acid polymer of high molecular weight (Mw: 450 000, referenced above).
The hydrogels in Examples 14 and 15 obtained are firm and do not flow.
Control Example 16: identical to Example 8 except that the cyclodextrin polymer used is synthesized by replacing the β-cyclodextrin with maltodextrin (which does not include a cavity). The gel formed is firm and does not flow.
Comparative Example 17: 0.3 g of chitosan (CHT1) (3% w / w), crushed and screened on a sieve having orifices of 125 μm, is solubilized in a volume of 9.3 ml of ultrapure water (93% w / w ) in which 0.1 mL of glacial acetic acid is added (1% w / w), the whole is mixed at about 10,000 rpm with an ultra turrax® for one minute. Then, 0.3 g of the cyclodextrin polymer (CDsl (3% w / w), also milled and sieved through a sieve having 125 μm orifices, is added to the acid solution of chitosan (CHT1), the solution is then mixed with approximately 10,000 rpm using an ultra-turrax® for 1 minute The measured gel time resulting from the G 'and G "values is greater than 5 days The gel formed is" liquid ", present lumps, is not homogeneous and is not moldable (it flows by the action of gravity) .The addition of the anionic polymer (CDsl) to an acidic solution of chitosan therefore does not allow to form A hydrogel of clean, firm and compact form The hydrogel obtained is shown in Figures IA and IB.It is noted that in the pot in which it was synthesized in Figure IA, the hydrogel flows on the walls, it n Therefore, in FIGURE 1B, the hydrogel does not retain the shape of the bead which has been imparted to it when it is deposited on a horizontal surface. ontale using a syringe.
Comparative Example 18: 0.3 g of chitosan powder (CHT1) (3% w / w), unscreened and unmilled, and 0.3 g of powder of the cyclodextrin polymer (CDsl) (3% w / w), not sieved and unmilled, are co-milled dry which reduces their particle size and mix. The coarse powders mixture is added in 9.3 ml of ultrapure water (93% w / w), the resulting aqueous solution is then mixed with vortex for 20 seconds, and then 0.1 ml (1% V / V) of a solution. glacial acetic acid are added. The measured gel time resulting from the values of G 'and G "is greater than 2.5 hours The firmness of the hydrogel is correct but it has lumps.
Comparative Example 19: 0.3 g of chitosan powder (CHT1) (3% w / w), milled and sieved through a sieve having 125 μm orifices, and 0.3 g of cyclodextrin copolymer powder (CDsl) (3% w / w), crushed and sieved through a sieve having 125 μm orifices, are co-milled dry. The cobweb powders mixture is suspended in 9.3 ml of ultrapure water (93% w / w) with stirring at about 10,000 rpm using an ultra-turrax® for 20 seconds. Then, 0.1 ml (1% V / V) of a solution of glacial acetic acid was then added to the suspension which will be mixed with stirring at about 10,000 rpm using an ultra-turrax® for 20 seconds. The measured gel time resulting from the values of G 'and G "is greater than 2.5 hours The gel formed has a good texture, is smooth, homogeneous and firm, that is to say that it does not flow under the action of gravity and will be able to be molded in a specific form.This hydrogel is shown in Figures 2A and 2B Note in Figure 2A that the hydrogel does not flow on the walls of the pot in which it was It is noted that the hydrogel retains its bead shape, which has been imparted to it at the outlet of a syringe, and that it is homogeneous. smooth and does not flow.
The gel times measured for Examples 17, 18 and 19 are derived from the curves of elastic and viscous modules G 'and G "established as a function of time, with a stress of 100%, a gamma amplitude of 100%, an angular frequency omega of 10s-1 at a temperature of 25 ° C using a dynamic mechanical spectrometer, such as those marketed by Anton Paar.
Example 20: 0.3 g of chitosan (CHT1) (3% w / w), 0.3 g (3% w / w) of the cyclodextrin polymer (CDsl) and 0.3 g of hydroxyapatite (3% w / w), ie 33.3 % of the total weight of the dry mixture of powders were co-milled in a mortar for 1 minute. The resulting powder mixture was suspended in 9 ml of ultrapure water and then vortexed for 15 seconds. 0.01 ml (0.1% w / w) of a solution of glacial acetic acid was then added to the suspension which would be vortexed for 45 seconds. A compact gel, homogeneous, and not flowing under the effect of gravity is obtained. III- Manufacture of a cellular material according to the invention
Example 21: The hydrogel of Example 8 underwent a lyophilization step for the formation of a cellular material using a Christ model alpha 1-2 / LD freeze-dryer at a temperature of -63 ° C. under vacuum at 0.06 mbar for at least 24 hours. The swelling rate is 1739.0% in water at room temperature after 6 hours and 445.0% in PBS (Phosphate Buffer Saline, pH 7.4, 0.1M) at room temperature after 6 hours ([( wet mass - dry mass) / dry mass * 100).
Example 22: The hydrogel of Example 9 underwent a lyophilization step for the formation of a cellular material using a Christ model alpha 1-2 / LD freeze-dryer at a temperature of -63 ° C. under vacuum at 0.06 mbar for at least 24 hours. The swelling rate is 262.0% in water at room temperature after 6 hours and 336.0% in PBS (Phosphate Buffer Saline, Ph7.4, 0.3M) at room temperature after 6 hours ([( wet mass - dry mass) / dry mass * 100).
Example 23: The cellular material of Example 21 undergoes heat treatment consisting of placing the latter in a chamber at 140 ° C for 1 hour. This heat treatment makes it possible to crosslink the cellular material by transforming the ionic bonds into covalent bonds, in particular amide bonds. It is then observed that the resistance to compression, that is to say to crushing, of the cellular material is very significantly improved. This is observed visually by crushing the honeycomb material of Example 23 between two fingers, the latter covers its shape after removal of the deformation almost instantly unlike the foam material of Examples 21 or 22. Note in Figure 3 representing the curves of the elastic modules G 'of Examples 22 and 21 that the elastic modulus G' of Example 23 having undergone heat treatment is significantly higher than the elastic modulus G 'of Example 21.
Example 24: Same as Example 21 except that the hydrogel was synthesized with 10% (w / w) of the cyclodextrin polymer (CDsl).
Control Example: The hydrogel of Example 16 underwent a lyophilization step for the formation of a cellular material.
Example 26: The hydrogel of Example 20 was lyophilized using a Christ model alpha 1-2 / LD freeze-dryer at -63 ° C under vacuum at 0.06 mbar. for at least 24 hours for the formation of a cellular material containing hydroxyapatite (33.3% w / w). IV- Measurement of the cytocompatibility
The cytocompatibility of the hydrogel obtained in Example 8 and the foam materials of Examples 21 and 22 was tested according to ISO 10993-5: 2009 - Biological evaluation of medical devices - Part 5: Tests for in vitro cytotoxicity. Cellular vitality method using the Alamar blue-extraction method-L132 cells (ATCC-CCL5).
The vitality measured for Example 8 is 80% after 1 hour and is 84% after rinsing for 1 hour in PBS (Phosphate Buffer Saline, pH 7.4, 0.1M). The vitality measured for Example 21 is 91% and is 85% for Example 24 after one hour. V-impregnation of the cellular materials 40 mg of the cellular materials of Examples 21, 22, 24 and 25 are impregnated in an aqueous solution at 2 mg / ml of ciprofloxacin at room temperature with stirring at 250 rpm for 4 hours.
The alveolar materials thus treated are placed for 24 hours in a 0.1N sodium hydroxide solution at 37 ° C. in order to extract the adsorbed ciprofloxacin. The solutions obtained are titrated with a UV spectrophotometer at a wavelength of 271 nm in order to measure the amount of ciprofloxacin absorbed (mg / g) for each of the cellular materials. The absorption curves obtained are shown in FIG. 4. The vertical bars on each histogram represent the standard deviations. It is thus noted that the standard deviation for example 25 which is based on maltodextrin is higher by that measured for the other examples based on cyclodextrins. This shows that the loading rate of the active ingredient is more random if the dextrin used does not have a hydrophobic cavity, and therefore does not form an inclusion complex. Examples 21, 22 and 24 indicate that the adsorption capacity of the hydrogels obtained from the cyclodextrin polymer varies according to the hydrogel preparation parameters, however the differences are not significant.
The ciprofloxacin release conditions are studied in closed circuit by injecting a flow of PBS at a temperature of 37 ° C. to 30 ml / min, from a 500 ml PBS reservoir, into 30 mg of cellular material impregnated with ciprofloxacin. The outflow of PBS from the cellular material is then passed through a UV spectrophotometer (wavelength 271 nm) which measures the amount of ciprofloxacin released, which flow is then redirected to the PBS reservoir. The release rate of ciprofloxacin (%) is measured in relation to the absorbed level measured previously and shown in FIG. 4. The curves of the ciprofloxacin release rates, represented in FIG. 5, show a very significant difference in the release profile. ciprofloxacin, which is very fast for the maltodextrin-based polymer (Example 25), and slowed down for the foam materials of Examples 21, 22 and 24. VI- Rheofluidifying Properties of the Hydrogel According to the Invention (Example 8)
Specifications of the measuring device used: Rheometer (MCR301-Anton-Paar):
Table 1
The graph shown in FIG. 6 represents the evolution of the elastic and viscous moduli G 'and G "of the hydrogel of Example 8 subjected to two stress cycles A and B at tO, G' (230 Pa)> G "(130 Pa) then the stress A applied for 45 minutes causes a decrease in G 'until its value is equal to that of G." The termination of the stress A followed by the immediate application of the constraint B causes an instantaneous increase in G 'which returns to a value close to that of the beginning of the experiment (200 Pa) After 5 minutes of stress B, the constraint A is reapplied, and G' returns to its minimum value. stress A and B over periods of 5 minutes during 3 successive cycles shows a reversible variation of the modulus G ', which indicates that the hydrogel exhibits a viscous or elastic type of behavior as a function of the applied stress. a material with rheofl behavior uidifier (and therefore thixotropic). By means of this measurement, it is shown that the hydrogel has the necessary properties to be considered as injectable, that is to say applicable by means of a syringe: when pushing on the piston of the syringe, the gel fluidizes in the needle or the catheter by the action of the shear forces, and once in place in the site of its implantation (bone defect for example), the hydrogel freezes again and finds a sufficient cohesion for stay in place. VII- Mechanical Thermo Dynamic Analysis (DMTA) of the foam material of Examples 21 and 23
Device Specifications: Rheometer (MCR301-Anton-Paar).
Table 2
Characteristics of the sample analyzed by DMTA and results of the DMTA:
Table 3
Table 3 above shows the viscoelastic results of the foam materials (such as sponges) of Examples 21 and 23. After 20 minutes of analysis at 25 ° C., it is observed that the elastic modulus (GO is greater than the modulus viscous (G "), which makes it possible to demonstrate that the cellular materials of Examples 21 and 23 both exhibit an elastic behavior, It is also noted that the values of the two modules G 'and G" of Example 23 are clearly higher than those of Example 21. The heat treatment applied to Example 23 thus improves the mechanical performance of the cellular material, it can thus be concluded that during this heat treatment step, the intramolecular behavior has been modified, probably because of transformation of ionic bonds into covalent bonds which gives the foam material of Example 23 a certain stiffening.

权利要求:
Claims (19)
[1" id="c-fr-0001]
1. A method of manufacturing a hydrogel characterized in that it comprises the following successive steps: a first step of supplying at least one powder of an anionic polymer (A) and at least one chitosan powder (B) comprising amine functions (-NH2); a second step of dry blending at least the powders (A) and (B) of the first step to form a mixture of powders; a third step of suspending the mixture of powders obtained at the end of the second step in an aqueous medium having a pH making it possible to solubilize the anionic polymer (A) without solubilizing the chitosan (B); - A fourth step of adding an acid to the suspension obtained at the end of the third step so as to form the hydrogel.
[2" id="c-fr-0002]
2. Method according to claim 1, characterized in that the powder (A) and / or the powder (B) in the first step and / or the mixture of the powders comprising at least the powders (A) and (B) at the second step esl / are sieved (s) on a sieve mesh less than or equal to 500 pm, in particular less than or equal to 150 pm.
[3" id="c-fr-0003]
3. Method according to either of claims 1 and 2, characterized in that the mixture of the second step is carried out by dry co-grinding at least powders (A) and (B).
[4" id="c-fr-0004]
4. Process according to any one of the preceding claims, characterized in that the anionic polymer comprises acidic sulphate functional groups (-O-S (= O) 2 -OH) and / or salts known as acid sulphate functional groups, and / or sulphonic acid functional groups (-S (= O) 2 -OH) and / or sulphonic acid functional salts, and / or phosphoric acid-based (-O-Ρ (= O) 2ΌΗ) and / or salts of said phosphoric acids, and / or carboxylic acid functions (-COOH) and / or salts known as carboxylic acid functions.
[5" id="c-fr-0005]
5. Method according to any one of the preceding claims, characterized in that the anionic polymer (A) is a cyclodextrin polymer obtained by the polymerization reaction of a mixture comprising at least one cyclodextrin and / or at least one derivative of cyclodextrin and / or at least one cyclodextrin inclusion complex and / or at least one inclusion complex derived from cyclodextrin, with at least one (poly) carboxylic acid and / or its corresponding (poly) carboxylic acid anhydride (Al); or - at least one pyrophosphate (A2); or at least epichlorohydrin, the polymer obtained undergoing a carboxyalkylation step in order to graft carboxylic acid functions (A3).
[6" id="c-fr-0006]
6. Process according to any one of the preceding claims, characterized in that the anionic cyclodextrin polymer (A) comprises at least 2 mmol / g of carboxylic acid functional groups (-COOH).
[7" id="c-fr-0007]
7. Method according to any one of the preceding claims, characterized in that the ratio of the mass (g) of chitosan powder (B), relative to the total mass (g) of the hydrogel at the end of the fourth step is greater than or equal to 1%, preferably less than or equal to 8%.
[8" id="c-fr-0008]
8. Method according to any one of the preceding claims, characterized in that the ratio of the mass (g) of the powder of the anionic polymer (A) relative to the total mass (g) of the hydrogel at the end of the fourth step is greater than or equal to 1%, preferably less than or equal to 20%.
[9" id="c-fr-0009]
9. Process according to any one of the preceding claims, characterized in that it comprises the addition of at least one mineral filler in powder form to the powder mixture produced during the second stage, preferably the ratio of mass (g) of mineral filler (s) relative to the total mass of the powder mixture is greater than or equal to 30%.
[10" id="c-fr-0010]
10. The manufacturing method according to claim 9, characterized in that said inorganic filler is selected from the list comprising: bioceramics, in particular calcium phosphates, such as hydroxyapatite, calcium betatriphosphate, calcium carbonate; alumina (Al2O3), zirconia (ZrO2), glasses, ionomer glasses, titanium dioxide, and a mixture thereof.
[11" id="c-fr-0011]
11. A method of manufacturing a cellular material, characterized in that it comprises a method of manufacturing a hydrogel according to any one of claims 1 to 10 wherein a blowing agent is added in powder form to the mixture of powders during the second stage.
[12" id="c-fr-0012]
12. A method of manufacturing a cellular material, characterized in that it comprises a method of manufacturing a hydrogel according to any one of claims 1 to 10 for obtaining the hydrogel and in that it further comprises a lyophilization step carried out on the hydrogel obtained at the end of the fourth step for the formation of a cellular material.
[13" id="c-fr-0013]
13. The manufacturing method according to either of claims 11 and 12, characterized in that it comprises a step of heat treatment of the cellular material at a temperature greater than or equal to 100 ° C, for at least 5 minutes. .
[14" id="c-fr-0014]
14. A method of manufacturing a hydrogel according to any one of claims 1 to 10, characterized in that it comprises a step of impregnating the hydrogel in a solution comprising at least one functional agent and / or at least one a living cell, and in that said functional agent is selected from a first list (I) comprising anticoagulants, anti-thrombogenic agents, anti-mitotic agents, anti-proliferation agents, anti-adhesion agents, anti-migration agents , cell adhesion promoters, growth factors, antiparasitic molecules, anti-inflammatory agents, angiogenesis, vitamins, hormones, proteins, antifungals, antimicrobial molecules, antiseptics, antibiotics, in particular ciprofloxacin, nicotine, one or more essential oils, and the mixture thereof; and said at least one living cell is selected from a second list (II) comprising human, animal and plant cells.
[15" id="c-fr-0015]
15. A method of manufacturing a cellular material according to any one of claims 11 to 13, characterized in that it comprises a step of impregnating the cellular material in a solution comprising at least one functional agent and / or at least one a living cell, and in that said functional agent is selected from a first list (I) comprising anticoagulants, anti-thrombogens, anti-mitotic agents, anti-proliferation agents, anti-adhesion agents, anti-migration agents , cell adhesion promoters, growth factors, antiparasitic molecules, anti-inflammatory agents, angiogenesis, vitamins, hormones, proteins, antifungals, antimicrobial molecules, antiseptics, antibiotics, in particular ciprofloxacin , nicotine, one or more essential oils, and the mixture thereof; and said at least one living cell is selected from a second list (II) comprising human, animal and plant cells.
[16" id="c-fr-0016]
16. A device for absorbing and draining and / or releasing a functional agent and / or carrier for living cells, comprising the hydrogel obtained by carrying out the process described according to any one of claims 1 to 10 and 14, characterized in that said device is a device chosen from: a syringe comprising at least one reservoir receiving a determined volume of hydrogel; a dressing capable of delivering at least one functional agent and / or capable of draining the skin, a patch capable of delivering at least one functional agent, such as nicotine.
[17" id="c-fr-0017]
17. A device for absorbing and draining and / or releasing a functional agent and / or carrier for living cells, comprising the cellular material obtained by carrying out the method described according to any one of claims 11 to 13 and 15, characterized in that said device is a device chosen from: a syringe comprising at least one reservoir receiving a determined volume of hydrogel; a dressing capable of delivering at least one functional agent and / or capable of draining the skin, a patch capable of delivering at least one functional agent, such as nicotine.
[18" id="c-fr-0018]
18. Hydrogel obtainable by the implementation of the manufacturing method according to any one of claims 1 to 10 and 14, characterized in that it comprises: - a cyclodextrin polymer (A) obtained by the reaction polymerizing a mixture comprising at least one cyclodextrin and / or at least one cyclodextrin derivative and / or at least one cyclodextrin inclusion complex and / or at least one cyclodextrin-derived inclusion complex, with at least one a (poly) carboxylic acid and / or its corresponding (poly) carboxylic acid anhydride (Al); or - at least one pyrophosphate (A2), or - at least epichlorohydrin, the polymer obtained undergoing a carboxalkylation step in order to graft carboxylic acid functions (-COOH) (A3), and - a polymer of chitosan (B ) comprising amine functions (NH2).
[19" id="c-fr-0019]
19. Hydrogel according to claim 18, characterized in that the cyclodextrin polymer (A) comprises at least 2 mmol / g of carboxylic acid functions (COOH).

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同族专利:

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公开号 | 公开日

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JP2018519120A|2018-07-19|

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US11168183B2|2021-11-09|

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EP3317326B1|2020-11-18|

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FR3038318B1|2017-08-04|

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ES2854712T3|2021-09-22|

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WO2017001808A1|2017-01-05|

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CN107949598A|2018-04-20|

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CN107949598B|2021-07-09|

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EP3317326A1|2018-05-09|

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US20180186939A1|2018-07-05|

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CA2991000A1|2017-01-05|

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优先权:

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申请号 | 申请日 | 专利标题

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FR1556283A|FR3038318B1|2015-07-02|2015-07-02|PROCESS FOR THE PRODUCTION OF CHITOSAN-BASED HYDROGEL AND NEGATIVELY LOADED POLYELECTROLYTES AND POROUS ALVEOLAR MATERIALS FROM SAID HYDROGEL|FR1556283A| FR3038318B1|2015-07-02|2015-07-02|PROCESS FOR THE PRODUCTION OF CHITOSAN-BASED HYDROGEL AND NEGATIVELY LOADED POLYELECTROLYTES AND POROUS ALVEOLAR MATERIALS FROM SAID HYDROGEL|

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US15/740,414| US11168183B2|2015-07-02|2016-07-01|Method for the production of hydrogel comprising chitosan and negatively charged polyelectrolytes, and cellular, porous material resulting from said hydrogel|

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EP16750922.3A| EP3317326B1|2015-07-02|2016-07-01|Method for the production of hydrogel comprising chitosan and negatively charged polyelectrolytes, and cellular, porous material resulting from said hydrogel|

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ES16750922T| ES2854712T3|2015-07-02|2016-07-01|Method for the production of hydrogels based on chitosan and negatively charged polyelectrolytes and foamed porous material obtained from said hydrogel|

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CA2991000A| CA2991000A1|2015-07-02|2016-07-01|Method for the production of hydrogel comprising chitosan and negatively charged polyelectrolytes, and cellular, porous material resulting from said hydrogel|

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JP2017568414A| JP2018519120A|2015-07-02|2016-07-01|Method for producing hydrogel comprising chitosan and negatively charged polyelectrolyte and cellular porous material obtained from said hydrogel|

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PCT/FR2016/051684| WO2017001808A1|2015-07-02|2016-07-01|Method for the production of hydrogel comprising chitosan and negatively charged polyelectrolytes, and cellular, porous material resulting from said hydrogel|