Patent Application
20110123589
The present invention relates to three-dimensional nanocomposite materials comprising a complex polymeric matrix consisting of a polysaccharidic composition of neutral or anionic polysaccharides and of branched cationic polysaccharides, in which metallic nanoparticles are uniformly dispersed and stabilized, said branched cationic polysaccharides so forming a metal-based nanocomposite. The invention further concerns the preparation and use of said three-dimensional nanocomposite materials in biomedical, pharmaceutical and food fields.
Natural polysaccharides have been generally recognized as biocompatible polymers; as such, they are well-studied materials employed since long time for applications in biomedical field, for example as carriers of biologically active compounds or cells for tissue engineering. Among the most used ones in both pharmaceutical and food industry, alginates and chitosan may be mentioned for their abundance, relatively low cost, high biocompatibility and ability to produce in appropriate conditions three-dimensional matrices in the form of hydrogels with high water content. However, chitosan exhibits some application limits linked to its marked dependence of its water solubility from pH, its non-miscibility in aqueous solutions with anionic polysaccharides such as alginate, with which it produces coacervates not usable for applicative purposes, such as for example in tissue engineering. Chitosan shares with alginates a further limit inasmuch as it does not carry any cell-specific signal thus lacking bioactivity. For these reasons chitosan derivatives, which can overcome the above-mentioned limits, are currently studied and developed.
In the recent years, different chitosan derivates were obtained by means of chemical modification of the polymeric chain. For these modifications, reactions involving the amino residue of the D-glucosamine units, forming the linear chitosan chain, are extensively used. In particular, introducing saccharidic units (mono- and oligo-saccharides) as the N-linked side chain, allowed to obtain water-soluble chitosan derivatives without the need of lowering pH down to acidic values, in this manner also avoiding the possible resulting problems of degradation of the polymer due to the acidity of the aqueous solutions.
In U.S. Pat. No. 4,424,346 (Hall, L. D. and Yalpani, M.) the synthesis of these derivatives was described for the first time as well as the aqueous solubility thereof in a non-acidic aqueous medium. In particular, U.S. Pat. No. 4,424,346 disclosed that the chitosan derivative with lactose produces rigid gels in aqueous solutions at concentrations higher than 3-5%, while it does not gel nor precipitate in salts or acids mixtures (in particular with Ca, Cr, Zn chlorides, K chromate, boric acid) and combinations thereof. Moreover, the aforesaid patent mentioned the fact that the chitosan derivatized with another oligosaccharide, that is cellobiose, does not form gels in aqueous solutions per se, while it forms rigid gels when mixed with alginate. This gel formation is due to the strong interaction between the positive polycation charges and the negative polyanion charges, which leads to a system coacervation, a process that otherwise is a limit in its use, for example, for microencapsulation of biologic material such as cells.
Patent Application WO2007/135116 (Paoletti S. et al.) describes methods for preparing polymeric solutions containing mixtures of anionic and cationic polysaccharides to overcome the problem of coacervation and the use thereof in biomedical field.
In addition, Patent Application WO2007/135114 (Paoletti S. et al.) describes three-dimensional structures, both hydrated or non-hydrated, and methods of preparing them from the above-mentioned polymeric mixtures of anionic and cationic polysaccharides gelled with appropriate gelling agents, useful for the purpose to encapsulate pharmacologically active molecules and cells.
Another remarkably interesting research area related to nanotechnologies and with a great topical interest for polysaccharides is their possible use for preparing nanocomposite materials, comprising in particular metallic nanoparticles. Indeed, in order to stabilize the nanoparticles, polysaccharidic solutions, which allow to obtain nanocomposite systems wherein the metallic particles are homogeneously dispersed due to the interactions with the polymeric chains, could be profitably used. Therefore, the role of polysaccharides is related to formation and stabilization of metallic nanoparticles by expecting the possibility of exploiting their particular properties; indeed, metallic nanoparticles are known to be provided with particular optical, catalytic and antimicrobial properties. In fact, the use of metals, such as silver, gold, copper, zinc and nickel, in the field of antimicrobial materials is greatly impacting on the market, especially for treating skin wounds. Companies such as Johnson&Johnson© and Convatec© recently have commercialized medications based on the antibacterial properties of silver nanoparticles. Similar applications could be found by appropriate polysaccharides-based nanocomposite materials to exploit the well-known antimicrobial activity of these metals, for example, for the development of gauzes, bandages, patches. The latter products could be endowed with a broad-spectrum antimicrobial activity or high water content gels with bactericidal activity. Indeed, the need for novel therapeutic aids for treating skin or mucosa lesions, such as burns and ulcerations, is still felt. These lesions are often very resistant to the currently adopted antibiotic therapies; in addition, they also need further biological effects for tissue repair, for example enhancing cell proliferation, and/or appropriate tissue hydration. The three-dimensional hydrogel structure may be particularly advantageous especially for the latter aspect, being able to ensure an appropriate environment for cell replication without interfering with cell phenotype.
Furthermore, the possibility of obtaining three-dimensional hydrated structures is also particularly interesting for tissue-engineering applications, where combining bioactive properties typical of polysaccharides with antimicrobial activity is desirable.
In the field of tissue-engineering, a great effort is being made to produce antimicrobial coatings on biomaterials to be implanted into human body; in this case, the major risk factor is related to the possible cytotoxicity of the antimicrobial agents themselves. For example, in the orthopedic surgery field, the prosthetic joint replacement operations and osteosynthesis of unexposed fractures represent a type of clean surgery with regards to surgery infections (Tucci G. et al., Giornale Italiano di Ortopedia e Traumatologia, 2005; 31:121-129). However, implantation of biomaterials within host tissues may promote the onset and subsistence of infections even with somewhat low bacterial loads. Despite the progress in perioperative prophylaxis, bacterial and fungal infections are still very common; this is caused by time-extended risk of adhesion of these microorganisms to the orthopedic device (Zimmerli W. et al., New England J. Med., 2004; 351(16):1645-54). These data support the importance of developing alternative antimicrobial agents to be associated with new-generation biomaterials.
U.S. Pat. No. 7,255,881 (Gillis et al.) provides a possible solution to the above-mentioned problems. In fact, the patent discloses silver-based coatings formed on various types of substrate through techniques such as chemical and physical depositions from a vapour phase (“chemical vapour deposition” CVD, “physical vapour deposition” PVD) and in a liquid phase for antimicrobial applications. Regarding the polysaccharidic substrates, on which silver is deposited, chitosan, alginate and hyaluronic acid are mentioned. It is noted that these techniques are not directed to the formation of metallic nanoparticles homogeneously dispersed within appropriate matrices, but address the formation of continuous, surface silver (nanocrystalline, polycrystalline or amorphous) layers. Furthermore, the temperature and pressure conditions required for these deposition techniques are not compatible with the stability of the polysaccharide nor of bioactive biomolecules (like peptides or proteins) that might be desirable to be part of the scaffold, nor, even more so, with tissue engineering applications involving living cells.
It is a first object of the present invention to provide three-dimensional nanocomposite systems, where size-controlled metallic nanoparticles are homogeneously dispersed into polysaccharidic matrices, being said matrices in the gel or in the solid form, and the properties of which are particularly suitable for biologic applications in the biomedical field.
It is a further object that such a three-dimensional nanocomposite is obtainable by a simple and economically convenient chemical approach, and in particular, but not exclusively, by producing biocompatible and bioactive hydrogels and dehydrated hydrogels.
It is a further object to improve these systems by employing readily commercially available polysaccharides and without these polysaccharides being subjected to chemical manipulations, as well as without the need for complex preparative manipulations of these systems.
In order to fulfill the above-mentioned objects, the inventors developed suitable polysaccharidic systems based on at least binary compositions comprising neutral or anionic polysaccharides, preferably derived from vegetal or bacterial sources, and branched cationic polysaccharides allowing the later polysaccharides to entrap metallic nanoparticles, and being the neutral or anionic polysaccharides able to form three-dimensional solid matrices hydrated or non-hydrated (e.g. hydrogels with various forms, microspheres, scaffolds, fibrous matrices) and/or high surface/volume ratio matrices (wet or dehydrated membranes and films). In this manner the system formed by branched cationic polysaccharides, uniformly entrapping metal nanoparticles, is itself a nanocomposite.
Therefore, in a first aspect the object of the invention consists in three-dimensional nanocomposite materials comprising a polymeric matrix consisting of at least one neutral or anionic (lyotropic, thermotropic or thermo-lyotropic) polysaccharide, and a metal-based nanocomposite consisting of at least one branched cationic polysaccharide wherein metallic nanoparticles are uniformly dispersed and stabilized, where the neutral or anionic polysaccharide is gelled by means of suitable physical or chemical gelling agents, depending on the type of the neutral or anionic polysaccharide itself.
It was possible to mix solutions of metal nanoparticles-containing cationic branched polysaccharides with neutral or anionic polysaccharide solutions and working with suitable pH value and ionic strength, in order not to cause formation of coacervates. By exploiting the neutral or acidic polysaccharide ability to form ionotropic or thermotropic gels, by means of suitable gelling agents, it was then possible to obtain three-dimensional matrices, hydrated or non-hydrated, consisting of mixtures of these neutral or anionic polysaccharides and branched basic polysaccharides, entrapping these latter metallic nanoparticles uniformly dispersed and stabilized through the branched basic polysaccharide itself.
Therefore, in a second aspect, it is an object of the invention a method of preparing three-dimensional nanocomposite materials comprising a polymeric matrix consisting of at least one lyotropic, thermotropic or thermo-lyotropic, neutral or anionic polysaccharide, and a metal-based nanocomposite consisting of at least one branched cationic polysaccharide wherein metallic nanoparticles are uniformly dispersed and stabilized, characterized in that said three-dimensional nanocomposite materials are obtainable from aqueous solutions of at least one lyotropic, thermotropic or thermo-lyotropic, neutral or anionic polysaccharide, and of a metal-based nanocomposite consisting of at least one branched cationic polysaccharide entrapping the metallic nanoparticles, wherein these aqueous solutions have a ionic strength of at least 50 mM and not higher than 350 mM and a pH of at least of 7 and wherein these aqueous solutions are treated with physical or chemical gelling agents capable to cause the gelation of lyotropic, thermotropic or thermo-lyotropic, neutral or anionic, polysaccharides. These aqueous solutions preferably have an osmolarity comprised in the range from 250 to 300 mM.
Thus, the three-dimensional nanocomposite materials obtainable with such a method of preparing are still an object of the invention.
Furthermore, the three-dimensional nanocomposite materials according to the invention showed to have a strong, broad-spectrum antimicrobial activity and no cytotoxic effects.
Therefore, it is a further object of the invention the use of these three-dimensional nanocomposite materials in biomedical field, in particular for antimicrobial applications. Indeed, the three-dimensional composite materials object of the present invention promise useful applications as biomaterials in both dermatological (e.g. vascular-metabolic cutaneous ulcerations) and orthopedic (e.g. bone prostheses coatings), dental (treatment of periodontal pathogen infections), cardiological, urological (stent coatings) and general surgery therapeutic fields.
Three-dimensional structure: the definition indicates for the purpose of the present application a structure, both hydrated or non-hydrated, capable of maintaining shape and size when not subjected to deformation.
The three-dimensional structure disclosed in the present application are nanocomposite material formed by a neutral or anionic polysaccharides matrix comprising a material formed by metal-nanoparticles uniformly and permanently dispersed in polycationic branched polysaccharides hereinafter described in detail. Thus, in first instance the definition “three-dimensional nanocomposite” is used to indicate the nanocomposite material of the invention.
Hydrogel: generally, the term “hydrogel” indicates highly hydrated three-dimensional semisolid structures capable of maintaining shape and size when not subjected to deformation. They may be obtained from semi-dilute solutions of suitably crosslinked polysaccharides.
In the following description “nanocomposite hydrogels” can also be used to indicate, when hydrated, the three-dimensional nanocomposite structures of the invention as previously defined.
Nanocomposite: generally, the term “nanocomposite” indicates a system consisting of particles with nanometric size (fillers) through a macroscopic material (matrix). Being the invention a three-dimensional nanocomposite deriving from the inclusion in a neutral or anionic polysaccharidic matrix of a nanocomposite material (e.g. metallic nanoparticles uniformly and permanently dispersed in branched cationic polysaccharides), this latter material is indicated herein mainly as “metal-based nanocomposite”. In particular, the metal-based nanocomposite consists of metallic nanoparticles formed by reduction of metal ions by or in alditolic or aldonic polysaccharidic derivatives of chitosan. Thus, in the following description, besides “metal-based nanocomposite”, “metallic-nanoparticles based nanocomposite” is used with reference to this material.
Colloidal solution (or colloid): system in which particles with sizes from 1 and 1,000 nm are dispersed in a continuous solvent medium.
“In situ” gelification: method of gelling in which there is a controlled release of the gelling agent (e.g., ion Ca2+ for alginate). This is achieved by using an inactivated form of the gelling agent (e.g. CaCO3) which is then released upon adding a second component (e.g. glucono-δ-lactone, GDL).
The objects and advantages of the three-dimensional nanocomposite material described in the present invention will be better understood from the following detailed description where, by the way of non-limiting example of the invention, some examples of preparing three-dimensional nanocomposites and their biological characterization to evaluate the antibacterial activity and cytotoxicity, will be described.
For the pursued objects, the aspect related to preparation and characterization of a polysaccharides-based nanocomposite system wherein properties related to nano-scale of metallic nanoparticles are exploited, has been addressed. According to the invention three-dimensional nanocomposite materials are formed from a polymeric matrix consisting of a composition of at least one lyotropic, thermotropic or thermo-lyotropic, neutral or anionic, polysaccharide, and a metal-based nanocomposite consisting of at least one branched cationic polysaccharide entrapping metallic nanoparticles uniformly dispersed and stabilized in such a branched cationic polysaccharide. The branched cationic polysaccharides has a double function in the three-dimensional nanocomposite material according of the invention: i) mainly on one side, in properly entrapping and stabilizing the metal nanoparticles and ii) additionally on the other side, in contributing in forming the matrix, which is substantially a composition of polysaccharides (e.g. at least one lyotropic, thermotropic or thermo-lyotropic, neutral or anionic, polysaccharide and at least one branched cationic polysaccharide), inasmuch as the three dimensional matrix is mainly due to the capability of the neutral or anionic polysaccharides to form gels with appropriate gellifying agents. Thus, such a composition of polysaccharides is in a possible embodiment binary and formed by a neutral or acid polysaccharide and a branched cationic polysaccharide.
The neutral or acid polysaccharides useful for the purpose of the invention are: a) acidic polysaccharides, capable of forming lyotropic gels, selected from the group consisting of alginates, pectates, pectinates; b) neutral polysaccharides capable of giving rise to thermotropic gels and, in this case, they are preferably selected from the group consisting of agarose, scleroglucan, schizophyllan, curdlan; c) acidic polysaccharides capable of giving rise to thermo-lyotropic gels and, in this case, are preferably selected from the group consisting of agarose sulphate, ι- and κ-carrageenan, cellulose sulphate, gellan gum, rhamsan gum, whelan gum (also addressed to as welan gum), xanthan gum.
The average molecular weight (MW) of neutral or acidic polysaccharides can be up to 2,000 kDa and preferably be from 100 kDa to 1,000 kDa and average molecular weights of 200 kDa are more preferably used.
As well known, these neutral or anionic polysaccharides have the feature of forming three-dimensional structures (gel-like or hydrogels, when hydrated), under suitable conditions. Indeed, the aspect related to hydrogel formation is substantially related to the ability of these neutral or acidic polysaccharides to instantly form hydrogels when contacted with solutions of ions for lyotropic polysaccharides, or with cooled solutions for thermotropic polysaccharides. In the case of acidic thermo-lyotropic polysaccharides, the gelling agents can be both/either physical and/or chemical and thus be either ions or appropriate temperatures or both.
On the contrary, the aspect related to forming and carrying metallic nanoparticles is substantially related to the second polysaccharidic component, that is the branched cationic polysaccharides. For the purposes of the present invention these are alditolic or aldonic branched derivatives of chitosan, wherein the D-Glucosamine units forming the linear chitosan chain bind, by means of the —NH-functional group on carbon atom C2, mono- or oligo-saccharidic alditolic or aldonic polyols residues, equal or different from each other, represented by the general formula (I)
where:
For representative purposes, the D-Glucosamine units substituted with mono- or oligo-saccharidic alditolic or aldonic polyols residues in the chitosan branched derivates is represented by the general formula (II), where “n” refers to the overall number of D-Glucosamine units constituting a linear chitosan chain:
For the purposes of the present invention, in preferred branched derivatives of chitosan, when R1 is a monosaccharide, said monosaccharide is selected from the group consisting of galactose, glucose, mannose, N-acetyl glucosamine, and N-acetyl galactosamine, and, when R1 is an oligosaccharide, said oligosaccharide can comprise 2 glycosidic units.
The alditolic or aldonic mono- or oligo-saccharidic residues of general formula (I) preferably are mono- or oligo-saccharides comprising from 1 to 3 glycosidic units and, according to a more preferred aspect, these alditolic or aldonic polyols residues are residues of oligosaccharides comprising from 2 to 3 glycosidic units and yet more preferably are selected from the group of oligosaccharides residues consisting of lactose, cellobiose, cellotriose, maltose, maltotriose, chitobiose, chitotriose, mannobiose as well as from their corresponding aldonic acids. For the purposes of the present invention the most preferred oligosaccharidic derivative of chitosan is the derivative with lactose (Chitlac; CAS registry number 85941-43-1). Furthermore, to uniformly disperse and stabilize the metallic nanoparticles, the chemical substitution degree of chitosan amino groups with these mono- or oligosaccharides of general formula (I) must be at least 40%. The substitution degree of chitosan amino groups with said mono- or oligo-saccharides is preferably comprised in the range from 50% to 80% and more preferably is 70%.
The average molecular weight (hereinafter referred to as MW) of the chitosan useable for obtaining the mentioned oligosaccharidic derivatives is up to 1,500 kDa and be preferably comprised in the range from 400 kDa to 700 kDa.
The metallic nanoparticles incorporated into the polymeric matrix consisting of these mono- or oligo-saccharidic branched derivates of chitosan are made of metals preferentially selected from silver, gold, platinum, palladium, copper, zinc, nickel and mixtures thereof.
The nanoparticles included into the polymeric matrix consisting of mono- or oligosaccharidic branched derivates of chitosan have a size in the range from 5 nm to 150, and in particular a controlled average metallic nanoparticle size between 30 and 50 nm.
An essential feature of these nanoparticles is that these nanoparticles are mostly metals in their reduced form, moreover without excluding the residual presence of clusters made of few atoms with an ionic character, and that in their dispersion/stabilization in the polysaccharidic matrix, mono- or oligo-saccharidic side chains close to amino groups of the chitosan itself are involved.
Without being bound to these, the preferred ratios of cationic polysaccharidic matrix and metals are referred to metal-based nanocomposites in the form of colloidal solutions, although said metal-based nanocomposite materials can be also in the form of dehydrated films or powders, and even dialyzed to remove the residual counter-ions from the preparation of the materials themselves. In the metal-based nanocomposites in the form of aqueous colloidal solutions, the ratio of the polysaccharide concentration (expressed as % w/v) over the concentration of the starting metal salt (expressed as molarity) is from 0.0025 to 20 and preferably is 0.2.
Therefore, the metal mass expressed as mg, which may be incorporated per gram of cationic polysaccharide, can be from 3,000 mg/g to 0.3 mg/g and preferentially is 50 mg of metal incorporated per gram of polysaccharide.
Such a component of the three-dimensional nanocomposite materials according to the invention may be prepared under appropriate conditions with aqueous solutions of basic polysaccharides in the presence or absence of exogenous reducing agents.
The method of preparing this component of the three-dimensional nanocomposite materials according to the invention comprises at least:
A reducing agent is optionally added to the obtained colloidal solutions.
The formation of the metal nanoparticles in the presence of branched cationic polysaccharides produces an exceptionally well-disperse and stabilized metal-nanoparticle system, avoiding the well-known tendency of pre-formed metal nanoparticle to give large agglomerated clusters in solution, which generally leads to loose the benefits related to the nanometric scale.
In its general features, the method of preparing the metal-based nanocomposite is as follows: aqueous solutions of these chitosan branched derivates with mono- or oligo-saccharides are prepared at different concentrations (up to 2% (w/v), preferably in the range from 0.05% (w/v) to 1% (w/v) and more preferably are 0.2%. The polysaccharide solutions are then mixed with solutions of metallic salts chosen from silver, gold, platinum, palladium, copper, zinc, nickel, preferably selected from chlorides, perchlorates and nitrates (e.g. AgNO3, HAuCl4, CuSO4, ZnCl2, NiCl2), in order to obtain final concentrations of these metals from 0.1 mM to 20 mM, more preferably from 1 mM to 14 mM, and still more preferably of 1 mM. Appropriate known reducing agents, preferably selected from ascorbic acid, sodium citrate, sodium borohydride and sodium cyanoborohydride, can optionally be added to the solutions in order to obtain metallic-state nanoparticles. The reducing agent is added at concentrations from 0.05 mM to 10 mM and preferably the concentration is 0.5 mM.
However, it was found that otherwise for other polymeric systems, the metal-based nanocomposites formed from chitosan branched derivates with mono- or oligosaccharides and metallic nanoparticles can be also prepared in the absence of reducing agents, since the side mono- or oligo-saccharidic chains act as reducing agent for metal ions per se, and allow to form in situ nanoparticles dispersed in the polymeric matrix. In this case, the metallic nanoparticles are obtainable by simply mixing the chitosan derivative solutions with salt solutions of the selected metal at appropriate concentrations. Also in this case, the polysaccharide and metal salt concentrations are as previously reported.
However, in both cases because of the chemical and physical-chemical properties of nitrogen atoms and side substituents existing on the mono- or oligo-saccharidic branched derivative of chitosan, the metal ions interact with macromolecules by means of coordination interactions, while the presence of the side chains of mono- or oligo-saccharides, for example lactose, offers an effective steric hindrance to hamper the natural tendency of nanoparticles to aggregate. The subsequent ion reduction, either caused by an exogenous reducing agent or by the mono- or oligosaccharidic chains of the branched derivatives of chitosan, leads to the formation of nanoparticles stabilized by polysaccharidic chains.
In both cases, the ratio of silver mass which may be incorporated and that of polysaccharide, reported as mg per gram, is as previously reported.
Unexpectedly, it was found that mixing in aqueous solutions the polymeric component consisting of the previously mentioned neutral or acidic polysaccharides, and in particular alginates, and the basic polysaccharidic polymeric component, that is branched derivatives of chitosan with the alditolic or aldonic polyols of general formula (I), comprising the metallic nanoparticles, being already a nanocomposite material in nature (e.g. the metal-based nanocomposite), the obtained nanocomposite materials are three-dimensional matrices or stable hydrogels and they are not coacervates in nature, despite the presence of metallic nanoparticles, as well as the nanoparticles remain uniformly dispersed in the branched derivatives of chitosan.
Indeed, hydrogel or three-dimensional matrix formation according of the invention is obtainable by mixing the two components (e.g. neutral or acid polysaccharides and the metal-based nanocomposite) in aqueous solutions having appropriate features by means of a subsequent treatment thereof with suitable agents capable of gelling the anionic or neutral polysaccharide.
In particular, the three-dimensional nanocomposite materials comprising a polymeric matrix consisting of at least one neutral or anionic, lyotropic, thermotropic or thermo-lyotropic polysaccharide, and a metal-based nanocomposite consisting of at least one branched cationic polysaccharide entrapping metallic nanoparticles uniformly dispersed and stabilized, are obtainable from aqueous solutions of the two components having the solutions an ionic strength at least of 50 mM and not higher than 350 mM and a pH at least of 7, and by treating these solutions with chemical or physical gelling agents capable of gelling the neutral or anionic, lyotropic, thermotropic or thermo-lyotropic polysaccharides.
The preferred conditions (substantially concentrations, pH, ionic strength) to obtain the three-dimensional matrices or hydrogels from these two components are typically aqueous solutions having a pH in a physiological range, and in particular between 7 and 8 and more preferably the pH is 7.4, and an osmolarity from 250 to 300 mM, with an ionic strength from 50 mM to 350 mM, and preferably of 150 mM, preferably obtained by adding NaCl at concentrations from 0.05 M to 0.35 M and more preferably of 0.15 M.
The gelling agents may be selected depending of the type of lyotropic anionic polysaccharide from suitable monovalent, bivalent or trivalent ions, and for thermotropic polysaccharides between temperatures not higher than 50° C. or not lower than 10° C. As known, for thermo-lyotropic polysaccharides the gelling agents may be both chemical agents, such as ions, and physical agents, such as temperature. The choice between the two types of gelling agents substantially depends as well known in the art on the acidic thermo-lyotropic polysaccharide to be gelled.
For polysaccharides such as alginate and pectate these ions are alkaline-earth ions, excluding magnesium, and transition metals, and preferably selected from the group consisting of calcium, barium, strontium, lead, copper, manganese and mixtures thereof, or they are rare earth ions and preferably selected from the group consisting of gadolinium, terbium, europium and mixtures thereof.
The concentrations of the aqueous solution of these ions adapted for the gelification are higher than 10 mM and preferably from 10 mM to 100 mM and more preferably of 50 mM. The gelling solution preferably contains a concentration of CaCl2 of 50 mM and an ionic strength of 0.15 M.
In the case of carrageenans, alkaline ions preferably chosen from the group consisting of potassium, rubidium and cesium, at concentrations not lower than 50 mM and preferably from 50 mM to 200 mM and more preferably of 0.1 M, can be used.
In the case of polysaccharidic solutions, which lead to thermotropic hydrogels, such as for example agarose, the hydrogels preparation is performed by cooling below the gel formation temperature. The polysaccharidic solutions are prepared at a temperature above the temperature at which the hydrogel formation by the thermotropic polysaccharide occurs. At this temperature, the thermotropic polysaccharide does not form hydrogels. The temperature at which polysaccharidic solutions are prepared, preferably is in the range from 50° C. to 30° C. and more preferably is 37° C. The hydrogel formation occurs by dripping the polysaccharidic solution into a gelling bath cooled to a temperature below the gel formation temperature. This temperature preferably is in the range from 10° C. to 40° C. and more preferably is 20° C.
For the purposes of the present invention, the at least binary mixtures of neutral or anionic polysaccharide and of branched basic polysaccharide comprising the metallic nanoparticles have total polymeric concentrations of neutral or anionic polysaccharide up to 4% (w/v). These total polymeric concentrations preferably are in the range from 1.5% to 3% (w/v) and more preferably are 2% (w/v).
For the purposes of the present invention, the weight ratios of acidic polysaccharides and cationic polysaccharides, wherein the metallic nanoparticles are entrapped, are from 8:1 to 1:1 (neutral or anionic polysaccharide: cationic polysaccharide), and preferably from 8:1 to 5:1, and more preferably 7.5:1.
Therefore, the three-dimensional nanocomposite materials of the invention are obtainable according to a method of preparing comprising at least the following steps:
In particular, this latter step can be realized by dripping through a needle into a solution containing the crosslinking ion for the lyotropic anionic polysaccharides, or into a solution at a suitable temperature for the thermotropic polysaccharides, or by “in situ” gelification. For the thermo-lyotropic polysaccharides both ionic solutions and solutions at appropriate temperatures for the gelification process can be employed.
With the above-described method, nanocomposite materials are obtained, in which the polymeric matrix made of polysaccharides is three-dimensional and in the form of a hydrogel or not hydrated if subjected to subsequent dehydration processes. Moreover, these matrices can take various forms as cylinders, microspheres, disks, dried films, powders, or can be extruded to produce fibers. In case of alginate, the cylinders can be prepared by adding a crosslinking ion in the inactive form, for example CaCO3 or the Ca-EDTA complex, to the polysaccharidic solution. A slowly hydrolyzing substance is then added, such as for example GDL (D-glucono-δ-lactone). For example, this suspension is transferred within the cylinder-shaped or discoid containers and there kept for 24 h. The gel cylinders of the polysaccharidic solutions are then extracted from the containers. The in situ formation of cylinders is due to release of calcium ions. For testing the antimicrobial activity of three-dimensional nanocomposites of the invention, bacterial growth tests on semisolid support and counting test of bacterial colonies in the presence of microspheres of three-dimensional nanocomposites gel are performed; it has been shown that because of the presence of metal nanoparticles, bacteria grow neither on such gel surface nor in a suspension placed in contact with the three-dimensional nanocomposites gel microspheres, thereby underlining a strong antibacterial activity.
Cytotoxicity tests on different eukaryotic cell lines demonstrate that these three-dimensional nanocomposite gels are not cytotoxic even maintaining an effective bactericidal effect.
For illustrative and not limitative purpose, the hydrogel or 3D matrix non hydrated preparation according to the invention as well as the antimicrobial-type biologic activity are described hereinafter.
Preparation of Three-Dimensional Nanocomposite Hydrogels from a Solution of One Anionic Polysaccharide and a Metal-Based Nanocomposite Consisting of One Oligosaccharidic Derivative of Chitosan with Metallic Nanoparticles
Chitosan (1.5 g, acetylation degree 11%) is dissolved into 110 mL of a methanol solution (55 mL) and 1% acetic acid buffer, pH 4.5 (55 mL). 60 mL of a methanol solution (30 mL) and 1% acetic acid buffer, pH 4.5 (30 mL) containing lactose (2.2 g) and sodium cyanoborohydride (900 mg) are added. The mixture is left to stir for 24 hours, transferred to dialysis tubes (cut off 12,000Da) and dialyzed against NaCl 0.1M (2 changes) and against deionized water until a conductivity of 4 μS at 4° C. is achieved. Finally, the solution is filtered on Millipore 0.45 μm filters and freeze-dried.
Chitosan (1.5 g, acetylation degree 11%) is dissolved into 110 mL of a methanol solution (55 mL) and 1% acetic acid buffer, pH 4.5 (55 mL). 60 mL of a methanol solution (30 mL) and 1% acetic acid buffer, pH 4.5 (30 mL) containing cellobiose (2.2 g) and sodium cyanoborohydride (900 mg) are added. The mixture is left to stir for 24 hours, transferred to dialysis tubes (cut off 12,000Da) and dialyzed against NaCl 0.1M (2 changes) and against deionized water until a conductivity of 4 μS at 4° C. is achieved. Finally, the solution is filtered on Millipore 0.45 μm filters and freeze-dried.
Nanoparticles are obtained upon reduction of metal ions with ascorbic acid in Chitlac solutions according to the following procedure: an aqueous Chitlac solution at a concentration of 0.4% (w/v) is prepared. The Chitlac solutions are then mixed with silver nitrate solutions, so as to obtain a final concentration of AgNO3 of 1 mM. Then, a solution of ascorbic acid, is added so as to obtain a final concentration of 0.5 mM.
Nanoparticles are obtained upon reduction of metal ions with ascorbic acid in Chitcel solutions according to the following procedure: an aqueous Chitcel solution at a concentration of 0.4% (w/v) is prepared. The Chitcel solutions are then mixed with silver nitrate solutions, so as to obtain a final concentration of AgNO3 of 1 mM. Then, a solution of ascorbic acid is added, so as to obtain a final concentration equal to 0.5 mM.
Nanoparticles are obtained upon reduction of metal ions by the polysaccharide Chitlac according to the following procedure: an aqueous Chitlac solution at a concentration of 0.4% (w/V) is prepared. The Chitlac solution is then mixed with a tetrachloroauric acid so as to obtain a final concentration of HAuCl4 of 1 mM.
To a Chitlac solution, an alginate solution in the presence of NaCl and Hepes buffer is added, so as to obtain the following final concentrations: 1.5% (w/v) alginate, 0.2% (w/v) Chitlac, 0.15 M NaCl, 0.01M Hepes buffer, pH 7.4. Then, a solution of CaCO3 (concentration 30 mM) is added and subsequently D-glucono-δ-lactone (GDL) ([GDL]/[Ca2+]=2) is added to allow a slow gelification. For the antibacterial tests 20% Mueller-Hinton medium is added (4.2 g/L). The final solution is transferred to plastic cylinders sized as desired (e.g. 16 mM (Ø)×18 mM (h)) and left to gel in the dark for 24 hours.
A Chitlac solution with metallic nanoparticles prepared according to example 3 is added to an alginate solution (final alginate concentrations up to 4% (w/v) and preferably in the range from 1% (w/v) to 2% (w/v)) in the presence of CaCO3 (final concentration up to 40 mM and preferably from 15 mM to 30 mM) and then D-glucono-δ-lactone (GDL) ([GDL]/[Ca2+]=2) is added to allow a slow gelification. For the antibacterial tests 20% final Mueller-Hinton medium is added (4.2 g/L).
To a Chitlac solution with silver nanoparticles prepared according to example 3, an alginate solution in the presence of NaCl and Hepes buffer is added so as to obtain the following final concentrations: 1.5% (w/v) alginate, 0.2% (w/v) Chitlac, 0.5 mM AgNO3, 0.25 mM C6H8O6, 0.15 M NaCl, 0.01M Hepes buffer, pH 7.4). Then, a solution of CaCO3 (concentration 30 mM) is added and subsequently D-glucono-δ-lactone ([GDL]/[Ca2+]=2) is added to allow a slow gelification. For the antibacterial tests 20% Mueller-Hinton medium is added (4.2 g/L). The final solution is transferred to plastic cylinders sized as desired (e.g. 16 mM (Ø)×18 mM (h)) and left to gel in the dark for 24 hours.
It is worth underlining that particle aggregation or polymeric phase separation is absent both during and after the gelification. As seen in
To a Chitlac solution with gold nanoparticles prepared according to example 5, an alginate solution in the presence of NaCl and Hepes buffer is added, so as to obtain the following final concentrations: 1.5% (w/v) alginate, 0.2% (w/v) Chitlac, 0.5 mM HAuCl4, 0.15M NaCl, 0.01M Hepes buffer, pH 7.4). Then, a solution of CaCO3 (concentration 30 mM) is added and subsequently D-glucono-δ-lactone (GDL) ([GDL]/[Ca2+]=2) is added to allow a slow gelification. For the antibacterial tests 20% Mueller-Hinton medium is added (4.2 g/L). The final solution is transferred to plastic cylinders sized as desired (e.g. 16 mM (Ø)×18 mM (h)) and left to gel in the dark for 24 hours.
An obtained three-dimensional nanocomposite hydrogel sample is shown in
A polysaccharidic solution with the following final concentrations was prepared. 1.5% (w/v) alginate, 0.2% (w/v) Chitlac, 0.5 mM AgNO3, 0.25 mM C6H8O6, 0.15 M NaCl, 0.01M Hepes buffer, pH 7.4. The solution was dripped using a syringe provided with a 23 G needle, into a solution containing 50 mM CaCl2 and 0.15 M mannitol, 10 mM Hepes buffer (pH 7.4) under stirring by means of a magnetic rod. The spheres were kept under agitation in the gelling bath for 10 min before being removed and washed with deionized water.
A polysaccharidic solution with the following final concentrations was prepared. 1.5% (w/v) alginate, 0.2% (w/v) Chitlac, 0.5 mM AgNO3, 0.25 mM C6H8O6, 0.15 M NaCl, 0.01M Hepes buffer, pH 7.4. The solution was dripped using a syringe provided with a 23 G needle, into a solution containing 50 mM CaCl2 and 0.15 M mannitol, 10 mM Hepes buffer (pH 7.4) under stirring by means of a magnetic rod. The spheres were kept under agitation in the gelling bath for 10 min before being removed and washed with deionized water.
A polysaccharidic solution with the following final concentrations was prepared. 1.5% (w/v) alginate, 0.2% (w/v) Chitlac, 0.5 mM HAuCl4, 0.15 M NaCl, 0.01 M Hepes buffer, pH 7.4. The solution was dripped using a syringe provided with a 23 G needle, into a solution containing 50 mM CaCl2 and 0.15 M mannitol (gelling bath) under stirring by means of a magnetic rod. The spheres were kept under agitation in the gelling bath for 10 min before being removed and washed with deionized water.
A polysaccharidic solution with the following final concentrations was prepared. 1.5% (w/v) alginate, 0.2% (w/v) Chitlac, 0.5 mM AgNO3, 0.25 mM C6H8O6, 0.15 M NaCl, 0.01M Hepes buffer, pH 7.4. The solution was dripped into a gelling bath containing 50 mM CaCl2 and 0.15 nm mannitol under stirring by means of a magnetic rod. The microsphere size is controlled by using an electrostatic generator, which allows to act on the surface tension of the drops so as to reduce the size thereof. The conditions employed typically were: voltage 5 kV, internal needle diameter 0.7 mM, distance between gelling bath and needle 4 cm, binary polymeric solution flow rate 10 mL/min. The microspheres were left in the gelling solution under stirring for 10 min before being removed and washed with deionized water.
Obtained three-dimensional nanocomposite microsphere samples are shown in
A polysaccharidic solution with the following final concentrations was prepared: 1.5% (w/v) alginate, 0.2% (w/v) Chitlac, 0.5 mM HAuCl4, 0.15M NaCl, 0.01M Hepes buffer, pH 7.4. The solution was dripped into a gelling bath containing 50 mM CaCl2 and 0.15 nm mannitol under stirring by means of a magnetic rod. The microsphere size is controlled by using an electrostatic bead generator, which allows to act on the surface tension of the drops so as to reduce the size thereof. The conditions employed typically are: voltage 5 kV, internal needle diameter 0.7 mM, distance between gelling bath and needle 4 cm, binary polymeric solution flow rate 10 mL/min. The microspheres are left in the gelling solution under stirring for 10 min before being removed and washed with deionized water.
To a Chitlac solution with silver nanoparticles prepared according to example 3, an alginate solution in the presence of NaCl and Hepes buffer is added so as to obtain the following final concentrations: 1.5% (w/v) alginate, 0.2% (w/v) Chitlac, 0.5 mM AgNO3, 0.25 mM C6H8O6, 0.15 M NaCl, 0.01M Hepes buffer, pH 7.4. Then, a solution of CaCO3 (concentration 30 mM) is added and subsequently D-glucono-δ-lactone (GDL) ([GDL]/[Ca2+]=2 is added to allow a slow gelification. For the antibacterial tests 20% final Mueller-Hinton medium is added (4.2 g/L). The final solution is poured onto smooth surfaces (slides, Petri dishes, etc.) and left to gel in the dark for 24 hours.
To a Chitlac solution with silver nanoparticles prepared according to example 3, an alginate solution in the presence of NaCl and Hepes buffer is added so as to obtain the following final concentrations: 1.5% (w/v) alginate, 0.2% (w/v) Chitlac, 0.5 mM AgNO3, 0.25 mM C6H8O6, 0.15 M NaCl, 0.01 M Hepes buffer, pH 7.4. Then, a solution of CaCO3 (concentration 30 mM) is added and subsequently D-glucono-δ-lactone (GDL) ([GDL]/[Ca2+]=2) is added to allow a slow gelification. For the antibacterial tests 20% final Mueller-Hinton medium is added (4.2 g/L). The final solution is poured onto smooth surfaces (slides, Petri dishes, etc.) and left to gel in the dark for 24 hours. Then, the three-dimensional nanocomposite gel is air-dried so as to obtain a three-dimensional nanocomposite solid dehydrated film.
To a Chitlac solution with gold nanoparticles prepared according to example 5, an alginate solution in the presence of NaCl and Hepes buffer is added so as to obtain the following final concentrations: 1.5% (w/v) alginate, 0.2% (w/v) Chitlac, 0.5 mM HAuCl4, 0.15M NaCl, 0.01M Hepes buffer, pH 7.4. Then, a solution of CaCO3 (concentration 30 mM) is added and subsequently D-glucono-δ-lactone (GDL) ([GDL]/[Ca2+]=2) is added to allow a slow gelification. For the antibacterial tests 20% final Mueller-Hinton medium is added (4.2 g/L). The final solution is poured on smooth surfaces (slides, Petri dishes, etc.) and left to gel in the dark for 24 hours.
To a Chitlac solution with gold nanoparticles prepared according to example 5, an alginate solution in the presence of NaCl and Hepes buffer is added so as to obtain the following final concentrations: 1.5% (w/v) alginate, 0.2% (w/v) Chitlac, 0.5 mM HAuCl4, 0.15M NaCl, 0.01M Hepes buffer, pH 7.4. Then, a solution of CaCO3 (concentration 30 mM) is added and subsequently D-glucono-δ-lactone (GDL) ([GDL]/[Ca2+]=2) is added to allow a slow gelification. For the antibacterial tests 20% final Mueller-Hinton medium is added (4.2 g/L). The final solution is poured on smooth surfaces (slides, Petri dishes, etc.) and left to gel in the dark for 24 hours. Then, the three-dimensional nanocomposite gel is air-dried so as to obtain a three-dimensional nanocomposite solid film.
The microspheres of the above-reported specific examples 13 and 14 were prepared according to known methods and in particular by: a) using syringes, with which of the solutions of one anionic polysaccharide and one metal-based nanocomposite mono- or oligo-saccharidic derivative of chitosan with metallic nanoparticles are manually dripped into a suitable gelling bath, b) using one Electrostatic Bead Generator, developed by Prof. Gudmund Skjåk-Bræk of Institute of Biotechnology of NTNU University of Trondheim (Norway) and described by Strand et al., 2002, J. of Microencapsulation 19, 615-630. Such an apparatus consists of an electrostatic bead generator with an adjustable voltage (up to 10 kV) by means of a suitable switch, connected to an autoclavable needle support contained in a safety stand made of Plexiglas.
By means of a system outside the stand, consisting of a syringe adjusted by a pump and connected to a pipe made of lattice having an internal diameter of 1 mm, the starting solution is dripped into a crystallizator (within the stand) containing the gelling solution, in which an electrode is inserted. The instrument generates a constant potential difference between the needle tip and the free surface of the gelling solution, which may be adjusted and ranges from 0 to 10 kV. The potential difference causes the sudden detachment of the polymer drop (negatively charged) from the needle tip and thus allows to have capsules even with small sizes (<200 μm). The capsule sizes may be adjusted by even varying other factors, such as the internal needle diameter, the distance of the needle from the gelling solution surface, the polymer flow rate.
The gel cylinders and disks of the above-reported specific examples 6, 8 and 9 were prepared by pouring the solution containing the polysaccharides and the metal-based nanocomposite into cylinder-shaped containers. The cylindrical hydrogel size depends on the size of the latter ones. The cylinder-shaped container dimensions typically are 18 mm in height and 16 mm in internal diameter, while those of discoid containers are 8 mm in height and 16 mm in internal diameter, even if different sizes (height and internal diameter) are fully allowable.
For testing the antibacterial activity of three-dimensional nanocomposite gels, different bacterial strains at various concentrations were smeared on the gel surfaces. Both Gram negative strains (Escherichia coli, Pseudomonas aeruginosa) and Gram positive strains (Staphylococcus aureus, Staphylococcus epidermidis) were tested. The controls are represented by agar gels and alginate-Chitlac gels without nanoparticles (AC gels). After “overnight” incubation the bacterial colonies are clearly evident on controls but completely absent on gels containing nanoparticles (AC-nAg gels) (
Moreover, nanocomposite gel microspheres containing silver nanoparticles (AC-nAg) are made and contacted with bacterial solutions (Escherichia coli); the control is represented by alginate-Chitlac gel microspheres (without silver nanoparticles). The results demonstrate that the concentration of bacterial colonies increases in the control but decreases by more than three logarithmic units in the case of microspheres with silver nanoparticles.
Even the nanocomposite microspheres obtained according to example 13 and nanocomposite hydrogels obtained according to examples 6 and 9 proved to be able to exert an effective antimicrobial action, as shown in
Tests to evaluate gel cytotoxicity on eukaryotic cell lines, such as osteoblasts (MG63), hepatocytes (HEPG2) and fibroblasts (3T3), were performed. In the test, the release of lactate dehydrogenase enzyme (LDH) by cells is measured assessed, which is related to cellular damage and death. The LDH tests demonstrate that these three-dimensional nanocomposite gels do not cause cytotoxic effects to the tested cells, as it can be seen in
Comparable results are reported in the case of similar three-dimensional nanocomposite alginate-Chitlac-based gels containing gold nanoparticles (AC-nAu gels); as seen in
The combination of these results allows to conclude that the three-dimensional nanocomposite according to the invention, such as alginate-Chitlac-based hydrogels containing nanoparticles formed and stabilized in Chitlac, are provided with a homogeneous structure in which the nanoparticles do not aggregate and have a strong bactericidal activity, without being toxic for the eukaryotic cells. These new three-dimensional nanocomposite systems provide the following advantages:
| Number | Date | Country | Kind |
|---|---|---|---|
| PD2008A000220 | Jul 2008 | IT | national |
| Filing Document | Filing Date | Country | Kind | 371c Date |
|---|---|---|---|---|
| PCT/EP2009/059432 | 7/22/2009 | WO | 00 | 1/21/2011 |
