Patent Description:
The invention finds application as a porous material for use as a biocompatible material for filling bone defects and/or regenerating bone tissue. Compositions and methods not comprising the peptide sequence referred to as "ug46" or SEQ3 are not part of the invention.

Biocomposites for bone tissue reconstruction should be biocompatible, nontoxic, non-carcinogenic and non-allergenic materials. Due to their place of application, they have high requirements as described in ISO <NUM> standards. In the publication "<NPL>] presents the direction that biomaterials should support the restoration of damaged tissues and that the implants should undergo controlled degradation. In the case of bone tissue implants, a great deal of attention is paid to their osteoconductive abilities and porosity. It is assumed that the pore layout and size should allow good cell migration and ensure easy delivery of nutrients within the implant. The optimal average pore size of implants for bone tissue cells should be in the range <NUM>-<NUM> "<NPL>]. Relevant there are also smaller pores that facilitate vascularisation, while pores with a diameter of more than <NUM> promote fibrous tissue formation. The prevention of post- implant bacterial infections is also receiving much attention in ongoing research, e.g. through the incorporation of bioglasses with antimicrobial activity into the composition of biomaterials <NPL>], "Controlling the microstructure of lyophilised porous biocomposites by the addition of ZnO-doped bioglass" [<NPL>].

There is information in the literature on the results of composite materials research, with a great deal of attention paid to bioactive glasses "<NPL>] and composites based on biodegradable polymers "<NPL>], as well as <NPL>]. One of the natural polymers used to create composites is chitosan, which is obtained by chitin deacetylation and contains linearly linked β-<NUM>,<NUM>-glycosidic bonds of D-glucosamine and N-acetyl-D- glucosamine molecules. It has high biocompatibility, antimicrobial and hemostatic properties and is biodegradable <NPL>]. Its osteoconductive abilities make it useful in hard tissue engineering "<NPL>], however, its mechanical properties and biological activity must be enhanced with e.g. bioglasses "<NPL>]. Bioactive glasses are a component of composites that can induce bioactivity, osteointegration and bactericidal activity of composites. In particular, bioglasses produced by the sol-gel method show high bioactivity, i.e. the ability to form an apatite interlayer "<NPL>]. The appropriate chemical composition of the glasses influences the qualitative composition of the released ions, which then play an important role in the healing process around the implant and bone regeneration "<NPL>]. Modification of the composition of bioglasses by partially replacing of CaO by MgO or SrO increases the surface reactivity, and this during contact between the biomaterial and body fluid increases the ability to form an apatite interlayer. Sr/Ca substitution is an established strategy for creating biomaterials for use in bone regeneration therapy <NPL>]. When metal ions or oxides with bactericidal capabilities are introduced into the chemical composition of glasses, antibacterial materials are obtained. Various substances have been used as bactericidal agents in composites "<NPL>].

Bactericidal activity is also characterised by ions of metals, and bioactive glasses containing them are a potential alternative for systemic delivery of antibiotics to prevent bacterial infections: "<NPL>], "<NPL>].

A hydrogel composite based on alginate-chitosan/admixed by calcium phosphate/ bioglass is described in <NPL>], however, calcium phosphate doped with ZnO and/or SrO and a bioglass composition of <NUM>% SiO<NUM> - <NUM>% CaO - <NUM>% P<NUM>O<NUM> is introduced as filler, and the entire system is not porous, but exists in gel form.

The inconvenience of this solution is the gel-like form of the material, which does not provide an environment for cell migration after implantation of the composite. Migration is only made possible by the porous form of the material, which has an adequate pore size.

A method for preparing porous chitosan scaffolds has been described in the literature, among others, using the example of a chitosan-agarose-based scaffold. The method involved preparing a solution of chitosan in an aqueous solution of acetic acid and an aqueous solution of agarose at <NUM> and then, after adding the chitosan solution to the agarose solution, freezing the whole at -<NUM> and freeze-drying. The resulting material was used in cartilage tissue engineering (<NPL>).

Experience in methods of obtaining porous polymer scaffolds enriched in bioglass particles is also available to some of the inventors of the present invention. The method described in <NPL> concerned the preparation of porous composite scaffolds with controlled pore size from the chitosan/bioglass, sodium alginate/bioglass, polylactide/bioglass system. For the chitosan/bioglass system, the method involved preparing a solution of chitosan in an aqueous acetic acid solution and adding ZnO-subsidised bioglass particles to it. After obtaining a stable dispersion of the bioglass in the chitosan solution, it was lyophilised, after which the resulting porous structure was stabilised using ethanol. The resulting scaffolds were produced as a biomaterial for filling bone defects and tested for biocompatibility and antimicrobial activity.

A chitosan-based material for bone substitutes is described in Polish patent description P411938. A method for obtaining a composite material based on chitosan, hydroxyapatite and silica is disclosed. The method is based on the fact that an aqueous solution of a chitosan salt such as chitosan acetate, chloride, lactate or citrate is mixed with hydroxyapatite nanopowder and possibly calcium glycerophosphate, using ultrasound to obtain a homogeneous paste, which is then introduced into a methsilicic acid sol, the whole is mixed, after which the obtained composite is dried convectively at <NUM>-<NUM>.

Patent description <CIT> discloses a material involving bioglass for use as implants capable of preventing surgical site infections, in particular, bioactive antibacterial materials. The disclosure includes bioactive glass with a defined bimodal grain size distribution, flexible and pliable bioactive antibacterial composites made of biocompatible polymer-collagen, ceramics and bioactive glass with a bimodal grain size distribution, as well as bone repair methods and methods to facilitate bone repair while preventing surgical site infection.

Patent description <CIT> discloses biodegradable polymeric materials for therapeutic implants with improved mechanical strength. The described material comprises a surface passivated bioactive glass and a biodegradable polymer selected from a group consisting of polymers: PLA, PGA and copolymers of PLA and PGA. The implants described provide improved mechanical properties and pH control, enabling the use of these materials for the design of porous and non-porous therapeutic implants used as cellular scaffolds for healing tissue defects or fixation devices, with desirable degradation times, mechanical properties, flexibility and biocompatibility.

The use of bioglass for tissue regeneration is disclosed in patent description <CIT>. Bioglass fillers in the form of glass beads, glass-ceramic beads and ceramic beads are described, having an internal porous microstructure in the form of a scaffold and surrounded externally by an amorphous coating that allows protection of the porous interior and mechanical reinforcement. The material according to the disclosure is intended to be used in the augmentation or regeneration of bone or soft tissues, where the open porosity present inside the bead will allow an increased degradability in vivo compared to solid particles, will promote tissue growth, including but not limited to all types of bone, soft tissues, blood vessels and nerves.

Bioglass, among others, was also used in the material of patent description <CIT> for synthetic polyurethane composites with osteoconductive properties. According to the description, the composition, in addition to the polyurethane and the osteoconductive component in the form of tricalcium phosphate or bioglass, may contain a growth factor in its composition and may be moldable and/or injectable. After implantation or injection, the composition may be solidified to form a porous composite that provides mechanical strength and promotes cell ingrowth.

Patent description <CIT>, on the other hand, discloses a bioglass-free composition for the controlled and prolonged release of macromolecular compounds containing a pure chitosan matrix for injection or in a porous form for implantation, containing a macromolecular compound dispersed therein. Examples of macromolecules used in this composition were pharmacologically active macromolecules selected from the group of proteins and polypeptides, or hormones and enzymes, such as bovine growth hormones, added to the system in an amount of <NUM>-<NUM>%. The chitosan in the system was surface crosslinked after obtaining a porous structure by using glutaraldehyde, glyoxal, epichlorohydrin, succinic aldehyde, <NUM>,<NUM>-decandial, trichlorotriazine, benzoquinone and bisepoxirane.

A report of the authors of the present invention with regard to a chitosan/bioglass/peptide composite is available in the literature [<NPL>], but the solution proposed there uses a model peptide with different biological properties than the peptides described in the present description.

Reports of other porous chitosan composites with antimicrobial and/or pro-regenerative and/or anti-inflammatory properties containing bioglass and active biological peptides introduced simultaneously in the bulk and/or on the scaffold surface are unknown.

In addition to bioglass and chitosan, compounds that exhibit pro-regenerative properties by stimulating bone cells to migrate or proliferate are also common components of implants. An extensive literature review on this subject can be found in the authors' publication [<NPL>].

Patent description <CIT> presented a disclosure for a peptide having the ability to both regenerate bone tissue and bind to the surface of the mineral apatite. The peptide was capable of stable immobilisation on the surface of apatite, maintaining effective activity and bone regeneration effect for a long time. Thirty-five peptides that are fragments of growth factors and four peptides with the ability to bind apatite were synthesised. A peptide consisting of an amino acid sequence having the ability to regenerate bone tissue (YGLRSKSKKFRRPDIQYPDAT - growth factor fragment BSP-I) with an amino acid sequence having the ability to bind apatite to itself (STLPIPHEFSRE) was cited as one example of the patent, with the aim of combining the bone-forming effect and the ability to bind to the surface of the mineral.

The invention presented in patent <CIT> describes the therapeutic use of amphiphilic peptides for the treatment and prevention of the progression of osteoporosis and pre-osteoporotic conditions, by direct administration of the peptides to patients with deteriorated or traumatised skeletons, in particular with low bone mineral density. Amphiphilic peptides contain mainly acidic amino acids that are capable, alone or in combination with ions and minerals, of forming β-structure and hydrogels at physiological pH. These peptides serve as scaffolds for mineralisation directly in bone. Compositions containing amphiphilic peptides administered according to the present invention serve as a matrix or nucleation centre for in vitro and in situ biomineralisation. This action is intended to mimic the natural formation of bone tissue, thereby ensuring rapid regeneration, increased mineral density and reduced risk of fractures.

Patent description <CIT> relates to tissue mineralisation in particular tooth remineralisation and bone regeneration by means of self-organising peptides. The use of the self-organising peptide P11-<NUM> and others in these processes ultimately leads to the formation of hydroxyapatite, which is also found in natural enamel, dentin and bone.

The inventors have discovered therein that both tooth remineralisation and bone regeneration can be significantly accelerated by adding amorphous calcium phosphate or calcium and phosphate ions to the P11-<NUM> peptide, which, when mixed in solution, can lead to the immediate precipitation of calcium phosphate. The disclosure describes a kit comprising a self-organising peptide and calcium and phosphate ions in separate compositions suitable for immediate formation of calcium phosphate precipitates. The disclosure provides a medical application of said kit, in particular in the tooth, for the remineralisation of lesions, mineralisation of pits and fissures.

A combination of pro-regenerative peptides with a polymer is presented in patent description <CIT>. It relates to an injectable bone regeneration material containing peptides that are fragments of growth factors (BMP-<NUM>, BMP-<NUM>, BMP-<NUM>, BMP-<NUM>, BSP-I, BSP-II). The material may comprise one or more peptides from among the <NUM> shown, and may be bound or mixed with a gel-forming base material selected from the group consisting of: chitosan, alginic acid, silk fibroin, propylene glycol, alginic acid, propylene glycol, poloxamer, chondroitin sulphate and combinations thereof. The injectable bone regeneration material according to the disclosure described in the US can increase the differentiation of bone marrow stromal cells and osteoblasts into bone tissue, thus maximising tissue regeneration. It is in the form of a gel and can therefore be applied to the surface of various medical devices, such as an implant, or mixed with bone graft particles to enhance the treatment effect. The proposed solution also uses peptides derived from other growth factors and presents a different way of combining the peptides with the polymer.

The inconvenience of the known solutions of porous polymer scaffolds enriched in bioglass molecules or the combination of pro-regenerative peptides with polymer/chitosan, is the form that does not provide an environment for cell migration after implantation of the composite, i.e. its effective use for filling bone defects and regenerating bone tissue, as well as the inconvenience of the lack of comprehensive action of such a biocompatible composite - implant. Effective novel biomaterials with a wide range of effects are still in demand and represent an attractive material for medicine.

The invention described in this application presents multifunctional composites containing components with proven pro-regenerative and antimicrobial and/or anti-inflammatory effects simultaneously. The developed composites are biocompatible at the cellular level in vitro and in vivo and are materials that readily adapt to the size and shape of the bone defect.

The subject matter of the invention is a biocompatible, non- cytotoxic, bioactive and porous (<NUM>% of pores in the range <NUM>-<NUM>) composite for filling bone defects and regenerating bone tissue, in which the matrix is a natural biodegradable polymer - chitosan, characterised by a degree of deacetylation DD≥<NUM>%, viscosity in the range <NUM> to <NUM> mPas and molecular weight in the range <NUM> to <NUM> kDa.

Four variants of the composite disclosed herein were developed:.

Compositions and methods not comprising the peptide sequence referred to as "ug46" or SEQ3 are not part of the invention.

The filler in the composite is a bioactive glass constituting in the composite according to variant a from <NUM> wt. % to <NUM> wt. % of the composition of the total composite, in composite b from <NUM> wt. % to <NUM> wt. % of the composition of the total composite, in composite c from <NUM> wt. % to <NUM> wt. % of the composition of the total composite, and in composite d from <NUM> wt. % to <NUM> wt. % of the composition of the total composite, produced by the sol-gel method and containing in total: SiO<NUM> in an amount of <NUM>-<NUM> wt. % and CaO in an amount of <NUM>-<NUM> wt. % and, in a variant disclosed herein, additionally: P<NUM>O<NUM> in an amount of up to <NUM> wt. % and/or SrO in an amount of up to <NUM> wt. % and/or ZnO in an amount of up to <NUM> wt. % and/or CuO in an amount of up to <NUM> wt. % and/or MgO in an amount of up to <NUM> wt. The bioglass has a grain size of <NUM>% below <NUM> and is characterised, due to the choice of composition, by enhanced bioactivity, bactericidal activity and/or pro-regenerative capacity.

The entire system, i.e. the composite in variant a, is enriched with two biologically active, engineered peptides - ug4 and ug46 with specific amino acid sequences, shown on SEQ1 - with pro-regenerative properties and SEQ3 - with antimicrobial and anti-inflammatory properties.

The ug4 peptide is between <NUM> wt. % and <NUM> wt. % of the total composition of the composite a. A peculiarity of the design of the engineered ug4 peptide is that a portion of this peptide - that is, a peptide called peptide ug1 with the sequence shown in SEQ2 - will be released at the site of medical action by enzymatic hydrolysis of the bond of the peptide in ug4 between Gly<NUM> and Leu<NUM>. The enzymatic cut between these amino acid residues is specific for metalloproteinases found in the bone environment. The ug1 peptide as part of ug4 has pro-regenerative activity in bone.

The peptide ug46 is between <NUM> wt. % and <NUM> wt. % of the total composition of the composite and exhibits antimicrobial and anti-inflammatory properties.

The entire system, i.e. the composite in variant b, is enriched with one biologically active engineered peptide - ug4 with a specific amino acid sequence, shown on SEQ1 - with pro- regenerative properties. The ug4 peptide is between <NUM> w. t% and <NUM> wt. % of the total composition of the composite in composition b.

The entire system, i.e. the composite in variant c, is enriched with a biologically active, engineered peptide, ug46, with the specific amino acid sequence shown on SEQ3, with antimicrobial and anti-inflammatory properties introduced in an amount of <NUM> wt. % to <NUM> wt. % of the total composition of the composite.

The entire system, i.e. the composite in variant d, is enriched with a biologically active, engineered peptide with the specific amino acid sequence shown on SEQ3, in the form of peptide fibrils - UG46, obtained by a known thermal incubation method, with antimicrobial properties, introduced in an amount of <NUM> wt. % to <NUM> wt. % relative to the total composition of the composite.

As for the amount of polymer used in the composite - chitosan, in each of the composite variants described - a, b, c, d it represents:.

The essence of the solution according to the disclosure is also a method of obtaining this composite for filling bone defects and regenerating bone tissue, in which the matrix is a natural biodegradable polymer - chitosan, characterised by a deacetylation degree of DD≥<NUM>%, a viscosity in the range of <NUM> to <NUM> mPas and a molecular weight in the range of <NUM> to <NUM> kDa, containing bioglass and two engineered peptides: ug4 and ug46 or one engineered peptide: ug4 or one engineered peptide: ug46 or peptide fibrils: UG46. The bioactive component in the form of a bioglass with antimicrobial and/or pro- regenerative properties is introduced into the composite at the further described step during the production of the stable dispersion after it has been obtained in an amount ranging from <NUM> wt. % to <NUM> wt. of the total composition of the composite - for variant a, in an amount from <NUM> wt. % to <NUM> wt. % of the total composition of the composite - for variant b, in an amount from <NUM> wt. % to <NUM> wt. % of the total composition of the composite in variant c and in an amount from <NUM> wt. % to <NUM> wt. % of the total composition of the composite in variant d.

The biologically active component in the form of the pro-regenerative peptide ug4 in composite variants a and b is introduced into the composite at the step described below in an amount ranging from <NUM> wt. % to <NUM> wt. % of the total composition of the composite for variant a and from <NUM> wt. % to <NUM> wt. % of the total composition of the composite for variant b, in the form of chitosan modified with this peptide by covalent bonding to this polymer.

The biologically active ingredient - the antimicrobial and anti-inflammatory peptide ug46 in composite variants a and c - is introduced into the composite at the stage described below by surface adsorption: for variant a on the porous chitosan/bioglass/ug4 peptide scaffold in an amount of <NUM> wt. % to <NUM> wt. % relative to the total composition of the composite, for variant c on the porous chitosan/bioglass scaffold in an amount of <NUM> wt. % to <NUM> wt. % relative to the total composition of the composite, or in a variant of composite d is introduced during the manufacture of the stable dispersion in the form of previously obtained peptide fibrils with antimicrobial activity of UG46 by the known method described previously DOI:<NUM>/ijms22083818 in an amount of <NUM> wt. % to <NUM> wt. % relative to the total composition of the composite.

The method of obtaining the composite varies depending on the composition of the composite and how the biologically active peptide is introduced.

In the second step, the ug4 peptide with the sequence Cys Pro Leu Gly Leu Tyr Gly Phe Gly Gly is produced by synthesis on a solid support, e.g. SPPS using the Fmoc methodology, using an automated microwave synthesiser, e.g. Liberty Blue from CEM Corporation. The reaction to cleave the peptide from the carrier with simultaneous removal of the side chain sheaths is carried out using a reaction mixture consisting of trifluoroacetic acid, phenol, water, <NUM>,<NUM>-ethanedithiol and triisopropylsilane. The peptide is subjected to purification using reversed-phase high-performance liquid chromatography.

In the third step - for composite a - the ug4 peptide is attached to the chitosan by the well-known click chemistry method at a rate of <NUM> per <NUM> of chitosan. This method consists in attaching ug4 peptide with the sequence Cys Pro Leu Gly Leu Tyr Gly Phe Gly Gly to the chitosan modified with maleimidoglycine. Modification of chitosan by maleimidoglycine follows the following procedure. Chitosan, e.g. <NUM>/<NUM> [<NUM>, <NUM> mmol, <NUM>/mol], was suspended in <NUM> to <NUM> of hot water and then stirred using e.g. a magnetic stirrer until the solution reached room temperature. The N-hydroxysuccinimidyl ester of aminoacetic acid, e.g. <NUM>, <NUM> mmol, was dissolved in tetrahydrofuran <NUM> to <NUM> relative to the weighed ester for <NUM> to <NUM> under ultrasound, then <NUM> to <NUM> of water was added, e.g. final volume water + THF=<NUM>. After at least <NUM>, the modified chitosan was drained. The modified chitosan was then washed with very cold water depending on the amount of chitosan, e.g. <NUM> of water per <NUM> of chitosan, and lyophilised with acetic acid.

Chitosan modified with peptide ug4 is produced by modification using a covalent bond between the peptide and a maleimide linker attached to the chitosan. Chitosan with a degree of maleimidoglycine modification of <NUM>% to <NUM>% is suspended in water and a concentrated peptide solution is added. The mixture is brought to a pH of <NUM> to <NUM> with sodium bicarbonate and maintained in an argon-filled environment at room temperature with continuous stirring for at least <NUM> hours. The chitosan is then drained The resulting product is washed with very cold water at a rate of <NUM> of water per <NUM> of modified chitosan. The peptide-modified chitosan is lyophilised.

The assumption for chitosan modified with ug4 peptide is that part of this peptide - that is, a peptide called ug1 peptide - will be released from chitosan by enzymatic hydrolysis of the peptide bond in ug4 between Gly<NUM> and Leu<NUM>. The enzymatic cut between these amino acid residues is specific for metalloproteinases found in the bone environment. In order to test the biological activity of the peptide released from chitosan, a peptide with the sequence Leu Tyr Gly Phe Gly Gly (ug1) was synthesised and for which cytotoxicity and pro-regenerative activity tests were performed.

In the fourth step for variant a, a solution of the mixture of chitosan and chitosan modified with ug4 peptide - obtained in the third step - is prepared at a concentration of <NUM>-<NUM> wt. %, in an acidic aqueous solution, in which the weight ratio of chitosan to chitosan modified with peptide ug4 is from <NUM> to <NUM>. At the same time, a paste is prepared on the basis of bioglass particles of known composition and grain size wetted with an acidic aqueous solution with a particle concentration in the range of <NUM> to <NUM> per <NUM> of solution, after which the produced paste is introduced into the chitosan solution and mixed e.g. magnetically for <NUM>-<NUM> minutes at room temperature with the formation of a stable dispersion of the bioglass particles in the acidic chitosan solution with the peptide in this solution so prepared. The produced suspension is then transferred to a mould of any shape and size and subjected to a freeze-drying process to obtain a porous composite structure, the whole system being stabilised by chemical or physical crosslinking before or after the freeze-drying process, and the finished porous structures being washed to neutral pH and freeze-dried again.

In the fifth step for variant a, a peptide ug46 with the sequence Ac Gln Ala Gly Ile Val Val Pro Leu Gly Leu Gly Leu Leu Lys Arg Ile Lys Thr Leu Leu is produced by synthesis on a solid support, e.g. SPPS using the Fmoc methodology, using an automated microwave synthesiser, e.g. Liberty Blue from CEM Corporation. The reaction to cleave the peptides from the carrier with simultaneous removal of the side chain sheaths is carried out using a reaction mixture consisting of trifluoroacetic acid, phenol, water, <NUM>,<NUM>-ethanedithiol and triisopropylsilane. The peptide undergoes purification using reversed-phase high- performance liquid chromatography.

In the sixth step, an aqueous solution of peptide ug46 at a concentration of <NUM> to <NUM>/ml is prepared and applied by adsorption to the surface of the porous chitosan/bioglass/peptide ug4 structures by immersing the porous scaffold in the peptide ug46 solution for <NUM>-<NUM> hours and again drying the porous composite by freeze-drying.

For composition variant b (chitosan/bioglass/ug4 peptide), the process follows the methodology described above - from step one to step four in the same way as for variant a.

In the case of the composition variant c (chitosan/bioglass/peptide ug46), a bioglass is produced in the first step for variant c - description of the methodology as described above - first step for variant a, and then the second step is carried out, i.e.: a solution of chitosan of <NUM>-<NUM> wt. % is prepared in an acidic aqueous solution and at the same time a paste based on bioglass particles of known composition and grain size, wetted with an acidic aqueous solution, with a particle concentration in the range of <NUM> to <NUM> per <NUM> of solution is prepared, after which the paste produced is introduced into the chitosan solution and mixed e.g. magnetically for <NUM>-<NUM> minutes at room temperature to produce a stable dispersion of the bioglass particles in the acidic chitosan solution, and then the suspension is transferred into a mould of any shape and size and lyophilised to obtain a porous composite structure, the entire system is subjected to stabilisation by chemical or physical crosslinking before or after the lyophilisation process, and the finished porous structures are subjected to washing to an inert pH and freeze-drying again. In the third step, the ug46 peptide is produced - description of the methodology identical to that described above - step five for variant a, and then a fourth step analogous to step six for variant a is carried out.

For the composition variant d (chitosan/bioglass/UG46 peptide fibrils), a bioglass is prepared in the first step - description of the methodology as described above - step one for variant a. In the second step, the ug46 peptide is produced with the sequence Ac Gln Ala Gly Ile Val Val Pro Leu Gly Leu Leu Leu Lys Arg Ile Lys Thr Leu Leu, as described in step five for variant a. In step three, UG46 peptide fibrils are produced using the thermal incubation method by dissolving the ug46 peptide in PBS phosphate buffer and placing the sample in a thermal block and incubating for <NUM> days at <NUM> using continuous shaking (<NUM> rpm), as described in publication : DOI: <NUM>/ijms22083818. The fourth step is then carried out analogously to the description for step two for variant c, except that after a stable dispersion of the bioglass in the acidic chitosan solution has been formed, a solution of UG46 peptide fibrils is introduced into the system and the whole is further mixed to homogenisation, and the process is then further carried out as in the description of the methodology as for step two for variant c.

Advantageously for the method of producing all four composite variants (a, b, c, d), the acidic aqueous solution for dissolving the chitosan and producing a paste based on the bioglass particles is a <NUM>-<NUM>% aqueous solution of acetic or lactic or malic or oxalic acid.

Advantageously for compositions a and b, the occupancy of the chitosan chains with the ug4 peptide is <NUM>-<NUM>%.

Advantageously for compositions a and c, the percentage of active peptide ug46 introduced on porous structures by surface adsorption is <NUM>- <NUM>%.

Advantageously for the manufacturing method in variants a and c, the concentration of the solution of peptide ug46 introduced on the porous structures by surface adsorption is between <NUM> and <NUM>/ml.

Advantageously for the manufacturing method in variant d, the concentration of the aqueous solution of peptide fibrils UG46 introduced into the system is between <NUM> and <NUM>/ml.

Advantageously for the method of manufacturing all four composite variants (a, b, c, d), in order to obtain a stable porous structure, the crosslinking of the chitosan chains is carried out during the manufacture of the composite matrix prior to the lyophilisation process using a <NUM>% ethanolic solution of genipin added to the composite mass in a chitosan/genipin weight ratio ranging from <NUM>:<NUM> to <NUM>:<NUM>, mixing the composite matrix with the genipin solution and conditioning the system for <NUM>-<NUM> hours at <NUM>-<NUM> or using a <NUM>% solution of <NUM>-water disodium β-glycerophosphate (BGP) added to the composite mass placed in an ice bath, in a weight ratio of chitosan/BGP ranging from <NUM>:<NUM> to <NUM>:<NUM>, mixing the composite matrix with the BGP solution and conditioning the system for <NUM>-<NUM> hours at <NUM>-<NUM> or in order to obtain a stable porous structure, freeze-dried porous structures not crosslinked during the manufacture of the composite matrix shall be stabilised after the freeze-drying process by immersion in <NUM>-<NUM>% ethanol for <NUM>-<NUM> hours or by crosslinking with the an aqueous solution of <NUM>-water sodium tripolyphosphate with a concentration in the range <NUM>- <NUM> or an ethanolic solution of vanillin with a concentration in the range <NUM>- <NUM>%, by immersing the scaffolds in these solutions for <NUM>-<NUM> hours or by the dehydrothermal method by conditioning the porous scaffolds under reduced pressure at a temperature in the range <NUM>-<NUM> for <NUM>-<NUM> hours.

Advantageously for the manufacturing method, the finished stable porous structures of the composite are washed for <NUM>-<NUM> using <NUM> NaOH and <NUM>-<NUM> hours to a pH in the range of <NUM> - <NUM> using deionised water or <NUM>-<NUM> hours to a pH in the range of <NUM> - <NUM> using deionised water.

In order to make use of the invention and to obtain a usable form of the porous composite (individual, personalised shape and dimension, adapted to the shape and dimension of the bone defect), a suspension is poured into a mould of the desired shape and dimension and then freeze-dried, or by mechanical processing (e.g. cutting or shearing) of the finished porous composite obtained by freeze-drying.

The object of the invention is illustrated in examples <NUM>-<NUM> and in figures <NUM>-<NUM>, wherein compositions and methods not comprising the peptide sequence referred to as "ug46" or SEQ3 are not part of the invention; in particular.

Peptides were synthesised on solid support (SPPS) using Fmoc methodology, using CEM Corporation's Liberty Blue automated microwave synthesiser with a constant flow of reagents on Rink Amide ProTide Resin with a capacity <NUM> mmol/g (<NUM>, <NUM> mmol). The peptides were cleaved from the resin with simultaneous removal of side chain sheaths was carried out using a trifluoroacetic acid (TFA), phenol, water, <NUM>,<NUM>-ethanedithiol (EDT) and triisopropylsilane (TIPSI) (<NUM>:<NUM>:<NUM>:<NUM>:<NUM>; v/v/v/v/v/v). For <NUM> of resin, <NUM> of the mixture was used. The reaction was carried out for three hours using a laboratory shaker, and then the resin was drained. The filtrate was concentrated using a vacuum evaporator. The crude product was precipitated from the mixture using diethyl ether. The resulting precipitate was centrifuged for <NUM> minutes at <NUM> at <NUM> rpm. The crude and dry product was dissolved in water and subjected to sublimation drying using a freeze-dryer.

Peptides were purified using reversed-phase high-performance liquid chromatography (chromatograph consisting of two pumps (K1001) and a UV detector (K-<NUM>) coupled to a Gilson collector) using a semipreparative Jupiter® Proteo-<NUM>-<NUM>-C8 column (Phenomenex) (<NUM> × <NUM>). Chromatographic separation was carried out in a linear gradient. The mobile phase was a solvent system:.

The eluent flow rate was <NUM>/min, UV detection at λ = <NUM>.

Reversed-phase high-performance liquid chromatography (Nexera X2 chromatograph, Shimadzu) was used to determine the purity of the synthesised peptides using an analytical Kromasil-<NUM>-<NUM>-C8 column (<NUM> × <NUM>), volumetric flow rate was <NUM>/min, eluents:.

The identity of peptides was confirmed by Bruker Briflex III MALDI-TOF spectrometer from Bruker Daltonics and/or LCMS-ESI-IT-TOF on a Kromasil-<NUM>-<NUM>- C8 column (<NUM> × <NUM>). The theoretical monoisotopic molecular weight of the compounds, experimental weights and retention times are shown in Table <NUM>. The mass spectra of the purified peptides are shown in <FIG>.

Chitosan <NUM>/<NUM> [<NUM>, <NUM> mmol, <NUM>/mol] was suspended in <NUM> hot water - stirred with a magnetic stirrer until the solution reached room temperature.

Aminoacetic acid N-hydroxysuccinimide ester [<NUM>, <NUM> mmol] was dissolved in <NUM> of tetrahydrofuran (<NUM> on ultrasound), then <NUM> of water was added. The solution thus prepared was added to the chitosan suspension. The whole mixture was left for <NUM> with intensive stirring using a magnetic stirrer. After this time, the pH was brought to a value of <NUM> with sodium hydrogencarbonate. The mixture was left for <NUM> with continuous stirring. After <NUM>, the modified chitosan was drained on a Schott funnel with the smallest possible pores. The modified chitosan was then washed with very cold water about <NUM> for this amount of chitosan. The washed chitosan was lyophilised from acetic acid. The ug4 peptide is then attached to the chitosan by a known click chemistry method at a rate of <NUM> per <NUM> of chitosan. This method involves the attachment of ug4 peptide with the sequence Cys Pro Leu Gly Leu Tyr Gly Phe Gly Gly to maleimidoglycine - modified chitosan. Chitosan with a <NUM>% degree of maleimidoglycine modification (<NUM>) was placed in a round-bottomed flask and <NUM> of water was added. A solution of ug4 peptide (<NUM> ug4 peptide was dissolved in deionised water) was added to the previously prepared suspension. The mixture was brought to pH~<NUM> by adding <NUM> of NaHCO<NUM>. Once the correct pH was achieved, a balloon filled with argon was placed over the neck of the flask to limit the oxidation of the free cysteine located at the N-terminus of the attached peptide. The reaction mixture was left at room temperature with continuous stirring for <NUM> (<FIG>). The chitosan was then drained using an oozing kit under reduce. The resulting product was washed with very cold water (<NUM> of water per <NUM> of modified chitosan). The peptide-modified chitosan was lyophilised.

The modified chitosan was analyzed for the degree of deposition. The procedure for the determination of the peptide differs from that used in the above-mentioned patent application. In this procedure the addition of the internal standard solution and the amino acid to be determined, i.e. a <NUM> solution of lysine in <NUM> hydrochloric acid was used to quantify the peptide attached to the chitosan. The amount of internal standard, was recalculated so that the mass of lysine added was equal to the expected mass of one of the amino acids contained in the attached peptide (leucine) contained in the sample. Samples after the hydrolysis procedure were analysed by high-performance liquid chromatography on normal phases using a Shimadzu NEXERA X2 chromatograph using a Phenomenex BioZen column of size: <NUM> × <NUM>. The flow rate was <NUM>/min. The composition of the mobile phases was: System A: <NUM> ammonium formate, <NUM> formic acid, <NUM>% ACN in water and System B: <NUM> ammonium formate, <NUM> formic acid, <NUM>% ACN in water. The time for a single analysis was <NUM>. To determine the degree of deposition, the ratio of leucine to lysine in the sample should be compared to the ratio of these amino acids from a standard curve of their mixture of equal and known masses.

Three samples (<NUM>) of modified chitosan were subjected to the hydrolysis reaction, and three chromatographic analyses were performed for each sample. The ratio of the area under the leucine to lysine peak on the common chromatogram was compared with the determined ratio of these amino acids from a standard curve performed under the same conditions as the analysis of the target samples. The results are shown in Table <NUM>. From the data obtained, it can be seen that maleimidoglycine bound to chitosan was fully deposited with peptide ug4 (<FIG>).

The ug46 peptide was thermally incubated to obtain mature peptide fibrils. For this purpose, <NUM> of the peptide was dissolved in <NUM> of PBS phosphate buffer. The sample was placed in a thermal block and incubated for <NUM> days at <NUM> using continuous shaking (<NUM> rpm). On subsequent days of incubation, samples were taken for characterisation of the growing peptide fibrils, starting when the peptide was dissolved in PBS buffer. The collected samples were analysed using the following techniques: atomic force microscopy (AFM), transmission electron microscopy (TEM) and thioflavin assay.

Microscopic analysis (TEM) of samples taken on consecutive days of incubation confirmed that the process of peptide fibre formation begins immediately after the peptides are dissolved in PBS buffer. The analysis was performed by placing a small amount of peptide on a microcellulose mesh and then staining with <NUM>% uranyl acetate. Images were taken using a TECNAI SPIRIT BIO TWIN FEI microscope at <NUM> kV excitation. The images show that already after <NUM> hours of incubation, the formed ug46 peptide fibers reach a length of <NUM> to <NUM>. During the following days of incubation, the formed protofibrils become organised, as evidenced by the mature filaments visible on day <NUM> of incubation, consisting of several parallel filaments that twist around their axis. The twisting of the fibrils visible in the images is reproducible and occurs throughout the length of the formed fibrils every <NUM> (<FIG>).

In the next experiment, the samples taken during incubation with the fluorescent dye thioflavin T were measured. The analysis was carried out to confirm the presence of β-structures, which form a complex with thioflavin T to give a characteristic emission spectrum at <NUM>. The spectra were recorded on a Tekan Infinite 200Pro spectrofluorimeter in COSTAR Flat plate Black <NUM>-well plates. A peptide solution of <NUM>/ml in PBS with thioflavin T solution, whose final concentration in the sample was <NUM>, was used for the measurement. The negative control was a PBS solution with thioflavin T. The sample was excited at <NUM> and the emission spectrum was recorded between <NUM> and <NUM>. The absorption maximum was at <NUM>. The increase in fluorescence emission intensity of the complex T peptide-thioflavin with advancing incubation time reaches its maximum at day <NUM> of incubation.

In addition, an experiment was performed to incubate previously obtained peptide fibrils in the presence of the enzyme metalloproteinase VII. The enzyme MMP-<NUM> (enzyme:substrate molar ratio used - <NUM>:<NUM>) (Sigma Aldrich, St. Louis, MO, USA) was added to ug46 fibrils formed by aggregation at a concentration of <NUM>/ml in PBS. The incubation process was carried out for <NUM> at <NUM> with agitation. Samples were taken at the following time points <NUM>, <NUM>, <NUM>, <NUM>, <NUM>, and a <NUM>% TFA solution was added to each sample to inhibit the digestion reaction. Experimental results were analysed using a Bruker Briflex III MALDI-TOF spectrometer from Bruker Daltonics.

MS analysis showed that, under the influence of the enzyme, a peptide containing the active sequence was released from the fibril. Enzymatic cutting occurred at the expected cutting site, i.e. between Gly and Leu residues, in the Pro Leu Gly Leu sequence specific for MMP-<NUM>. Two main products of enzymatic hydrolysis were observed in the MALDI mass spectra: an active sequence with an enzyme-specific fragment (Leu Gly Leu Leu Lys Arg Ile Lys Thr Leu Leu; <NUM> [M+ H]) and a second fragment (Ac Gln Ala Gly Ile Val Val Pro Leu Gly; <NUM> [M+Na]+ ) comprising a fibrillogen sequence (Ac Gln Ala Gly Ile Val Val) and a part of the peptide with an MMP-<NUM>-specific fragment (Pro Leu Gly).

Cytotoxicity was tested by an indirect method based on the guidelines in ISO <NUM>- <NUM> on the hFOB human osteoblast cell line (ATCC) using the LDH assay (Roche). The results presented were averaged from two technical repeats and presented as % relative to control cells treated with <NUM>% Triton X- <NUM> solution. proliferation was tested by an indirect method based on the guidelines in ISO <NUM>- <NUM> on the hFOB human osteoblast cell line (ATCC) using the WST-<NUM> assay (Abcam). The results shown were averaged from two technical repeats and presented as % in relation to control cells cultured without added peptides.

None of the concentrations of the tested peptides induced cytotoxicity exceeding <NUM>% (<FIG>, <FIG>).

For most concentrations of ug1/ug4 peptide, proliferation reached values above <NUM>% of proliferation of control cells (<FIG>). None of the ug1/ug4 peptide concentrations resulted in proliferation lower than <NUM>% of proliferation of control cells.

Only for peptide ug46 at a concentration of <NUM>µg/ml proliferation value dropped below <NUM>%. Proliferation values exceeding <NUM>% were observed for the other ug46 peptide titrations (<FIG>).

Proliferation and cytotoxicity data were analysed and visualised using GraphPad Prism <NUM> software (GraphPad Software, USA). Statistical analysis was performed using the Kruskal- Wallis test (p = <NUM>). In the next step, the Benjamini, Krieger and Yekutielli multiple comparisons test was performed to control the false discovery rate (p = <NUM>). Comparisons were made between results obtained for individual peptide concentrations.

For ug1/ug4 peptides - the presence of different concentrations of ug1/ug4 peptides did not induce statistically significantly different cytotoxicity. Statistically significant differences occurred between proliferation of cells growing in the presence of <NUM>µg/ml and <NUM>µg/ml ug1/ug4 peptide (p = <NUM>).

For peptide ug46 - statistically significant differences occurred between the cytotoxicity of cells growing in the presence of <NUM>µg/ml and <NUM>µg/ml of peptide ug46 (p = <NUM>). Statistically significant differences also occurred for the comparison of the proliferation observed for peptide ug46 at <NUM>µg/ml with the other tested concentrations of this peptide (p <<NUM> ,<NUM>). The tested peptides are not cytotoxic and, at appropriate concentrations, do not have a detrimental effect on cell proliferation. Peptide ug46 for most concentrations tested stimulates cell proliferation.

The antimicrobial properties of the peptide were tested based on Clinical and Laboratory Standards Institute (CLSI) guidelines according to CLSI M07-A9 <NUM> using the microdilution method. Two bacterial pathogens were used for the study: Gram-positive Staphylococcus aureus PCM <NUM> and Gram-negative Pseudomonas aeruginosa PCM <NUM>.

The bacterial inoculum for the experiment was prepared by direct inoculation of Brain-Heart Infusion medium (BHI) with bacteria from a <NUM>-hour culture on solid medium. The density of the suspension was <NUM> on the McFarland scale. The peptide concentration analysed : <NUM> - <NUM>µg/ml. Serial dilutions were performed in a <NUM>-well, flat-bottomed, hydrophobic cell culture plate using BHI liquid medium. Then the previously prepared bacterial suspension was added. The final number of pathogens in each well was approximately <NUM> × <NUM><NUM> CFU/ml (Colony Forming Units per millilitre). Microplates were incubated for <NUM> hours at <NUM> under aerobic conditions. The minimum inhibitory concentration (MIC) for a peptide was defined as the lowest concentration of peptide in a well where no bacterial growth was observed. All experiments were performed in triplicate.

The anti-inflammatory properties of peptide ug46 were tested on the human fibroblast cell line WI-<NUM> (ATCC). Inflammation was stimulated using lipopolysaccharide (LPS) with a final concentration in the culture medium of <NUM> ng/ml. The level of interleukin <NUM> (IL-<NUM>) secreted by WI-<NUM> cells, which is one of the markers of inflammation, was determined using the IL-<NUM> Human Uncoated ELISA Kit (Invitrogen). Immediately before the experiment, dilutions of ug46 peptide were prepared in culture medium at concentrations of <NUM>, <NUM>, <NUM>, <NUM>, <NUM>, <NUM>, <NUM>, <NUM>, <NUM> and <NUM>µg/ml. Dilutions were made in medium with <NUM> ng/ml LPS and in medium without LPS. The results obtained indicate for a slight stimulation of inflammation by peptide ug46 alone at peptide concentrations above <NUM>µg/ml. In contrast, at peptide ug46 concentrations in the range <NUM>-<NUM>µg/ml, an approximately <NUM>-<NUM>% decrease in the amount of LPS-mediated interleukin <NUM> was observed, indicating an anti-inflammatory effect of the peptide. In addition, at these concentrations, no deviation was observed for cells incubated without the addition of LPS (<FIG>).

One at a time, <NUM> of anhydrous ethanol was measured into a PTFE beaker and <NUM> of C<NUM>H<NUM>O<NUM>Si was slowly added using intense stirring with a magnetic stirrer. Then <NUM> of C<NUM>H<NUM>O<NUM>P<NUM> was added catalysing the system with <NUM> HNO<NUM>. After homogenisation, <NUM> of a Ca(NO<NUM>)<NUM>·<NUM><NUM>O <NUM> wt. % solution was added. The whole mixture was homogenised using a magnetic stirrer. The beaker with the reaction mixture was then placed in a drying oven and held at <NUM> for <NUM> days. After each additional <NUM> days, the drying temperature was increased to <NUM>, <NUM>, <NUM> and <NUM>. After holding for <NUM> days at <NUM>, the dried gel was transferred to a ceramic crucible and placed in an electric oven. Heating was carried out at <NUM>° C for <NUM> and then at <NUM> for <NUM>. After removal from the furnace, the bioglass was crushed in a mechanical mortar to a grain size where <NUM>% of the grains were below <NUM>. The crushed glass was then placed in a rotary-vibrating mill with <NUM> diameter alundum grinders and ground to a grain size where <NUM>% of the grains were below <NUM>.

The characterisation of the P5_II bioglass was carried out according to the methodology described below. This methodology was applied to the characterisation of all bioglass (Examples <NUM>-<NUM>).

The grain size analysis of the glass obtained was carried out with a Malvern Instruments Mastersizer <NUM> laser analyser, using the low-angle laser light scattering (LALLS) method. The instrument used allows the grain size to be examined over a wide range from <NUM> to <NUM> with an error of <NUM>%. The following characteristic values were determined: Dv (<NUM>) - value of the particle size below which the is <NUM>% of the test sample population by volume, Dv (<NUM>) - the particle size value below which <NUM>% of the test sample population by volume occurs, Dv (<NUM>) - the particle size value below which <NUM>% of the test sample population by volume occurs. FTIR analysis of the glass produced was performed using a Bruker TENSOR27 FTIR spectrophotometer. To prepare a suitable sample for the test (KBr tablet), a weight of approximately <NUM> of dried KBr was mixed with approximately <NUM>-<NUM> of glass sample. Measurements were performed in ATR mode. The following abbreviations were used in the description of the FTIR spectra: v - tensile vibrations, νas - asymmetric tensile vibrations, νs - symmetric tensile vibrations, δ - bending vibrations. The effect of bioglass on human cells was tested using the LDH assay (Roche) cytotoxicity assay and the WST-<NUM> assay (Abcam) cell proliferation. A human hFOB osteoblast cell line (ATCC) was exposed to <NUM> of bioglass placed on cell culture inserts (Sarstedt) (PET, translucent, pore size: <NUM>). Measurements were taken after <NUM> of incubation of the cells with the test material. Cytotoxicity results were averaged from two technical runs and presented as % for control cells exposed to <NUM>% Triton X-<NUM> solution. Proliferation results were averaged from two technical runs and presented as % for control cells cultured with the insert without bioglass.

In order to test the antimicrobial effect of the bioglass, <NUM> of a bacterial suspension with an optical density of <NUM> on the McFarland scale (~<NUM> × <NUM><NUM> CFU/ml) was added to the <NUM> weights (in sterile <NUM> eppendorf tubes). The control sample was silicon (IV) oxide and the antibiotic gentamicin at a final concentration of <NUM>µg/ml. Each sample was agitated for <NUM> using a vortex mixer. The samples were then incubated at <NUM> under aerobic conditions for <NUM>. After incubation, serial dilutions of each sample were made and then a volume of <NUM>µl of the suspension was seeded onto agar solidified LB (lysogeny broth) plates. Plates were incubated at <NUM> for <NUM>. After incubation, bacterial colonies were counted and the percentage reduction in the number of microorganisms was determined according to the formula: <MAT> Where:.

LALLS analysis results: dv(<NUM>,<NUM>) <NUM>; dv(<NUM>,<NUM>) <NUM>; dv(<NUM>,<NUM>) <NUM>.

FTIR analysis result: <NUM>-<NUM>-<NUM> - v O-H (SiO-H)(HO-H), <NUM>-<NUM> - δ O-H (HO-H), <NUM>-<NUM> and <NUM>-<NUM> - νas Si-O-Si, <NUM>-<NUM> - νs Si-O-Si, <NUM> and <NUM>-<NUM> - δ P-O in PO<NUM><NUM>-, <NUM>-<NUM> - δ Si-O-Si.

The labelled cytotoxic effect of the bioglass is below the designated threshold of <NUM>% (<FIG>). The labelled proliferation of the bioglass exceeds the designated threshold of <NUM>% (<FIG>).

The determined bactericidal activity of the bioglass in contact with the micro-organisms Staphylococcus aureus PCM <NUM> and Pseudomonas aeruginosa PCM <NUM>, in combination with gentamicin and silicon oxide, is shown in the graph (<FIG>).

One at a time, <NUM> of anhydrous ethanol was measured into a PTFE beaker and <NUM> of C<NUM>H<NUM>O<NUM>Si was slowly added using intense stirring with a magnetic stirrer. Then <NUM> of C<NUM>H<NUM>O<NUM>P<NUM> was added catalysing the system with <NUM> HNO3. After homogenisation, <NUM> of a Ca(NO<NUM>)<NUM>·<NUM><NUM>O and <NUM> of a Sr(NO<NUM>)<NUM> solution of <NUM>% w/w was added. The synthesis was then carried out as described in Example <NUM>, except that the heating of the dried gel was carried out in an electric oven at <NUM> for <NUM>. After removal from the oven, the bioglass was crushed in a mechanical mortar to a grain size where <NUM>% of the grains were below <NUM>. The crushed glass was then placed in a rotary-vibrating mill with <NUM> diameter alundum grinders and ground to a grain size where <NUM>% of the grains were below <NUM>.

The cytotoxic effect of the vitreous is below the designated threshold of <NUM>% (<FIG>). Proliferation exceeds the designated threshold of <NUM>% (<FIG>).

The reduction [%] in the number of micro-organisms is shown in the graph (<FIG>).

One at a time, <NUM> of anhydrous ethanol was measured into a PTFE beaker and <NUM> of C<NUM>H<NUM>O<NUM>Si was slowly added using intense stirring with a magnetic stirrer. Then <NUM> of C<NUM>H<NUM>O<NUM>P<NUM> was added catalysing the system with <NUM> HNO3. After homogenisation, <NUM> of a Ca(NO<NUM>)<NUM>·<NUM><NUM>O and <NUM>,<NUM> of a Zn(NO<NUM>)<NUM>·<NUM><NUM>O <NUM>% w/w solution was added. The synthesis was then carried out as described in Example <NUM>, except that the heating of the dried gel was carried out in an electric oven at <NUM> for <NUM>. After removal from the oven, the bioglass was crushed in a mechanical mortar to a grain size where <NUM>% of the grains were below <NUM>. The crushed glass was then placed in a rotary-vibrating mill with <NUM> diameter alundum grinders and ground to a grain size where <NUM>% of the grains were below <NUM>.

The cytotoxic effect of the glasses is below the designated threshold of <NUM>% (<FIG>). Proliferation exceeds the designated threshold of <NUM>% (<FIG>). The reduction [%] in the number of micro-organisms is shown in the graph (<FIG>).

To <NUM> of chitosan, <NUM> of chitosan modified with ug4 peptide and <NUM> of <NUM>% (v/v) acetic acid were added, and the contents of the vessel were stirred until the chitosans were completely dissolved. At the same time, <NUM> of P5Zn2_II bioglass and <NUM> of <NUM>% (v/v) acetic acid were placed in a separate vessel and stirred until a homogeneous paste of bioglass particles was formed. The resulting paste was then introduced into a vessel with the chitosan solution and stirred until a stable dispersion of the bioglass particles in the acidic chitosan solution was obtained. The suspension produced was transferred to a mould of the desired shape and size and subjected to the freeze-drying process. After removal from the freeze-dryer chamber, the dried materials were protected against moisture. The resulting composite porous scaffolds were stabilised by immersion in <NUM>% ethanol for <NUM> hours. After this time, the stabilised scaffolds were washed with <NUM> NaOH for <NUM> hour and then with deionised water for <NUM> hours, changing the water several times until the pH was in the range of <NUM>-<NUM>. The washed scaffolds were subjected to freeze-drying again. The final product had a chitosan/bioglass content of <NUM>/<NUM>, with <NUM> wt. % chitosan as modified chitosan containing <NUM> wt. % of ug4 peptide.

The characterisation of the CH_CH_ug4_0.8_P5Zn2II composite was carried out according to the methodology described below. This methodology was also applied to the characterisation of the porous composites in the following examples <NUM> - <NUM>.

The porous microstructure of the composite and its pore size range were confirmed by scanning electron microscopy SEM. The specific surface area was determined using the BET method. The product structure was confirmed by Fourier transform infrared spectroscopy. The bioactivity of the composite, defined as the growth of an apatite layer on the composite surface, was confirmed by SEM observations and EDS analysis of composites incubated in simulated body fluid (SBF) at <NUM> for <NUM> weeks. Cytotoxicity was tested by an indirect method based on guidelines from ISO <NUM>-<NUM> on a human hFOB osteoblast cell line (ATCC) using an LDH assay (Roche). Results shown were averaged from two technical runs and presented as % relative to control cells treated with <NUM>% Triton X-<NUM> solution. Proliferation was tested by an indirect method based on guidelines from ISO <NUM>-<NUM> on a human osteoblast cell line hFOB (ATCC) using the WST-<NUM> assay (Abcam). The results shown were averaged from two technical runs and presented as % relative to control cells not in contact with the composite extract. Peptide release from the composite was determined by immersing the composite in water with MMP-<NUM> enzyme and analysing the compounds released into solution over time, qualitative and quantitative analysis was performed by UPLC and mass spectrometry. Release experiments were performed in a <NUM>-well plate at <NUM> with continuous shaking. The discs were placed in the well of the plate and <NUM> of deionised water and <NUM>µl of MMP-<NUM> enzyme were added. At each time point, <NUM>µl of the sample solution was taken and the volume taken was replenished with <NUM>µl of deionised water. Performed over a time interval of <NUM> - <NUM>, <NUM> discs were used for the experiment. High-performance reversed-phase liquid chromatography (Nexera X2, Shimadzu) was used to quantify the peptide content of the samples using an analytical Kromasil column (<NUM> × <NUM>; C-<NUM>; <NUM>), the volumetric flow rate was <NUM>/min, eluents: A - <NUM>% TFA in H<NUM>O (v/v), B- <NUM>% CH<NUM> CN in <NUM>% TFA in H<NUM>O (v/v). Qualitative analysis was performed using a Bruker Briflex III MALDI-TOF spectrometer from Bruker Daltonics.

SEM, SEM/EDS: The resulting composite has a porous structure with a pore size in the range <NUM>-<NUM> (<FIG>).

BET: The specific surface area of the composite was <NUM> ± <NUM> [m<NUM>/g].

FTIR-ATR: <NUM>-<NUM>-<NUM> and <NUM>-<NUM> - v OH, v NH, <NUM>-<NUM>, <NUM>-<NUM> - v CH, <NUM>-<NUM> - ν C=O, <NUM>-<NUM> - δ N-H, <NUM>-<NUM>-<NUM>-<NUM>- δ - OH, δ C-H and v C-O w (-CH<NUM>-OH) and v C=N, <NUM>-<NUM> - νas C-O-C, <NUM>-<NUM> and <NUM>-<NUM> - νas Si-O-Si, <NUM>-<NUM> - v C-O-C, <NUM>-<NUM> - δ O=CN (in ug4) and <NUM>-<NUM> and <NUM>-<NUM> - δ P-O.

Bioactivity: EDS analysis of the surface of the composite incubated in SBF for <NUM> weeks showed the presence of intense Ca and P signals, indicating that an additional layer of calcium phosphate is formed on the surface of the incubated composite and that the composite therefore exhibits bioactivity. The SEM image of the incubated composite shows characteristic hydroxyapatite islands (<FIG>).

Cytotoxicity: the mean cytotoxicity of the composite was -<NUM>% (± <NUM>%) relative to control cells. The composite showed no cytotoxic properties (<FIG>).

Proliferation: the average proliferation of the composite was <NUM>% (± <NUM>%) relative to control cells. The composite showed pro-proliferative properties (<FIG>).

Peptide release: the amount of peptide released was below the limit of quantification.

To <NUM> of chitosan, <NUM> of chitosan modified with ug4 peptide and <NUM> of <NUM>% (v/v) acetic acid were added, and the contents of the vessel were stirred until the chitosans were completely dissolved. At the same time, <NUM> of P5Zn2_II bioglass and <NUM> of <NUM>% (v/v) acetic acid were placed in a separate vessel and stirred until a homogeneous paste was formed. The process of obtaining the composite was then carried out identically to Example <NUM>. In the final product, the content of chitosan relative to the bioglass was <NUM>/<NUM>, with <NUM> wt. % chitosan being a modified chitosan containing
<NUM> wt. % of ug4 peptide.

FTIR-ATR: <NUM>-<NUM>-<NUM> and <NUM>-<NUM> - v OH, v NH, <NUM>-<NUM>, <NUM>-<NUM> - v CH, <NUM>-<NUM> - ν C=O, <NUM>-<NUM> - δ N-H, <NUM>-<NUM>-<NUM>-<NUM> - δ - OH, δ C-H and v C-O in (-CH<NUM>-OH) and v C=N, <NUM>-<NUM> - νas C-O-C, <NUM>-<NUM> and <NUM>-<NUM> - νas Si-O-Si, <NUM>-<NUM> - v C-O-C, <NUM>-<NUM> - δ O=CN (in ug4) and <NUM>-<NUM> and <NUM>-<NUM> - δ P-O.

Bioactivity: The composite shows bioactivity after <NUM> weeks of incubation in SBF (<FIG>). Cytotoxicity: The average cytotoxicity of the composite was -<NUM>% (± <NUM>%) relative to control cells. The composite showed no cytotoxic properties (<FIG>).

To <NUM> of chitosan, <NUM> of chitosan modified with ug4 peptide and <NUM> of <NUM>% (v/v) acetic acid were added, and the contents of the vessel were stirred until the chitosans were completely dissolved. At the same time, <NUM> of P5Zn2_II bioglass and <NUM> of <NUM>% (v/v) acetic acid were placed in a separate vessel and stirred until a homogeneous paste was formed. The process of obtaining the composite was then carried out identically to Example <NUM>. In the final product, the content of chitosan relative to the bioglass was <NUM>/<NUM>, with <NUM> wt. % chitosan being a modified chitosan containing <NUM> wt. % of ug4 peptide.

FTIR-ATR: <NUM>-<NUM>-<NUM> and <NUM>-<NUM> - v OH, v NH, <NUM>-<NUM>, <NUM>-<NUM> - v CH, <NUM>-<NUM> - ν C=O, <NUM>-<NUM> - δ N-H, <NUM>-<NUM> -<NUM>-<NUM> - δ - OH, δ C-H and v C-O w (-CH<NUM>-OH) and v C=N, <NUM>-<NUM> - νas C-O-C, <NUM>-<NUM> and <NUM>-<NUM> - νas Si-O-Si, <NUM>-<NUM> - v C-O-C, <NUM>-<NUM> - δ O=CN (in ug4) and <NUM>-<NUM> and <NUM>-<NUM> - δ P-O.

To <NUM> of chitosan, <NUM> of chitosan modified with ug4 peptide and <NUM> of <NUM>% (v/v) acetic acid were added, and the contents of the vessel were stirred until the chitosans were completely dissolved. At the same time, <NUM> of P5Sr2_II bioglass and <NUM> of <NUM>% (v/v) acetic acid were placed in a separate vessel and stirred until a homogeneous paste was formed. The process of obtaining the composite was then carried out identically to Example <NUM>. In the final product, the content of chitosan relative to the bioglass was <NUM>/<NUM>, with <NUM> wt. % chitosan being a modified chitosan containing <NUM> wt. % of ug4 peptide.

FTIR-ATR: <NUM>-<NUM>-<NUM> and <NUM>-<NUM> - v OH, v NH, <NUM>-<NUM>, <NUM>-<NUM> - v CH, <NUM>-<NUM> - v C=O, <NUM>-<NUM> - δ N-H, <NUM>-<NUM>-<NUM>-<NUM> - δ - OH, δ C-H and v C-O in (-CH<NUM>-OH) and v C=N, <NUM>-<NUM> - νas C-O-C, <NUM>-<NUM> and <NUM>-<NUM> - νas Si-O-Si, <NUM>-<NUM> - v C-O-C, <NUM>-<NUM> - δ O=CN (in ug4) and <NUM>-<NUM> and <NUM>-<NUM> - δ P-O.

Bioactivity: The composite shows bioactivity after <NUM> week of incubation in SBF (<FIG>). Cytotoxicity: The average cytotoxicity of the composite was -<NUM>% (± <NUM>%) relative to control cells. The composite showed no cytotoxic properties (<FIG>).

Release of peptide: Released amount of peptide was found located below the limit of quantification.

To <NUM> of chitosan, <NUM> of chitosan modified with ug4 peptide and <NUM> of <NUM>% (v/v) acetic acid were added, and the contents of the vessel were stirred until the chitosans were completely dissolved. At the same time, <NUM> of P5Zn2_II bioglass and <NUM> of <NUM>% (v/v) acetic acid were placed in a separate vessel and stirred until a homogeneous paste was formed and the process of obtaining the composite was continued according to the method described in Example <NUM>. The porous composite produced was then immersed in an aqueous solution of ug46 peptide at a concentration of <NUM>/ml for <NUM>, after which it was freeze-dried again. The final product had a chitosan/bioglass content of <NUM>/<NUM>, with <NUM> wt. % chitosan as modified chitosan containing <NUM> wt. % of ug4 peptide.

FTIR-ATR: <NUM>-<NUM>-<NUM> and <NUM>-<NUM> - v OH, v NH, <NUM>-<NUM>, <NUM>-<NUM> - v CH, <NUM>-<NUM> - v C=O, <NUM>-<NUM> - δ N-H, <NUM>-<NUM>-<NUM>-<NUM> - δ - OH, δ C-H and v C-O in (-CH<NUM>-OH) and v C=N, <NUM>-<NUM> - νas C-O-C, <NUM>-<NUM> and <NUM>-<NUM> - νas Si-O-Si, <NUM>-<NUM> - v C-O-C, <NUM>-<NUM> - δ O=CN (peptides) and <NUM>-<NUM> and <NUM>-<NUM> - δ P-O.

Bioactivity: The composite shows bioactivity after <NUM> weeks of incubation in SBF (<FIG>). Cytotoxicity: The average cytotoxicity of the composite was <NUM>% (± <NUM>%) against control cells. The composite showed no cytotoxic properties (<FIG>).

For the composite CH_CH_ug4_3.4_P5Zn2II_ug46, and other composites enriched with the ug46 peptide (Examples <NUM>-<NUM>), the antimicrobial surface activity was determined according to the adapted ASTM E2180-<NUM><NUM> standard using the Gram-positive bacterium Staphylococcus aureus PCM <NUM> and the Gram-negative bacterium Pseudomonas aeruginosa PCM <NUM> against a control sample - a composite without the addition of the bioglass/peptide (CH).

Antimicrobial activity: The average percentage reduction in the number of bacteria relative to the control sample (CH) was <NUM>% against S. aureus bacteria and <NUM>% against P. aerugionosa bacteria (<FIG>).

For the CH_CH_ug4_3.4_P5Zn2ll_ug46 composite, in vivo biocompatibility was tested. The tests were performed in accordance with EN ISO <NUM>-<NUM>: "Biological evaluation of medical devices - Part <NUM>: Tests for local effects after implantation" and EN ISO <NUM>-<NUM>: "Biological evaluation of medical devices - Part <NUM>: Tests for systemic toxicity".

The study was performed according to the recommendations of EN ISO <NUM>-<NUM>: "Biological evaluation of medical devices - Part <NUM>: Tests for systemic toxicity". Samples of the CH_CH_ug4_3.4_P5Zn2ll_ug46 composite were formed into <NUM> × <NUM> discs and subjected to radiation sterilisation. A systemic acute toxicity study was carried out on <NUM> albino Swiss strain, male mice, allocating <NUM> animals to the biocomposite study and <NUM> animals to the control group. The initial mean body weight of the animals was <NUM> (±<NUM>) g in the control group and <NUM>(±<NUM>) g in the group allocated to the composite study. The animals, housed in groups, were subjected to handling training during the acclimatisation period in order to become accustomed to the touch of the investigator. Tests were carried out after intraperitoneal injection of aqueous extracts from the test biocomposite at a rate of <NUM>/kg of mouse body weight (i.e. from <NUM> to <NUM>, averaging <NUM> for individual mice) in the test group and similarly-injection from saline for injection in the control group. The extract of the tested biocomposite was prepared after flooding the samples - with saline solution for injection at a ratio of the bilateral surface area of the samples to the volume of the extraction mixture - <NUM><NUM>/ml. The extracts were then incubated with a parallel control, which was saline - solution for injection at <NUM> for <NUM>. Observations of the injected animals were carried out for <NUM> days and included changes in appearance, behavioural abnormalities, stunted weight gain and mortality. Mice were weighed daily, normal function was observed, feed and water consumption was measured, and differences in weight gain between animals of the test and control groups were assessed.

No physical or behavioural changes indicative of disease were found in either the test group or the control group during the health observations carried out on the animals. Each physical examination considered the test animal to be clinically healthy. During the <NUM>-day experimental (post-inoculation) period, there were no behavioural deviations or any signs of disease in the animals, either in the control group or the test group. All mice were considered clinically healthy. Feed and water consumption and body weight gain in the test groups were comparable to the data obtained in the control group, and the differences were not statistically significant. All mice survived until the scheduled postmortem date. There were no abnormalities in behaviour, appearance or differences in weight gain between the test groups and the control group. After <NUM> days, euthanasia (with pentobarbital) and postmortem examinations were performed. Postmortem examinations of the animals, both from the control group and the test group, revealed no skin lesions, skeletal or muscular changes. The natural body orifices (external ear, eyes, nostrils, mouth, anus) and external genitalia showed no lesions. In the peritoneal cavity and thorax, all organs were positioned correctly, with preserved anatomical shape, colour and size. None of the visually inspected organs showed macroscopic pathological changes. No pathological changes were found at autopsy. On the basis of tests carried out on the basis of EN ISO <NUM>-<NUM>: "Biological evaluation of medical devices - Part <NUM>: Tests for systemic toxicity", it was concluded that the samples of the tested biocomposite do not show systemic acute toxicity.

For the CH_CH_ug4_3.4_P5Zn2ll_ug46 composite, in vivo biocompatibility was tested using a rabbit model (New Zealand rabbits, both sexes). The tests were performed in accordance with EN ISO <NUM>-<NUM>: "Biological evaluation of medical devices - Part <NUM>: Tests for local effects after implantation" and EN ISO <NUM>-<NUM>: "Biological evaluation of medical devices - Part <NUM>: Tests for systemic toxicity" (bioethics committee approval for experiments number <NUM>/<NUM>/P1). The study plan included: implantation into the femur of rabbits (<NUM> implants were placed in each trochanter), macroscopic (postmortem) and histological examinations at <NUM>, <NUM> and <NUM> months after surgery, and radiological examinations. After implantation of the tested composite, observation of the rabbits' general health was carried out, with particular consideration on postoperative wound healing, active and passive mobility of the hip joint and feed intake. During the dissections performed, the post- operative wound and the appearance of the tissues at the site of implantation of the specimens were evaluated macroscopically first, followed by an assessment of the appearance of selected internal organs. Subsequently, femurs with implants were collected for further histological and radiological examination.

After implantation of the CH_CH_ug4_3,4_P5Zn2II_ug46 composite at <NUM>-month to <NUM>-month follow-up, the condition of the animals did not deviate from normal. The animals retained active and passive mobility in the hip joints. Postoperative wounds healed by rapid growth. Early in the post-operative examination, a slight protrusion containing small amounts of serous fluid was found in the wound area, which disappeared after <NUM>-<NUM> days and the wounds healed normally. On microscopic examination, the composite was visible up to day <NUM> after implantation. Histological examination at <NUM> month after implantation revealed a band of loose connective tissue that separated the implant from the surrounding cancellous bone tissue. In the immediate vicinity in the bone, high osteoblast activity was visible, and in the connective tissue band inflammatory granulation tissue associated with regenerative processes was present (<FIG>). At <NUM> and <NUM> day after implantation, the indentation process was similar to the previous study period. The implants remained visible undergoing gradual reduction and deformation. In the centre of the implants, foci of mineralisation were more numerous than in the previous study period. On radiographic imaging, the surgically performed cavities remained filled with ossein, the biocomposite remained invisible. No osteosclerotic reactions were found at the implant site, and there were no abnormal changes in the bone structure (<FIG>).

To <NUM> of chitosan, <NUM> of <NUM>% (v/v) acetic acid was added and the contents of the vessel were stirred until the chitosan was completely dissolved. At the same time, <NUM> of P5Zn2_II bioglass and <NUM> of <NUM>% (v/v) acetic acid were placed in a separate vessel and stirred until a homogeneous paste of bioglass particles was formed. The resulting paste was then introduced into a vessel with chitosan solution and stirred until a stable dispersion of the bioglass particles in the acidic chitosan solution was obtained. A <NUM> aqueous solution of UG46 peptide fibrils (including <NUM> UG46) was then added and the whole mass was stirred for <NUM>. The suspension produced was transferred into a mould of the desired shape and size and lyophilised. The composite porous scaffolds obtained by freeze-drying were stabilised by immersion in <NUM>% ethanol for <NUM> hours. After this time, the stabilised scaffolds were washed with <NUM> NaOH for <NUM> hour and then with deionised water for <NUM> hours, changing the water several times until the pH was in the range of <NUM>-<NUM>. The washed scaffolds were subjected to freeze-drying again. SEM, SEM/EDS: The resulting composite has a porous structure with a pore size in the range of <NUM>-<NUM> (<FIG>).

BET: The specific surface area of the composite is <NUM> ± <NUM> [m<NUM>/g].

FTIR-ATR: <NUM>-<NUM>-<NUM> - v OH, v NH, <NUM>-<NUM>, <NUM>-<NUM> - v CH, <NUM>-<NUM> - v C=O, <NUM>-<NUM> - δ N-H, <NUM>-<NUM>-<NUM>-<NUM> - δ - OH, δ C-H and v C-O w (-CH<NUM>-OH) and v C=N, <NUM>-<NUM> - νas C-O-C, <NUM>-<NUM> and <NUM>-<NUM> - νas Si-O-Si, <NUM>-<NUM> - v C-O-C, <NUM>-<NUM> - δ O=CN (UG46) and <NUM>-<NUM> and <NUM>-<NUM> - δ P-O.

Bioactivity: the composite shows bioactivity after <NUM> weeks of incubation in SBF (<FIG>). Cytotoxicity: mean cytotoxicity was <NUM>% (± <NUM>%) relative to control cells (<FIG>). Proliferation: mean proliferation was <NUM>% (± <NUM>%) relative to control cells (<FIG>).

Antimicrobial activity: The average percentage reduction in the number of bacteria relative to the control sample was <NUM>% against S. aureus bacteria and <NUM>% against P. aerugionosa bacteria (<FIG>).

For the CH_P5Zn2ll_UG-<NUM>(<NUM>) composite, in vivo biocompatibility was also tested according to the methodology described in Example <NUM>, except that the baseline mean body weight of mice in the acute toxicity test was <NUM> (±<NUM>) g in the control group and <NUM> (±<NUM>) g in the test group.

During the acute toxicity tests, no physical or behavioural changes indicative of disease were found in either the test group or the control group during the health observations carried out on the animals. Each physical examination considered the test animal to be clinically healthy. During the <NUM>-day experimental (post-inoculation) period, there were no behavioural deviations or any signs of disease in the animals, either in the control group or the test group. All mice were considered clinically healthy. Feed and water consumption and body weight gain in the test groups were comparable to the data obtained in the control group, and the differences were not statistically significant. All mice survived until the scheduled postmortem date. There were no abnormalities in behaviour, appearance or differences in weight gain between the test groups and the control group. After <NUM> days, euthanasia (with pentobarbital) and postmortem examinations were performed. Postmortem examinations of the animals, both from the control group and the test group, revealed no skin lesions, skeletal or muscular changes. The natural body orifices (external ear, eyes, nostrils, mouth, anus) and external genitalia showed no lesions. In the peritoneal cavity and thorax, all organs were positioned correctly, with preserved anatomical shape, colour and size. None of the visually inspected organs showed macroscopic pathological changes. No pathological changes were found at autopsy. On the basis of tests carried out on the basis of EN ISO <NUM>-<NUM>: "Biological evaluation of medical devices - Part <NUM>: Tests for systemic toxicity", it was concluded that the samples of the tested biocomposite do not show systemic acute toxicity.

When examining the post-implantation local response of the CH_P5Zn2II_UG-<NUM>(<NUM>) composite at <NUM>-month to <NUM>-month follow-up, the condition of the animals did not deviate from normal. The animals retained active and passive mobility in the hip joints. Post-operative wounds healed by rapid growth. Early in the post-operative examination, a slight protrusion containing small amounts of serous fluid was found in the wound area, which disappeared after <NUM>-<NUM> days and the wounds healed normally. On microscopic examination, the composite was visible up to <NUM> days after implantation. Histological examination at <NUM> month after implantation revealed a band of loose connective tissue that separated the implant from the surrounding cancellous bone tissue. In the immediate vicinity in the bone, osteoblast activity was visible slightly lower than in the composite of example <NUM>, and in the connective tissue band inflammatory granulation associated with regenerative processes was visible (<FIG>). At <NUM> and <NUM> days after implantation, the indentation process was similar to the previous study period. The implants remained visible undergoing gradual reduction and deformation. In the centre of the implants, foci of mineralisation were more numerous than in the previous study period. On radiographic imaging, the surgically performed cavities remained filled with ossein, the biocomposite remained invisible. A formed ossin was found at the implant site, in one case an osteolytic reaction was visible around the CH_P5Zn2ll_UG- <NUM> (<NUM>) composite implant after <NUM> days. Other than that, no osteosclerotic reactions were found, and no abnormal changes in the bone structure were observed (<FIG>).

The process of obtaining the composite was carried out as described in Example <NUM>, except that aqueous solutions of peptide fibrils were added to the stable dispersion of the bioglass in acidic chitosan solution in an amount of <NUM> (including <NUM> of UG46) and the process was again continued as described in Example <NUM>.

SEM, SEM/EDS: The resulting composite has a porous structure with a pore size in the range of <NUM>-<NUM> (<FIG>).

Bioactivity: the composite shows bioactivity after <NUM> weeks of incubation in SBF (<FIG>).

Cytotoxicity: the mean cytotoxicity was <NUM>% (± <NUM>%) against control cells (<FIG>).

Proliferation: mean proliferation was <NUM>% (± <NUM>%) relative to control cells (<FIG>).

BET: The specific surface area of the composite is <NUM>-<NUM> [m<NUM>/g].

Bioactivity: the composite shows bioactivity after <NUM> week of incubation in SBF (<FIG>).

Cytotoxicity: mean cytotoxicity was <NUM>% (± <NUM>%) relative to control cells (<FIG>). Proliferation: mean proliferation was <NUM>% (± <NUM>%) relative to control cells (<FIG>).

To <NUM> of chitosan, <NUM> of <NUM>% (v/v) acetic acid was added and the contents of the vessel were stirred until the chitosan was completely dissolved. At the same time, <NUM> of P5Sr2_II bioglass and <NUM> of <NUM>% (v/v) acetic acid were placed in a separate vessel and stirred until a homogeneous paste of bioglass particles was formed. The process to obtain the composite was then carried out identically as in Example <NUM> and to the stable dispersion of the bioglass in the acidic chitosan solution, aqueous solutions of peptide fibrils were added in an amount of <NUM> (including <NUM> of UG46) and the process was again continued as described in Example <NUM>.

FTIR-ATR: <NUM>-<NUM>-<NUM> - v OH, v NH, <NUM>-<NUM>, <NUM>-<NUM> - v CH, <NUM>-<NUM> - v C=O, <NUM>-<NUM> - δ N-H, <NUM>-<NUM> -<NUM>-<NUM> - δ - OH, δ C-H and v C-O w (-CH<NUM>-OH) and v C=N, <NUM>-<NUM> - νas C-O-C, <NUM>-<NUM> and <NUM>-<NUM> - νas Si-O-Si, <NUM>-<NUM> - v C-O-C, <NUM>-<NUM> - δ O=CN (UG46) and <NUM>-<NUM> and <NUM>-<NUM> - δ P-O.

Bioactivity: the composite shows bioactivity after <NUM> week of incubation in SBF (<FIG>). Cytotoxicity: the mean cytotoxicity was <NUM>% (± <NUM>%) against control cells (<FIG>).

To <NUM> of chitosan, <NUM> of <NUM>% (v/v) acetic acid was added and the contents of the vessel were stirred until the chitosan was completely dissolved. At the same time, <NUM> of P5Zn2_II bioglass and <NUM> of <NUM>% (v/v) acetic acid were placed in a separate vessel and stirred until a homogeneous paste of bioglass particles was formed. The resulting paste was then introduced into a vessel with the chitosan solution and stirred until a stable dispersion of the bioglass particles in the acidic chitosan solution was obtained. The suspension produced was transferred into a mould of the desired shape and size and lyophilised. After removal from the freeze-dryer chamber, the dried materials were protected against moisture. The resulting composite porous scaffolds were stabilised by immersion in <NUM>% ethanol for <NUM> hours. After this time, the stabilised scaffolds were washed with <NUM> NaOH for <NUM> hour and then with deionised water for <NUM> hours, changing the water several times until the pH was in the range of <NUM>-<NUM>. The washed scaffolds were subjected to freeze-drying again. The dry porous composites were then immersed in an aqueous solution of ug46 peptide at a concentration of <NUM>/ml for <NUM> and freeze-dried again. The final product had a chitosan/bioglass content of <NUM>/<NUM> and the amount of ug46 peptide adsorbed on the composite was <NUM> peptide /<NUM> composite.

FTIR-ATR: <NUM>-<NUM>-<NUM> - v OH, v NH, <NUM>-<NUM>, <NUM>-<NUM> - v CH, <NUM>-<NUM> - v C=O, <NUM>-<NUM> - δ N-H, <NUM>-<NUM>-<NUM>-<NUM> - δ - OH, δ C-H and v C-O w (-CH<NUM>-OH) and v C=N, <NUM>-<NUM> - νas C-O-C, <NUM>-<NUM> and <NUM>-<NUM> - νas Si-O-Si, <NUM>-<NUM> - v C-O-C, <NUM>-<NUM> - δ O=CN (ug46) and <NUM>-<NUM> and <NUM>-<NUM> - δ P-O.

Bioactivity: The composite shows bioactivity after <NUM> weeks of incubation in SBF (<FIG>).

Cytotoxicity: The average cytotoxicity of the composite was -<NUM>% (± <NUM>%) relative to control cells. The composite showed no cytotoxic properties (<FIG>).

Antimicrobial activity: the average percentage reduction in the number of bacteria relative to the control sample (CH) was <NUM>% against Staphylococcus aureus and <NUM>% against Pseudomonas aerugionosa (<FIG>).

Claim 1:
A composite with antimicrobial and anti-inflammatory activity for filling bone defects and regenerating bone tissue, in which the matrix is a natural, biodegradable polymer constituted by chitosan, characterized in that the chitosan has a deacetylation degree of DD≥<NUM>%, a viscosity in the range of <NUM> to <NUM> mPas and a molecular weight in the range of <NUM> to <NUM> kDa and it represents <NUM> wt.% to <NUM> wt.% of the total composition of a four-component composite, and further contains bioactive glass representing <NUM> wt.% to <NUM> wt.% of the total composition of the four-component composite, produced by the sol- gel method and containing SiO<NUM> in an amount of <NUM>-<NUM> wt.% and CaO in an amount of <NUM>-<NUM> wt.%, and: P<NUM>O<NUM> in an amount of <NUM>-<NUM> wt.%, and/or SrO in an amount of <NUM>-<NUM> wt.%, and/or ZnO in an amount of <NUM>-<NUM> wt.%, and/or CuO in an amount of <NUM>-<NUM> wt.%, and/or MgO in an amount of <NUM>-<NUM> wt.% and has a grain size of <NUM>% less than <NUM> and the composite contains a biologically active, engineered ug4 peptide with an Cys Pro Leu Gly Leu Tyr Gly Phe Gly Gly (SEQ1) sequence representing from <NUM> wt.% to <NUM> wt.% of the total composition of the four-component composite, wherein the peptide with sequence SEQ1 contains a biologically active peptide with sequence Leu Tyr Gly Phe Gly Gly (SEQ2) and the composite contains a biologically active engineered peptide ug46 with sequence Ac Gln Ala Gly Ile Val Val Pro Leu Gly Leu Gly Leu Leu Lys Arg Ile Lys Thr Leu Leu (SEQ3) representing from <NUM> wt% to <NUM> wt% of the total composition of the composite.