MULTIFUNCTIONAL, HYDROGEL HYBRID MATERIAL, THE METHOD OF ITS PREPARATION AND THE USE IN THE TREATMENT OF BONE LOSSES

Abstract

A multifunctional hydrogel hybrid material and a method of its preparation and use in the treatment or prophylaxis of bone tissue loss is disclosed.

Claims

1. A multifunctional, hydrogel hybrid material, wherein it contains: a) a biopolymer matrix containing: collagen, chitosan, preferably modified hyaluronic acid, b) the silica-apatite particles functionalized with amino groups, c) the active substance in the form of alendronate attached to silica-apatite particles, d) a cross-linking substance.

2. The hybrid material according to claim 1, wherein the biopolimer matrix contains: collagen, chitosan, modified hyaluronic acid in a weight ratio 5:2:3, respectively.

3. The hybrid material according to claim 1, wherein the hyaluronic acid is modified with lysine.

4. The hybrid material according to claim 1, wherein the cross-linking substance is genipin.

5. A method of producing of the multifunctional hydrogel hybrid material wherein it comprises the following steps: a) the silica particles are functionalized with amino groups, b) the particles obtained in step a) are suspended in an aqueous SBF solution, preferably at a concentration of 1.5 M, to obtain, after 10 days of incubation, the silica particles coated with the mineral phase, c) sodium alendronate is bonded to the particles obtained in the step b), d) a solution of collagen, chitosan and lysine-modified hyaluronic acid is added to the aqueous suspension of the particles of the step c), e) the mixture obtained in step d) is subjected to a cross-linking reaction with genipin.

6. The method according to claim 5, wherein it is carried out by the sol-gel method.

7. The multifunctional hydrogel hybrid material obtained by a method as defined in claim 5, for use in the treatment or prophylaxis of bone losses.

8. The hybrid material according to the claim 7, wherein the bone losses are due to osteoporosis.

9. The hybrid material according to claim 2, wherein the hyaluronic acid is modified with lysine.

10. The multifunctional hydrogel hybrid material obtained by a method as defined in claim 6, for use in the treatment or prophylaxis of bone losses.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

[0035] For a better understanding of the essence of the invention, the present description is illustrated with the accompanying figures.

[0036] FIG. 1 shows the SEM microphotographs of SiO.sub.2-Ap and SiO.sub.2-Ap-ALN submicron particles.

[0037] FIG. 2 summarizes the diffractograms of SiO.sub.2-Ap and SiO.sub.2-Ap-ALN particles.

[0038] FIG. 3 summarizes XPS spectra of SiO.sub.2-Ap and SiO.sub.2-Ap-ALN particles.

[0039] FIG. 4 summarizes the thermogravimetric profiles of SiO.sub.2-Ap and SiO.sub.2-Ap-ALN particles.

[0040] FIG. 5 shows SEM microphotographs demonstrating morphology of the obtained hybrid materials as well as the ColChHA.sub.mod control material.

[0041] FIG. 6 summarizes results of the rheological studies, the G′ values measured after 10, 35 and 70 minutes of the experiment, where the results are presented on a logarithmic scale. Statistical significance (p<0.05) was demonstrated using the Student's test. * indicates statistical significance relative to the KolChHA.sub.mod results at 70 min, # indicates statistical significance relative to the KolChHA.sub.mod C1 results after 70 min.

[0042] FIG. 7 summarizes the results of the swelling degree tests.

[0043] FIG. 8 summarizes the results of the enzymatic degradation studies.

[0044] FIG. 9 shows SEM microphotographs of the hybrid materials together with the values of calcium to phosphorus ratio (Ca/P), as determined by EDS for the mineral phase formed on the surface of the materials after 3 days of incubation in SBF.

[0045] FIG. 10 shows (A) the results of the Alamar Blue test on the days 1, 3 and 7 of growing the MG-63 cells on the tested materials. (B) Alkaline phosphatase activity after 3 and 7 days of growing the MG-63 cells on the tested materials. Statistical significance (p<0.05) was demonstrated using the Student's test. (A) % indicates statistical significance relative to the result for ColChHAmod day 3, $ indicates statistical significance relative to the result for the ColChHAmod day 7 (B) * indicates statistical significance relative to the result for the control day 3, ** indicates statistical significance relative to the result for the control day 7, # indicates statistical significance relative to the result for ColChHAmod C1 day 3. Cells grown in the culture dish were used as controls.

[0046] FIG. 11 shows (A) a summary of SEM microphotographs showing the morphology of the fixed MG-63 cells after 3 days of growing on the surface of the tested materials (B) a graph showing the surface distribution of the MG-63 cells after 3 days of growing (estimated based on the obtained SEM microphotographs).

[0047] FIG. 12 shows the results of the Alamar Blue assay after 1, 3 and 7 days of growing of the J774A.1 cells on the tested materials. Statistical significance (p<0.05) was demonstrated using the Student's test. The % indicates statistical significance relative to results for ColChHAmod day 1.

[0048] FIG. 13 shows a scheme of formation of the SiO.sub.2-Ap-ALN particles (SiO.sub.2—NH.sub.2-amine functionalized silica particles; Ap—apatite layer formed on the surface of silica particles after incubation in 1.5 M SBF; ALN—sodium alendronate).

[0049] FIG. 14 shows a pattern of the obtained SiO.sub.2-Ap-ALN particles (SiO.sub.2—NH.sub.2-amino functional silica particles; Ap—apatite layer; ALN—sodium alendronate). The obtained product (SiO.sub.2-Ap-ALN) was suspended in a biopolymer sol (collagen-chitosan-hyaluronic) and cross-linked with genipin to obtain the hybrid material useful as the material for filling osteoporotic defects.

[0050] FIG. 15 shows a schematic view of formation of the hybrid material.

[0051] FIG. 16 shows: (A) fragments of isolated skin with hydrogel-based materials, (B) a decrease in hydrogel volume observed after various periods followed material injection, (C) representative SEM images of ColChHAmodC1 isolated from mice skin after 60 days post injection. White circle indicate hydroxyapatite aggregates as determined by EDS analysis. White arrow points out blood vessel in hydrogel.

[0052] FIG. 17 shows blood hematology analyses performed for mice exposed to hydrogels.

[0053] FIG. 18 shows biochemical serum analyses performed for mice exposed to hydrogels.

[0054] FIG. 19 shows cytokine detection in sera after materials administration.

[0055] FIG. 20 shows hydrogel ColChHAmod stained with Masson's Trichrome. The white arrow indicates neutrophils and dark grey arrow indicates macrophages.

[0056] FIG. 21 shows hydrogel ColChHAmod C1 stained with Masson's Trichrome. The square is marked with an area that is shown at a larger magnification. The white arrow indicates neutrophils and dark grey arrow indicates macrophages.

DESCRIPTION OF PREFERRED EMBODIMENTS

[0057] Moreover, the essence of the invention is explained in the following examples.

[0058] Examples 1, 2 and 4 disclose consecutive steps of an exemplary implementation of the method according to the invention, while Examples 3 and 5 disclose properties of the materials obtained according to the invention.

Example 1. Preparation of SiO.SUB.2.-Ap Submicron Mineral Particles

[0059] Controlled deposition of apatite (Ap) on the surface of the silica particles was performed in contact with artificial plasma (1.5 SBF).

Preparation of the Artificial Plasma

[0060] For this purpose, 1000 mL of 1.5 SBF were prepared. 700 mL of deionized water was added to a 1000 mL plastic beaker. The beaker was placed on a magnetic stirrer in a water bath at 36.5±1.5° C. Reagents 1 to 8 were dissolved following the order shown in Table 1 (the next reagent was added after the previous one had completely dissolved). Deionized water was added to a volume of 900 mL and temperature of the solution was set again to 36.5±1.5° C. Then the pH control was started, for this purpose the electrode of the pH meter was placed in the solution. In the next step, Tris was dissolved in the solution, with constant control of pH, by adding small portions of the reagent. When the pH came to 7.30±0.05, the temperature was checked to maintain it within 36.5±1.5° C. After checking the temperature, Tris was added again, to raise the pH to 7.45. When the pH rose to 7.45±0.01, the dissolution of the Tris was stopped and 1 M HCl was added to bring the pH down to 7.42±0.01, taking care not to drop the pH below 7.40. After lowering the pH to 7.42±0.01, the remaining Tris was dissolved without exceeding a pH of 7.45. After all the Tris had dissolved, the temperature of the solution was adjusted to 36.5±0.2° C. The pH of the solution was adjusted by dropwise addition of 1 M HCl to 7.42±0.01 at a temperature of 36.5±0.2° C. The pH was finally adjusted to 7.40 at 36.5° C. The solution was then poured into a plastic flat bottom flask, made up to 1000 mL and stored in a refrigerator.

TABLE-US-00001 TABLE 1 Reagents and their amounts needed to prepare 1000 ml of 1.5 SBF no reagent mass/volume 1 NaCl 12.0525 g 2 NaHCO.sub.3 0.5325 g 3 KCl 0.3375 g 4 K.sub.2HPO.sub.4•3H.sub.2O 0.3465 g 5 MgCl.sub.2•6H.sub.2O 0.4665 g 6 1.0M HCl 58.5 mL 7 CaCl.sub.2 0.438 g 8 Na.sub.2SO.sub.4 0.108 g 9 Tris 9.117 g 10 1.0 M HCl 0-7.5 mL

Deposition of Apatite (Ap) on the Surface of Amine-Functionalized Silica Particles

[0061] Amine-functionalized silica particles were obtained by the sol-gel method according to the procedure described in [J. Lewandowska-Łańcucka et al., Int. J. Biol. Macromol. 136 (2019) 1196-1208] as follows: 1.0 mL of tetraethoxysilane (TEOS) and 0.1 mL of aminopropyltriethoxysilane (APTES) were sequentially added to a mixture of ethanol (5.1 mL) and water (5 mL). The resulting mixture was left on a magnetic stirrer and stirred for 30 min at room temperature. The material obtained in this way was subjected to the centrifugation process and then it was cleaned by washing with ethanol and centrifugation. The washing in ethanol/centrifugation cycle was repeated four times. The material was dried in a vacuum oven at 60° C. After purification, a white powder (SiO.sub.2—NH.sub.2) was obtained.

[0062] In the next step, 20 mg of SiO.sub.2—NH.sub.2 particles was placed in 50 mL vials and 20 mL of 1.5 M SBF solution was added. The samples were sonicated continuously for 10-15 minutes. The vials were then protected with Parafilm and placed in an incubator set at 37° C. and shaken (50 rpm). The materials prepared in this way were incubated for a period of 10 days, replacing the SBF solution with the fresh one every 2-3 days. For this purpose, the suspension of particles in SBF was centrifuged at 10,000 rpm for 5 minutes, the supernatant was removed, a fresh aliquot of buffer was introduced, vortexed and incubated again. After a 10-day incubation in artificial plasma, the material was centrifuged, then cleaned by washing with water and centrifugation (the procedure was repeated three times), and then dried at room temperature. The material (SiO.sub.2-Ap) was obtained in the form of a white powder.

Example 2. Preparation of the Submicron Bioactive Mineral Particles Carrying Alendronate (SiO.SUB.2.-Ap-ALN)

[0063] Sodium alendronate was attached to the SiO.sub.2-Ap system obtained as a result of controlled deposition under SBF conditions. For this, 20 mg of the SiO.sub.2-Ap material was suspended in 3 mL of sodium hydroxide (5 mM) and sonicated for 5 min. Then 4 mg of sodium alendronate (ALN) was dissolved in 2 ml of NaOH solution (5 mM). The electrode of the pH-meter was placed in the solution and the pH was adjusted to 10 by adding NaOH (20 mM) solution. Then the sodium alendronate solution prepared in this way was added to the SiO.sub.2-Ap suspension. The sample was placed on a magnetic stirrer with heating function (500 rpm, 37° C.) for 3 days. The resulting alendronate attached material (SiO.sub.2-Ap-ALN) was purified by dialysis into water (24 hours, room temperature) and lyophilized to give a white powder.

Example 3. Physicochemical Properties of the Submicron Mineral Particles (SiO.SUB.2.-Ap) and the Submicron Bioactive Mineral Particles Carrying Alendronate (SiO.SUB.2.-Ap-ALN)

[0064] The particles obtained in examples 1 and 2 were characterized in detail using a number of physicochemical techniques-the morphology (SEM) as well as the chemical composition (EDS, XRD, XPS, TG) were determined. SEM and EDS studies (FIG. 1) showed the presence of a mineral phase with the morphology and composition (Ca/P ratio=1.2) characteristic of apatite structures.

[0065] The results of the X-ray diffraction analysis (XRD) (FIG. 2) unambiguously confirmed the presence of the crystalline phase in the obtained material. Moreover, the signals appearing on the diffractograms at 2θ equal to: 25.9; 32.0; 39.4; 42.2; 46.8; 53.2 are in agreement with literature values of signals attributed to hydroxyapatite.

[0066] The results of the studies confirmed the effectiveness of the proposed methodology for obtaining bioactive hybrid material (SiO.sub.2-Ap) under mild conditions simulating the biomineralization process. Moreover, stability of the obtained material is based on interactions resulting from the strong affinity of ALN for apatite. The deprotonated oxygen atoms of the phosphate groups in ALN interact electrostatically with the calcium ions present on the surface of the apatite. The resulting Ap-ALN conjugate does not affect the apatite crystal structure.

[0067] The obtained submicron SiO.sub.2-Ap-ALN particles, as described in Example 2, were characterized by a number of complementary physicochemical methods (SEM, XPS, XRD, TG) (FIGS. 1-4). The XPS (FIG. 3) and TG (FIG. 4) analysis confirmed the efficiency of binding alendronate to the SiO.sub.2-Ap bioactive carrier. Changes in the elemental composition of the surface of the obtained SiO.sub.2-Ap-ALN material were demonstrated (XPS analysis, Table 2), as well as differences in the thermogravimetric profile (for the material with the drug attached, a weight loss greater by 3.3% in relation to the SiO.sub.2-Ap carrier alone was found.). The obtained diffractogram for the material with the attached drug (FIG. 2) did not show significant differences compared to the diffraction pattern obtained for the carrier itself, which confirms that the process of ALN to SiO.sub.2-Ap conjugation did not affect its crystal structure.

TABLE-US-00002 TABLE 2 Results of XPS analysis Elemental composition (%) O Si C N Ca P of the studied materials 1s 2p 1s 1s 2p 2p SiO.sub.2-Ap 62 3 4 1 26 4 SiO.sub.2-Ap-ALN 60 3 8 2 23 4

Example 4. Preparation of the Chemically Cross-Linked Hydrogel Hybrid Materials with Dispersed Bioactive Mineral Phase Carrying Alendronate (SiO.SUB.2.-Ap-ALN)

[0068] The submicron SiO.sub.2-Ap-ALN particles obtained in the Example 2 were suspended in a biopolymer sol consisting of collagen, chitosan and lysine-functionalized hyaluronic acid, and cross-linked with genipin to obtain a hybrid material. For this purpose, three batches of the submicron bioactive mineral particles carrying sodium alendronate (SiO.sub.2-Ap-ALN) were prepared, 5 mg, 2.5 mg, 1 mg, respectively, and each was suspended in 0.1 mL of water. Then, appropriate volumes of biopolymer solutions were added: 76 μl of chitosan (Ch) solution (1% by weight solution in 1% acetic acid), 540 μl of collagen (Col) solution (solution in hydrochloric acid with a concentration of 3.5 mg/mL-solution provided by the manufacturer BD Biosciences), 114 μl of solution of the lysine-modified hyaluronic acid (HA.sub.mod) (1% by weight solution in 10×phosphate buffer (PBS); composed of: NaCl (c=1.37 M), KCl (c=27 mM), Na.sub.2HPO.sub.4 (c=43 mM), KH.sub.2PO.sub.4 (c=14 mM), pH adjusted to 7.4 with concentrated (c=35%) hydrochloric acid HCl solution). The obtained sol was shaken vigorously and then 170 μl of genipin solution (20 mM solution, prepared in 10×PBS) was added and incubated at 37° C. until complete cross-linking occurred. The obtained material was in the form of a hydrogel. The weight ratio of biopolymers in the obtained material was: Col:Ch:HA.sub.mod—50:20:30.

[0069] Three concentrations of SiO.sub.2-Ap-ALN particles suspended in the sol were tested. Using three different concentrations of suspensions/dispersions of the bioactive mineral particles (C1=5 mg/mL, C2=2.5 mg/mL, C3=1 mg/mL), three types of hybrid materials were obtained: ColChHA.sub.mod C1, ColChHA.sub.mod C2 and ColChHA.sub.mod C3. A hydrogel with an analogous biopolymer composition, but without the addition of the SiO.sub.2-Ap-ALN particles (0.1 ml of water was added) was obtained as a control material (ColChHA.sub.mod).

[0070] The procedure for preparation of the lysine-modified hyaluronic acid was presented in the publication (Gilarska, A et al., (2020), Int. J. Biol. Macromol, 155, 938-950).

[0071] In the first step, the MES buffer (50 mM) was prepared. For this purpose, 0.97 g of 2-(N-morpholino)ethanesulfonic acid (MES) was dissolved in 100 ml of deionized water and the pH was adjusted to 4 with 0.1 M NaOH solution. The whole mixture was filtered through a syringe filter. 500 mg of hyaluronic acid (HA) was dissolved in 20 mL of the MES buffer (50 mM, pH=4) and then 0.73 g of lysine, 360 mg of EDC (N-(3-dimethylaminopropyl)-N′-ethylcarbodiimide hydrochloride) and 220 mg of NHS (N-hydroxysuccinimide) was sequentially added (each of these reagents was first dissolved in 5 mL of MES buffer due to the gel consistency of the mixture). The mixture was stirred for 24 hours on a magnetic stirrer at room temperature, and then dialyzed overnight into 0.1 M aqueous Na.sub.2CO.sub.3 solution (lasting about 12 hours), followed by an 8-day dialysis against water. In the next step, the mixture was concentrated on evaporator (to a volume of about 50 mL) and freeze-dried for three days. The degree of lysine substitution of the product thus obtained (HA.sub.mod) was determined by elemental analysis and .sup.1H NMR spectroscopy, it came to about 25%.

Example 5. Characterization of the Chemically Cross-Linked Hydrogel Hybrid Materials with Dispersed Bioactive Mineral Phase Carrying Alendronate (SiO.SUB.2.-Ap-ALN).

[0072] The obtained hydrogel hybrid materials, ColChHA.sub.mod C1, ColChHA.sub.mod C2, ColChHA.sub.mod C3, respectively, were subjected to physicochemical characteristics. The morphology, lyophilicity, swelling degree, and rheological properties were determined.

[0073] Using the SEM technique, the microstructure of the obtained hybrid materials as well as the control material ColChHA.sub.mod was characterized. Analysis of the obtained microphotographs (FIG. 5) revealed the presence of the submicron SiO.sub.2-Ap-ALN particles in each of the obtained hybrid systems. The particles existed both as individual objects as well as in the form of aggregates partially covered with the created biopolymer network.

[0074] In order to confirm the possibility of using the developed systems as injectable materials, rheological measurements were carried out in the oscillatory mode. Elastic modulus (G′) values measured after 10, 35 and 70 minutes of the experiment are shown in FIG. 6 (the experiment was carried out at 37° C., after adding genipin solution to the sol as described above). By tracking the changes of the elastic modulus (G′) over time, it was possible to verify the transition from the sol to gel state and thus to demonstrate the injectable potential of the obtained materials. At the beginning of the gelling process (10 minutes after preparing the mixture), the values of the elastic modulus for all materials were at a low level (in the range of 10-14 Pa), confirming their viscoelastic state and the injectable form. The G′ values increased significantly after 35 minutes, reaching a maximum value within 70 minutes from the start of the crosslinking process (gel formation). Thus, a comparison of the G′ value at the beginning and the end of the rheological experiment proved that the developed materials can function as injectable materials.

[0075] Moreover, the obtained results demonstrated that introduction of the bioactive carrier into the biopolymer matrix significantly improved mechanical properties of the obtained hybrids. A statistically significant difference was demonstrated for the G′ value after 70 min of gelation for all hybrid materials, in comparison with the elasticity modulus (G′ after 70 min) obtained for the control material. An increase in the value of the elasticity modulus (G′) from the value of 900 Pa for the polymer matrix, to 2500 Pa for the system with the highest carrier content (ColChHA.sub.mod C1) after 70 min of the gelling process was also observed (FIG. 6) (statistical significance in relation to all the materials).

[0076] The above results clearly prove that after the end of the gelation process (after 70 min) the hybrid materials, while maintaining the injectability typical for the polymer matrix itself, are characterized by significantly higher (statistical significance) values of the elastic modulus.

[0077] The degree of swelling (SP) was also determined for the obtained hybrid materials. The experiment was carried out under physiological conditions (pH=7.4; temp=37° C.), the results are shown in FIG. 7. Analyzing the obtained results, it can be seen that all tested materials show the swelling capacity (SP in the range of 6700-11700%), while the presence of SiO.sub.2-Ap-ALN particles has a significant impact on the swelling properties of the hybrid systems. The performed swelling tests showed that with increasing concentration of SiO.sub.2-Ap-ALN particles, the degree of swelling decreased (FIG. 7). Therefore, this result indicates that the obtained particles affect the stiffness of the hydrogel structure, which was also confirmed by rheological tests.

[0078] The lyophilicity of the surfaces of the obtained materials was also examined. The results obtained on the basis of the measurements of contact angles are summarized in Table 3. Analyzing the obtained data, it can be noticed that introduction of SiO.sub.2-Ap-ALN particles into the biopolymer matrix causes the surface of the hybrid materials to become more hydrophilic, as evidenced by lower values of contact angles, as compared with the control material (ColChHA.sub.mod). It was observed that the material with the highest concentration of the particles (ColChHA.sub.mod C1) had the most hydrophilic surface (66°). The improvement in hydrophilicity can be explained by the presence of SiO.sub.2-Ap-ALN hybrid particles on the surface of the materials (SEM micrographs presented in FIG. 5) containing surface-exposed hydrophilic amine groups derived from the attached alendronate (as confirmed by XPS analysis).

TABLE-US-00003 TABLE 3 Values of contact angles for the obtained materials Material type Contact angle value [°] ColChHA.sub.mod 77.7 ± 1.3 ColChHA.sub.mod C1 65.8 ± 0.6 ColChHA.sub.mod C2 70.9 ± 1.3 ColChHA.sub.mod C3 67.1 ± 0.8

Enzymatic Degradation

[0079] The obtained materials were also subjected to the enzymatic degradation process in the presence of the enzyme—collagenase. The enzymatic degradation was studied for 144 hours. FIG. 8 shows changes in the mass of materials during incubation in a collagenase solution. A significant slowdown of the enzymatic degradation process was observed for all the materials with an introduced carrier. After 4 hours of enzymatic degradation, a slight weight loss was noted for the hybrid materials (about 3-7%) and 12% for the ColChHA.sub.mod material. At subsequent measurement points, significant changes in the remaining weight of the control material were observed (31% after 144 h), while the weight loss for the hybrid materials went off much slower. After 144 h of degradation of the hybrid materials, weight loss of about 44-52% was observed. When analyzing the weight loss of all the tested materials at a given point of the experiment, a tendency can be indicated that with an increase in the content of SiO.sub.2-Ap-ALN particles, the speed of the degradation process decreases. These results are in line with the results of the rheological experiment, which confirmed the improvement of the mechanical properties of the hybrid materials along with the increasing concentration of SiO.sub.2-Ap-ALN particles in the system.

Bioactive Properties

[0080] In order to demonstrate that the obtained hybrid materials, thanks to the presence of silica-apatite particles, will favor the bio-integration of the material with the bone and thus support the bone mineralization process disturbed in the process of osteoporosis, their bioactive properties were examined. An in vitro biomineralization experiment was carried out under conditions of simulated body fluid (SBF). Literature data show that materials showing the ability to produce an apatite layer on their surface under SBF conditions will also undergo biomineralization in a living organism, thus ensuring effective integration of the scaffold with natural bone. The biomineralization experiment under model conditions included a 5-day incubation of the materials in SBF at 37° C. Subsequently, the materials were tested using SEM and EDS techniques. FIG. 9 shows the obtained SEM microphotographs and the values of the calcium to phosphorus ratio (Ca/P) determined by the EDS technique for the mineral phase formed on the surface of the materials after 3 days of incubation in SBF.

[0081] Detailed analysis of the results (SEM/EDS) allowed to state that the formation of the mineral phase in the form of a flower structure, in which the Ca/P ratio is characteristic of apatite, was observed for the hybrid materials ColChHA.sub.mod C1 and ColChHA.sub.mod C2, after 3 days. In addition, due to the fact that the hydrogel matrix according to the present invention consists of 30% by weight of the modified hyaluronic acid, additional support for biomineralization from hyaluronic acid was observed (formation of the mineral phase in the form of layers on the surface of ColChHA.sub.mod and ColChHA.sub.mod C3). In case of the previous invention, the polymer matrix with 10 wt. % of unmodified hyaluronic acid did not exhibit this property. It is worth noting that the material presented in the previous application was subjected to a similar experiment (bioactivity study in SBF); in that case, the process of biomineralization took place only after 7 days.

[0082] The obtained results clearly indicate that the discussed hybrid materials with the SiO.sub.2-Ap-ALN particles in concentration in the range of 1-5 mg/ml are characterized by bioactive properties ensuring a significant acceleration of biomineralization process, namely up to 3 days, and thus by more effective biointegration of the material with natural bone.

Studies of the Biological Properties of the Hybrid Material

[0083] The obtained hydrogel-based hybrid materials were also subjected to preliminary biological tests in vitro with the use of MG-63 osteoblastic cells. Proliferation, alkaline phosphatase activity, morphology and adhesions of cells grown on the surface of the tested materials were determined. The performed biological tests in vitro demonstrated that introduction of SiO.sub.2-Ap-ALN particles at the tested concentrations of C1, C2 and C3 into the hydrogel matrix did not deteriorate the biocompatibility of hybrid materials compared to the control material ColChHA.sub.mod. The results of the cell viability tests (the Alamar Blue test was used) carried out at the 1st, 3rd and 7th day of culture (FIG. 10A) showed that all the obtained hybrid materials supported the proliferation capacity of MG-63 cells. A similar (without statistically significant differences) increase in the number of cells was observed in the consecutive days (1, 3, 7) of the experiment performed with the use of hybrid materials containing the SiO.sub.2-Ap-ALN particles in C1 and C2 concentrations, as compared to the results for the control (ColChHA.sub.mod).

[0084] Activity of the alkaline phosphatase (ALP) as a marker confirming the phenotype and mineralization of osteoblasts on the 3rd and 7th day of culturing was also tested (FIG. 10B). For all the analyzed materials, an increase in activity was observed after 7 days of the experiment. The level of ALP on both the third and the seventh day of culture was significantly higher compared to the ALP activity of the cells on the culture plate. When analyzing the effect of SiO.sub.2-Ap-ALN particles concentration on ALP activity, statistically significant differences were observed only for ColChHAmod C3 material on the 3rd day of the experiment (against ColChHA.sub.mod C1 on the 3rd day). On day 7 of culturing, no significant differences in ALP activity between the obtained hybrid systems were found.

[0085] The morphology and adhesion of MG-63 cells after 3 days of culture on the surface of the materials were also analyzed. Cells were fixed and imaged using the SEM technique. FIG. 11 summarizes the SEM microphotographs showing morphology of the fixed cells (FIG. 11A) as well as a plot of the MG-63 cell surface distribution after 3 days of growing (estimated based on the obtained SEM microphotographs) (FIG. 11B). While analyzing the obtained microphotographs (FIG. 11A), it can be concluded that the cells adhere equally well to the surface of the hybrid materials and to the surface of the control hydrogel (ColChHA.sub.mod). The estimated cell surface distribution (FIG. 11B) shows that cells grown on the ColChHA.sub.mod control material and in the hybrid system with the lowest concentration of the SiO.sub.2-Ap-ALN (C3) particles occupy a comparable surface area and have a similar morphology. The morphology of cells grown on the hybrid materials with C1 and C2 particle concentration is more diverse. A population of flattened, occupying larger area cells with elongated shapes was observed. Therefore, the data demonstrate that the presence of SiO.sub.2-Ap-ALN particles has a positive effect on cell adhesion.

Study of the Therapeutic Properties

[0086] In order to demonstrate the ability of the developed hybrid material to inhibit bone resorption, preliminary biological studies were carried out in vitro using a model osteoclast line (J774A.1 cells). This line constitutes the reference line used in in vitro analyzes of metabolism of compounds belonging to the bisphosphonate group.

[0087] The results of cell viability tests (the Alamar Blue test was used) performed after 1, 3 and 7 days of cell growing are shown in FIG. 12. The preliminary biological studies showed that proliferation of osteoclastic cells grown on hybrid materials was inhibited after 7 days of the experiment. A tendency to increase this effect with the increase in concentration of SiO.sub.2-Ap-ALN particles present in the hydrogel matrix was observed, and was most visible for the ColChHA.sub.mod C1 system. Thus, it was shown that the tested hybrid materials with the proposed content of the SiO.sub.2-Ap-ALN particles (C1, C2 and C3) have a therapeutic potential manifested by impairment of the activity of the model osteoclastic cells. Therefore, taking into account the form of the developed formulation and the possibility of its local administration by injection directly into the less, it will be possible to ensure the local action of the drug, thus minimizing the systemic side effects of application of alendronate. The material presented in the scope of the previous application had no therapeutic properties.

Example 6. Biological Evaluation In Vivo

[0088] Considering the potential applications of the developed materials biological evaluation in vivo was performed. Based on the results of physicochemical characterization as well as in vitro biological studies, the hybrid with the highest SiO.sub.2-Ap-ALN concentration (ColChHAmod C1) and pristine ColChHAmod hydrogel as a control were selected for further biological research. The experiments on the mouse model was performed to evaluate the biocompatibility of the selected systems and examine the potential and safety of obtained materials in in vivo conditions. The injectability as well as the ability to gel in vivo was verified while the panel of biochemical and histopathological analyses enabled the determination of hemo-, hepato-or nephrotoxicity of developed systems.

Hydrogel-Based Hybrid Materials Injectability and Degradation In Vivo

[0089] In in vivo studies, the tested materials were injected subcutaneously (right flank, shoulder area) into the healthy C57Bl/6 mice. Before administration, all components were mixed, transferred into a syringe, and incubated for 15 minutes at 37° C. (to induce gel formation). After incubation, the color of the tested materials was light grey to blue-green; all the materials continued to be liquid; hence no problems were encountered with their subcutaneous administration. Moreover, no hydrogel leakage was observed immediately after administration (through the hole created when the needle was removed) thus, and the entire mixture was injected. It was therefore confirmed that all tested materials had very good injectability. Mice were sacrificed at 1.sup.st, 7.sup.th, 30.sup.th, 60.sup.th day of the experiment, and both ColChHAmod and ColChHAmod C1 visualized after skin removal (FIG. 16A). The color of both tested materials was blue. ColChHAmod was softer, more hydrated, and had a decidedly less compact structure than ColChHAmod C1. The progress of volume change quantitively over time only for ColChHAmod C1 was observed. A significant, rapid decrease in ColChHAmod C1 volume was revealed after seven days (volume was 2.5 times smaller than this observed after one-day post-injection), indicating their biodegradation (FIG. 16B). Between 7 and 30 days of the experiment, the volume of ColChHAmod C1 did not change significantly, and finally, at the end of the experiment lasting 60 days, the volume was almost 60 times smaller than this observed after one day post-injection (FIG. 16). Also, ColChHAmod C1 had not gel's consistency anymore, and this material was hard, light blue-green in color, and blood vessels were observed near it. The significant postmortem degradation of ColChHAmod was also revealed. On the 60th day of the experiment, the material no longer resembled a gel; its debris/residues were visible under the skin as black fibers.

Biosafety In Vivo of ColChHAmod and ColChHAmod C1 Materials

[0090] Analysis of systemic biocompatibility aimed to exclude adverse reactions provoked by subcutaneous administration of materials and products of their degradation. Although the materials have been injected subcutaneously, their degradation products may cause systemic toxicity by entering the bloodstream. The animals were euthanized at different times after administering the materials (1 day, 7 days, 30 days, 60 days), which allowed investigating the potential acute and chronic toxicity. No weight loss or disturbing changes in the animals' appearance and behavior were observed during the experiment. As shown in FIG. 17 and FIG. 18, no changes were observed in blood morphology or in the activity or concentration of hepatotoxicity (ALT, T-Pro), nephrotoxicity (BUN, Cre), or other tissue damage (ALP) markers.

[0091] Finally, serum concentrations of cytokines, including proinflammatory cytokines, confirmed the absence of subcutaneously administered hydrogels' or products of their degradation immunotoxicity (FIG. 19). These results indicate a lack of systemic toxicity that could result from administration to animals of hydrogel containing potentially toxic products of degradation.

[0092] They, therefore, confirm that the use of biomaterials loaded with SiO.sub.2-Ap-ALN can be a promising method of repair of osteoporotic bone without the risk of systemic toxicity caused by the drug or other products of materials degradation.

Biological Changes Occurring Within the Hydrogels and Their Interaction with Cells In Vivo

[0093] The changes in tested materials (isolated with skin fragments) at various times after their administration was also investigated. First of all, the recruitment of the host cells to the material was analysed. Twenty-four hours after the subcutaneous administration of ColChHAmod and ColChHAmod C1, an influx of immune cells (mainly neutrophils) responsible for developing local inflammation (FIG. 20 and FIG. 21) was observed. Immune cells were present in materials at all time points. However, the longer time after the biomaterials' administration, more leukocyte populations were recruited. Therefore, on the 7th day after administration, macrophages and lymphocytes were also visible in addition to neutrophils. The influx of immune cells occurs throughout the material volume; however, this phenomenon was much more intense at the periphery of materials. With ColChHAmod C1, a more intense inflammation was observed. The result was the production by fibroblasts of animal skin a clear layer of collagen (fibrotic capsule formation) around the hydrogel with SiO.sub.2-Ap-ALN, visible on the 30th and 60th day after administering the material. This phenomenon was much less severe with ColChHAmod hydrogel. For ColChHAmod material, inhibition of the proinflammatory response was observed on the 60th day after administration. Moreover, the newly created blood vessels in isolated sections of materials 60 days after the administration was observed. The presence of blood vessels within the materials was also confirmed by SEM analysis (FIG. 16C).

[0094] Overall, the systemic proinflammatory response manifested by elevated proinflammatory cytokines in the blood (as it is demonstrated in FIG. 21) was not revealed. Thus, our results indicate that only local inflammation can be induced after administering the tested materials.

[0095] Based on the performed research, the following unexpected advantages of the obtained hybrid material can be indicated: [0096] therapeutic potential—preliminary in vitro biological tests were performed using the osteoclast cell line (J774A.1 cells), and demonstrated that hybrid materials with the proposed composition and content of alendronate have therapeutic potential manifested by impairment of the activity of the model osteoclastic cells, [0097] improvement of bioactivity—accelerated biomineralization of the hydrogel material was observed. Detailed analysis of the results (SEM/EDS) allowed to state that in case of higher SiO.sub.2-Ap-ALN (C1, C2) contents, after 3 days of incubation of the material in simulated body fluid (SBF), a new mineral phase is formed, ensuring faster biointegration of the material with natural bone, [0098] injectability of the hybrid materials characterized by very good mechanical properties. Therefore, taking into account the form of the developed formulation and the possibility of its local administration by injection into the loss, it will be possible to ensure the local action of alendronate, thus minimizing its systemic side effects related to oral or intravenous administration, [0099] biocompatibility—the performed in vitro biological tests have shown that the presence of the SiO.sub.2-Ap-ALN particles does not reduce biocompatibility of the hybrid materials (compared to the KolChHA.sub.mod control material), as well as their ability to support adhesion, proliferation, and also to maintain the phenotype of osteoblastic cells (MG-63), [0100] the safety of developed materials in in vivo conditions. The results of in vivo experiments indicated a lack of systemic toxicity of developed systems and thus demonstrated that the use of hybrid with SiO2-Ap-ALN can be a promising method for repair of osteoporotic bone, [0101] lack of the systemic proinflammatory response—there was only local inflammation observed, [0102] the materials induced the angiogenesis—novel blood vessels were observed within the hybrid material after 60 days of in vivo experiment, [0103] the injectability of the materials and their ability to gel in vivo was confirmed.