Characterization and in vitro release studies of tetracycline and rolitetracycline imobilized on anionic collagen membranes

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Characterization and in vitro release studies of tetracycline and rolitetracycline imobilized on anionic collagen membranes

Gilberto GoissisI, ^*; Maria Helena de SousaII, ^*

^IDepartamento de Produção, Biotech Biomédica Produtos Médicos e Odontológicos Ltda. Rua Santos Dumont, 800, Vila Celina, 13566-445 São Carlos - SP, Brazil

^IIFaculdade Farmácia, Campus de Jatai, Universidade Federal de Goiás - UFG, Jatai - GO, Brazil

ABSTRACT

This work reports the covalent immobilization of tetracycline and rolitetracycline over anionic collagen membranes and the drug release studies as an effort to develop a two stage drug release based on diffusion (fast release) and on the rate of membrane biodegradation (slow release). Independent from casting conditions antibiotics incorporated by dispersion were released in the range from 80 to 100% within 7 hours in concentrations significantly higher than those described for the prevention of bacterial growth. Antibiotic release within this period was predominantly diffusion controlled. Covalent immobilization by a modified azide procedure occurred with preservation of collagen structure independently from pH of casting and reaction conditions. Its expected that anionic collagen membranes with dispersed and covalently bound rolitetracycline or tetracycline, in association with conventional therapy, may significantly reduce membrane induced infections observed post-implantation, one of the major problem associated with periodontal ligaments reconstruction by the Guided Tissue Regeneration procedure.

Keywords: antibiotic, immobilization, covalent, release, collagen, membranes

1. Introduction

Sustained drug release technology¹ is being applied from protein hormones such as insulin for the treatment of diabetes² to antibiotics for the prevention or minimization of bacterial infection^3-5. Advantages of this technology are associated with reduction in side effects, decreased systemic toxicity and higher efficiency due to high drug concentrations at the site of damage^6,7. Improvements on the field has also been based on the development new biocompatible synthetic⁸ and natural polymers⁹ and bioceramic^4,10,11. Among the natural polymers, collagen has been investigated as natural candidate for drug delivery matrix due to its high biocompatibility, low antigenicity^12,13, controlled biodegradability by cross-linking reagents¹³ and the easy that may form composites with ceramics or synthetic polymers^4,15,16. Some examples include gentamicin supported in collagen sponges for the control of osteomyelitis, the prevention of wound infection in elective colorectal surgery and in ophthalmology, in the form therapeutic shields, containing cyclosporine and metilmicin for the promotion of corneal epithelial healing¹⁷. As with most sustained delivery systems involving molecules with low molecular masses, drugs release from collagen devices are predominantly diffusion controlled with high release coefficients, thus preventing long term maintenance of therapeutically levels^18,19. One alternative way to modulate release over an extended period time would be through covalently binding of the drug so that sustained release may be maintained by the rate of biodegradation²⁰. In association with diffusional mechanisms may provide highly efficient sustained drug delivery system for a variety of applications such as in the treatment of periodontal diseases²¹. For this purpose formulations include tetracycline fibber, doxycycline polymer, chlorhexidine chip, minocycline ointment and metronidazole²¹. While this therapy produce favorable results for the control and elimination of the disease they are unsatisfactory for the treatment of the anatomical lesions produced by the disease. In this case the indicated treatment for periodontal tissue regeneration is the Guided Tissue Regeneration technique²². One significant advance in the field was the introduction of controlled biodegradable materials^23,24 that in comparison to non-biodegradable polymers, do not require a second surgical intervention for membrane removal. One major problem with this technique is the membrane induced infections observed post implantation, a common event associated with the guided tissue regeneration procedure^5,26.

This work reports the covalently immobilization of rolitetracycline and tetracycline over anionic collagen membranes (ACM) by a modified azide procedure or dispersion and the release studies, as an effort to develop a two stage release, based on diffusion (fast release) and on the rate of ACM biodegradation (slow release)¹⁴. ACM was the material of choice due to its biocompatibility, the ability of this membranes to reconstitute the periodontal ligaments²³ and increased carboxyl groups content as a result of the selective hydrolysis of carboxyamides of asparagine and glutamine present in the collagen matrix¹⁵, thus allowing for a high level of antibiotic incorporation by esterification in comparison to native collagen biomaterials. Under these conditions the total COOH mEq.g^-1 of collagen will be approximately 1.0 in comparison to 0.84 for native.

2. Material and Methods

2.1. Anionic collagen gels

These were prepared after the treatment of bovine tendon with an alkaline solution, 6% in dimethylsulfoxide containing sulfate and chloride salts of sodium, potassium and calcium for a period of 24 hours (15). Excess salts were removed by extensive washes with 3% boric acid solution (3 times for 6 hours), 0.3% EDTA pH 11.0 (3 times for 6 hours) deionized water (6 times for 2 hours) and after extraction with a pH 3.5 acetic acid solution the concentration was adjusted to 1.0% (w.w^-1). Part of the gel was dialyzed to equilibrium against a pH 7.4, 0.13 M, phosphate buffer and after centrifugation at a 20 °C gel concentration was adjusted to 0.7% (w.w^-1).

2.2. Antibiotic immobilization

2.2.1. By dispersion on collagen gels

The antibiotics under studies, of tetracycline (hydrochloride) and rolitetracycline (monohydrate 0.25 mol isopropanol) were dispersed in 0.7% (w.w^-1) collagen gels equilibrated at pH 3.5. After homogenization, ACM were cast by the introduction of 7 mL of the dispersion in acrylic molds with 4.5 cm of diameter. The gels were dried under laminar flow at room temperature and protected from light. Antibiotics concentrations were respectively 0.87 and 0.92 mg of tetracycline and rolitetracycline/cm² of collagen membrane. Similar procedure was used for membranes cast at pH 7.4 except that dispersion of tetracycline was done on collagen gels previously equilibrated at pH 7.4 as described above.

2.3. Covalent immobilization

2.3.1. Glutaraldehyde cross-linking

Collagen membranes cast under the same conditions as described and after equilibration in PB buffer were immersed in a 0.05% glutaraldehyde solution in the same buffer for 15 minutes After this period the membranes were washed throughout with deionized water, dried under the same conditions as described above and submitted to the azide procedure as described in the literature²⁷ except that the 0.2 M hydrochloric solution in methanol was prepared by the reaction of thionyl chloride with methanol in order to assure complete anhydrous conditions in the esterification step.

2.3.2. Esterification

ACM were treated at 25 °C with 30 mL/membranes with a methanol:HCl, 0.2 M for a period of 4 and 7 days with continuous agitation. After this period, ACM was washed 6x with 20 mL of 1.0 M NaCl solution. The methanol:HCl solution was prepared by the addition of 1.8 mL of thionyl chloride over the alcohol (200 mL) followed by titration²⁸.

2.3.3. Hydrazinolysis

ACM was treated at 25 °C with a 100 mL/ACM of a 1% hydrazine solution in NaCl 1.0 M for a period of 24 hours. After this periods ACM was washed as described in the esterification procedure.

2.3.4. Azide formation and antibiotic incorporation

ACM were suspended in 30 mL of a 1.0 M NaCl solution made 0.5 M in NaNO₂ 0.3 M cooled to 4 °C and the reaction allowed to proceed for 3 minutes. After this period ACM was washed 3x with PB (4 °C) followed by the addition of 50 µmoL of antibiotic (22 mg of tetracycline; 28.3 mg of rolitetracycline/ACM) dissolved in 30 mL of PB and the reaction allowed to proceed for a period of 20 days. Disappearance of antibiotic from solution was performed by UV-spectroscopy at 269.0 nm (λ_max for tetracycline) and 271.6 nm (λ_max for rolitetracycline).

2.3. Material characterization

2.3.1. Infrared spectroscopy (IR)

Infrared absorption spectra were obtained from 0.4 mg.cm^-2 membranes prepared as described above except from 0.35% collagen gel at pH 3.5. Collagen IR absorption spectra were recorded from 400 to 4,000 cm^-1 with a resolution of 4 cm^-1, in a Bomen FTIR MB-120 spectrophotometer and the 1,235/1,450 cm^-1 ratio compared with that of gelatin membranes for comparative IR for the measure of collagen triple helix integrity.

2.3.2. Thermal stability

Was determined as shrinkage temperature (Ts) with 2.0 x 0.2 cm strips of collagen membranes in a melting point equipment adapted for Ts evaluations. Materials were immersed in the phosphate buffer (PB) with samples enclosed in a 20 mm graduated Pyrex tubing, immersed in a silicone oil bath. Heating rate was fixed at 2.0 °C/min, from room temperature up to 120 °C. Ts values correspond to the average of 3 independent determinations.

2.4. Release studies

Membranes with antibiotic incorporated by dispersion (tetracycline and rolitetracycline) or by the azide procedure (tetracycline) were fixed in a chamber containing 150 mL of saline phosphate buffer (PBS) pH 7.4 with the temperature kept at 37 ± 0.1 °C and continuous stirring. Release studies were performed by UV absorption readings at 271.6 and 269.0 nm for rolitetracycline and tetracycline in an UV-visible spectrophotometer HITACHI^® Mod. U-1100 in samples removed for a period of 7.5 hours. The volumes of removed samples were immediately replaced with the same volume of PBS.

3. Results and Discussion

The ratio for the infrared absorbances of bands 1,235/1,450 cm^-1 determined for anionic collagen membranes cast from bovine tendon at pH 3.5 and 7.4, which is a measure of integrity of the triple helix structure²⁹ were 1.0 e 1.1 respectively, suggesting that collagen triple helix secondary structure was preserved. Typical values for collagen membranes cast under some conditions are close to 1.0 while those for denatured collagen and gelatin membranes are significantly lower and in the range of 0.60²⁹. The infrared spectrum of membranes with antibiotics did not show any bands due to incorporated antibiotics, probably due to their low concentration.

The maintenance of collagen triple helix secondary structure was also confirmed by thermal stability determined as Ts since independently the antibiotic immobilization procedure (dispersion or azide) all ACM were characterized by thermal transitions, which is absent in denatured collagen materials (Table 1) in the temperature range studied. For ACM cast at pH 3.5 and 7.4 and in the absence of antibiotics Ts values were respectively 49.1 ± 0,7 and 58.0 ± 0.6 °C. The higher thermal stability found for ACM equilibrated at pH 7.4 is in agreement with the disruption of collagen macromolecular fibrillar assembly that is known to occur with collagen matrices submitted solution with pH lower than 4.25³⁰. After glutaraldehyde crosslinking these values increased 77.9 ± 0.2 and 77.3 ± 0.4 °C (Table 1) as described for similar ACM with controlled biodegradability and used in the treatment of periodontal diseases by the guided tissue regeneration technique^14,23.

No significant changes were detected in Ts for ACMs equilibrated at pH 3.5 or 7.4 with rolitetracycline and tetracycline incorporated by dispersion (Table 1) suggesting the absence of any interaction between ACM and the antibiotics.

Release studies of rolitetracycline and tetracycline incorporated by dispersion on ACM cast at pH 3.5 (Figure 1a, curves a and b) showed that after 4 hours these antibiotic were almost completely released from RCM and at levels of respectively 86.6 ± 1.5 and 97.2 ± 2.1%. After 7.5 hours the amount released were respectively 92.2% ± 0.6 and 98.5 ± 0.7. For tetracycline dispersed on RCM cast from gels previously equilibrated at pH 7.4, the amount of antibiotic release after 3 hours was 84.5 ± 1.2% remainning constant after this period (Figure 1a, curve c), and may be attributed to electrostatic binding of the antibiotic (a cation at this pH) to the polyanionic RCM¹⁴.

Under these conditions the average rolitetracycline concentration that may be immediately released within the periodontal pocket post surgically in the first 4 hours period will be 489.78 µg.mL^-1/h, which is significantly higher than MIC values for this antibiotic and of 8 µg.mL³¹ and compatible with the necessary concentration of 150 µL/h established as ideal in the gingival flow³². After this time (Figure 1a, curve b), during the remaining 3.5 hours post operation, the average rolitetracycline release would be 69.1 µg.mL/h which is still significantly higher than MIC for this antibiotic. With tetracycline effective concentration was observed only within the first 4 hours with an average release of 422.8 µg.mL^-1/h. The calculations above were based on the amount of antibiotic present in 2 cm² of ACM, the average of membrane size normally used in the treatment of furcation II lesion²³. Under these conditions the total disposable tetracycline and rolitetracycline concentration will be 1.7 and 1.8 µg.

Antibiotics release from ACM for releases from 60 to 70% were analyzed by means of the Higuchi equation M_t = Kt^{n 33} and independent from the antibiotic or membrane casting conditions showed values of n close to 0.50 (Figure 1b, Table 2). These results suggest that most of the antibiotics are released from ACM predominantly by diffusion with high release coefficient. The calculated Higuchi constants for tetracycline and rolitetracycline in ACM cast from gels equilibrated at pH 3.5 were respectively 0.80 ± 0.02 and 0.75 ± 0.02 g.h^1/2 (Table 2). For tetracycline dispersed in membranes cast at pH 7.4 in ACM cast the Higuchi constant was 0.88 ± 0.02. Correlation coefficient in all cases were close to 0.99 (Table 2). These results are consistent with those described for sustained delivery systems involving collagen matrices and drugs with small molecular masses ^19-21.

Glutaraldehyde cross-linking was performed under the same conditions as described for ACM used in the biocompatibility and periodontal ligament repair studies^14,23, a conditions where glutaraldehyde concentration is sufficient to promote complete reaction with free ε -amino groups of lysine residues (Schiff base formation). This was also necessary to avoid the formation of amide bond type of crosslinking that could be formed by reaction of the azide function with ε -amino groups of lysine and thus competing with antibiotic ester bond formation to the collagen matrix (Figure 2). This was indicated by maintenance of Ts values determined after the azide procedure for the introduction of the antibiotic by esterification and, described below.

Independently from pH casting conditions or the esterification period, Ts values in all case were similar to that found for ACM after glutaraldehyde cross linking and of 79.0 ± 0.5 °C (Table 1). For membranes cast at pH 3.5 Ts values after 4 and 7 days esterification were respectively 77.9 ± 0.2 and 77.3 ± 0.4 °C (Table 1). After rolitetracycline immobilization by azide Ts values were 78.7 ± 0.4 and 78.2 ± 0.7 °C. Under similar conditions and 7 days esterification introduction of tetracycline produced a RCM with a Ts values of 77.7 ± 0.8 °C

Other minor change, but significant change in routine was the preparation of methanol: HCl esterifying reagent by the addition of thionyl chloride to methanol in order guarantee complete anhydrous conditions, since esterification is probably the most sensitive step affecting process repeatability, in comparison to hydrazinolysis, azide formation and antibiotic incorporation. Under this conditions, the required amount of HCl for the acid catalyzed esterification of collagen is provided by the reaction of thionyl chloride with residual water present in the system. Besides, the reaction of methanol with thionyl chloride also generates the esterifying reagent dimethylsulphite²⁸. Although the 7 day esterification procedure was established in advance based on the esterification data described for bovine pericardium intended for the manufacture of valvular bioprostheses²⁷ a 4 day esterification procedure was also studied.

Results in Figure 3a (curves a and b) correspond to the disappearance of rolitetracycline in contact with azide ACM (membranes cast at pH 7.4) from solution showing that under the conditions used no significant difference in antibiotic incorporation was detected between membranes esterifyed for 4 days (Figure 3a) and 7 days (Figure 3b), suggesting esterification is over a 4 day period. After 21 days of reaction total antibiotic incorporation amounted to 9.3 ± 1.6 and 9.0 ± 1.3 mg for 4 and 7 days esterification respectively.

Nevertheless, extraction of ACM with PB showed that not all of the incorporated antibiotic by the membrane was covalently bound since 2.7 ± 1.1 and 2.5 ± 0.9 mg were removed from the 4 and 7 days esterifyed ACM respectively. Extractions were performed until no traces of antibiotic could be detected in solution by UV spectroscopy. As a result the total amount of rolitetracycline covalently bound to ACM after 4 and 7 days esterification were respectively 6.6 (12.3 µEq) and 6.5 (12.5 µEq) mg/RCM. Based on the average weight of ACM of 49.57±1.53 mg and the number of COOH groups available for esterification of 1.07 µEq.mg^-1, the yields for rolitetracycline incorporation for 4 and 7 days esterification were respectively 23.2 and 23.6%, confirming the end of ACM esterification after 4 days of reaction.

Although the total incorporation of 14.1 ± 0.19 mg observed for tetracycline (Figure 3c) would suggest a more efficient covalent immobilization (Figure 3), 7.1 ± 1.3 mg of the antibiotic was extracted with PB. As a result, the total amount of antibiotic covalently bound to ACM was only around 7.0 mg, that based on the total amount of carboxyl groups available in ACM, corresponds to an yield of reaction 29.6%.

Assuming for the ACM used in this work a biodegradation period of 40 days and that in the treatment of periodontal diseases approximately 2 cm² of membrane is normally used²³ the calculated amount of free antibiotic in the periodontal pocket for rolitetracycline and tetracycline will be respectively 0.85 and 0.91 µg/h. Although slow release biodegradable devices intended for the control of periodontal diseases are characterized by higher rates of antibiotic releases within the periodontal pocket^21,33,34 the numbers for tetracycline and rolitetracycline described above are close to the serum concentrations observed for doxycycline in oral administration and in the range from 0.91 to 2.26 µg.mL^-1 over the first 8 days³³.

As shown in Figure 4a ACM membranes cast at pH at pH 7.4 is still characterized by the presence of the collagen microfibril structure in spite of the increase in negative charge content at physiological pH and preliminary result in the dog periodontium after 20 days from implantation was characterized by a high degree of biocompatibility (Figure 4b).

4. Conclusions

The results above showed that rolitetracycline or tetracycline incorporated by dispersion over ACM may be immediately released within the periodontal pocket post surgically with concentrations which are significantly higher than MIC values for this antibiotic and compatible with the necessary ideal concentration in the gingival flow. Independent from the antibiotic or membrane casting conditions, up to 60 to 70% release, the Higuchi equation suggest that most of the antibiotics are released from ACM predominantly by diffusion in association with high release coefficient, in agreement with sustained delivery systems involving collagen matrices and drugs with small molecular masses. The azide procedure showed that under the conditions used covalent immobilization was achieved at levels in the range from 23 to 29% (calculated on the basis of the total COOH groups available for esterification) and independently from pH casting and esterification conditions or reaction time (methyl ester formation or antibiotic incorporation) collagen structure was preserved in all cases. Although esterification yields may be considered low, it is expected that ACM with dispersed and covalently bound rolitetracycline or tetracycline and in association with conventional therapy will reduce membrane induced infections observed post implantation, a major problem associated with ligaments reconstruction by the Guided Tissue Regeneration procedure applied treatment of periodontal diseases^25,26.

Acknowledgements

Thanks to Ezer Biazin and Glauco D. Broch for technical assistance. This work was supported by PADCT, n° 62.0001 and RHAE/CNPq n° 610.490. M.H. Sousa was a fellowship from CNPq at the Master Post-graduation in Physicochemistry at the Inst. of Chem. São Carlos - Universidade de São Paulo

Received: June 20, 2008

Revised: January 6, 2009

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Publication Dates

• Publication in this collection
  18 May 2009
• Date of issue
  Mar 2009

History

• Received
  20 June 2008
• Reviewed
  06 Jan 2009