Manufacture and Characterization of Mucoadhesive Buccal Films Based on Pectin and Gellan Gum Containing Triamcinolone Acetonide

Fernandes, Felipe Pereira; Fortes, Amanda Campos; da Cruz Fonseca, Said Gonsalves; Breitkreutz, Jörg; Ferraz, Humberto Gomes

doi:https://doi.org/10.1155/2018/2403802

International Journal of Polymer Science

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Abstract Introduction Materials and Methods Results and Discussion Conclusions Data Availability Conflicts of Interest Acknowledgments References Copyright Related Articles

Research Article | Open Access

Volume 2018 | Article ID 2403802 | https://doi.org/10.1155/2018/2403802

Manufacture and Characterization of Mucoadhesive Buccal Films Based on Pectin and Gellan Gum Containing Triamcinolone Acetonide

Felipe Pereira Fernandes,¹Amanda Campos Fortes,¹Said Gonsalves da Cruz Fonseca,²Jörg Breitkreutz,³and Humberto Gomes Ferraz¹

Academic Editor: Karthikraj Rajendiran

Received31 Jan 2018

Accepted29 Apr 2018

Published19 Jul 2018

Abstract

The treatment of canker sores can be quite compromised by the short period of the drug in the place of action. In this context, there is a need to develop drug dosage forms that allow more contact with the oral mucosa providing prolonged drug release. Therefore, the aim of this work was to obtain and characterize buccal films based on pectin and gellan gum in order to evaluate the potential use of these natural polymers in the production of pharmaceutical dosage forms for controlled release of TA in the oral mucosa. Using a 2³ full factorial design, eight formulations were prepared by solvent casting method. The raw materials and films were characterized using techniques such as FTIR, DSC, and TG. In addition, thickness, mechanical properties, mucoadhesive strength, swelling, drug content, and dissolution profile of the films were evaluated. The results of FTIR, DSC, and TG showed that new chemical species are not formed in the production of films, and that these dosage forms have an adequate thermal behavior. All formulation showed a high degree of swelling, good mechanical resistance and elasticity, and a good mucoadhesive strength as well as able to act as a controlled release system.

1. Introduction

The oral cavity connects the external environment to interior of the body and is subject to different types of pathologies that require local treatment, such as periodontal disease, gingivitis, oral candidiasis, halitosis, herpes, and canker sores [1]. Specifically in the case of canker sores, the treatment consists of mouthwash with antiseptics, as well as the application of ointments for oral use containing anti-inflammatory drugs [2]. However, due to the short residence time of the drug at the site of action, this treatment can be greatly compromised, requiring multiple doses throughout the day [3].

For this reason, several buccal formulations like gels [4, 5], mucoadhesive tablets [6–8], patches, and buccal films [9–15] have been developed using polymers that allow the most direct contact with the mucosa and provide a prolonged release of the drug, reducing the need for administration of repeated doses [10, 16].

In particular, buccal films show greater accuracy and flexibility in relation to dose and better mechanical resistance when compared to other dosage forms. Besides, it can act as a controlled release system and can be easily removed in emergency cases [17, 18].

According to Patel et al. [19], films are flexible and elastic which provide greater comfort to patient. However, they are strong enough to resist breakage caused by movements of the mouth [10, 20]. Due to these features, films can be used at night, during sleep, increasing adherence to treatment.

In this work, films were formulated using natural polymers, pectin (PEC) and gellan gum (GG). Triamcinolone acetonide (TA), a synthetic glucocorticoid, was used as a model drug, since it is used in long-acting relief of signs and symptoms of many oral inflammatory conditions, particularly canker sores [2, 21, 22].

Pectin is a natural polysaccharide found in the cell wall of several plant species, mainly composed by alternating galacturonic acid, rhamnose residues, and some arabinan and/or galactan side chains. It presents both mucoadhesive and swelling properties and moreover can be used either alone or associated with natural or synthetic polymers in the designing of different drug delivery systems [23–25].

Gellan gum is an exocellular polysaccharide secreted from the bacterium Sphingomonas elodea and consists of repeating tetrasaccharide of glucuronic acid, rhamnose, and glucose [26, 27]. It is widely used in the food industry due to its gelling properties [28].

Both polymers are nontoxic, biocompatible, and biodegradable and possess mucoadhesive properties which make them a promising material for pharmaceutical application [24, 29–32].

There are some studies about films using gellan [33, 34] and pectin singly [35–37], but the preparation of the films has some drawbacks such as the use of acids, organic solvents, or crosslinking agents.

Moreover, as far as we know, there are no works in the literature using GG and PEC together to the development of buccal films. Therefore, the aim of this work was to obtain, through a simple method, and characterize buccal films for evaluating the potential use of these natural polymers in the production of pharmaceutical forms for controlled release of TA in the oral mucosa.

2. Materials and Methods

2.1. Materials

Triamcinolone acetonide was kindly provided by Prati-Donaduzzi (PR, Brazil). The polysaccharides, low acetylated gellan gum (KELCOGEL® CG-LA type) and low esterified citrus pectin (GENU® Pectin USP-B type), were kindly donated by CP Kelco (SP, Brazil). Glycerol (GLY) (Synth Reagentes Ltda, SP, Brazil) was used as plasticizer.

2.2. Design of the Buccal Films

Buccal films were prepared by solvent casting technique [38]. First, the polymers and the drug (100 mg) were dissolved in 100 ml of water at 50°C, using a magnetic stirrer at 150 rpm for 12 hours. Then, the plasticizer was added and homogenized for 2 hours. Finally, 100 g of this solution was poured into a glass Petri dish and dried in a circulating oven air at 40°C for 24 hours, resulting in a thin film after solvent evaporation.

A 2³ full factorial design was used to evaluate the influence of independent variables—amounts (%) of pectin, gellan, and glycerol at two levels—on the response of swelling, mechanical properties, and cumulative drug release after 1 and 10 hours (%). This experimental design resulted in eight films formulations, which contained a fixed amount of the drug (Table 1).

2.3. Physicochemical Characterization

The isolated raw materials (TA, PEC, GG, and GLY) and the buccal films were subjected to Fourier transform infrared spectroscopy (FTIR), differential scanning calorimetry (DSC), and thermogravimetry (TG).

The FTIR spectra (infrared spectrophotometer, Bruker Vertex-70, USA) were obtained, in an inert atmosphere (N₂), with a resolution of 4 cm⁻¹ from the 4000 to 500 cm⁻¹ region.

DSC curves were obtained using a DSC 7020 cell (Exstar, Japan), and the TG/DTG curves were taken with a TG/DTA 7020 thermobalance (Exstar, Japan) under a nitrogen flow and heating rate of 10°C min⁻¹. Highly pure indium (m.p., 156.6°C; , 28.54 J g⁻¹) was used to calibrate the DSC cell, and calcium oxalate was used to calibrate the thermobalance, under the same conditions as the samples.

2.4. Swelling

Swelling of the films was determined using a method described by Yang et al. [27]. The calculation to determine the percentage of swelling is shown in where m1 and m2 represent the mass of dry samples before and after immersion in the solution, respectively.

2.5. Disintegration

The disintegration was determined using a disintegrator (Ethik Technology, Brazil). Saline buffer (pH 6.8) at a temperature of 37 ± 2°C was used as the test media. The buccal films () were subjected at successive vertical immersion and the time until total disintegration was recorded.

2.6. Drug Content Uniformity

The drug content was determined using a method adapted from the United States Pharmacopeia [39]. A piece of each film () equivalent to 1.5 mg of drug was weighed, dissolved in ethanol, and transferred to a 25 ml flask. The sample was subjected to ultrasound for 60 minutes to ensure complete solubilization of the active. Then, the flask volume was completed, and an aliquot was removed and filtered through a 0.20 μm filter aid Minisart RC 25 (Sartorius, Göttingen, Germany). The amount of drug in the resulting solution was determined by UV spectrophotometer DU-640 (Beckman Coulter, USA) at a wavelength of 242 nm.

2.7. Film Thickness

Micrometer screw (Mitutoyo, Neuss, Germany) was used to determine film thicknesses of samples. Five points were measured for each formulation.

2.8. Folding Endurance

Folding endurance of each film () was determined by folding the film, 180° in the same place, up to a maximum 300 times or until the film breaking.

2.9. Mechanical Properties

The mechanical properties as puncture strength and elongation to break were determined according to Preis et al. [38].

The system started recording force and displacement of the probe when having contact to the sample. Using a probe of area 18.10 mm², the measure of puncture strength and elongation percentage was calculated. where is the initial length of the film sample that is not punctured by the probe, is the penetration depth/vertical displacement by the probe, and is the radius of the probe.

2.10. Determination of Mucoadhesive Strength

Mucoadhesion properties were assessed by adapting the methodology used by Sathe et al. (2015). The mucoadhesive strength of each formulation () was calculated. where is the weight required for detachment in kg, is the acceleration due to gravity (9.81 m/s²), and is the area of the film exposed.

2.11. Dissolution Profile

In vitro dissolution studied was performed, in triplicate, using a paddle over disk apparatus (USP 5). The buccal films were cut into circular patches (equivalent to 8 mg of drug), placed over the disk, and covered with a polyester mesh. This apparatus was settled in the bottom of the dissolution vessel, containing 900 ml of saline buffer (pH 6.8) at 37 ± 1°C. The dissolution test was carried out in a D-800 Logan dissolution tester (Logan Instruments Corp, USA) with paddle speed of 75 rpm. At prespecified time intervals, 5 ml of aliquots was withdrawn by filtration (0.45 μm) and equal volume of fresh prewarmed medium was replaced in the vessel. The absorbance of aliquots was taken at 242 nm by UV spectrophotometer DU-640 (Beckman Coulter, USA), and percentage of drug released to the dissolution medium was calculated.

The mechanism of drug release was analyzed using different mathematical models (Korsmeyer-Peppas, Higuchi, first-order, and Hixson-Crowel) by the DDSolver software. All the experiments were performed in triplicate. Results are expressed as mean ± SD. ANOVA and -test were used to determine statistical significance of studies. Differences were considered to be significant for values of .

3. Results and Discussion

3.1. Infrared Spectroscopy (FTIR)

Figure 1 shows infrared spectra of isolated raw materials (TA, PEC, GG, and GLY) and the buccal films (F1–F8). The bands observed to TA included the OH group in the range of 3390–3462 cm⁻¹, C=O bands between 1500 and 1750 cm⁻¹, C=C bands in the range 1660–1600 cm⁻¹, C–H stretching of sp³ and sp² carbons in the range of 3100 and 2900 cm⁻¹, and C–O stretching at 1200 cm⁻¹ [40].

The characteristic FTIR peaks of pectin were a broad band at 3100–3550 cm⁻¹ which was assigned to -OH stretching, a band between 2900–3000 cm⁻¹ due to the stretching vibration of methyl group of methyl ester. Bands between 1756 and 1530 cm⁻¹ assigned to the C=O stretching vibration of methyl-esterified carboxylic groups and vibrations of the carboxylate (-COO-) group, respectively. The absorption bands at 1220 and 1008 cm⁻¹ corresponded to ether (R–O–R) and C–C bond in the ring structure of pectin molecules. Weak symmetric carbonyl stretching vibrations were observed in the range of 800–1000 cm⁻¹ [36, 41].

The spectra of GG show a broad absorption band due to free OH group in the range of 3000 cm⁻¹ and 3500 cm⁻¹; a shoulder around 2900 cm⁻¹ can be attributed to C–H stretch of alkane. Further, the spectra show bands in the range of 1600 cm⁻¹ and 1400 cm⁻¹ which can be ascribed to C–O stretching of carboxylate ion. The band around 1000 cm⁻¹ can be attributed to C–O stretch of carboxylic acid [26, 33].

Glycerol showed bands similar to the other components of the film, intense absorption band in the region of 3550–3100 cm ⁻¹ corresponding to the vibration of the OH group of alcohol, an absorption band around 1250 to 900 cm ⁻¹ strong intensity due to the stretching of C–O bond, and a band at 2950 cm⁻¹ which corresponds to CH stretching [42].

The FITR of the films showed the maintenance of characteristic bands of the raw materials. Only the band around 3500–3000 cm⁻¹ shows quite intense, but this is due to the presence of residual water in the formulations. The absence of new bands in the FTIR shows that the components of the films do not react between them forming new chemical species [32].

3.2. Thermal Analyses

DSC curves (Figure 2(a)) show an endothermic spike for TA which corresponds with the melting point at 284.6°C and is indicative of a crystalline anhydrous state for TA. The DSC curves for the GG and PEC are quite similar. Both have two characteristic peaks, around 190–200°C assigned depolymerization of the polymer chains and a peak around 240–250°C attributed to degradation releasing common organic compounds in the thermal decomposition of natural polymers such as CO₂, CO, and H₂O [25, 32].

(a)

(b)

The DSC curves to films show no major differences in the curves presented for raw materials. The absence of a sharp endothermic peak corresponding to the melting point of the TA might be due to the conversion of crystalline drug to amorphous or disordered crystalline phase in the polymeric matrix [18].

DTG curve of TA (Figure 2(b)) shows that thermal degradation occurred only after 290°C, in two steps, with the first occurring in the range of 290–350°C and the second occurring in the range of 350–450°C. These results are in accordance with the published data from da Silva-Junior et al. [43]. DTG curves to GG and PEC show peaks between 230 and 250°C representing the degradation temperatures of these polymers [44, 45]. The mass loss profile of the films is similar to raw material. It shows a peak near 100°C, indicates loss of water, and peaks around 200–250°C, indicating the degradation of polymers and plasticizer. Nevertheless, after the temperature of degradation of the polymers, the films continue to lose mass, but more slowly. It happens due to the elimination of carbonaceous material and of presence of TA in the polymeric film.

3.3. Film Properties

Swelling capacity is one of the most important features to application in polymeric drug delivery systems because it exerts an important effect on the release kinetics of drug incorporated in the films. Furthermore, it is directly related with mucoadhesivity, since the bioadhesive sites in the polymers chain are exposed during the swelling process when the absorption of the medium by the polymers happens [46].

The swelling polymer mechanisms can be described in three main steps. Initially, the adsorption on the surface of the medium occurs. Second, due to saturation of the surface, the molecules tend to migrate into the matrix up to the linking polar groups weakening the intermolecular hydrogen bonds, which leads to an expansion of the chains. Third, the spacing of the chains provides the generation spaces in the matrix which facilitates the penetration of water or other medium used [47].

Table 2 shows that the swelling percentage of the films was greater than 250% and it increased, proportionally, with the amount of polymer present in each formulation. This water absorption by the films is due to the formation of hydrogen bonds and the strong hydrophilic characteristics of carboxylic and hydroxyl groups present in the structures of polymers and plasticizer. PEC and GG are hydrophilic polymers that in pH around 7, the carboxyl groups remain in the ionized form, which increases the hydrophilicity [32].

Figure 3(a) indicates that all the components of the formulations have an effect on the swelling of the films, wherein the gellan gum is the component with greater influence in this property. However, glycerol, a hydrophilic plasticizer, that increases the space between the polymer chains also have positive effects either alone or interact with each other.

(a)

(b)

(c)

(d)

Regarding disintegration, all formulations showed disintegration time exceeding 8 hours. Results are quite satisfactory, since a drug delivery system designed for oral administration should resist the action of saliva, the tongue movements, and swallowing, thus allowing a more prolonged contact of the drug with its site of action.

Besides, the results of disintegration and swelling indicated that even without the addition of crosslinking agents, films retained their structure for a long period. These properties would hardly be achieved in films produced with the polymers isolated in the absence of crosslinking [48]. The similar structures of PEC and GG appear to be determinant to explain their synergistic interaction as it allows the development of an intermolecular bonding of these polysaccharides.

Drug content was satisfying for all formulations. The low standard deviations led to the conclusion that the drug was homogeneously distributed in the formulations. Table 2 shows the values of the mechanical properties. It is observed that generally when there is a larger amount of polymers in the formulation, the greater the strength and flexibility of the film. However, in formulations containing the same proportion of polymers but with different amounts of glycerol, films having more plasticizers are more fragile and have greater elasticity.

All films have an acceptable thickness (between 50 μm and 1 mm) for use as buccal device. Regarding the folding endurance, the F1 and F2 did not show good resistance. The F1 values were 120 ± 12 and for F2 were 90 ± 9 times, and all the other formulations did not break even after being folded up by more than 300 times. This is highly desirable because it would not allow easy dislocation of the films from the site of application or breaking of film during administration.

Figures 3(b)–3(d) show the influence of the components of the films in mechanical properties. It is noted that for force measurements Figure 3(b) and strength puncture Figure 3(c), GG and PEC separately have a positive effect; however, GG has a slightly larger positive effect. In relation to elongation Figure 3(d), the interactions between PEC and GG and PEC and GLY are the factors that influence this property. Glycerol, due to the increasing distance between the polymer chains, decreases the resistance of the films making them more fragile, but increases the elongation percentage of the formulations.

Due to the presence of hydroxyl and carboxylic groups in the polymer constituents of the films, all the formulations showed good mucoadhesion strength values. The hydrophilic groups present in the polymers bind to the mucin through hydrogen bonds; in addition, the presence of glycerol facilitates swelling and increases the distance between the polymer chains; consequently, this higher flexibility can improve the interpenetration and entanglement of bioadhesive polymer chains with mucous polymer (mucin), leading to the strengthening of mucoadhesive interactions. It can be seen that F1 and F2 have the smaller amounts of polymers; therefore, they have the lowest values of mucoadhesion.

The F7 and F8 formulations showed the greatest mucoadhesion values; however, a very high adhesive strength can make the removal of the attached device in the oral cavity difficult, which might cause discomfort to the patient.

3.4. Dissolution Profile

The dissolution profiles of TA from GG/PEC films (Figure 4) show that different formulations exhibited different times of total drug release. Initially, all the films had a burst effect. This effect can be explained due to a part of the drug that is only adsorbed on the polymer matrix, because the drug migrates to the surface of the film during the drying process. The burst effect is greater in formulations containing smaller amount of polymer; due to the fact that the polymeric film has fewer layers, the drug can easily migrate to the surface [49].

Formulations with higher amount of glycerol demonstrated a greater percentage of release, since this substance is hydrophilic and possesses a low molecular weight, promoting the relaxation of polymer chains during the initial of the swelling process, which originates a structure with new channels throughout the matrix, facilitating the diffusion of the drug [32, 50].

Figure 5(a) shows the influence of the components of the films in the TA release profile. During the early drug release, there is an influence of glycerol due to its hydrophilic groups interacting with the polymer through hydrogen bonds. However, being a highly hydrophilic substance, glycerol dissolves in the medium, decreasing its interaction with the other components of the film in the end of dissolution [51, 52].

(a)

(b)

GG and PEC also influence the TA release rate. This occurs because GG forms gels in aqueous solution, in the presence of salts, independent of pH, and due to its double helix structure, that in aqueous medium forms “clusters,” a kind of crosslinking, between the chains of this polymer, slowing down the release of drug [30, 31, 53]. However, pectin forms stronger gels at pH less than 3 [54].

During the dissolution test, the amount of polymer in the film is the main factor controlling the drug release. It can be observed in Figure 5(b) that formulations, which showed a higher release time of TA, were the films that contained larger amount of polymers.

Indeed, erosion, diffusion, and swelling of the polymeric matrices are the mechanisms by which these systems can control the release of drugs. In general, when the matrix structures have been exposed to the dissolution medium (or biological fluid), they can maintain their structure constant during the dissolution process or may suffer swelling phenomenon and subsequently erosion [55, 56]. In the case of buccal films, they maintained their structure throughout the dissolution test, suggesting that swelling and diffusion are the factors that influence drug release.

Despite the complexity of the phenomena involved in drug release from hydrophilic matrix systems, some well-known models are used extensively to examine the release of active substance from such systems.

Table 3 shows the kinetic model most suitable to represent the release of TA from the buccal films. The model that best fitted the release data was evaluated by correlation coefficient (²).

The mathematical treatment of the dissolution profiles showed that the most appropriate model to describe the kinetics of dissolution for all the formulations developed was the Korsmeyer-Peppas. This model is generally used to analyze the release of drug from polymeric dosage forms where the release mechanism is not well known or when more than one type mechanism that acts in the drug delivery. In the case of the buccal films developed, the transport of drug obeys the Fick laws (diffusion) because the release exponent is less than 0.5 [32, 57, 58].

4. Conclusions

In this work, new buccal films based GG and PEC were successfully obtained through a simple method without the use of crosslinking agents, acids, or organic solvents.

All formulations showed a high degree of swelling, good mechanical resistance and elasticity, and good mucoadhesive strength, and they were able to act as a controlled release system, controlling the release of TA for a period exceeding 8 hours in some cases.

However, formulations F1 and F2 showed the smallest value for all measurements and proved to be more brittle and have a low mechanical strength. Films F7 and F8 showed the highest values in all parameters, but they are not the best formulations, because of its high degree of swelling, low flexibility, and its high mucoadhesive strength which can bring discomfort to the patient.

Thus, the best films were F3, F4, F5, and F6. These formulations have intermediate values of polymers and good characteristics for an act as mucoadhesive release system, because they can release the drug gradually further and they can serve as a mechanical protection.

The results showed that only the interaction between hydrophilic polymers is sufficient to obtain films with adequate characteristics for use as drug release devices. This opens the way for future research for the production of films without the use of organic solvents and crosslinking agents, making the manufacturing easier and obtaining a safer final product to the patient.

Data Availability

The data used to support the findings of this study are available from the corresponding author upon request.

Conflicts of Interest

The authors declare that they have no conflicts of interest.

Acknowledgments

The authors of this paper thank Dr. Nágila Ricardo, from the Department of Chemistry of the Federal University of Ceará, for the provision of infrared equipment for conducting the tests. This work had the financial support of CAPES (Proc. 6364/15-2) and FAPESP agencies.

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Copyright © 2018 Felipe Pereira Fernandes et al. This is an open access article distributed under the Creative Commons Attribution License, which permits unrestricted use, distribution, and reproduction in any medium, provided the original work is properly cited.

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