Diclofenac Potassium Transdermal Patches Using Natural Rubber Latex Biomembranes as Carrier

Barros, Natan Roberto de; Chagas, Paulo Augusto Marques; Borges, Felipe Azevedo; Gemeinder, Jose Lucio Padua; Miranda, Matheus Carlos Romeiro; Garms, Bruna Cambraia; Herculano, Rondinelli Donizetti

doi:https://doi.org/10.1155/2015/807948

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Abstract Introduction Experimental Results and Discussion Conclusions Acknowledgments References Copyright Related Articles

Research Article | Open Access

Volume 2015 | Article ID 807948 | https://doi.org/10.1155/2015/807948

Diclofenac Potassium Transdermal Patches Using Natural Rubber Latex Biomembranes as Carrier

Natan Roberto de Barros,¹Paulo Augusto Marques Chagas,²Felipe Azevedo Borges,¹Jose Lucio Padua Gemeinder,²Matheus Carlos Romeiro Miranda,¹Bruna Cambraia Garms,¹and Rondinelli Donizetti Herculano³

Academic Editor: Eugen Culea

Received29 Jun 2015

Accepted25 Oct 2015

Published08 Nov 2015

Abstract

The aim of this study was to design a compound transdermal patch containing diclofenac potassium (Dic-K) using natural rubber latex (NRL) biomembrane. The NRL from Hevea brasiliensis is easily manipulated and low cost and presents high mechanical resistance. It is a biocompatible material which can stimulate natural angiogenesis and is capable of adhering cells on its surface. Recent researches have used the NRL for Transdermal Drug Delivery Systems (TDDSs). Dic-K is used for the treatment of rheumatoid arthritis and osteoarthritis and pain relief for postoperative and posttraumatic cases, as well as inflammation and edema. Results showed that the biomembrane can release Dic-K for up to 216 hours. The kinetics of the Dic-K release could be fitted with double exponential function. X-ray diffraction and Fourier Transform Infrared (FTIR) spectroscopy show some interaction by hydrogen bound. The results indicated the potential of the compound patch.

1. Introduction

Diclofenac (Dic) is a well-known nonsteroidal anti-inflammatory drug (NSAID) with anti-inflammatory, analgesic, and antipyretic properties, comparable or superior to other NSAIDs [1]. Dic shows preferential inhibition of the cyclooxygenase-2 (COX-2) enzyme [2]. Diclofenac sodium (Dic-Na) is mainly indicated in the treatment of osteoarthritis, rheumatoid arthritis, and ankylosing spondylitis. Dic-K is claimed to dissolve faster and hence absorbed faster than the sodium salt and is recommended for the treatments that need short onset of action, mainly for its analgesic properties. Dic-K is also indicated for the treatment of primary dysmenorrheal and mild to moderate pain [3]. As with other NSAIDs, Dic is known to increase higher risk of gastrointestinal bleeding and cardiovascular side effects [3]. However, Dic has a relatively high therapeutic index in comparison to other NSAIDs [4].

The majority of pharmacokinetic data concerns Dic-Na. Literature reports indicate that Dic-Na and Dic-K are similar in terms of extent of oral absorption, patterns of distribution, metabolism, and elimination [5].

Dic is 100% absorbed after oral administration, compared to intravenous administration, based on urine recovery studies [6]. Dic shows linear pharmacokinetics. Absorption of Dic occurs throughout the intestinal tract; its rapid and complete absorption suggests a high permeability through the intestinal membrane [7]; however only about 60% of drug reaches the systemic circulation due to first pass metabolism [8]. This observation of high permeability throughout the intestinal tract is also supported by reports of rapid absorption of Dic from effervescent tablets and the high permeability of Dic in the colon after administration of the drug as a suppository [9, 10].

The apparent volume of distribution is 1.3 L·kg⁻¹ for Dic-K and 1.4 L·kg⁻¹ for Dic-Na [3, 11]. Circulating Dic is known to be greater than 99% bound to human serum protein, primarily to albumin [12]. However, this binding has been described as pharmacokinetically insignificant due to the rapid association-dissociation of Dic to albumin, such that the drug readily dissociates and permeates across the vascular membrane to the tissues [5]. The chemical name of Dic is 2-[(2,6-dichlorophenyl)amino]-benzeneacetic acid. Its structure is shown in Figure 1.

People who use nonsteroidal anti-inflammatory drugs (NSAIDs) (other than aspirin) may have a higher risk of having a heart attack or a stroke than people who do not use these medications. These events may happen without warning and may cause death. The risk may be higher for people who use NSAIDs for a long time [13].

Transdermal Drug Delivery offers many advantages such as reduced side effects, less frequent administration to produce the desired constant plasma concentration associated with improved patient compliance, elimination of the first-pass effect, sustained drug delivery, and interruption of treatment when necessary. NSAIDs are mostly used for the preparation of transdermal patches for treatment of pain or inflammation [14].

So, the aim of this study was to design a compound transdermal patch (biomembrane) containing Dic-K as an alternative way of drug delivery which can maintain a uniform plasma concentration and avoid the gastrointestinal action [15].

Polymers have played a key role in advancing drug delivery technology, providing the controlled release of therapeutic agents at constant rates over long periods, cyclic and adjustable release dosage of hydrophilic as well as hydrophobic drugs. The demand for biomaterials with features that provide controlled release of drugs is constant and necessary; a candidate for this application is a biopolymer, the NRL.

Poly(cis-1,4-isoprene), the major polymer from NRL obtained from Hevea brasiliensis, has interesting properties such as biocompatibility, high mechanical resistance, and capability to form a film. Mrue et al. (2014) were the first to use NRL membranes as a prosthesis of a cervical esophagus segment in dogs [16]. Sader et al. (2000) studied the behavior of NRL membrane as a partial substitute of dogs pericardium [17]. Herculano et al. (2009) have demonstrated the use of natural latex extracted from the rubber tree Hevea brasiliensis as a template for controlled release systems, showing promising results for future biomedical applications [18].

The rubber particles in the latex represent 30–45% of the total volume and 90% by dry weight of latex. These particles are generally spherical and ovoid but may be pear-shaped and vary considerably in size between 60 Å and 5-6 μm [19]. They consist mainly of poly(cis-1,4-isoprene), a polymer of high molecular weight: 500–2000 kDa [20]; the particles are coated with a thin layer of phospholipids and proteins. Negative charges present in this layer ensure the stability of the colloidal middle [21]. Lipids and phospholipids which form this layer consist in 1.4 to 3.2% by weight of rubber and contain 0.4 to 1.2% of neutral lipids [22].

Recently, the use of a polymer from NRL for TDDSs has been reported [23, 24]. NRL biomembrane is an important inductor of the healing process of wounds, being used in several medical applications like prosthetics and bone grafts [25]. Moreover, the treatment of diabetic and phlebopathic ulcers with this membrane leads to a faster healing process due to a vascular growth factor found in the latex and due to a physical blockage of the entrance of new infectious agents in the treated site [26]. To summarize, the NRL biomembrane has some interesting characteristics such as easy manipulation, low cost, the ability to stimulate natural angiogenesis and cellular adhesion, being a biocompatible material, and the ability to present high mechanical resistance [25].

In this study, novel Dic-K transdermal patches using NRL biomembrane are proposed for a sustained release of the drug, for further optimization of the local anti-inflammation action, avoiding some complications and possibly being a future application in medicine as surgical bandage for bone and tissue regeneration. Results showed that the NRL biomembrane can release Dic-K for up to 216 h, which is relevant for biomedical applications. In addition, the X-ray diffraction (XRD), Scanning Electron Microscopy (SEM), and Fourier Transform Infrared (FTIR) are also reported and showed that it is relevant for biomedical applications.

2. Experimental

In the present study the NRL used was commercial high-ammonia from BDF Rubber Latex Co. Ltd. (producer and distributor of concentrated rubber latex, Guarantã, Brazil) of about 60% dry rubber content, 4-5% weight of nonrubber constituents such as protein, lipids, carbohydrates, and sugar, and 35% of water [27]. After extraction, ammonia was used to keep the latex liquid. NRL was centrifuged at 8,000 g to reduce particularly the allergenic content. The cream fraction after centrifugation was redispersed to make the desired 60% of dry rubber content latex and then washed twice by centrifugation to reduce the cytotoxic protein content on the solution.

Dic-K (C₁₄H₁₀Cl₂KNO₂) was obtained in gel capsules, without excipients. Each of them contained 100 mg of ciprofloxacin in powder form. The capsules were purchased from Callithea Pharmaceutics Ltd., Brazil.

The NRL biomembranes loaded with Dic-K were prepared by mixing 3 mL of NRL and 3 mL of Dic-K solution (3 mg mL⁻¹); then, the mixture was poured onto glass plates with cm diameter and μm thickness. Membranes were maintained at room temperature (25°C) for two days until complete polymerization. For the release study, NRL biomembranes with Dic-K were placed in 300 mL of an aqueous solution in triplicate, from which aliquots were collected during an interval ranging from 0 to 250 hours. The Dic-K released into the solution was monitored by measuring the UV-vis spectra with a Bel Engineering SF200 ADV spectrophotometer, as Dic-K has a maximum absorption at 261 nm.

Figure 2 shows the absorbance intensity as a function of Dic-K concentration in solution. This calibration curve is important to make one relationship between absorbance and the Dic-K concentration. For this experiment several Dic-K concentrations from 1.2 10⁻³ to 3.1 10⁻²mg mL⁻¹ were made. After this, the absorbance was measured. Each drug concentration (point) was made in triplicate, where the estimated error was minor as 5%. The calibration curve shows straight line and obeys Lambert-Beers Law. The regression coefficient is 0.9761, intercept is , and slope is .

(a)

(b)

The biomembranes were characterized by X-ray powder diffraction (XRD), using a Siemens D5005 X-ray diffractometer and a graphite crystal as monochromator to select Cu Kα1 radiation (1.5406 Å), in a step of 0.02° s⁻¹. The surface morphology of the NRL membrane was observed using a Scanning Electron Microscopy (SEM) model Zeiss EVO 50 (20 KV) and a take-off angle of 35°.

The FTIR spectra of the pure Dic-K, pure NRL, and NRL + Dic-K were obtained to prove the chemical integrity of the drug in the polymer. The samples were measured directly by Attenuated Total Reflection (FTIR-ATR) method, which is an excellent method for obtaining infrared information for the powder sample surface. The biomembranes were characterized using a TENSOR 27 (Bruker, Germany) (4000–500 cm⁻¹) with a resolution of 4 cm⁻¹ with 64 scans.

3. Results and Discussion

Controlled release drug delivery systems are being developed to address many of the difficulties associated with traditional methods of administration. This system employs devices—such as polymer-based disks, rods, pellets, or microparticles—that encapsulate drug and release it at controlled rates for relatively long periods of time. Such systems offer several potential advantages over traditional methods of administration. First, drug release rates can be tailored to the needs of a specific application, for example, providing a constant rate of delivery or pulsatile release. Second, controlled release systems provide protection of drugs, especially proteins, which are otherwise rapidly destroyed by the body. Finally, controlled release systems can increase patient comfort and compliance by replacing frequent (e.g., daily) doses with infrequent (once per month or less) injection [28].

The aim of this study was to prepare the Dic-K transdermal delivery systems patch using NRL biomembrane. The structure of drug transdermal patches using NRL biomembrane is showed as in Figure 3.

As can be seen in Figure 4, the intensity of the absorbance due to the increase of drug concentration increases with time. A large drug release in solution during the first hours of the experiment can be noticed due to the portion of the drug present on the surface of the membranes. This is followed by a slower release which occurs due to the membrane water permeability. The functionalized membranes with Dic-K were able to release 20% of the drug in solution over a period of 216 hours (9 days); the failure to release larger amount of the drug could be associated, possibly, with the pore density on the membrane surface. When NRL membranes are made at room temperature (25°C), the surface pore density is lower as compared to NRL membranes made at lower temperatures [29].

Another factor that may have influenced the amount of drug released is the possibility of forming “pockets,” small spaces formed by drug crystals wrapped in NRL, with absence of pores, which may preclude a more efficient release. One strategy that can be used to increase the percentage of drug released is the production of membranes with greater pore density.

The experimental release studies were fitted using a biexponential function, , where is the amount of Dic-K in the NRL at a given time, , is the initial content of the drug, and and are constants, equal to and , respectively, and the characteristic times ( and ) are hours and hours. The slower release process is associated with the Dic-K diffusing slowly through the matrix. Thus, the drug is also found in the inner portion of the polymeric matrix. The Dic-K release depends mainly on the amount of encapsulated material (as a reservoir).

Figure 5 shows the FTIR spectra for pure Dic-K, pure NRL, and NRL + Dic-K. The FTIR of Dic-K showed that the principal IR bands at 1269 cm⁻¹ resulted from C-N stretching, and bands at 1501 cm⁻¹ and 1576 cm⁻¹ resulted from C=C stretching and C=O stretching of carboxylate group, respectively. The FTIR of NRL showed that the principal IR band at 836 cm⁻¹ corresponding to =CH out of plane bending resulted from cis-1,4 stretching, frequently used for identifying this molecule. Besides this, other characteristics absorption bands were also observed for the NRL, and the absorption band observed at 572 cm⁻¹ corresponds to the C-C deformation of NRL backbone, 1240 cm⁻¹ corresponding to O-P-O asymmetric stretching of phospholipids. The CH₂ symmetric stretching vibrations are observed at the region 2852–2925 cm⁻¹. The CH₃ asymmetric stretching is observed at 2961 cm⁻¹. These FTIR correlations for NRL are consistent with the earlier work [30]. Additionally, the FTIR spectrum of NRL + Dic-K showed the characteristic bands observed to Dic-K as by NRL, proving the stability of the drug after its incorporation into the biomembrane.

The XRD pattern for NRL membranes, powder Dic-K, and NRL membranes prepared with 3 mL solution 3 mg mL⁻¹ of Dic-K is shown in Figure 6, where we can see the amorphous nature of NRL biomembranes, as expected, with a broad peak at 19° in 2θ. In contrast, powder Dic-K exhibits an XRD pattern of a crystalline material with no amorphous component with sharp peaks appearing in 7, 8, 9, 11, 15, 22.5, and 27.20° according to Semalty et al. (2009) [31]. But when drug was incorporated into the polymer the intensities of peaks were decreased due to decreased crystallinity of the Dic-K [32]. The absence of crystallinity in the NRL membrane with Dic-K indicates that the Dic-K is molecularly dispersed or captive in the NRL microparticles.

Although NRL biomembranes with Dic-K show a broader spectrum DRX than the accented spectrum of pure NRL biomembranes, the FTIR spectrum shows that there is no chemical interaction between the NRL and Dic-K, since no new absorption peaks appeared.

Figure 7 shows the pure Dic-K and NRL membrane functionalized with Dic-K; note that a reasonable amount of drug is found on the membrane surface; this drug moiety on the surface is responsible for the fast release during the first hours.

(a)

(b)

In this study, the method proposed by Langer and Folkman was used [33], that is, to mix the drug with the polymer (latex) in a colloidal state, in order to create a biomembrane that works as a delivery system, without use of additives or organic solvents.

Various approaches have been used for delivery of drugs which include coating with design of time release dosage forms and the utilization of carriers (as chitosan, pectin, inulin, alginate, and guar gum).

Suksaeree et al. (2012) [24] developed one novel nicotine transdermal patch (NTP) using deproteinized natural rubber latex (DNRL) blended with hydroxypropylmethyl cellulose (HPMC) and dibutylphthalate (DBP).

Already Löbler et al. (2011) [34] developed a device based on polyhydroxyalkanoates (PHA) for implantation of a glaucoma drainage system. In this study, PHA based on hydroxybutyric acid was tested in terms of its potential suitability to manufacture mechanically stable tube components of drug delivery drainage systems and in terms of biocompatibility.

Goddard et al. (1990) [35] showed that the presence of an adsorbed layer of surface-active phospholipids on the surface of the mucus that covers the surface epithelium is suggested to protect the GI tissues by providing a hydrophobic layer between the epithelium and the luminal contents.

Herculano et al. (2010) [29] proposed a drug release system based on NRL for the sustained and controlled delivery of nitric oxide (NO). They concluded that the release time of nitric oxide in in vitro assays was very promising for the kinetics of release. In addition, Murbach et al. (2014) [25] proposed Transdermal Drug Delivery Systems (TDDSs) based on latex for the sustained and controlled delivery of ciprofloxacin (CIP), although the NRL were able to release 59% of ciprofloxacin.

Moreover, Maswadeh et al. (2004) [36] improved the efficiency of encapsulation of Dic-Na into uncoated and chitosan-coated liposomes. The encapsulation varied from 59 to 99%. By the methodology employed in this work, all drugs were retained in the membrane.

Wang et al. (2006) [37] prepared uniform-sized chitosan microspheres by membrane emulsification technique. Uniform chitosan microspheres were further used as a carrier of a protein drug bovine serum albumin (BSA). They observed that BSA loading efficiency was highest when pH value was 8.09, and it decreased with an increase of the cross-linking degree. The controlled release of drug/proteins/molecules/extracts is of interest for medical applications, since the dose can be adjusted according to the application envisaged.

Tariq et al. (2012) [38] observed that with lower polymer/Dic-K ratio the rate and extent of drug release were higher than from higher polymer/Dic-K ratio, due to its decreased porosity. Also, the release was retarded from carnauba wax matrix due its hydrophobicity. Ray et al. (2011) [39] also observed that the alginate/polymer ratio controls the release rate of the drug. The Dic-K release is decreased when the HPMC polymer concentration is increased.

4. Conclusions

We have prepared NRL biomembranes containing Dic-K as a model system for transdermal patches. The method of preparation is reproducible and the latex biomembrane is very stable. The XRD shows that the absence of crystallinity in the Dic-K/NRL biomembrane indicates that Dic-K is molecularly dispersed within the microparticles. FTIR indicated that Dic-K did not interact chemically with the biomembrane. Nevertheless, the NRL biomembrane was able to release 20% of the Dic-K in 9 days and could be fitted by a biexponential equation which can help to predict the release of the drug. The SEM photographs indicated that drug was present both inside and on the surface of the polymeric matrix, thus making it a promising material for drug release in in vivo applications. This study presented a novel transdermal patch specific drug delivery system containing Dic-K.

Conflict of Interests

The authors declare that there is no conflict of interests regarding the publication of this paper.

Acknowledgments

This work was supported by PROPe/UNESP, CNPq/PIBIC, FUNDUNESP (Process: 193/2011), and FAPESP (Process: 2011/17411-8).

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Copyright © 2015 Natan Roberto de Barros 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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