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Journal of Nanomaterials
Volume 2012 (2012), Article ID 372725, 11 pages
Chitosan Nanoparticles as a Percutaneous Drug Delivery System for Hydrocortisone
Drug Delivery and Novel Targeting Research Group, Faculty of Pharmacy, Universiti Kebangsaan Malaysia, Kuala Lumpur Campus, Jalan Raja Muda Abdul Aziz, 50300 Kuala Lumpur, Malaysia
Received 9 February 2012; Revised 23 March 2012; Accepted 26 March 2012
Academic Editor: Zhongkui Hong
Copyright © 2012 Haliza Katas 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.
Hydrocortisone (HC) has formed the mainstay for the management of atopic dermatitis. Hence, HC-loaded chitosan nanoparticles were prepared by ionic crosslinking of high, low molecular weight chitosan (HMwt, LMwt CS) and N-trimethyl chitosan (TMC) with tripolyphosphate. HC loading into CS nanoparticles was confirmed by FT-IR. The particle size of HC-loaded HMwt, LMwt, and TMC nanoparticles was increased from , and nm to , and nm, respectively, by increasing the pH of CS solution. Their respective zeta potential and entrapment efficiency (EE) were significantly decreased by increasing the pH of CS solution. The swelling ratios of HC loaded HMwt, LMwt, and TMC NPs were increased when the pH of incubating media (PBS) was increased. The same increasing trend was observed in particle size and EE of HC loaded as the CS concentration was increased. The HC loaded CS NPs were generally nonspherical. In-vitro permeation studies showed that HC was efficiently released from the CS NPs in QV cream while in aqueous cream CS NPs provided a sustained release for HC. Thus, it is anticipated that CS NPs are the promising delivery system for anti-inflammatory drugs.
Atopic dermatitis (AD) is a chronically relapsing, noncontagious and exudative dermatosis, associated with perivascular infiltration of IgE antibodies and CD4 lymphocytes . AD is more prevalent during infancy and childhood. It is evident that the intense itching, dry scaly skin, and chronic inflammation are the symptoms commonly associated with AD . Topical corticosteroids (TCs) have been recognized as the first-line pharmacological measure for the management of AD . TCs provoke their pharmacological action by immunosuppressive, vasoconstrictive, anti-inflammatory and anti-proliferative effects . In present study, hydrocortisone (HC) was used as the model drug due to its potential proficiency as topical agent since 1950s . However, the chronic use of TCs was also associated with topical as well as systemic adverse effects [6, 7]. However, in order to alleviate the TCs-associated deleterious effects and to rationalize the therapy, it is pertinent to use a suitable drug carrier system which can improve the rate and extent of drug permeation across the skin  and can improve the patient compliance.
Biodegradable polymeric nanoparticles (NPs) have attracted prominent interests in the past few decades as a novel drug carrier  due to its longer half life and greater drug entrapment efficiency . Furthermore, the polymeric NPs embraced the site-specific targeting and tend to permeate deeply into the skin substructures  that are attributed to its nanoscale particle size [12, 13]. Moreover, the biodegradable NPs can protect the drug from harsh environment  and prolong the duration of drug mucoadhesion at target tissues. Among all the recent materials used for polymeric NPs synthesis, chitosan (CS), a natural plentiful biopolymer obtained by chitin deacetylation has gained considerable interest. CS has promising biological implications such as nontoxic, biocompatible, biodegradable, bacteriostatic, and fungistatic [15, 16]. In addition, CS also has strong mucoadhesive and adherence ability to conjugate with negatively charged sialic acid on the physiological membranes [15, 17]. The main aim of the present study was to develop an occlusive and anti-inflammatory drug delivery system for the management of AD.
In current research, CS NPs were successfully coloaded with HC by ionic crosslinking of CS with tripolyphosphate (TPP). The successful loading of HC into CS NPs was confirmed by FT-IR analysis. The physical characteristics (particle size, zeta potential, and EE) of HC-loaded CS NPs prepared at various preparation conditions such as different molecular weight, type, and concentration of CS were investigated. The swelling characteristics of HMwt, LMwt, and TMC NPs were also studied at various pH of incubating media with a view to comprehend the release behavior of HC from CS NPs. Moreover, the in-vitro drug permeation study of HC from CS NPs either in aqueous or commercial QV cream was carried out at different pH of release media, using Franz diffusion cell. Incorporation of HC-loaded CS NPs into a commercial cream was carried out as to evaluate their versatility and simplicity in term of formulating them into various types of cream.
2. Materials and Methods
Low molecular weight (LMwt) CS (deacetylation degree (DD) 75–85% & 70 kDa), high molecular weight (HMwt) CS (DD 85%), hydrocortisone (98%), and cellulose dialysis tubing (molecular cut-off of 12 to 14 kDa) were purchased from Sigma-Aldrich (USA). N-trimethyl chitosan (TMC) was obtained from Heppe Medical GmbH (Germany). Penta-sodium tripolyphosphate (TPP), disodium hydrogen phosphate, and methanol (HPLC grade) were sourced from Merck kGaA (Germany). Ethanol (95%) was acquired from HmbG Chemicals (Selangor, Malaysia). Ego QV cream was purchased from Ego Pharmaceuticals PTY LTD (Malaysia). All other chemicals used were of analytical grade.
2.2. Preparation of CS NPs
CS NPs were prepared via ionic-gelation method developed by Calvo et al.  with some modification. CS solutions (2 mg/mL) were prepared by dissolving HMwt and LMwt, CS in glacial acetic acid (1% v/v) while, TMC was dissolved (2 mg/mL) in distilled water at room temperature. TPP solution (1 mg/mL) was prepared by dissolving it in distilled water. CS NPs were prepared spontaneously by adding 8 mL of TPP solution dropwise into 20 mL of CS solution, under a constant magnetic stirring at 700 rpm. Thereafter, CS NPs were centrifuged twice (28 000 rpm) by using Optima L-100 XP Ultracentrifuge (Beckman-Coulter, USA) with a rotor NV 70.1 Ti (Beckman-Coulter, USA) for 30 min and lyophilized at −40°C for 24 hrs.
2.3. Preparation of HC-Loaded CS NPs
For association of drug with CS NPs, the pure HC powder was dissolved into 30% ethanol with distilled water, to produce 1 mg/mL HC solution. Afterward, the HC solution was mixed with 0.2% w/v HMwt, LMwt or TMC CS at different pHs ranging from 3.0 to 7.0. To study the effect of CS concentrations, HC solution (1 mg/mL) was also mixed with various concentrations (0.1, 0.2, 0.3, 0.4, 0.5% w/v) of LMwt CS, and the mixtures were incubated for 15 min at room temperature. Then, 8 mL of TPP solution (1 mg/mL) was added dropwise into each reaction mixtures under magnetic stirring at 700 rpm, and HC-loaded CS NPs were simultaneously obtained. The nanoparticles were washed with distilled water and harvested by ultracentrifugation twice (Beckman-Coulter, USA) at 28 000 rpm and 10°C for 30 min. The resulting pellets were lyophilized at −40°C for 24 hrs further analysis.
2.4. Particle Size and Zeta Potential of CS NPs
Mean particle size, polydispersity index (PDI), and zeta potential of CS NPs were measured by ZS-90 Zetasizer (Malvern Instruments, UK) which was based on the Photon Correlation Spectroscopy (PCS). Samples were dispersed in distilled water prior to measurement. All measurements were performed in triplicate at 25°C with a detection angle of 90°, and results were reported as mean ± standard deviation.
2.5. Measurement of Entrapment Efficiency (EE%) of HC
EE of HC was determined by measuring the ultraviolet (U.V) absorption of the respective supernatants of HC-loaded CS NPs obtained after ultracentrifugation. The corresponding calibration curves were made by subjecting the supernatants of standard HC solutions (0.01, 0.02, 0.03, 0.04, 0.05, 0.06, 0.07, 0.08, 0.09, 0.1% w/v) under U.V/Vis spectrophotometer (U.V-1601; Shimadzu, Japan). The data obtained from U.V/Vis spectrophotometer and reverse phase HPLC (Waters 600 controller, In-line Degasser AF, 2707 Autosampler, 2998 Photodiode Array Detector, USA) were compared. HC was measured at 248 nm (λmax). EE of HC was calculated according to the following formula : where, is the total initial amount of HC and is the amount of free HC in the supernatant after ultracentrifugation. All measurements were performed in triplicate and results were reported as mean ± standard deviation.
2.6. Swelling Study
The dry samples of HC-loaded HMwt, LMwt, and TMC NPs (100 mg) were immersed in phosphate-buffered saline (PBS) at different pHs (2, 3, 4, 5, 6, 7, and 8) and at room temperature for 24 hrs until a swollen equilibrium was reached. The swollen samples were then collected by filtration, blotted with filter paper for the removal of the adsorbed water on the surface, and weighed immediately. The swelling ratio was calculated using the following formula : where, and are the weights of swollen and dry samples, respectively. The results were reported as mean ± standard deviations.
2.7. FT-IR Analysis
The FT-IR analysis of LMwt CS, pure HC, and HC-loaded LMW CS NPs were measured using a Fourier transform infrared spectrometer (Spectrum 100, Perkin Elmer, USA). Briefly, 2-3 mg of sample was mixed with 200–300 mg KBr and compressed to form transparent pellet. These pellets were scanned in transmission model. The FTIR spectra were recorded in the mid-IR region of 4000–400 cm−1 at resolution of 4 cm−1 with 32 coadded scans.
2.8. Morphological Analysis
Morphological characterization of HC-loaded CS NPs was carried out by using transmission electron microscopy (TEM). For TEM analysis, a drop of HC-loaded CS NPs dispersion was placed on the copper microgrid that was natively stained by phosphotungstic acid and evaporated at room temperature (°C) and then viewed under the electron microscope.
2.9. In-Vitro Drug Release Kinetics
In-vitro drug release profile of HC-loaded LMwt CS NPs (0.2% w/v CS & 0.1% TPP w/v) was carried out using a Franz diffusion cell. To study the rate and extent of HC release, two different formulations (QV cream and aqueous cream) were compounded, and their release behavior was examined at different pHs of release media.
2.9.1. Compounding of QV Cream Containing Pure HC or HC-Loaded CS NPs
For compounding 5 g of QV cream containing HC-loaded CS NPs, the commercial QV cream (Ego Pharmaceuticals PTY LTD, Malaysia) was melted at 50°C. Subsequently, the CS NPs suspension containing HC-loaded CS NPs equivalent to 25 mg of HC was blended into the molten cream and shaken until a homogenous dispersion was obtained. A 0.5% HC cream (control positive) was compounded by the same protocol as above which 25 mg of pure HC was added into 5 g of QV cream.
2.9.2. Compounding of Aqueous Cream Containing HC or HC-Loaded CS NPs
For preparing 5 g of aqueous cream containing 0.5% HC (control positive), the required amount of pure HC powder was dissolved in melted emulsifying ointment. The subsequent procedure was performed as specified in British pharmacopoeia (B.P, 2010). A 5 g of aqueous cream containing HC-loaded CS NPs was prepared by adding the CS NPs suspension equivalent to 25 mg of HC into the molten emulsifying ointment, and remaining procedure was performed as specified in B.P, 2010.
2.9.3. Drug Permeation Kinetic
A Franz diffusion cell was used to monitor the release profile of HC from both formulations (QV cream and aqueous cream) containing either HC-loaded CS NPs or pure HC 0.5% (control positive). The receptor phase was PBS (pH 7.4 & 4.0) containing 30% ethanol, thermostatically maintained at 37°C with circulating water. Dialysis membrane with molecular weight cut off of 12–14 kDa was used to separate receptor and donor compartments. Thereafter, 1 g of each formulation (QV cream and aqueous cream) containing CS NPs or pure HC was placed into the donor compartment. After an appropriate time interval, 1 mL of sample was taken from the receptor phase and supplemented with an equal volume of fresh receptor medium. Diffusion of HC from the donor compartment was estimated spectrophotometrically at 248 nm (λmax). The cumulative drug permeation percentage was determined by the following formula: where, is the amount of HC released from the CS NPs at time , and is the amount of HC initially loaded into the CS NPs.
2.10. Rheology Study
Rheology study was carried out to determine the apparent viscosity of QV cream and aqueous cream containing pure HC and HC-loaded CS NPs. The values of apparent viscosity of both the formulations were investigated before and after drug loading by using Bohlin Gemini Rheometer (U.K) with cone and plate system 1°/40 mm. The applied shear rate was ranged from 0.005 to 300 s−1 and each test was run for 2 min. All measurements were performed at 32°C with controlled shear rates. Each run was performed in triplicate, and the results were presented as mean ± standard deviation.
2.11. Statistical Analysis
All the data were presented as mean ± standard deviation (SD). Data were analyzed with either paired t-test or independent t-test and analysis of variance (One-way ANOVA) by using SPSS 19.0. For independent t-test, paired t-test, and ANOVA, showed significant difference between the tested groups.
3. Results and Discussions
3.1. Effects of pH of CS Solution on the Characteristics of CS NPs
Physical characteristics (particle size, zeta potential, and EE) of HC-loaded CS NPs prepared from HMwt, LMwt, and TMC CS (0.2% w/v CS & 0.1% TPP w/v) were investigated at various pH of CS solution to comprehend the effects of molecular weight and pH of CS on their physical characteristics.
3.1.1. Particle Size and Zeta Potential
The mean particle size of HC-loaded CS NPs was influenced by the molecular weight and type of CS as well as pH of CS solution. When comparing two different molecular weights, a larger particle size of HC-loaded CS NPs was obtained with HMwt CS at various pH of CS solutions. As summarized in Figure 1(a), the mean particle size of HC-loaded HMwt CS NPs was significantly varied (ANOVA post-hoc tukey, ) fromto nm with varying pH of CS solution from 3 to 7. The mean particle size of LMwt and TMC was also significantly increased by increasing the pH of CS solution from pH 3.0 to 7.0 (one-way ANOVA post hoc tukey ). However, the mean particle size between LMwt and TMC at the same pH was not significantly different. The increasing trend in particle size with increasing pH could be due to the formation of agglomeration as repulsive forces between CS NPs decreased with increasing the pH of CS solution . The reduction in repulsive forces between particles was contributed by the decrease in the protonation of the −NH2 groups on the contour of CS. This was also corroborated with the findings that a considerable decrease in the zeta potential of HMwt, LMwt, and TMC CS NPs was observed when the pH of CS solution was increased as shown in Figure 1(b). Data also demonstrated that the zeta potential of HMwt CS NPs was remarkably decreased from to mV by increasing the pH from 3 to 7. Similar to that, the zeta potential of LMwt CS and TMC NPs was reduced from to mV and to mV, respectively, when the pH of CS solution was increased. As previously mentioned, decrease in the zeta potential could be explained by the reduction in the protonation extent of −NH2 groups on the CS backbone . The mean value of the zeta potential of HC-loaded HMwt CS NPs was comparatively higher than the HC-loaded LMwt as well as TMC CS NPs at pH 4 and 6. This could be occurred as a higher molecular weight of CS contains higher density of positively charged groups on the CS chain that is responsible to increase the surface charge of CS NPs. In addition to that, during the crosslinking process, TPP ions were counteracted by the positively charged groups of HMwt CS which were quantitatively more than the phosphoric groups of TPP. However, less groups were available for LMwt CS and TMC to counter balance the negatively charged phosphoric groups of TPP . Furthermore, the derivatization of TMC may also decrease the groups on the backbone of TMC which rendered its low zeta potential. However, the differences among the mean value of the zeta potential of HC-loaded HMwt, LMwt CS, and TMC NPs were not statistically significant (one-way ANOVA post hoc tukey) at other pHs. Therefore, it could be concluded that different molecular weights and types of chitosan used in this study had no major impact on the surface charge of the NPs at pH other than pH 4 and 6.
3.1.2. EE of HC-Loaded HMwt, LMwt and TMC NPs
The EE of HC decreased significantly (one-way ANOVA, ) from 86 to 63% for HMwt CS NPs with increasing the pH of CS solution as shown in Figure 1(c). This was expected to be due to the decreased positively charged groups along the CS chain which therefore reduced the entanglement efficiency of CS with HC and decreased the EE. Besides, it was also observed that the EE of HC for HMwt, LMwt, and TMC NPs was not significantly different from each other over the range of pH used in the present study except at pH 7.0. These results were also corroborated with the previously reported findings. The findings showed that the EE of NPs prepared from different molecular weights of CS was not statistically different . Furthermore, Vila et al. proposed that the entanglement of drug with CS is highly irrespective of the CS molecular weights and predominantly dependent on the degree of CS deacetylation .
Besides, TMC NPs showed a decrease pattern in the mean value of HC EE from pH 3 to 7 as shown in Figure 1(c) which might be caused by the derivatization of amino groups (−NH2) with ethyl groups (−CH3CH2) along the CS-contour TMC.
3.2. Swelling Analysis
In order to investigate the effects of pH values on the physical behavior of HC-loaded HMwt, LMwt, and TMC NPs, a series of experiments were carried out. This study was performed at different pH of incubating media, ranging from pH 3 to 7 as to determine physical behavior of HC-loaded CS NPs at physiological and pathological environments. pH of intact skin ranges from 4.8 to nearly 6.0. This condition is mainly due to the presence of “acid mantle”. It acts as a natural skin barrier to the external environment. The wound site of AD patient would normally have a higher pH which ranging from neutral to alkaline due to the leakage of exudates and transudates (interstitial fluid) as well as disruption of “acid mantle". Thus, the knowledge regarding the impact of pH on the swelling ratio of various types of CS NPs is vital. It is known that the pKa value of CS is 6.5 . At pH 2, the swelling may be caused by the strong electrostatic repulsion between CS molecules as most of the amino groups of CS were in form, the molecules therefore had net positive charge. Thus, it is probably assumed that the extended swelling conformation of CS at low range of pH could be caused by both the hydration of groups as well as strong positive-positive charge repulsion among the groups along the contour of CS. Contrary to that, at higher pH values, probably 3.0–5.0, the amino groups in CS are less extensively protonated and the phosphoric groups of TPP are ionized; thus, the week electrostatic attractions produced between CS and TPP that restrain the swelling of CS NPs. Whereas, at further higher pH values (pH = 6–8), most of the amine groups of CS and phosphoric groups of TPP were in the −NH2 and form, respectively. As a result, the electrostatic attractions between CS and TPP became weakened which favor the swelling of CS NPs as shown in Figure 2. This pH-responsive characteristic of CS NPs can be used for the development of pH-responsive drug delivery systems.
3.3. Effect of CS Concentration on the Characteristics of CS NPs
3.3.1. Particle Size and Zeta Potential
For this and the following experiments, CS NPs were prepared by ionic crosslinking of LMwt CS with TPP. LMwt CS was chosen because it produced the desired size of nanoparticles with high EE. To investigate the effects of CS concentration on the physical characteristics of resultant CS NPs, various concentrations (0.1, 0.2, 0.3, 0.4, and 0.5%) of LMwt CS were prepared at pH 3.0 as to obtain HC-loaded CS NPs of nanosized and positively charged particle with the highest EE of HC. The data obtained (Table 1) revealed that the particle size of HC-loaded LMwt CS NPs was significantly increased () fromto nm, with increasing the CS concentration from 0.1% to 0.5% w/v. These results were in accordance with other reports [18, 26]. The increase in particle size was expected to be due to the presence of intermolecular hydrogen bonding (due to −OH groups) and intermolecular electrostatic repulsion (due to groups) which exist along the contour of CS . As the concentration of CS increases, more molecules of CS tend to entangle with each other and crosslink with counter ion (TPP) to form a single larger particle .
The zeta potential of HC-loaded CS NPs was also increased from to mV, when the CS concentration was increased from 0.1 to 0.3% w/v. However, the surface charge of CS NPs decreased suddenly when LMwt CS concentration was increased from 0.4% to 0.5% w/v as shown in Table 1. The increase in zeta potential from 0.1% to 0.3% w/v could be explained by the fact that the positive surface charge on CS NPs was mainly due to the residual amine groups of CS that were not interacted with the TPP ions. Thus, the zeta potential of NPs was increased linearly with increasing the CS concentration as more nonneutralised groups were present on the surface of NPs. However, in case of 0.4 and 0.5% w/v CS solutions, a slight decrease in surface charge was expected to be caused by the less H+ ions liberated from the acetic acid (CH3COO−H+) which had been fully used up to protonate the −NH2 groups on CS. Moreover, TPP solution donated some extent of the hydroxide ions, besides phosphoric ions . Therefore, when the liberated H+ ions from the acetic acid were not sufficient to neutralize the hydroxide ions of TPP, the ions would then tend to ionically crosslink with the protonated groups of CS  and thus reduced the zeta potential of CS NPs .
3.3.2. EE of HC-Loaded CS NPs
Table 1 also represents the effect of CS concentrations on the EE of HC-loaded CS NPs. It was found that the EE of HC-loaded CS NPs was slightly (not significantly, one-way ANOVA, ) improved fromto % with increasing the CS concentration from 0.1% to 0.3% w/v. The increase in EE may be due to the increase in groups on the particle surface. The increased groups would facilitate a stronger electrostatic entanglement between HC and CS  and thus promote the entrapment of HC. In contrary to that, the high EE of HC-loaded CS NPs for 0.4 to 0.5% w/v CS solutions was also observed despite their low zeta potential values. This could be explained by the fact that increase in CS concentration will increase the viscosity of the CS solution and prevent the HC molecules from leaving the nanomatrix. This therefore, enhances the EE . These results were also in accordance with some previously reported results [29, 31]. In this study, the results of EE obtained from both U.V/Vis-spectrophotometer and RP-HPLC were also compared as shown in Table 1. The results from both methods were similar and comparable.
3.4. FT-IR Analysis
FT-IR spectra of LMwt CS, HC, and HC-loaded LMwt CS NPs are presented in Figure 3. The results showed that the intense characteristic peaks of CS (Figure 3(a)) were appearing at 3430 cm−1 (−OH stretching), 2914 and 2882 cm−1 (−CH stretching), 1656, 1595 cm−1 (−NH2 stretching), 1324, 1256 cm−1 (C–N stretching), and 1076 cm−1 (C−O−C stretching). Figure 3(b) shows that the characteristics peaks of HC were appearing at 3435 cm−1 (−OH stretching), 2972, 2931 cm−1 (C−H stretching), and 1714 cm−1 (−C=O bending). For HC-loaded CS NPs (Figure 3(c)), the intense peaks of 3403 cm−1 was become broader, indicating that hydrogen bonding has been enhanced between the −OH bending groups of HC at 3435 cm−1 and CS at 3430 cm−1 . The amide I and amide II bending vibrations in CS spectra shifted from 1656 cm−1 and 1595 cm−1 to 1636 cm−1 and 1535 cm−1, respectively, which indicated that some interaction has occurred between groups of CS with TPP and HC within HC-loaded CS NPs spectra . The peak at 1324 cm−1 (C–N bending) in CS spectra shifted to 1307 cm−1 in HC-loaded CS NPs spectra (Figure 3(c)). This indicated interaction between −C=O group of HC and primary amide group of CS. The results may indicate that HC was successfully loaded into CS NPs.
3.5. Morphology of HC-Loaded CS NPs
Morphology of different HC-loaded CS NPs was investigated by using a TEM. The morphology of HC-loaded CS nanoparticles was found to be influenced by the molecular weight and type of chitosan used. LMwt CS produced a more spherical particle compared to HMwt CS as depicted by Figures 4(a) and 4(b), respectively. Contrary to that, TMC produced an elongated particle (Figure 4(c)). The mean particle size was observed to be decreased in the order of HMwt to LMwt CS NPs and TMC NPs. Morphology of LMwt CS NPs was also studied at different pH of CS solutions. It was observed that the LMwt HC-loaded CS NPs were spherical at a low pH (pH 3) as depicted from Figure 4(c) and more of irregular shapes at higher pHs (Figures 4(d) to 4(g)).
3.6. In-Vitro Drug Permeation of HC-Loaded LMW CS NPs
In-vitro cumulative drug permeation of 0.5% pure HC from aqueous and QV cream (served as positive controls) was investigated at different pHs of release media (4.0 and 7.4) as shown in Figures 5(a) and 5(b). The permeation of HC from HC-loaded CS NPs incorporated into both creams was also monitored as depicted by Figures 5(c) and 5(d). The results demonstrated that a higher pH of release media favored the permeation of HC from the positive controls as well as both creams containing HC-loaded CS NPs. A higher permeation of HC from formulations containing CS NPs at pH 7.4 could be due to the porosity of CS NPs which was influenced by the pH of release media. The conversion of positively charged amino groups () of CS into the unionized state at a higher pH value resulted in the reduction of CS crosslinking extent with the counterion (TPP). As a result, the swelling of CS NPs might be increased  at higher pH value (7.4) as explained in Section 3.2. The swelling of CS NPs would facilitate the penetration of release media into the inner part of the polymer matrix and convert the glassy polymer to rubbery form. This subsequently facilitated the diffusion of HC molecules out from the CS NPs. The permeation of HC from positive controls was also found to be higher at a higher pH of release media. The release behavior was expected to be influenced by the pKa and pH values of the drug and release media.
Furthermore, the permeation of HC was higher from both creams without the addition of CS NPs. However, this was not observed for HC-loaded CS NPs in QV cream which had comparable cumulative drug release to the positive control at pH 7.4. The data also explored that the HC permeation from QV cream for both control and containing CS NPs was more efficient than aqueous cream as shown in Figure 5. The reason for a higher release of HC from QV cream than the aqueous cream was expected to be associated to the hydrophobicity of the QV cream contents which contributed to the consistent diffusion and dissolution of HC molecules. Moreover, it was expected that a high HC release from QV cream was attributed to the presence of glycerol (CH2OH–CHOH–CH2OH) which is viscous and hygroscopic in nature . The hygroscopicity of glycerol could draw some release medium (PBS : Ethanol) and facilitated the penetration of medium inside the polymer matrix. This penetrated liquid could cause swelling of polymer matrix and led to the rapid diffusion and release of entrapped HC. Besides, a lower HC release from the aqueous cream could be due to the hydrophobic nature of HC which could not diffuse easily in the aqueous vehicle and perhaps due to the fact that the CS NPs remained intact in the aqueous vehicles . Despite low permeation of HC from the CS NPs in aqueous cream, it is anticipated that this formulation may serve as a sustained release delivery system for HC which thought to be necessary to reduce side effects of HC.
3.7. Rheological Characterization
To improve the release performance and stability of formulation, the rheological status is a very important physical parameter [37, 38]. The apparent viscosity of the QV cream and aqueous cream before and after adding HC-loaded CS NPs is presented in Figure 6(a). The data illustrated that the apparent viscosities (300 s−1) of QV cream and aqueous cream before adding NPs were higher than the apparent viscosities after adding NPs into the formulations. Moreover, the apparent viscosity of QV cream was higher (0.6762 Pa·s) than the aqueous cream (0.4147 Pa·s). QV cream had also shown a significant reduction in the apparent viscosity from 0.6762 Pa·s to 0.3847 Pa·s after adding NPs (, paired t-test). From the rheogram of QV cream and aqueous cream (Figures 6(b) and 6(c)), it was observed that both creams showed shear rate dependency behavior or pseudoplastic flow. The decrease in the apparent viscosity with increasing shear rate was expected to be due to the structural breakdown of bonds which held the particles together . This resulted in the formation of clusters or aggregates of droplets and finally led to the sharp reduction of the apparent viscosity .
In present research, the successful loading of HC into CS NPs via ionic-gelation method was confirmed by FT-IR analysis. It was demonstrated that the particle size, zeta potential, and EE of HC-loaded CS NPs were influenced by the molecular weight and type of CS as well as the concentration and pH of CS solution. The swelling behavior of HMwt, LMwt, and TMC NPs was also found to be modulated by the pH of incubating media. The resulted HC-loaded CS NPs were observed to be nonspherical and were influenced by the pH of CS solution. The findings suggested that the permeation of HC from the QV cream was more efficient than the aqueous cream and more profound at pH 7.4 than 4.0. Despite low permeation of HC from CS NPs in aqueous cream, this formulation was considered to be a good candidate as a sustained release drug delivery system for HC. These findings therefore suggested that HC-loaded CS NPs held a promising potential as a potential delivery system for anti-inflammatory moieties which could improve drug efficacy and reduce related side effects.
Conflict of Interests
The authors declare that they have no conflict of interests.
Authors gratefully acknowledge the Ministry of Higher Education, Malaysia and Universiti Kebangsaan, Malaysia, for funding and support this research project. This research was funded by Arus Perdana Grant (UKM-AP-TKP-09-2010) and Fundamental Research Grant Scheme (UKM-FARMASI-07-FRGS0015-2010).
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