Preparation and evaluation of polymeric beads composed of Chitosan–Gellan Gum–Gum Ghatti/-Gum Karaya polyelectrolyte complexes as polymeric carrier for enteric sustained delivery of Diclofenac sodium

An enteric coating is a multistep technique that involves deposition of a polymeric barrier over uncoated orally administered tablets to prevent them from dissolving or disintegrating in the stomach. However, as soon as the coating dissolves in the alkaline environment of intestine, the whole of the drug come in direct contact with gastric mucosa leading to irritation to distal parts of the gastrointestinal tract (GIT). Considering the above facts, there is clear need to develop a simple and effective enteric release formulation for gastric irritant drugs like Diclofenac sodium (DS). The goal of this study was to create enteric release polymeric polyelectrolyte complex (PEC) beads made up of cationic Chitosan (CH) and anionic Gellan Gum (GG) for sustained DS delivery to the intestine. The beads were prepared by extruding a solution of GG and Gum Ghatti (GT) or GG and Gum Karaya (GK) bearing DS into CH solution in 1% w/v acetic acid, with the help of a syringe fitted with a 18 gauge hypodermic needle. Instantly created spherical beads were dried in a hot air oven 60 °C overnight. In 0.1 M HCl and 6.8 pH phosphate buffer, the dried beads were tested for drug entrapment in the beads, in vitro swelling of beads and in vitro drug release studies from the beads. The % drug entrapment efficiencies (% DEE) of these PEC beads ranged from 59.54 ± 2.09 to 81.03 ± 4.22%. In 0.1 M HCl, the PEC beads swelled the least in vitro, but expanded significantly in phosphate buffer (pH 6.8). The in vitro release of Diclofenac sodium from different PEC beads in 0.1 M HCl was found to be less than 7.5 percent, whereas the release was sustained for 6 h in phosphate buffer (pH 6.8). From the experimental data, it may be concluded that these PEC beads can be useful as potential multiple-unit enteric release polymeric carrier systems for sustained delivery of gastric irritant drugs like Diclofenac sodium.

and anti-inflammatory medication. It's one of the most often given nonsteroidal anti-inflammatory medications on the planet (1). The symptomatic treatment of rheumatoid arthritis, osteoarthritis, and ankylosing spondylitis is indicated with DS. It's also used to treat acute musculoskeletal injuries, acute shoulder pain, postoperative pain, and dysmenorrhea in the short term. However, DS causes negative effects in roughly 20% of individuals, necessitating prescription discontinuation. Gastrointestinal hemorrhage and abnormally high liver enzymes are among the side effects [1,2].
Because of its short biological half-life (less than 2 h) and rapid clearance rate (mean elimination half-life 1.2-1.8 h), DS must be given often to maintain therapeutic concentrations, which may raise the risk of adverse effects. Modified-release dosage forms are essential to reduce stomach damage and make the Diclofenac dosing regimen safer and more convenient for patients. [3,4]. Most commonly used oral DS formulations available in the market are enteric-coated tablets. Enteric coating is a specialized technique which requires sophisticated instrumentation and thus very expensive. Another problem associated with enteric coated products is the fact that as soon as the coating dissolves, the whole of the drug come in direct contact with gastric mucosa leading to irritation to distal parts of the gastrointestinal tract (GIT) [5]. Given the foregoing, it is clear that a simple and effective enteric release formulation for DS is required, in which the drug is released in a pH 6.8 mixed phosphate buffer from an enteric polymer matrix in a sustained manner, with the negligible release in the stomach's acidic pH (0.1 M HCl, pH 1.2), reducing the risk of gastric irritation. In the quest to find out suitable polymer matrix, we have carried out some preparatory work in our laboratory exploring the potential of Gellan gum-Chitosan (GG-CH) polyelectrolyte complexes (PECs) beads as an enteric polymer matrix. The fact that PECs generated between a polycation and a polyanion have a high degree of ordering and crystal-like qualities, as well as compact structures, is why they were chosen as a polymeric carrier. Because these PEC beads will be composed of nontoxic biopolymers, they are expected to have a variety of unique physicochemical features of various polyelectrolytes [6,7]. Their formation may occur through one or more of the following mechanism: the coulombic attraction or other interactions such as hydrogen bonding, charge transfer interaction, dipole-dipole interaction, van der Waal's interaction and hydrophobic effect [8,9]. The formations of PECs avoid the use of chemical cross-linkers. Therefore, it is expected that these PECs are devoid of any possible toxicity and other undesirable effects of chemical cross-linkers [9]. PEC beads were prepared by dropping the GG (1% w/v in deionized water) into the acidic Chitosan solution (0.4% w/v in 1% w/v acetic acid). The beads were formed instantaneously. We have observed that dried GG-CH PEC beads swell very little in acidic pH, but swelled to a great extent in the intestinal environment (pH 6.8, mixed phosphate buffer). However, these beads were not able to curtail the release of DS in acidic dissolution medium with more than 10% DS was released in 120 min.
After this observation, in order to increase the strength of GG-CH PEC beads we have decided to combine the GG with anionic Gum Ghatti or Gum Karaya in varying concentration, keeping the GG concentration constant. Recently, numerous PECs made of various ionic polysaccharides have been extensively investigated for the use in various biomedical applications such as drug delivery, tissue engineering, enzyme immobilization, and biosensor. [6,10]. Considering the versatility of PECs, in the present study, an attempt was made to explore the utility of PECs comprised of a cationic polymer, Chitosan and anionic polymers such as Gum Ghatti and Gum Karaya in combination with Gellan Gum as release retarding enteric polymeric carrier for the oral enteric delivery of Diclofenac sodium.

Materials
Diclofenac sodium (DS) was obtained as gift sample from Unique Life Sciences, India. Deacetylated Gellan Gum (Gelzan ™ CM, DD =) was purchased from Sigma-Aldrich. Chitosan (Viscosity 25 cps; 0.4% solution in 1% acetic acid at 26 °C; degree of deacetylation = ≥ 75%) was obtained as gift sample from Central Institute of Fisheries Technology, Cochin, India. Gum Ghatti and Gum Karaya were purchased from Loba Chemie Pvt. Ltd., India. Double-distilled water was used throughout the study. All other reagents were of analytical grade.

Preparation of Gellan gum-Gum Ghatti and Gellan gum-Gum Karaya solutions
The solutions were made by dispersing the appropriate gum mixtures in deionized water and then heating the system to 90 °C with constant stirring until it became homogeneous.

Preparation of drug polymer mixture
After the preparation of homogenous aqueous polymeric dispersion, DS was added into it. It was observed that addition of DS into the almost semisolid polymeric dispersion, the dispersion become fluid at system room temperature (28 °C).

Preparation of Chitosan solution
The needed amount of Chitosan (0.4 percent w/v) was added to a 1 percent acetic acid solution in deionized water, and the combination was maintained at room temperature overnight for complete polymer ionization.

Preparation of PEC beads
A simple ionotropic gelation process was used to make the polymeric beads. Using a hypodermic syringe fitted with an 18 G needle, mixtures of homogeneous dispersions (10 ml) of anionic polymer-blends (Gellan Gum-Gum Ghatti or Gellan Gum-Gum Karaya) with or without drug were extruded into the gelation medium composed of Chitosan (0.4 percent w/v in 1 percent w/v acetic acid, volume 100 ml ( Table 1). The produced beads were then allowed to cure in the Chitosan solution for 30 min before being strained and thoroughly cleaned with deionized water until they were free of surface adherent drug.

Confirmation of PEC formation and drug-excipient interaction studies
The PEC generation and drug-excipient interactions were studied using Fourier transform spectroscopy (FTIR) and Differential Scanning Calorimetry. To eliminate the moisture, the samples were heated. In the DSC analysis, samples (5 mg) were placed in hermetically sealed crimped aluminium pans. Thermograms were taken at a rate of 5 °C per minute. A Differential Scanning Calorimeter was used to conduct these tests (Universal V4.5A TA Instrument). KBr pellets of approximately 1 mm diameter were produced for FTIR characterization by grinding 3-5 mg of samples with 100-150 mg of KBr in a pressure compression machine. The sample pellets were placed in an FTIR compartment, and spectrum scanning was performed using an FTIR at wavelengths ranging from 450 to 4000 cm −1 .

%Drug entrapment efficiency (%DEE) One hundred mg of Diclofenac sodium-containing PEC beads was taken and smashed with pestle and mortar
These beads were crushed and placed in flasks with 50 cc of phosphate buffer (pH 6.8). The flasks were shaken for 2 h with an orbital shaker to extract the DS entirely. After that, the solutions were filtered using Whatman ® filter paper (No. 40) and the filtrate was centrifuged to remove the polymeric debris using a tabletop centrifuge (Remi Motors, India). The polymeric debris was then rinsed twice with fresh solvent (water) to remove any DS that had clung to it. A UV-VIS spectrophotometer (Shimadzu 1800, Japan) was used to measure the DS content of the clear supernatant solution at a wavelength of 285 nm. The drug entrapment efficiencies (%) of various PEC beads containing Diclofenac sodium were calculated using this formula:

In vitro swelling studies
The swelling behavior of PEC beads was studied using 0.1 M HCl and phosphate buffer at pH 1.2 and 6.8, respectively. The pre-weighed amount (100 mg) of PEC beads was immersed in 0.1 M HCl (pH 1.2) for 2 h and in phosphate buffer (pH 6.8) for 6 h in vessels of dissolution apparatus USP paddle type (Electrolab TDP-08L, India) containing 900 ml respective medium. The swelling experiment was carried out at 37 °C with a paddle speed of 50 rpm. The swelling beads were removed on a regular basis and weighed after tissue paper was used to dry the surface. The weight change of these PEC beads was used to determine the swelling behavior of the beads. The following formula was used to calculate the swelling index [7,8]: Swelling index (%) = Weight of beads after swelling − Dry weight of beads Dry weight of beads × 100  7:196 In vitro drug release studies The in vitro release of DS from PEC beads was carried out for 6 h in a dissolution apparatus of the USP paddle type (Electrolab TDP-08L, India) containing 900 ml of phosphate buffer (pH 6.8) as dissolution medium, kept at 37 0.5 °C with a stirring speed of 50 rpm and maintained at 37 0.5 °C. Each time, 5 ml of aliquot was withdrawn at regular intervals. Every sample time, the volume of the dissolving medium was adjusted to 900 ml by replacing 5 ml of phosphate buffer (pH 6.8). The absorbance was measured using a UV-VIS spectrophotometer (Shimadzu 1800, Japan) at 285 nm after the aliquots were filtered and diluted appropriately.

Drug release kinetics
Drug release kinetics can be interpreted using a variety of kinetic models, including zero-order, first-order, and square root (Higuchi). A zero-order release refers to the release of a drug from a solid dosage form into an aqueous environment at a constant or nearly constant rate, regardless of the drug concentration in the dosage form at any given time.
Dosage formulations with zero-order release provide the most therapeutic benefit with the fewest negative effects. Many extended release formulations have a quick rise in drug release followed by a rapid drop in drug release. The first-order release is the most common sort of medication release. Such a dosage form may not maintain consistent medication concentration levels in the system. [9,10]. According to the Higuchi release equation, drug release is mostly driven by diffusion: where Q is the amount of medication released in time t and K is the equation's release constant. As shown in equation, the data were additionally treated to the Korsmeyer-Peppas power law (2). The Korsmeyer-Peppas model elucidates the type of drug release mechanism that occurs when swellable polymeric matrices are used. [11,12]: time t, K is the structural and geometric constant, and n, the release exponent, is calculated from the logarithmic release data using linear regression. In practice, regardless of the physical shape of the delivery device, the first 60% of a release curve must be used to estimate the slope obtained from equation [2]. The combined effect of diffusion and relaxation mechanisms for the release is shown by a good fit to the Korsmeyer-Peppas equation.

Statistical analysis
All data were analyzed and expressed as mean, standard deviation using MedCalc software, version 11.6.1.0. (S.D.). Each measurement was carried out three times (n = 3). Figure 1 shows the DSC thermograms of Chitosan, Gellan Gum, Gum Ghatti, and Gum Karaya, as well as dried blank Chitosan-Gellan Gum-Gum Ghatti beads and dried blank Chitosan-Gellan Gum-Gum Karaya beads. Chitosan's DSC thermogram revealed a large endothermic peak at around 71.01 °C, which corresponded to water vaporization (Fig. 1a). It also showed a large exothermic peak at 298.03 °C, which corresponded to sluggish Chitosan breakdown. A wide endothermic peak was observed in the DSC thermogram of pure Gellan Gum at 75 °C, which corresponded to the loss of water (Fig. 1b). There was also an exothermic peak at roughly 245 °C, indicating that the Gellan Gum was degrading. At 192.81 °C, 209.81 °C, and 332.25 °C, the DSC thermogram of pure Gum Ghatti revealed three endothermic peaks (Fig. 1c). The first endothermic peak can be attributed to water loss owing to vaporization, but the second and the third endothermic peak can be attributed to twostage decomposition, with the beginning and ultimate decomposition of the polymer occurring at 209.81 °C and 332.25 °C, respectively. The DSC thermogram of Gum Karaya revealed a sharp endothermic peak at 52.88 °C, which corresponded to water loss, and a broad endothermic peak at 316 °C, which corresponded to Gum Karaya degradation (Fig. 1d). The DSC thermogram of dried blank Chitosan-Gellan Gum-Gum Ghatti beads revealed an endothermic peak at 230 °C, which corresponded to polymeric-matrix degradation of Chitosan-Gellan Gum-Gum Ghatti beads. Ghatti (Fig. 1e). The DSC thermogram of dried blank Chitosan-Gellan Gum-Gum Karaya beads revealed a large endothermic peak at 219.29 °C, which corresponded to polymericmatrix degradation of Chitosan-Gellan Gum-Gum Karaya (Fig. 1f ).   (Fig. 2b). Gum Karaya's FTIR spectra revealed an absorption band at 3459.42 cm −1 relating to carbohydrate O-H stretching, a peak at 2929.09 cm −1 due to -CH2 asymmetric stretching, and a strong band at 1428.15 cm −1 due to -CH2 in-plane bending (Fig. 2c). Due to OH-outof-plane bending and NH-out-of-plane bending, it also showed maxima at 896.29 cm −1 and 780 cm −1 , respectively. The absorption band at 3434.20 cm −1 related to O-H stretching was demonstrated in the FTIR spectrum of dried blank Chitosan-Gellan Gum-Gum Ghatti beads (Fig. 2d). At 1730.14 cm −1 , a novel band was discovered, which was linked to the presence of -COO-groups in blank Chitosan-Gellan Gum-Gum Ghatti beads. Furthermore, bands at 1450.67 cm −1 and 1620.09 cm −1 in Gellan Gum (spectra not shown) could be caused to asymmetric and symmetric stretching of -COO-groups, which were found moved to lower wave-numbers, showing participation of -COO-groups in the coordination process. The absorption band at 3415.14 cm −1 in the FTIR spectra of dried blank Chitosan-Gellan Gum-Gum Karaya beads corresponded to O-H stretching (Fig. 2e). Similarly, in the FTIR spectra of dried blank Chitosan-Gellan Gum-Gum Karaya beads, a novel band at 1739.77 cm −1 was observed, which might be attributable to the presence of -COO-groups. Bands at 1447.59 cm −1 and 1620.35 cm −1 in Gellan Gum (spectra not shown) could be due to asymmetric and symmetric stretching of -COO-groups, which were shifted to lower wave-numbers, showing that -COO-groups were involved in the coordination process.

Preparation of Chitosan-Gellan Gum-Gum Ghatti and -Gum Karaya PEC beads containing DS
Extrusion of homogeneous dispersions of anionic polymerblends (Gellan Gum-Gum Ghatti or Gellan Gum-Gum Karaya) with DS into a gelation solution including chitosan (0.4 percent w/v, in 1 percent w/v acetic acid) resulted in the formation of spherical PEC beads. Table 1 shows the formula for these DS-containing Chitosan-Gellan Gum-Gum Ghatti and -Gum Karaya PEC beads. Figure 3 depicts photos of all of the Chitosan-Gellan Gum-Gum Ghatti/-Gum Karaya PEC beads containing DS.

Drug-excipient interaction analyses of Chitosan-Gellan Gum-Gum Ghatti and -Gum Karaya PEC beads containing DS
DSC analyses were used to assess Chitosan-Gellan Gum-Gum Ghatti and -Gum Karaya PEC beads containing DS to see if there was any drug-excipient interaction. Figure 4 shows the DSC thermograms of DS, Chitosan-Gellan Gum-Gum Ghatti PEC beads containing DS (P4), and Chitosan-Gellan Gum-Gum Karaya PEC beads containing Diclofenac sodium (P6). The melting endotherms of pure DS were seen on a DSC thermogram at 294.23 °C, which corresponded to its melting point (Fig. 4a). The endothermic peak was found at 227.20 °C in the DSC thermogram of Chitosan-Gellan Gum-Gum Ghatti PEC beads containing DS (P4), which could be due to PEC matrix breakdown (Fig. 4b). Because of the poor heat transport across the stiff PEC network, the melting peak of the DS was pushed to a higher temperature (317.06 °C). The DSC thermogram of Chitosan-Gellan Gum-Gum Karaya PEC beads containing DS (P6), on the other hand, did not display DS melting endotherm, indicating that the medication was uniformly dispersed in the PEC network of the beads. However, it showed the endothermic peak at 225.63 °C corresponding to the degradation of PEC matrix.

Drug entrapment efficiency
Chitosan-based PEC beads containing DS had drug entrapment efficiency (%) ranging from 59.54 2.09 to 81.03 4.22 percent (Table 1). In Chitosan-Gellan Gum-Gum Ghatti PEC beads containing DS, the greatest drug entrapment efficiency was recorded when the Gellan Gum to Gum Ghatti ratio was 1:1.5. (P3). When Gellan Gum to Gum Ghatti ratios of 1:1 (P2), 1:2 (P4), and 1.5:2.5 (P1) were used, the drug entrapment efficiencies were nearly comparable. The drug entrapment efficacy of Chitosan-Gellan Gum-Gum Karaya PEC beads containing DS enhanced when the concentration of Gum Karaya in the beads formula was increased (increased Gellan Gum to Gum Karaya ratio) (P5 and P6). Table 1 shows the in vitro swelling patterns of several Chitosan-based PEC beads containing DS after 2 h in 0.1 M HCl (pH 1.2) and 6 h in phosphate buffer (pH 6.8).

In vitro drug release
In vitro release of DS from different Chitosan-based PEC beads carrying DS was tested in phosphate buffer (pH 6.8) and revealed a consistent drug release profile over 6 h. Figure 5 depicts the in vitro drug release pattern. The release data was subjected to the best-fitting evaluation using zero-order, first-order, Higuchi, and Korsmeyer-Peppas models to evaluate the release mechanism and kinetics of drug release from Chitosanbased PEC beads carrying DS (Tables 2 and 3). PEC beads formulations P1 and P2 followed the Higuchi release pattern, as indicated by their r2 values, based on kinetic analysis data ( Table 2). According to the Higuchi model, cumulative drug release from a swelling hydrogel is proportional to the square root of time and is diffusion regulated. The conditions of pseudosteady state, constant diffusivity, rapid drug dissolution, and sinks are all assumed. The Higuchi model can be utilized if the release is primarily regulated by diffusion through water-filled pores in the matrix [9,10].

Discussion
Chitosan (deacetylated chitin) is a cationic natural polysaccharide and is regarded as generally recognized as safe (GRAS) material [13]. It is composed of α-1, 4-linked 2-amino-2-deoxy-α-d-glucose (N-acetyl glucosamine) [14]. Chitosan possesses excellent biocompatibility and biodegradability [15,16]. In drug delivery industry, chitosan has been exploited as a very promising biopolymer for use as carrier material for encapsulation of drugs [17,18]. Though Chitosan is a promising carrier material in the formulation of polymer-based oral drug delivery systems, it displays poor mechanical behavior and limited capability for controlling drug release due to its greater solubility in lower pH through promoting faster dissolution of in the stomach pH [19]. The pH-sensitivity of Chitosan is because of the protonation of free amino groups in response to external pH alterations [20]. Because Chitosan is a cationic polymer, it interacts with the negatively charged silicic acid residues in mucin, the glycoprotein that makes up mucus [21]. Chitosan's mucoadhesive properties are due to this interaction. Additionally, Chitosan's hydroxyl and amino groups may form hydrogen bonds with mucus [22]. During past few years, numerous Chitosan-based PECs with a number of anionic polymers are being researched as drug delivery carrier materials by several research groups [1,2,6,23]. In the present investigation, PEC beads were prepared using cationic Chitosan and anionic polymer-blends of Gellan Gum-Gum Ghatti or Gellan Gum-Gum Karaya for prolonged drug release. DS, a non-steroidal anti-inflammatory drug (NSAID) of about 1-2 h biological half-life [9,12,24], was investigated as model drug to assess the prolonged drug release properties. The proposed Chitosan-based PEC beads were expected to retard the release of encapsulated DS in alkaline pH (6.8) with minimal release in the acidic environment of stomach (pH 1.2).

Confirmation of Chitosan-Gellan Gum-Gum Ghatti and -Gum Karaya PEC beads formation
Because of the protonation of amino groups on the backbone, chitosan becomes a cationic polyelectrolyte in acidic medium, which is able to form PECs with negatively charged polyelectrolytes [23]. Considering the versatility of Chitosan-based PECs, in the present study, an attempt was made to prepare PEC beads comprised of cationic Chitosan and anionic polymers like Gum Karaya and Gum Ghatti in combination with Gellan Gum. During the preliminary trial experimentation, it was observed that PEC beads was formed using Chitosan along with Gum Ghatti-Gum Karaya blends were very weak; therefore, to provide mechanical strength to the beads, Gellan Gum was added into the system. For the confirmation of PEC formation, these formed spherical beads were characterized by DSC analyses and FTIR Spectroscopy analyses.

Chitosan-Gellan Gum-Gum Ghatti beads
The change(s) in appearance and temperature of the endothermic peak(s) in the DSC thermograms of dried blank Chitosan-Gellan Gum-Gum Ghatti beads compared to DSC thermograms of Chitosan, Gellan Gum and Gum Ghatti suggested the formation of new polymeric system of PEC between Cationic Chitosan and anionic Gellan Gum-Gum Ghatti.

Chitosan-Gellan Gum-Gum Karaya beads
Similarly, when comparing DSC thermograms of dried Chitosan-Gellan Gum-Gum Karaya beads to DSC thermograms of Chitosan, Gellan Gum, and Gum Karaya, the change(s) in appearance and temperature of the endothermic peak(s) in the DSC thermograms of dried Chitosan-Gellan Gum-Gum Karaya beads suggested the formation of PEC between cationic Chitosan and anionic Gellan Gum-Gum Karaya.

Fourier transform-infrared (FTIR) spectroscopy analyses Chitosan-Gellan Gum-Gum Ghatti beads
The FTIR spectrum of dried blank Chitosan-Gellan Gum-Gum Ghatti beads showed shifting of bands due to amide I of Chitosan to lower wave-number, whereas bands due to amide II and III were found disappeared in the FTIR spectrum of dried blank Chitosan-Gellan Gum-Gum Ghatti beads. This phenomena suggested PEC formation between cationic Chitosan and anionic polymers (here Gellan Gum-Gum Ghatti) in the dried blank Chitosan-Gellan Gum-Gum Ghatti beads.

FTIR spectrum of dried blank Chitosan-Gellan Gum-Gum Karaya beads
The band due to amide I of Chitosan was found to be shifted to a lower wave-number in the FTIR spectrum of dried blank Chitosan-Gellan Gum-Gum Karaya beads, whereas bands due to amide II and III were found to have vanished. These shifting and disappearances of bands suggested PEC formation between cationic Chitosan and anionic polymers (here Gellan Gum-Gum Karaya) in the dried blank beads.

Preparation of Chitosan-Gellan Gum-Gum Ghatti and -Gum Karaya PEC beads containing DS
During the preparation of beads, it was observed that when DS was added to the homogenous aqueous dispersion of anionic polymer(s), the viscosity of the system decreased and the system became fluid. This has resulted in easy extrusion of drug-polymer liquid mix through the hypodermic syringe even though high concentrations of anionic polymer were used. This could be explained as when Gellan gum/Gum Ghatti or Gellan gum /Gum Karaya were added to the deionized water, the polymer blend became fully hydrated due to application of heat (90 °C). This has resulted in their ionization (pH of aqueous dispersion was around 6.0) and because of this they carry a negative charge due to COO − . This led to increased charge density and thus increased electrostatic repulsion leading to thicker hydrogel. Diclofenac, 2-{2-[(2, 6-dichloro phenyl) amino] phenyl} acetic acid, is a weak acid having the pKa of 4.15 [24]. It is more soluble in alkaline pH than acidic pH. Its solubility at neutral pH is around 1.13 g/L (DS) [25]. In the present study, the pH of the aqueous dispersion of polymeric blends was 6.0, which is 2 pH units above the pKa of Diclofenac. Therefore, more of the drug is expected to be ionized as Diclofenac anions. This might have resulted in a decrease in degree of swelling due to the screening of electrostatic repulsion between charged groups on the polymer chains and, thus, a reduction in viscosity.

Drug-excipient interaction analyses of Chitosan-Gellan Gum-Gum Ghatti and -Gum Karaya PEC beads containing DS
No drug-polymer interaction was observed in both the chitosan-based PEC beads containing DS.

Drug entrapment efficiency
Highest drug entrapment efficiency (%) was found in case of P6 Chitosan-Gellan Gum-Gum Karaya PEC beads containing DS (81.03 ± 4.22%). This occurrence could be attributed to the increased viscosity of the drug-polymer mixture, which hindered drug migration towards the acidic Chitosan-based gelation medium during the formation of Chitosan-Gellan Gum-Gum Karaya PEC beads containing DS. The high drug entrapment efficiencies shown by the Chitosan-based PEC beads P3 and P6 could also be attributed to the stoichiometry related with the polyanion to polycation ratio, which might provide strong PEC structure that could entrap more amount of the drug.

In vitro swelling
Overall swelling index values of these Chitosan-based PEC beads were found low. This could be attributed to the formation of more compact structure due to PEC formation. The Chitosan-based PEC beads swelled to a significantly greater extent at pH 6.8. The fluctuation in the degree of ionization of functional groups controlled by the pH of the swelling media could explain the pH responsive swelling behavior of these PEC beads. An acid-base type PEC system is formed when the negatively charged -COO-groups of anionic polysaccharide(s) bond to the positively charged amino groups of Chitosan in an acidic solution. The amino groups are deionized when the pH rises, and the binding affinity between two polyelectrolyte molecules decreases, causing the PEC to inflate and disintegrate, modulating the release. [26]. This pH responsive swelling behavior should be advantageous for the PEC beads in sustained drug release applications, where inhibition of the drug release in the gastric environment (low pH values) is desired. It is possible to precisely tune medication release at the target spot by altering elements that produce PEC's swelling features [26].

In vitro drug release
The in vitro release of DS from various PEC bead formulations was found faster initially. Within the first hour, about 59-64% of the entrapped drug were found to be released from these Chitosan-based PEC beads containing DS. The ionic interactions between cationic Chitosan and anionic polymer-blends might have been reduced at pH 6.8 forming a loose network of the tested beads with increased porous surface, which could allow a large amount of dissolution medium to enter into the PEC matrix. This might have resulted in rapid dissociation of the PEC bead-matrix, leading to drug release with a burst effect. Another possible explanation of the initial burst drug release from these PEC beads within the first hour of drug release study could most likely be due to the presence of drug crystals onto bead surface. The drug crystals might be formed onto these PEC bead surfaces because of their migration along with water to the surface during drying [27]. At pH 6.8, because of higher solubility of entrapped drug (here DS) and suppressed ionization of polyelectrolytes within these formulated PEC beads, the in vitro drug release was found increased [1,18]. After the first hour, comparatively slower DS release was observed. About 94 to 97% of in vitro DS release was released from these Chitosan-based PEC beads at the end of 6 h. The release kinetics of the PEC bead formulations P3-P5 were zero-order. When a release rate is basically constant over time, the zero-order release is appropriate. The PEC bead formulation P6 followed first-order drug release pattern. In this case, an initial burst release effect was evidenced where the entrapped drug (here DS) was being rapidly dissolved and released from the bead-surface before the formation of gel-layer. After that the drug release rate of PEC bead formulation P6 was found decreased continually until the end of the drug release process. Since more than 60% of DS were released within the first hour, then values were calculated by Korsmeyer-Peppas model using drug release result up to first hour ( Table 3). The n value of different PEC bead formulations ranged between 0.97 and 0.99, indicating a super case-II transport mechanism. This type of release describes a transport in which the rate of dissolution medium uptake into the polymer matrix is substantially dictated by the rate of swelling and relaxation of the polymer chains, and in which the drug diffusion varies on both concentration and time.

Conclusions
In the present investigation, an attempt has been made to formulate and evaluate PEC beads containing DS, which were made of cationic Chitosan and anionic polymer-blends of Gellan Gum-Gum Ghatti or Gellan Gum-Gum Karaya. When the mixtures of homogenous dispersions of Gellan Gum-Gum Ghatti or Gellan Gum-Gum Karaya with DS were extruded into the gelation medium composed of Chitosan (0.4% w/v, in 1% w/v acetic acid), spherical PEC beads containing DS were formed instantaneously due to electrostatic interaction between oppositely charged polymers. The PEC formation between cationic and anionic polymers in these newly formulated Chitosan-based beads were suggested by DSC and FTIR analyses. No drug-polymer interaction was observed in these Chitosan-based PEC beads containing DS and this was suggested by the results of DSC analyses. The drug entrapment efficiencies (%) of these PEC beads containing DS ranged from 59.54 ± 2.09 to 81.03 ± 4.22%. Highest drug entrapment efficiency (%) was found in case of P6 Chitosan-Gellan Gum-Gum Karaya PEC beads containing DS (81.03 ± 4.22%). All these Chitosan-based PEC beads containing DS exhibited pH responsive swelling behavior when tested in vitro. The in vitro release of DS from various Chitosan-based PEC beads in phosphate buffer (pH 6.8) showed a sustained drug releasing profile over 6 h. From the experimental data, it is clear that these types of Chitosan-Gellan Gum-Gum Ghatti and -Gum Karaya PEC beads can be useful as potential multipleunit polymeric carrier systems for sustained delivery of gastric irritant drugs like Diclofenac sodium.