*Corresponding Author:
A. I. Mohamed
Department of Pharmaceutics and Industrial Pharmacy, Faculty of Pharmacy, Cairo University, Egypt
E-mail: [email protected]
Date of Submission 14 August 2018
Date of Revision 20 November 2018
Date of Acceptance 27 February 2019
Indian J Pharm Sci 2019;81(2):354-364  

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pH-sensitive colon targeted microspheres loaded with dicyclomine hydrochloride were prepared using both emulsion crosslinking and solvent evaporation techniques to retard the release of dicyclomine in the upper gastrointestinal tract and to deliver it directly to colon. Several factors were used to evaluate the product, Eudragit RS100-coated chitosan-based microspheres, such as production yield, entrapment efficiency, and cumulative drug release. Three factorial central composite design was applied to examine the effect of the independent variables, concentrations of chitosan, Tween 80, and Eudragit RS100 on the physicochemical properties of the microspheres. Design-Expert software was used to design fifteen formulations during this study and the quadratic model was best fitted with the response data. In vitro dissolution studies proved that the release of dicyclomine hydrochloride from the microspheres fits Korsmeyer-Peppas model. F1, F10 and F12 exhibited best patterns of dicyclomine hydrochloride release with negligible drug release at pH 1.2, and maximum drug release at pH 7.4, indicating their ability to target the colon.


Colon-targeted drug delivery systems, dicyclomine HCl, chitosan, Eudragit RS100, response surface methodology, central composite design

Colon is located at the end of the digestive tract, between the cecum and the rectum. The key technique for producing successful oral colon-targeted drug delivery systems (OCTDDS) is to choose the right matrix carrier, which is capable of protecting the drug substance in the upper gastrointestinal tract (GIT), and directly carry the drug substance to the human ileocecum, to exert its therapeutic effect in the colon. OCTDDS can protect drug substances from being exposed to hydrolysis, and enzymatic degradation in the small intestine, due to the less intensity of digestive enzymes and less proteolytic activity of the colon mucosa, which produces higher systemic bioavailability of the drug. OCTDDS can also increase local concentration while reducing the systemic side effects that may occur due to the absorption of the drug in the upper GIT. Colon targeting can be achieved by using several approaches such as pH-triggered or timedependent drug delivery systems by using natural and synthetic polymers [1].

Natural polysaccharide biodegradable polymers such as chitosan has been the focus of a large number of research studies, which reported its potential uses in biomedical research applications. Chitosan is an abundant hetero-polysaccharide, which is structurally similar to glycosaminoglycans (main component of the bone extracellular matrix) and could be produced through deacetylation of chitin. It is mainly characterized for biocompatibility, biodegradability, cytocompatibility, and hemocompatibility [2]. Chitosan depolymerisation in the acidic medium is the main disadvantage for using it in formulating controlled drug delivery system. Chemical crosslinking of chitosan with glutaraldehyde could form a pH-sensitive matrix that swells and releases a drug through its porous structure [3].

Eudragit RS100 is a synthetic methacrylate copolymer, which consists of 4.5 to 6.8 % of quaternary ammonium groups. These groups make the surface of the polymer positive leading to interactions with specific cells on targeted tissues. This property increases the cellular uptake of the drug-polymer conjugates to allow controlled and prolonged delivery of any drug substances to specific target sites [4]. Eudragit RS100 was chosen as a coating material because it can withstand the acidic pH 1-3.5 in lower GIT and pH 5-6.5 in the small intestine but at alkaline pH 7 in the colon it starts to dissolve [5].

Model drug candidates to be formulated as colontargeted drug delivery systems include drug substances that treat colonic disorders such as ulcerative colitis, Crohn’s syndrome, and irritable bowel syndrome. Dicyclomine HCl, (1,1'-bicyclohexyl)-1-carboxylic acid, 2-(diethylamino)ethyl ester hydrochloride, is an antispasmodic and anticholinergic drug, classified as BCS class I drug whose peak plasma concentration is attained after 60-90 min of its oral administration. It acts by relaxing the spasms and cramps of smooth muscles of GIT, biliary tract, and ureter. It is widely used for the treatment of intestinal hypermotility and irritable bowel syndrome. The conventional dose of dicyclomine HCl for treating irritable bowel syndrome is 20 mg, 4 times daily, which might cause several adverse effects such as constipation, nausea, dizziness and tachyarrhythmia. The formulation of dicyclomine HCl as a colon-targeted drug delivery system would be beneficial due mainly to reduction of these systemic side effects, increasing patient compliance through reducing the frequency of dosing, and improving the therapeutic outcomes of dicyclomine HCl by localizing its effects at the colon, which is the main site of action for treating irritable bowel syndrome symptoms [6].

Response surface methodology (RSM) combined with central composite design (CCD) were used for designing this study, which can be defined as the collection of both statistical techniques and mathematical methods for building an experimental design model based on fitted polynomial equations with experimental data [7]. Different computer software applications are available for the processing of the experimental data such as Design-Expert® and Minitab, which can help in reducing the time needed for the experiment design, while increasing the accuracy of the design analysis [8].

The purpose of this study was to apply CCD for the formulation of polymeric microspheres prepared using crosslinked chitosan with or without Eudragit RS100 coating for colonic delivery of dicyclomine HCl. In vitro evaluation of the produced microspheres was conducted to identify the optimal formulation with the desired dicyclomine HCl release profile.

Materials and Methods

Dicyclomine HCl was received as a gift sample from Luna Co. for Industrial Investments, Egypt. Chitosan (medium molecular weight from crab shells) was purchased from Roth Company, Germany. Eudragit RS100 was received as a gift sample from Evonik Industries AG, Germany. Glutaraldehyde solution (50 %) was purchased from El Nasr Pharmaceutical Chemicals Co., Egypt. All chemical reagents used during analysis were of analytical grade.

Preparation of the controlled release chitosan microspheres:

Dicyclomine HCl-loaded polymeric microspheres were prepared by using chitosan as the matrix polymer, while using the single emulsion crosslinking technique. First, chitosan polymeric solutions were prepared with different concentrations by dissolving the accurately weighted chitosan powder in 100 ml of acetic acid (1 % v/v) on a magnetic stirrer. Second, 1 g of dicyclomine HCl was dispersed gradually in the chitosan aqueous solutions. Third, Tween 80 was used as a surfactant with varying ratios and it was homogenized in 150 ml of liquid paraffin. Finally, the emulsion that was formed by addition of the aqueous phase (dicyclomine HCl dissolved in chitosan solution) to the oil phase (liquid paraffin treated with Tween 80) while stirring at 800 rpm on a Branson mechanical stirrer model 250 for 3 h. Crosslinking was achieved by the addition of 0.5 ml of glutaraldehyde solution to the emulsion in the middle of the experiment. The produced dicyclomine HCl-loaded chitosan microspheres were collected by direct filtration, washed with petroleum ether and dried overnight at 40° in a hot air oven [9-12].

Eudragit RS100 coating of dicyclomine-loaded chitosan microspheres for pH-triggered delivery:

To formulate colon-targeted dicyclomine HCl-loaded microspheres, the previously prepared microspheres had to be protected with pH-sensitive polymer, Eudragit RS100 using the solvent evaporation technique. Eudragit RS solution was prepared by dissolving varying concentration of the synthetic polymer in 10 ml of ethyl alcohol. The microspheres were then transferred to a solution of Eudragit RS100 in ethanol and emulsification was achieved using 100 ml of liquid paraffin treated with Tween 80 (1 %) as the oil phase while stirring at 800 rpm for 2 h using a Branson mechanical stirrer to allow the evaporation of ethanol. The Eudragit RS100-coated dicyclomine HCl microspheres were obtained by direct filtration, washed by using petroleum ether and dried at 40° for 4 h in a hot air oven [9,13,14].

Experimental design model for the preparation of the polymeric microspheres:

The design of experiment by means of RSM depends on using the quantitative experimental data from previous screening experiments, in order to fit the Eqns. of regression models and to establish the optimum operating conditions. The optimization experiment of dicyclomine HCl microspheres were designed as a three-factorial CCD by using Design- Expert® software (version 11; Stat-Ease, USA). The three selected independent variables were; chitosan concentration (%), Tween 80 concentration (ml), and Eudragit RS100 concentration (mg), while the recorded responses were; particle size (μm), drug loading (%), entrapment efficiency (%), and the percent released dicyclomine HCl at different pH values (%). A total of 15 experiments as described were performed. CCD made it possible to distinguish the effect of each variable on the selected response based on the following formula: Y = b0+b1 X1+b2 X2+b3 X3+b2 X1 X2+b23 X2 X3+b13 X1 X3+b11 X12+b22 X22+b33 X32, where (Y) is the selected measured response, (bo) is the intercept, (b1-b33) are the linear regression coefficients of the factors, (X1, X2, X3) are the independent variables, (X1X2, X2X3, X1X3) are the interactions effects, and (X12, X22, X32) are the quadratic effects [15,16].

Morphology of chitosan-based microspheres using scanning electron microscopy (SEM):

For examining the morphology of the produced microspheres, their external surfaces were photographed by scanning electron microscope. The microspheres samples were fixed on an aluminium stub and then they were coated with gold by using gold sputter module under high vacuum. The samples were scanned by using Jeol scanning electron microscope, and the selected magnification was appropriate for describing the morphology details of the microspheres [17-19].

Evaluation of the prepared microspheres, drug loading, entrapment efficiency and yield:

Percent yield was determined by comparing the weight of the formed dicyclomine HCl microspheres against the total initial weight of the used polymer and dicyclomine HCl according to the following Eqn., % yield = (mass of dicyclomine HCl microspheres formed)/(total initial mass of dicyclomine HCl and the polymer)×100.

For determining loading capacity of prepared microspheres, 50 mg of microspheres were accurately weighed and crushed inside a glass mortar and dispersed in 100 ml of hydrochloric acid buffer (pH 1.2). The mixture was then stored in a thermostatic water bath in which it was shaken for 12 h at 37±0.5° at 50 strokes/min speed. The resulting suspension was filtered through 0.45 μm Millipore syringe filter and diluted appropriately. The concentration of dicyclomine HCl in each batch was estimated on a Shimadzu UV spectrophotometer at 213.90 nm with reference to the previously constructed calibration curves. Drug loading and entrapment efficiency were calculated using the Eqns., drug loading (%) = (mass of dicyclomine HCl in microspheres)/(total mass of microspheres)×100; entrapment efficiency (%) = (actual drug loading)/ (theoretical drug loading)×100.

Statistical analysis:

Statistical analysis of the data obtained was carried out using Design-Expert software. Independent variable effects were calculated by using analysis of variance (ANOVA). Variables having (p-value<0.05) were considered as statistically significant [9,20-22].

In vitro release from the prepared formulations:

In vitro drug release studies on the chitosan-based microspheres were performed using a USP type II dissolution paddle apparatus (DIS6000; Copley, UK) at a dissolution speed of 100 rpm, and the temperature was kept constant at 37±0.5°. Accurately weighed 50 mg of microspheres were placed in a cellulose tube dialysis bag (previously soaked for 12 h in deionized water) containing 5 ml of the release medium and then the dialysis bag was tied to the paddle. Five hundred millilitres of the buffer solutions at different pH values (pH 1.2, 6.8, and 7.4) were used as the dissolution mediums. Samples were taken after fixed time intervals: 0.5, 1, 2, 3, 4, 6, 7, 8, and 10 h from the beginning of dissolution. The withdrawn samples (5 ml) were then filtered through 0.45 μm Millipore syringe filters, and the concentration of dicyclomine HCl in each sample was determined on a Shimadzu UV spectrophotometer at 213.90 nm with reference to the previously constructed calibration curves. To maintain the sink conditions, 5 ml of fresh buffer solution was added to the medium immediately after sample collection. The UV spectroscopy measurements for each sample was performed in triplicate [23-26].

Dicyclomine HCl release kinetics from chitosan microspheres:

In vitro dicyclomine HCl release data were analysed by using DDsolver (an Add-in software for Microsoft Excel 2016), and they were fitted with different kinetic models: zero order model, first order model, Higuchi model, and Korsemeyer-Peppas model. R2, the coefficient of determination, was used for the purpose of fitting of dissolution profile with mathematical Eqns. [27-29].

Results and Discussion

The surface morphology of the prepared coated and uncoated microspheres was examined and imaged by SEM are illustrated in figure 1. The particle size of the microspheres ranged from 133.17 to 482.82 μm. The diameter of the microspheres increased with increasing the concentration of chitosan and with the application of the Eudragit Rs100 coating [9,14]. The CCD, a statistical approach for optimizing and planning experiments, was used. A total of 15 experiments were proposed for the three variables; chitosan concentration (X1), Tween 80 concentration (X2), and Eudragit RS100 concentration (X3). The recorded responses were particle size (Y1), drug loading (Y2), entrapment efficiency (Y3), yield production (Y4), % dicyclomine HCl released at pH 1.2 (Y5), at pH 6.8 (Y6), at pH 7.4 (Y7), and the cumulative percent released (Y8). The 15 runs with the investigated independent variables and the recorded responses are illustrated in Table 1. The Design-Expert® software provided the appropriate polynomial Eqns. involving the main factors after fitting the experimental data. Quadratic model was fitted with the response data. The effect of each of the tested factors (X1, X2, and X3) on each response was analysed, whereas the positive value indicated a synergistic effect on the response and the negative value suggested an antagonistic effect on it. The high values of the measured R-squared (R2>0.90) indicated the high correlation between observed and predicted experimental values in the resulting polynomial Eqns. [15,16,30].


Figure 1: SEM images of dicyclomine HCl-loaded microspheres (A) F11, uncoated, (B) F12, coated

F. N. Coded Values of Independent Variables Actual Values of Independent Variables Response Variables
X1 X2 X3 Chitosan Conc (%) Tween 80 Conc (ml) Eudragit RS100 Conc (mg) Y1 (μm) Y2 (%) Y3 (%) Y4 (%) Y5 (%) Y6 (%) Y7 (%) Y8 (%)
F1 0 0 1.414 1.5 0.5 250 421.77 26.92 74.05 83.03 0.35 20.62 61.79 82.76
F2 0 0 0 1.5 0.5 100 339.41 28.18 73.29 80.33 7.62 22.01 55.54 85.53
F3 1 1 -1 2 0.75 0 328.41 26.77 80.33 88.78 20.97 20.17 53.02 94.16
F4 1.414 0 0 2.25 0.5 100 465.47 24.85 83.25 91.67 2.15 18.05 60.79 80.99
F5 0 0 0 1.5 0.5 100 333.08 28.06 73.37 80.25 7.67 23.83 55.57 87.13
F6 0 0 0 1.5 0.5 100 340.24 28.21 73.48 79.9 7.49 21.98 55.43 84.9
F7 0 -1.414 0 1.5 0.15 100 310.19 27.65 72.03 76.75 8.9 26.95 53.25 89.1
F8 0 0 -1 1.5 0.5 0 256.23 29.02 72.55 76.43 24.75 21.34 49.09 95.18
F9 -1 0 0 1 0.5 100 201.02 36.56 69.47 74.35 11.7 28.9 57.36 97.88
F10 -1 1 1 1 0.75 200 299.07 32.65 71.85 77.46 0.85 25.41 64.49 90.75
F11 -1 -1 -1 1 0.25 0 133.17 34.9 69.8 75.05 26.23 27.9 44.87 98.91
F12 1 -1 1 2 0.25 200 482.82 24.84 79.5 87.05 0.65 20.75 60.19 81.59
F13 0 0 0 1.5 0.5 100 335.71 28.15 73.32 80.5 7.79 24.25 55.61 87.67
F14 0 1.414 0 1.5 0.85 100 372.31 28.94 75.25 85.39 6.57 20.36 55.96 82.89
F15 0 0 0 1.5 0.5 100 330.68 25.56 73.45 80.15 7.95 24.77 55.95 88.67

Table 1: Experimental Design Matrix of the Central Composite Design with Experimental Results

For estimating the significance of the fitted model (quadratic model) for the effect of the tested factors (X1, X2, and X3) on the measured responses (Y1- Y8), ANOVA was conducted and the results were summarized in Table 2. Descriptive statistics were used to assess the results ad p-value was measured. All the resulted p-values resulting from the applied model were less than (0.05), indicating the significance of quadratic model in predicting the measured responses (Y1-Y8) accurately.

Factors P-Value
Y1 Y2 Y3 Y4 Y5 Y6 Y7 Y8
Chitosan Conc (X1) <0.0001 0.0006 <0.0001 <0.0001 <0.0001 0.0014 0.0646 0.0002
Tween 80 Conc (X2) <0.0001 0.4843 0.0033 0.0003 0.0021 0.0121 0.0016 0.0250
Eudragit RS100 Conc (X3) <0.0001 0.3975 0.1527 0.0018 <0.0001 0.7101 <0.0001 0.0010
X1X2 0.0232 0.7440 0.6724 0.0069 0.0363 0.4620 0.0102 0.4672
X1X3 0.0007 0.5565 0.2201 0.0094 0.0827 0.1253 0.0002 0.0200
X2X3 0.0009 0.1244 0.5596 0.5080 0.0001 0.1222 0.1035 0.0087
X12 < 0.0001 0.0074 0.0008 0.0116 0.6332 0.1055 <0.0001 0.0061
X22 0.0838 0.9379 0.0855 0.0323 0.3852 0.5042 0.0024 0.4205
X32 0.0031 0.8407 0.4069 0.4664 <0.0001 0.0668 0.0004 0.0161
Model P value <0.0001 0.0069 <0.0001 <0.0001 <0.0001 0.0103 <0.0001 0.0011
Significant Significant Significant Significant Significant Significant Significant Significant

Table 2: Analysis of Variance (ANOVA) Results for Response (Y1-Y8)

According to the CCD matrix produced from the Design-Expert software, a total of 15 experiments, containing 4 factorial points, 6 axial points, and 5 central points, were conducted. Figures 2 to 4 depict the resulting three dimensional and contour response surface plots showing the effects of the tested factors (A, B and C) on the recorded responses, where the red colour represented the high values of the response and its values decrease by moving to blue colour on the plot [15].


Figure 2: 3D and contour response surface plots of the recorded response drug loading (Y2)
(A) Effects of chitosan concentration and Tween 80 concentration, (B) effects of chitosan concentration and Eudragit RS100 concentration, (C) effects of Eudragit RS100 concentration and Tween 80 concentration


Figure 3: 3D and contour response surface plots of the recorded response entrapment efficiency (Y3)
(A) Effects of chitosan concentration and Tween 80 concentration, (B) effects of chitosan concentration and Eudragit RS100 concentration, (C) effects of Eudragit RS100 concentration and Tween 80 concentration


Figure 4: 3D and contour response surface plots of the recorded response yield production (Y4)
(A) Effects of chitosan concentration and Tween 80 concentration, (B) effects of chitosan concentration and Eudragit RS100 concentration, (C) effects of Eudragit RS100 concentration and Tween 80 concentration

Increasing the chitosan concentration and Eudragit RS100 concentration led to significant increase in the particle size to reach 482.82 μm with 200 mg of Eudragit RS100 and using concentrated chitosan solution (2 %). There was a slight increase in the particle size with increasing the surfactant concentration, however the effect was still significant on the resulting microspheres particle size. The 3 factors had a p-value less than 0.0001, which indicated statistical significance [9,14,29].

Figure 2 illustrates that the actual drug loading (Y2) decreased significantly (p<0.0001) with increasing the concentration of chitosan, from 36 to 24 %. On the other hand, the actual drug loading increased with increasing the surfactant concentration, but it was not a significant synergistic effect [10-12]. The effects on the entrapment efficiency (Y3) are shown in figure 3. It was observed that the chitosan has a significant positive effect on the entrapment efficiency increasing it from (69 %) at the lowest chitosan concentration to (83 %) at the highest chitosan concentration. Tween 80 also had a mild positive effect on the entrapment efficiency of the formulated microspheres [10-12]. The value of the % production yield (Y4) ranged from 74 to 91 % as shown in figure 4. The effects of increasing chitosan, Eudragit RS100 and Tween 80 concentrations were proven to be significant on increasing the yield production of microspheres with a p-value less than 0.05 [9-12].

Responses (Y5) to (Y8) were calculated using the in vitro dissolution testing data of the prepared formulations. It is known that the release of dicyclomine HCl from the microspheres is related mainly to the matrix polymer and the coating materials. Microspheres coated with sufficient concentration of Eudragit RS100 were protected and showed negligible release at the acidic pH 1.2. It can be indicated that all the three tested variables had a significant negative effect on Y5 having a p value ≤0.0021 [9,12-14,29].

The release of dicyclomine HCl at a higher pH 6.8 ranged from 18 to 28 %. The release at pH 6.8 was significantly decreased with increasing the concentrations of both A (chitosan) B (Tween 80), which can be considered as significant in model terms. However, the mild negative effect of Eudragit RS100 was not significant [9,13,14,29].

From the generated quadratic model, Tween 80 and Eudragit RS100 had significant positive effects on the release at pH 7.4 (p-value less than 0.001). The main cause for increasing the drug release at pH 7.4 is that the microspheres with high Eudragit RS100 concentration were protected in the acidic pH, so the actual release of dicyclomine HCl content from the microspheres started to happen in the alkaline pH indicating a positive relation between Eudragit RS100 and response (Y7). The effect of chitosan was not significant on Y7 with p-value higher than 0.05 [9,13,14,29].

The cumulative % released of dicyclomine HCl from the prepared formulation was calculated as response (Y8). Chitosan, Tween 80, and Eudragit RS100 had antagonistic significant effect on the total amount of dicyclomine HCl released during the in vitro dissolution testing. The total release ranged from 81 to 98 %, while the p-value resulting from the ANOVA analysis of the 3 independent variables was less than 0.05 indicating their significant negative effect [9-11,13,14,29].

The in vitro release study of the Eudragit RS100- coated dicyclomine HCl-loaded chitosan microspheres were conducted in gastrointestinal simulating fluids at pH 1.2, 6.8 and 7.4 using dialysis bag attached to the paddle of USP type II dissolution apparatus at a speed 100 rpm, and the temperature at 37±0.5° for 10 h. Release profiles of various formulations performed at different pH values are shown in (figure 5).


Figure 5: In vitro release profiles of formulations F1 to F15
image F1; image F2; image F3; image F4; image F5; image F6; image F7; image F8; image F9; image F10; image F11; image F12; image F13; image F14; image F15

Uncoated formulations (F3, F8, and F11) released dicyclomine HCl from chitosan microspheres in the acidic medium pH 1.2 simulating the gastric fluid, from 20.97-26.23 % in the first 2 h depending on the chitosan concentration, which indicated the burst of the chitosan microspheres, because of the chitosan solubilisation in the acidic medium and the release of dicyclomine HCl. These patterns of drug release in acidic pH cannot be used for colon-targeted delivery systems, so it was necessary to use a coating polymer with a pH-dependent solubility with the threshold pH around 7.0±0.2 such as Eudragit RS100 [9-11].

Coating the chitosan microspheres with 100 mg of Eudragit RS100 in formulations (F2, F4, F5, F6, F7, F9, F13, F14, and F15) helped in protecting the microspheres in the acidic medium and the release of dicyclomine HCl in pH 1.2 ranged from 2.15- 8.9 % relying on the used chitosan concentration. Increasing the concentration of Eudragit RS100 to 200 mg reduced the release of dicyclomine HCl in acidic medium to a negligible amount from 0.65-0.85 % in formulations (F12 and F10). Excess amounts of Eudragit RS100 (250 mg) in coating microspheres in formula (F1) resulted in a minor release around 0.35 % of dicyclomine HCl [9,13,14,29].

In the following 2 h in the dissolution study at pH 6.8, the Eudragit RS100 coating started to dissolve exposing the chitosan microspheres to the medium, which resulted in the bursting of chitosan matrix and the release of dicyclomine HCl. The release profile of the prepared formulations ranged from 18.05-28.90 %. The dissolution continued in the alkaline medium for another 5 h at pH 7.4, where the release of dicyclomine HCl ranged from 44.87-64.49 % [9,13,14,29].

Release profile of dicyclomine HCl from microspheres could be summarized as, first, the Eudragit RS100 coating started to dissolve at pH 7.0±0.2. Second, the surrounding dissolution medium penetrated the exposed chitosan matrix. Finally, the chitosan microspheres did swell and released dicyclomine HCl from the chitosan gel that formed. Increasing the concentration of the core polymer led to increasing the distance the drug must pass to be released, in other words a reduction of the rate and extent of drug release. As well as increasing the thickness of the coating polymer would require a longer period for the coat to be dissolved, which means slower rate and reduced extent of drug release [9,29]. The criteria used for choosing the optimal formulations was based on the fact that colon targeting required minimal drug release in the stomach with maximum drug release in the colon. Formulations that fulfilled these criteria were F1, F10 and F12, with dicyclomine HCl release at pH 1.2, was 0.35, 0.85 and 0.65 %, respectively, while the total dicyclomine HCl release at pH 7.4 was 61.79, 64.49 and 60.19 %, respectively. So, these formulations could be chosen for further study as these exhibited minimum drug release in the acidic medium and maximum drug release in the alkaline medium which simulated the colon [9,13,14,29].

The in vitro dissolution data of the prepared microspheres was applied to different release models, zero-order model, first-order model, Higuchi model, Korsmeyer-Peppas model, and Hixson-Crowell model. Release kinetics results are summarized in Table 3. In accordance to value of R2 (determination coefficient) and Akaike Information Criterion (AIC) which is an estimator of the relative quality of statistical models for a given set of data, the In vitro release of Dicyclomine HCl from the prepared microspheres can be fitted with the Korsmeyer-Peppas Model (highest R2 value with the least AIC). That model allows for the determination of the mode of kinetics by the the calculation of (n) value which is the diffusion exponent [28,31,32].

Model F1 F2 F3 F4 F5 F6 F7 F8 F9 F10 F11 F12 F13 F14 F15
   Zero       R2       0.9455       0.9816       0.9746       0.952       0.9802       0.981       0.9768       0.9445       0.9653       0.9518       0.919       0.9491       0.9808       0.9787       0.981   
   Order       k0       7.853       8.696       10.26       7.525       8.937       8.634       9.53       10.822       10.701       8.918       11.447       7.756       9.031       8.294       9.155   
           AIC       78.777       66.0057       70.503       76.025       67.496       66.223       70.428       80.356       77.61       79.888       85.951       77.543       67.27       67.021       67.405   
   First       R2       0.8672       0.9227       0.9648       0.875       0.9203       0.9228       0.9246       0.9711       0.9159       0.8665       0.9708       0.8727       0.921       0.916       0.9203   
   Order       k1       0.11       0.132       0.183       0.104       0.138       0.131       0.154       0.208       0.19       0.133       0.237       0.108       0.14       0.122       0.143   
           AIC       89.467       83.2025       74.416       87.51       84.213       83.061       84.564       72.521       88.214       92.118       73.694       88.548       84.259       83.475       84.611   
Higuchi       R2       0.7294       0.8152       0.92       0.7343       0.8162       0.8137       0.8345       0.9403       0.8492       0.7496       0.9464       0.7339       0.8195       0.7988       0.8217   
   kH       19.631       22.165       26.816       18.822       22.791       21.998       24.441       28.495       27.604       22.418       30.268       19.402       23.05       21.053       23.379   
   AIC       98.009       93.6574       84.257       96.557       94.243       93.632       93.997       81.225       95.226       99.664       81.008       97.395       94.179       93.963       94.273   
Hixson-Crowell       R2       0.8952       0.9482       0.9849       0.9019       0.9468       0.948       0.9516       0.9879       0.9473       0.8984       0.9883       0.9001       0.9478       0.9414       0.9476   
   kHC       0.033       0.039       0.051       0.031       0.04       0.038       0.045       0.057       0.054       0.039       0.065       0.033       0.041       0.036       0.042   
   AIC       86.625       78.3942       64.228       84.596       79.363       78.315       79.236       62.11       82.607       88.846       62.768       85.643       79.297       79.168       79.572   
Korsmeyer-Peppas       R2       0.981       0.9858       0.9911       0.991       0.9837       0.9855       0.977       0.9854       0.9664       0.9737       0.9793       0.9836       0.9837       0.9878       0.983   
   kKP       3.493       6.865       14.932       3.144       7.228       6.772       9.053       18.627       11.897       4.904       21.445       3.493       7.455       5.768       7.667   
   n       1.399       1.117       0.813       1.429       1.105       1.12       1.026       0.728       0.947       1.295       0.686       1.393       1.095       1.18       1.088   
   AIC       68.145       64.9026       59.868       57.878       67.185       65.031       70.308       66.298       76.224       74.628       71.564       65.956       67.022       62.322          67.034      

Table 3: Release Kinetic Analyses of the Prepared Formulations (F1-F15)

Formulations (F3, F8, F9, and F11) had a diffusion exponent in the range of (0.5<n<1) indicating an anomalous non-Fickian transport, which is a hybrid of both diffusion and erosion-controlled release mechanisms. While the remaining formulations had a diffusion exponent value (n>1) indicating a super case II transport, that means the drug release is controlled by polymer swelling and erosion [27,31,32]. Cross-linked chitosan microspheres with a single layer of Eudragit RS100 were found to be an effective approach for targeting the colon by using emulsification-solvent evaporation techniques. RSM based on CCD was applied to assess and optimize the effects of different concentrations of chitosan, Tween 80, and Eudragit RS100 on the following responses, particle size, drug loading, entrapment efficiency, and the percent released of dicyclomine HCl at different pH values. A pH-dependent delivery of dicyclomine HCl was achieved by using cross-linked chitosan coated with Eudragit RS100. Optimal formulations F1, F10, and F12 had an insignificant dicyclomine HCl release in acidic dissolution medium simulating the stomach, with a significant release in alkaline dissolution medium simulating the colon; making it a promising technique for controlling irritable bowel syndrome symptoms. Further research can be conducted for in vivo evaluation of the optimal formulations on experimental animals.

Conflict of interest

The authors declared that they have no conflict of interest.