Abstract
The aim of the proposed research work was to develop a novel dual-compartment capsule (NDCC) with polymeric disc for gastroretentive dosage form, which will ultimately result in better solubility and bioavailability of Ofloxacin. Floating ring caps were formulated by using different natural polymers, separating ring band and swellable polymer located at the bottom of capsule. Formulated ring caps were assessed for coating thickness, In vitro buoyancy, In vitro drug release, release kinetics and stability studies. Coating attained by the capsule shell was found to be 0.0643 mm. Depending on nature of natural polymer used, most of the formulations showed buoyancy for more than 9 hrs. Developed formulation demonstrated considerably higher drug release up to 9 hrs. The developed formulation depicted the drug release according to Korsmeyer-Peppas model. There was not any significant change in performance characteristics of developed ring caps after subjecting them to stability studies. The present study suggests that the use of NDCC for oral delivery of Ofloxacin could be an alternative to improve its systemic availability which could be regulated by the floating approach. The designed dosage system can have futuristic applications over payloads which require stomach-specific delivery.
1. Introduction
Although tremendous advances have been made in drug delivery, considering costs and patient compliance, the oral route still remains the preferred route of administration for therapeutic agents. The environment of gastrointestinal tract significantly varies from stomach to large intestine (Table 1) [1]. This variation could serve a promising platform for the site-specific drug delivery of therapeutics.
The presence of a dosage form in the upper part of the gastrointestinal tract is important especially for drugs that are degraded or metabolized in the intestine or for drugs with local activity in the stomach [2, 3]. Likewise Singh and Kim [4] suggested that floating drug delivery is of particular interest for drugs which (a) have local action in the stomach, (b) are primarily absorbed in the stomach, (c) have poor solubility at an alkaline pH, (d) have a narrow window of absorption, and (e) are unstable in the intestinal or colonic environment. Gastrointestinal retention depends on many factors such as density and size of the dosage form, the fasting or fed condition of the patient, and the nature of the meal as well as posture [5–7]. Several gastroretentive formulation approaches such as high density [8], swelling [9], bioadhesive [10], magnetic [11], and floating [12] systems have been developed for enhanced gastroretention.
Local action in stomach is often used for curing gastric infection and better bioavailability of drugs which shows pH-dependent solubility. Ofloxacin is known to have pH-dependant solubility; it is more soluble in acidic pH and slightly soluble at neutral or alkaline pH conditions [13].
In the present investigation, for better solubility and bioavailability of ofloxacin an attempt was made to develop (gastroretentive drug delivery system) (GRDS) of ofloxacin by fabricating it in form of novel dual-compartment capsule (NDCC) for gastroretentive dosage form. The present study also reveals the effects of different polymers with varying concentration on drug release and floating property of prepared formulation.
The objective of the current investigation was to develop a novel dual-compartment capsule (NDCC) with polymeric disc for gastroretentive dosage form. The study was inspired from patented RingCap technology for enhanced drug release by augmentation of surface area approach and OROS push-pull osmotic system.
2. Materials and Methods
2.1. Materials
Ofloxacin was generously gifted by Ajanta Pharma, Mumbai, India. Carbopol 934P, Carbopol 940P, HPMC A15, HPMC E15, and HPMC K15 were procured from HI-MEDIA, Eudragit S100 was purchased from Loba Chemie, Mumbai, and Xanthan gum, Guar gum, Sodium Alginate, and Glycerol were procured from Merck Mumbai, India. All other chemicals and reagents used were of analytical grade.
2.2. Solubility of Ofloxacin in Different pH Conditions
In concordance with Chavanpatil et al. the study was conducted to depict the solubility of ofloxacin at varying pH conditions. Saturated solutions of ofloxacin were prepared by dispersing an excess amount of drug in the buffer with pH 1, 1.2, 3, 4.5, 5.8, 6.8, 7.2, and 7.5. The samples were subjected to orbital shaker (Remi Instrument Ltd. CIS-24) for 72 hours to aid maximum dissolution of the drug. After the incubation period, clear saturated solutions were obtained by filtration (0.45 μm Millipore filter paper), and the concentration of the drug was determined spectrophotometrically (UV-1800 PC Shimadzu, Japan) at the wavelength of 291 nm, after the appropriate dilution in the corresponding pH buffer. All solubilities were measured in triplicate at room temperature [14].
2.3. Preparation of Separating Polymeric Disc
It was prepared by making 4% HMPC K15 solution in water, followed by the addition of 5% glycerol which was preoptimized. Then the mixture was poured to petridish and was allowed to dry at 45°C for 12 hours. The dried film was cut uniformly to obtain circular discs with punch to have 1 mm thickness and diameter of 5.1 mm.
2.4. Preparation of Enteric Coated Gelatin Body
Enteric coated gelatin bodies were coated in a coating pan rotated at 50 rpm by spraying with a 10% solution of Eudragit S100 in acetone to get uniform coating over the surface of gelatin body. As Eudragit S100 is insoluble in gastric environment and buffer solutions with pH below 6, thus it provides protection to the prepared formulation [15, 16].
2.5. Fabrication of NDCC
In enteric coated gelatin body, initially 50 mg Carbopol 934P was placed at the base; over this circular separating polymeric disc of 1 mm thickness it was placed.
As shown in Table 2, prepared polymeric mixture of ofloxacin in combination with different polymers was placed over this barrier disc. Thereafter uncoated gelatin cap was joined over the enteric body of capsule to complete the design of NDCC. The polymers used with model drug are swellable and show hydration when they come in contact with acidic media of stomach. As the enteric gelatin body remains intact in acidic environment, it protects the formulation and allows the exposure only from open face. The disc pushes the drug polymeric mixture due to the swelling of Carbopol 934P on hydration which is located deep at the base. When the prepared capsule was assessed in vitro in simulated gastric fluid, it was observed that the cap quickly gets dissolved, but the enteric body still remains intact. Air trapped inside the intact capsule shell offers the buoyancy.
2.6. Evaluation of Coating Thickness
The prepared enteric coated capsules were evaluated for the thickness attained by Eudragit S100 coating. The thickness was measured by Digimatic caliper (Mitutoyo Corporation, Japan). Initially, the bare capsule shells were subjected for thickness measurement at three different positions. This was followed by final measurement at three different positions of the coated capsules. The changes in thickness indicate the final Eudragit coating acquired by the capsules. The evaluation was done in triplicate:
2.7. Preparation of Novel Floating Capsules
Enteric gelatin bodies were filled with 50 mg powder Carbopol 934 P at the bottom on which a separating polymeric disc was placed. The polymeric mixture of ofloxacin (Table 1) was filled over it with light compression, and finally the capsule body was sealed with hard gelatin cap. Figure 1 demonstrates the fabrication and drug release from prepared capsule.
2.8. In Vitro Buoyancy Studies
The in vitro buoyancy was determined by the floating time and was studied here by two methods. Firstly, by placing the formulated capsule in a beaker containing 100 mL of pH 1.2 HCl. The floating duration of all capsules was determined by visual observation (Figure 3). Secondly, the duration of buoyancy was determined in the USP dissolution Apparatus II in an acid environment. The time interval between the introduction of the capsule into the dissolution medium and its buoyancy to the top of dissolution medium was taken as the duration of buoyancy observed visually [17].
2.9. In Vitro Drug Release
The release of ofloxacin from the capsules was studied using USP type II (paddle) dissolution apparatus (EDT-08Lx, Electrolab, India). The dissolution media included 900 mL of phosphate buffer pH 1.2 (without pepsin) for entire study. The temperature was maintained at °C with paddle rotation speed of 50 rpm. Five milliliters of aliquot were withdrawn at predetermined time intervals of 0.5, 1, 2, 3, 4, 5, 6, 7, 8, and 9 hours and filtered. The medium was replenished with 5 mL of fresh buffer each time. Sample was analyzed by using UV spectrophotometer (UV-1800 PC) at the wavelength of 291 nm. The studies were performed in triplicate.
2.10. Stability Study
To assess the drug and formulation stability, stability studies were carried out according to ICH guidelines [18]. The drug polymer mixtures were filled in hard gelatin capsule size 00 and stored in air tight glass container. Samples were placed in stability chamber (Remi Programmable Environmental Test Chamber, India) under accelerated storage conditions (°C, RH) for 3 months. At the end of studies, samples were evaluated for appearance, in vitro drug release, and infrared spectroscopy (Shimadzu FT-IR Affinity 1700).
3. Results
3.1. Solubility of Ofloxacin at Different pH Range at Room Temperature
Solubility of Ofloxacin substantively decreased with an increase in a pH of media (Figure 2). It was found to be much higher in acidic pH compared to neutral and alkaline one. The solubility was found to be 41.2 mg/mL, 38.42 mg/mL, 29.57 mg/mL, 4.53 mg/mL, 3.79 mg/mL, 3.55 mg/mL, 3.39 mg/mL, and 3.24 mg/mL in media with pH 1, pH 1.2, pH 3, pH 4.5, pH 5.8, pH 6.8, pH 7.2, and pH 7.4, respectively.
(a)
(b)
(c)
3.2. Evaluation of Coating Thickness
The thickness measurement was performed to check uniform deposition of enteric coat on capsule shell body because it is necessary for the capsule to stay intact in acidic media for entire duration of residence in stomach. Initially, the bare capsule showed the thickness of mm, while after coating, the thickness appeared to be mm. Hence, the coating attained by the capsule shell was evaluated to be 0.0643 mm.
3.3. Buoyancy Time for the Various Formulations
Buoyancy of formulation depends on the type and concentration of excipients used. The formulations with HPMC grades showed better floating time while Carbopol 940 provided reduced floating property as negative effect on floating behavior of delivery system. This was previously suggested by Li et al. by moisture absorption isotherm of Carbopol 934P, HPMC K4M, and K100LV. The moisture gain for Carbopol 934P was significantly higher compared with HPMC K4M and K100LV (55% weight gain for Carbopol 934P versus ~33% for HPMC K4M and K100LV at RH of 95%). This results in a dramatic increase in the density of the GFDDS which, in turn, shows a corresponding decrease in the floating capacity of floating delivery devices. Xanthan gum depicted satisfactory floating property when used in higher concentration (60 mg).
Table 3 reveals that floating property of formulation containing Carbopol 940 and Xanthan gum increases with an increase in polymer concentration. The formulations FA1, FA2, FE1, FE2, FK1, FK2, FG1, FG2, and FX1 showed desired floating time for more than 9 hrs and seemed to be developed formulations.
3.4. In Vitro Drug Release
The sustained release polymers used in formulation on contact with aqueous media get hydrated forming gel matrix that entrapped the air responsible for buoyancy. This gel structure acts as a reservoir system for sustained drug release which is governed by slow diffusion through hydrated gel barrier [19, 20]. Figure 4 represents comparative release of ofloxacin from various formulations containing different sustained release polymers. The effective sustained release was obtained from all formulations. The formulations FG1, FG2, FK1, FK2, and FC1 showed much sustained drug release 35.01%, 52.01%, 31.66%, 54.52%, and 73.47%, respectively in 9 hours. The formulations FE1, FE2, FX1, and FC2 successfully sustained the drug release till 9 hours and depicted the drug release as 88.08%, 99.08%, 89.70%, and 98.65%, respectively. Formulations FA1, FA2, and FX2 showed the complete drug release within 6, 7, and 8 hours, respectively. The formulations FE2 and FA2 were able to sustain the drug release up to 9 hrs with considerably higher drug release 98.65% and 99.08% respectively, and proved to be developed batches.
3.5. Release Kinetics
Release behavior of prepared formulations was essentially studied by various mathematical models. Equation (2) describes zero order kinetics, where the drug release rate in a system is independent of its concentration [21] and ideal to describe coated dosage forms or membrane controlled dosage form [22]. The first-order Equation (3) describes the release from system where release rate is concentration dependent [23, 24]; it described the release of drugs from insoluble matrix as a square root of time-dependent process based on Fickian diffusion equation (4). Korsmeyer-Peppas equation (5) suggests the drug release from swellable polymer [25, 26]. The Hixson-Crowell cube root law Equation (5) describes the release from systems where there is a change in surface area and diameter of particles or tablets. where is the amount of drug released at time, is the initial amount of the drug in the formulation and , , , , and are the release rate constants for zero order, first-order, Higuchi model, Korsmeyer-Peppas model and Hixson-Crowell model, respectively. In (6), and are the amount of drug released at time and time 0 while is the diffusional coefficient.
The graphs for each formulation plotted according to the above equations were used to calculate correlation factors () and release exponents (). All formulations suggested the Korsmeyer-Peppas as best fit model except FE2 and FX2 where drug release was in concordance with Higuchi model. As the fabricated capsule is exposed only from single planar side where there is absence of edge effect on dissolution media, it would behave as polymeric film like geometry for drug delivery in diffusion study of different release exponent. The value indicates an anomalous drug transport. The release exponent of 0.5 can serve as an indication for diffusion controlled drug release [27, 28].
3.6. Stability Testing
Intention behind stability study of drug and polymer was to yield evidence regarding the quality of formulation which varies with time under the influence of various environmental factors such as temperature and humidity. The samples tested for drug release and infrared spectroscopy after the specified time proved that the formulation remained stable and absence of drug polymer interaction. The in vitro drug release from formulations subjected to stress condition was quite similar to that of initial formulations. Also, peaks observed in infrared spectroscopy of pure ofloxacin, stretching vibration 1750–1700 cm−1 and O–H stretching at 3050–3000 cm−1 remained unchanged in drug polymer mixture subjected to stability study indicating compatibility of ofloxacin with used polymers.
4. Discussion
4.1. Solubility Study of Ofloxacin at Different pH
The solubility of ofloxacin varied significantly with the change in pH of the media. In acidic media the solubility was found to be much higher compared to neutral and alkaline media. The solubility was highest (41.2 mg/mL) in pH 1 media which considerably decreased with increase in pH of solvent. The solubility drastically reduced to 29.4 mg/mL when the pH 3 media was used. Also, in neutral and alkaline media the solubility remained less than 4 mg/mL. The bioavailability of drug with higher dose gets affected by this pH dependent solubility condition.
4.2. Evaluation of Coating Thickness
The efficient thickness was achieved on capsule by Eudragit S100 coating. The thickness was sufficient to resist the deformation in acidic media for more than 2 hrs. From the results obtained by measurement of coating thickness, it can be assumed that there will not be any deformation of capsule body in vivo due to less deviation found in study; it indicates uniform deposition of enteric coat. It was also confirmed by visual observation of intactness of capsule shell in simulated gastric fluid (SGF) in vitro for more than 9 hrs.
4.3. In Vitro Buoyancy Studies
The formulations comprising of different grades of HPMC (FA1, FA2, FE1, FE2, FK1, and FK2) and Guar gum (FG1 and FG2) provided better floating property. These formulations showed floating time for more than 9 hrs. As Carbopol has negative effect on floating, formulations FC1 and FC2 failed to maintain the buoyancy for desired span. Formulations with Xanthan gum also exhibited the good buoyancy of capsules. However, the formulation FX2 failed to maintain buoyancy for 9 hrs where the concentration of Xanthan gum was lesser (40 mg).
4.4. In Vitro Drug Release
All the prepared formulations were able to control the release of the drug efficiently over the span of 9 hours, except the formulations FA1, FA2, and FX2 which showed total drug release within 7, 8, and 9 hours, respectively. Drug release was undesirably much sustained from formulations FG1, FG2, FK1, FK2, and FC1 which remained less than 50% till 9 hrs. The formulations comprising of HPMC polymers showed better results. However, FA1 and FA2 containing HPMC A failed to sustain the release up to 9 hrs. Formulations FE2 and FC2 produced the better results by providing maximum drug release in sustained manner till 9 hrs. Hence, it indicates that when HPMC E and Carbopol 940 were used in concentration of 40 mg, they exhibited desired outcome, as formulation FC2 has poor floating property which leads to unfavorable batch. Thus, FE2 turned out to be best developed formulation where 40 mg HPMC E15 was taken into account.
4.5. Drug Release Kinetics
All the formulations except FE2 and FX2 followed the Korsmeyer-Peppas model for drug release indicating the drug release from swellable polymers. The release exponent suggests the drug release mechanisms from polymeric controlled delivery systems. Korsmeyer-Peppas model was found to be best fitted with anomalous diffusion for all the formulations with values between 0.5 and 1 except for formulation FE2 and FX2, where they followed Higuchi model and diffusion-controlled drug release mechanism. The developed formulation FE2 depicted the drug release according to Korsmeyer-Peppas model as shown in Table 4.
4.6. Stability Studies
Stability study of formulations was investigated successfully indicating that formulation subjected to stress remained stable after 3 months. The drug release behavior remained similar to the unsubjected formulations. Also, FT-IR spectroscopy data reported no interaction between drug and polymers
5. Conclusion
The present study suggests that the use of NDCC for oral delivery of Ofloxacin could be an alternative to improve its systemic availability which could be regulated by the floating approach. As Ofloxacin efficiently absorbed from stomach, bioavailability of Ofloxacin could be considerably increased by gastroretentive NDCC. This study shows the release behavior and buoyancy of formulations by using various sustained release polymers. The release behavior of developed formulation FE2 showed release kinetics according to Korsmeyer-Peppas model indicating drug release from swellable polymer. Also, the floating behavior of formulations with Guar gum and HPMC grade polymers was satisfactory. The designed dosage system can have futuristic applications over payloads which require stomach-specific delivery.