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Brazilian Journal of Pharmaceutical Sciences

On-line version ISSN 2175-9790

Braz. J. Pharm. Sci. vol.50 no.1 São Paulo Jan./Mar. 2014

https://doi.org/10.1590/S1984-82502011000100021 

Articles

Design and optimization of self-microemulsifying drug delivery system (SMEDDS) of felodipine for chronotherapeutic application

Khalid Akhter Ansari 1   *  

Kunal Pratap Pagar 1  

Shoeb Anwar 2  

Pradeep Ratilal Vavia 1  

1 Department of Pharmaceutical Sciences and Technology , Institute of Chemical Technology , Nathalal Parikh Marg , India ,

2 M.C.E Society’s Allana College of Pharmacy , Azam campus Pune -4000019, India


ABSTRACT

The objective of this research work was to design, develop and optimize the self micro-emulsifying drug delivery system (SMEDDS) of Felodipine (FL) filled in hard gelatine capsule coated with polymer in order to achieve rapid drug release after a desired time lag in the management of hypertension. Microemulsion is composed of a FL, Lauroglycol FCC, Transcutol P and Cremophor EL. The optimum surfactant to co-surfactant ratio was found to be 2:1. The resultant microemulsions have a particle size in the range of 65-85 nm and zeta potential value of -13.71 mV. FL release was adequately adjusted by using pH independent polymer i.e. ethyl cellulose along with dibutyl phthalate as plasticizer. Influence of formulation variables like viscosity of polymer, type of plasticizer and percent coating weight gain was investigated to characterize the time lag. The developed formulation of FL SMEDDS capsules coated with ethyl cellulose showed time lag of 5-7 h which is desirable for chronotherapeutic application.

Key words: Felodipine/self-microemulsifying delivery; Felodipine/chronotherapeutic application; Self-microemulsifying drug delivery system/development; Drugs/controlled release; Ethyl cellulose/drugs coated; Hypertension/treatment; Chronotherapeutics/hypertension treatment

RESUMO

O objetivo desse trabalho de pesquisa foi planejar, desenvolver e otimizar sistema de liberação de fármaco auto-microemulsificante(SMEDDS) de felodipino (FL) em cápsulas de gelatina dura revestidas com polímero, a fim de obter liberação rápida após tempo desejado no manejo da hipertensão. A microemulsão é composta de FL, lauroglilcol FCC, Transcutol P e Cremophor EL. A proporção ótima de tensoativo e de co-tensoativo foi de 2:1. As microemulsões resultantes têm tamanho de partícula na faixa de 65-85 nm com potencial zeta de -13,71 mV. A liberação de FL foi ajustada adequadamente, utilizando-se polímero independente de pH, como etilcelulose com ftalato de dibutila como plastificante. A influência das variáveis da formulação, como viscosidade do polímero, tipo de plastificante e ganho percentual de peso do revestimento foi investigada para caracterizar o intervalo de tempo de liberação. A formulação de cápsulas de FL SMEDDS revestidas com etilcelulose mostrou intervalo de tempo de liberação de 5 a 7 horas, o que é desejável para uma aplicação cronoterapêutica.

Palavras-Chave: Felodipino/liberação de fármaco auto-emulsificante; Felodipino/aplicação cronoterapêutica; Sistema de liberação de fármaco auto-emulsificante/desenvolvimento; Fármacos/liberação controlada; Etilcelulose/revestimento de fármacos; Hipertensão/tratamento; Cronoterapia/tratamento da hipertensão

INTRODUCTION

The key to the success of any drug delivery system depends upon the development of formulations that accomplish the therapeutic needs associated with particular pathological condition or disease state ( Lemmer, 1991 ). It has been observed that many physiological functions (e.g. blood pressure, hormonal levels) and pathophysiological disease states (e.g. hypertension, myocardial infarction, cancer, bronchial asthma and rheumatic disease) show a circadian pattern in their manifestations i.e. the disease symptoms do not occur evenly for the twenty-four hours of the day but undergo significant daily variations ( Lemmer, 2012 ; Francis et al., 2010 ). Therefore, the ideal remedy for such disease states should preferentially involve formulations that release drugs after a specified delay period (lag period-time of no drug release) after dosing by the patient ( Michael 2007 ). Thus, drug release from the formulation will be targeted to a specific period of the day when there is higher chances of clinical manifestation of the disease. Such a delivery approach is termed as chronotherapeutic (chronos-time) ( Mandal 2010 ; Youan, 2004 ).

Hypertension is a common chronic condition affecting up to 35% of human adults and showed circadian variation in manifestations ( Hermida 2007 ). Cardiovascular events happen more often in the morning, and ambulatory blood pressure (BP) exhibits a diurnal variation with increase in the morning (morning BP surge). The morning BP surge was reported to be associated with high risk of cardiac death, and ischemic and hemorrhagic stroke ( Nayak 2009 ; Cohen 1997 ; Behrens 1997 ). Blood pressure which arises notably just before waking up is usually responsible for these attacks and deaths ( Karavas 2006 ). Therefore, the chronotherapeutic drug delivery approach should be the ideal remedy for the treatment of hypertension in order to tackle the early morning mortality associated with such disease state.

Felodipine (FL), which is used in the proposed research, belongs to a category of dihydropyridine derivative. It is chemically described as ethylmethyl-4-(2,3-dichlorophenyl)-1,4-dihydro-2,6-dimethyl-3,5-pyridine-carboxylate [USP (United States Pharmacopoeia 29). FL is a calcium antagonist used commonly for its excellent antihypertension and antianginal effects ( Teberekidis 2007 ). FL is a poorly water soluble drug belonging to the category of BCS class II ( Yasir 2010 ). The bioavailability of FL is strongly limited by its high lipophilic character (aqueous solubility <0.5 mg/L) ( Abrahamsson 1994 ). Literature reports the chronotherapeutic drug delivery of FL using polyvinyl pirrolidone/hydroxypropyl methylcellulose (PVP/HPMC) nanodispersion which is responsible for bioavailability enhancement of FL ( Lemmer, 1991 ; Evangelos 2006 ) and also the extended release FL self-nanoemulsifying system ( Patil 2009 ). Thus, effective formulation design can be a useful approach which results in improved solubility, absorption and in total oral bioavailability of such drug candidates ( Pouton 2006 ). There are the several formulation approaches to increase the solubility of poorly water soluble drugs like cyclodextrin, nanosponges and nanoparticles (Khalid et al., 2011; Khalid et al., 2011; Satyen et al. 2010; Francesco 2011; Ridhurkar 2012 ; Nekkanti et al., 2011 ). However, Self-microemulsifying drug delivery systems (SMEDDS) are among the methods used to improve the oral bioavailability of poorly soluble drugs ( Hong et al., 2006 ). SMEDDS comprise isotropic mixtures of natural or synthetic oils with surfactants and co-surfactants. These systems spontaneously emulsify when exposed to gastrointestinal (GIT) fluids to form oil in water microemulsion with nanometric droplet size, in the range of 20–200 nm ( Basalious 2010 ). Furthermore, they can improve oral bioavailability through enhancing permeation across the intestinal membrane, solubilization, droplet size reduction and improvement of drug dissolution ( Wang 2010 ; Wasan 2009 ). Self-microemulsifying system of FL would be an efficient, convenient and more patient compliant approach as SMEDDS can be filled in hard gelatine capsules due to their anhydrous nature enabling its administration as unit dosage form.

In the present work, FL SMEDDS was prepared which was subsequently used in chrono-capsules formulation. The objectives of the present study were, first, to develop a SMEDDS of FL to increase the bioavailability and to formulate time delayed chronotherapeutic capsule formulation of FL using pH independent polymer as a functional coating material. Different viscosity grades of ethyl cellulose along with hydrophobic plasticizer will be used as functional coating material. Such a hydrophobic coating layer will act as an alarm clock releasing the drug amount from the active core at the predictable time.

MATERIAL AND METHODS

Raw Material

Felodipine (FL) was procured from Nivedita Chemicals Pvt. Ltd. (Mumbai, India). Cremophor EL (CEL) (BASF, Mumbai, India), Transcutol P (TP) (BASF, Mumbai, India), Lauroglycol FCC (LFCC) (Colorcon Asia Pvt. Ltd., Mumbai, India), Ethyl cellulose (EC N7, EC N10, EC N22) (Colorcon Asia Pvt. Ltd., Mumbai, India) and Hard gelatin capsules (Associated Capsules, Mumbai, India) were obtained as gift samples. All other chemicals and reagents were of analytical grade. HPLC grade solvents were used in case of HPLC analysis. Milli-Q water was used in all experiments.

Methods

Solubility studies

Solubility of FL in various components (oils, surfactants and co-surfactants) was determined. Briefly, 500 mg of each of the selected vehicle were added in vial containing an excess of FL (1 gram). After sealing the vial, the mixtures were shaken at 30 ± 0.5 ºC for 48 h with thermostatically controlled water bath shaker (Remi, India). After 48 h, the mixtures were centrifuged at 3000 rpm for 5 min (Research Compufuge, Remi, India) and an excess insoluble FL was discarded by filtration using a membrane filter (0.45 µm, 13 mm, Whatman, USA). Concentration of FL in each component was quantified by HPLC. The analysis was carried out on a Waters 717 autosampler chromatographic system (Waters, India) equipped with waters 515 HPLC pump and waters 2487 dual wavelength detector using Lichrosphere C-18 Merck (250 mm × 4.6 mm; 5 µm) (Thermoelectron, USA) at a flow rate of 1.0 mL/min [Mobile Phase- buffer: acetonitrile: methanol (40:40:20] (USP 29). The analysis was carried out at 254 nm. The linearity of FL was accomplished in the range of 240-360 µg/mL. The HPLC chromatogram of drug showed very sharp peak at retention time of 20.288 min ( Figure 1 ). Each experiment was carried out in triplicate. The components showing maximum solubilization were selected for further studies.

FIGURE 1 – HPLC Chromatogram of standard drug. 

Selection of surfactant to co-surfactant ratio

Ratio of surfactant to co-surfactant is an important consideration for formulating microemulsion based system. Cremophor EL (CEL) as a surfactant and Transcutol P (TP) as a co-surfactant were used during the study. Turbidimetric method was used to assess relative efficacy of the co-surfactant to improve the microemulsification ability of the surfactants and to select best one from the large pool of co-surfactants available for peroral delivery (Date 2007). CEL: TP (2:1 v/v) was mixed with oil and the mixture was homogenized with the aid of the gentle heat (40-50 °C). The isotropic mixture was accurately weighed and diluted to 50 mL with water to yield fine emulsion. The ease of formation of emulsion was observed by noting the number of volumetric flask inversions required to give uniform emulsion. The resulting emulsions were observed visually for the relative turbidity.

Preparation of SMEDDS

SMEDDS containing FL was prepared by mixing oil phase with surfactant and co-surfactant using vortex mixer. Oil Phase i.e. lauroglycol FCC (LFCC) was accurately weighed and transferred into microemulsion tube followed by addition of surfactant (CEL) and co-surfactant (TP) in order to prepare blank SMEDDS. Concentration of the three components totalled to 100%. Drug loaded SMEDDS were prepared by keeping drug content constant as 0.1 mg/g of the prepared SMEDDS. The composition of FL SMEDDS formulation is given in Table I .

TABLE I Composition of felodipine SMEDDS formulation 

Components Amount (mg)
Felodipine 10
Lauroglycol FCC 40
Cremophor EL: Transcutol P (2:1 v/v) 60

Self emulsification and flowability

Evaluation of self-emulsifying properties of SMEDDS formulation was carried out by visual assessment as previously reported ( Khoo 1998 ). Briefly, different compositions having oil and different surfactant to co-surfactant ratios of were categorized on apparent clarity of the resultant emulsion. Visual assessment was performed by drop wise addition of the pre-concentrate (SMEDDS) into 250 mL water. This was performed in a glass beaker at room temperature and the contents were gently stirred magnetically at approximately 100 rpm. The compositions were categorized based on the appearance of resultant emulsion as clear (transparent with bluish tinge) and non-clear (turbid). Compositions were also evaluated for flowability by visual observation as the final aim was to fill the formulation into Hard Gelatin Capsules (HGCs).

Construction of Pseudo ternary phase diagram

Pseudo-ternary phase diagrams of oil, surfactant: co-surfactant and water were developed using water titration method. Mixtures of oil and surfactant to co-surfactant at certain weight ratios were diluted with water in a drop wise manner. For each phase diagrams at a specific ratio of surfactant to co-surfactant (S/CoS), 2:1, 1.5:1, 1:1 and 0.5:1 (w/w), transparent and homogenous mixture of oil and S/CoS were formed by application of vortexing for 5 min. Each mixture was further titrated with water and visually observed for phase clarity and flowability. The concentration of water at which turbidity-to-transparency and transparency-to-turbidity transitions occurred were derived from the weight measurements. These values were then used to determine the boundaries of the microemulsion domain corresponding to the chosen value of oils, as well as the S/CoS mixing ratio. Phase diagrams were then constructed using Tri plot v1-4 software.

Evaluation of FL loaded SMEDDS

Optimized SMEDDS formulations were evaluated for robustness to dilution, globule size, in-vitro dissolution profile and dispersion time and precipitation.

  • Robustness to dilution

Robustness of FL SMEDDS to dilution was studied by diluting it to 50, 100 and 1000 times with various dissolution media viz. water, buffer pH 1.2, buffer pH 4.5 and buffer pH 6.8. The diluted microemulsions were stored for 12 h and observed for any signs of phase separation or drug precipitation.

  • Emulsion droplet size analysis of FL SMEDDS

The size of FL SMEDDS formulations were determined by Delsa™Nano C (Beckman Coulter, USA). SMEDDS formulation (100 mg) was diluted with water to 500 ml in a beaker and gently mixed using a glass rod. The resultant emulsion was further subjected to droplet size analysis using DelsaTM Nano.

  • Determination of zeta potential

Zeta potential was measured by using DelsaTM Nano C (Beckman Coulter, USA). SMEDDS formulation (100 mg) was diluted with water to 500 mL in a beaker and analyzed for zeta potential measuring instrument. All measurements were carried out at 25 °C

  • Dispersion time and precipitation assessment

Dispersion time is defined as the time taken for lipid or surfactant based system to disperse in the dispersion medium ( Khoo 1998 ). In case of SMEDDS, it determines the time taken for pre-concentrate to form a well-dispersed, clear microemulsion. Dispersion time was determined using USP XXIV type 2 apparatus. Medium used for study was water and 0.1 N hydrochloric acid (HCl) (500 mL). The study was carried out by adding the formulation to the medium containing vessels and noting the time taken to form clear dispersion. The paddle shafts were rotated at 25 rpm to provide gentle stirring. Precipitation was evaluated by visual inspection of resultant emulsion after 24 h. The compositions were then categorized as stable (no precipitation at the end of 24 h) and unstable (precipitation).

Capsule filling

The optimized FL SMEDDS were filled as unit doses in HGCs of size 4 having maximum volume of 0.21 mL. Liquid filling was carried out at lab scale by accurately transferring measured dose (Formulation equivalent to 10 mg of FL) of formulation into body of capsules followed by sealing. The sealing was performed using organic solvent ethanol.

Coating of FL SMEDDS capsules

FL SMEDDS capsules were coated with a non-aqueous coat of 5 % w/v ethyl cellulose dispersion (Dispersion medium – dichloromethane (DCM): isopropyl alcohol (IPA). The coating was carried out a lab-scale pan coater (Alfred Herbert Ltd., India) previously cleaned, dedusted. The coating liquid was filled into the spray gun with the help of attachment. All the essential parameters for coating are shown in Table II. As the capsules rolled, the film forming liquid was sprayed intermittently allowing the solvent to evaporate. The process was continued until the desired weight gain was achieved.

TABLE II The adjusted process parameters during coating 

Process variables Adjusted specifications
Pan design/Baffling 12 cm diameter with 3 baffles
Rotational Speed of Pan 30 rpm
Spray Pressure (Operational) 40 - 50 p.s.i.
Bed to Gun Distance 25 - 30 cm
Bed temperature 30 ± 5 °C
Dry air temperature 60 ± 5 °C
Spray pattern type Circular, occasionally elliptical

Effect of different grades of polymer on time lag and release profile

Three different grades of the hydrophobic polymer i.e. ethyl cellulose (N7, N10, N22) in the same concentration (10 mg wt. gain/capsule) were used for coating FL SMEDDS capsules. Coated capsules were evaluated for appearance, leakage, stability of cap and body of capsules, and drug content. Effects of these different grades of the coating polymer on the time lag and in-vitro drug release profile were studied.

Effect of different types of plasticizers on time lag and release profile

Different plasticizers viz. polyethyleglycol-400 (PEG-400), triethyl citrate (TEC), diethyl phthalate (DEP) and dibutyl phthalate (DBP) in the same concentration (10% w/w of coating polymer) were used for coating FL SMEDDS capsules. Coated capsules were evaluated for appearance, leakage, stability of cap and body of capsules, and drug content. Effects of these different types of plasticizers on the time lag and in vitro drug release profile were studied.

Effect of coating weight gain on time lag and release profile

FL SMEDDS capsules were loaded with different weight gains of the coating polymer viz. 2.5%, 5% and 10%. Coated capsules were evaluated for appearance, leakage, stability of cap and body of capsules and drug content. Effects of increasing coating weight gain (which is a function of coating thickness) on the time lag and in-vitro drug release profile were studied.

Evaluation of FL SMEDDS chronotherapeutics capsules

  • Rupture Test

The time taken for the coat to rupture was determined visually. The SMEDDS capsules were subjected to dissolution in USPXXIV dissolution apparatus (Type II), using different media at 37 °C; paddle speed being 50 rpm. The time lag was defined as the time point at which the polymer coating rupture (n=6).

  • In vitro drug release study

In vitro drug release was carried out in distilled water, pH (1.2, 4.5, 6.8, and 7.4) buffers. In order to simulate GIT conditions in vivo , the drug release was also carried out in sequential buffer change i.e. 1.2 pH buffer (0-2 h), 4.5 pH buffer (2-4 h) and followed next by pH 6.8 buffer and then by pH 7.4 buffer. The dissolution studies were carried out in 500 mL of buffer in USPXXIV dissolution apparatus (Type II) (Electrolab TDT-08L, Electrolab, India) paddle speed being 50 rpm at 37 ± 0.5 °C. The drug release was then determined spectrophotometrically at 362 nm (n=6). The linearity concentration for in vitro drug release testing was 5-25 µg/ml in all the dissolution media. The linearity equation for FL in water, pH 1.2 buffer, pH 4.5 buffer, pH 6.8 buffer and pH 7.4 buffer were y = 0.021x - 0.017, y = 0.024x-0.008, y = 0.029x + 0.003, y = 0.018x + 0.001 and y = 0.0217x + 0.0013 respectively.

RESULTS AND DISCUSSION

The self-emulsifying formulations comprising oil, surfactants, co-surfactants, and drug should be a clear and monophasic liquid at ambient temperature when added in to aqueous phase and should have good solvent properties to allow visualization of the drug in solution ( Basalious et al., 2010 ). Solubility studies were aimed at identifying suitable oil phase and surfactant to co-surfactant ratio for the development of FL SMEDDS formulation. Distinguishing the suitable oil, surfactant to co-surfactant ratio having maximal solubilizing potential for drug under investigation is very important to achieve optimum drug loading ( Pouton, 2000 ; Embleton et al., 1997 ). Solubility of FL in different types of oils, surfactant and co-surfactant are shown in Figure 2 . Solubility studies clearly indicated that amongst the various oils that were screened, lauroglycol FCC and Labrafill M1944 CS could solubilize relatively large amount of FL. Transcutol P (TP) was found to be a very efficient solubilizer for FL. As it is a very good solubilizer and absorption enhancer and thus was chosen as a co-surfactant in the development of SMEDDS formulations aiming to improve the drug loading capabilities.

FIGURE 2 Solubility of FL in various oils, Surfactants and Co-surfactants. 

The selection of surfactant or co-surfactant in the further study was governed by their emulsification efficiency and their ability to solubilise FL. Generally, surfactants are selected based on the continuous phase or disperse phase of the emulsion (hydrophilic surfactant for emulsion with aqueous phase as the dispersion phase and vice-versa). Since SMEDDS is meant to be diluted in aqueous phase to obtain microemulsion, inclusion of hydrophilic surfactant is an obvious choice. Among the surfactants screened during study, Cremophor EL (CEL) was found to give clear systems with lauroglycol FCC. The results demonstrated that TP was found to be a good co-surfactant in combination with CEL and thus it was selected for further studies. We have used CEL as surfactant and TP as co-surfactant in different ratios, which gives the FL SMEDDS with good emulsification and flowability characteristics as shown in Table III .

TABLE III Effect of surfactant to co-surfactant ratios on particle size, polysdispersity index, zeta potential, clarity and precipitation 

S/CoS ratio Evaluation parameters
Particle size (nm) Polydispersity Index Zeta potential (mV) Clarity Precipitation
0.5:1.0 231.33 ± 10.2 0.213 ± 0.032 -15 Clear Unstable
1.0:1.0 150.89 ± 12.3 0.292 ± 0.091 -19 Clear Stable
1.5:1.0 133.80 ± 7.9 0.119 ± 0.024 -18 Clear Stable
2.0:1.0 65.230 ± 9.2 0.211 ± 0.031 -13 Clear Stable

In the present investigation, lauroglycol FCC was tested for phase behavior studies with CEL and TP as S/CoS mixture. As seen from the ternary plot ( Figure 3 ), it was observed that lauroglycol FCC gave a wider microemulsion region at all S/CoS ratios. Hence, lauroglycol FCC was found to be the preferred vehicle for the FL SMEDDS formulation. Figure 3 showed that the microemulsion existence was found to be increased by some extent with the increasing ratio of S/CoS mixtures. These results are in agreement with the observations of initial trials of all batches with lauroglycol FCC. However, as mentioned above, increasing surfactant ratio resulted in loss of flowability. Thus, S/CoS ratio of 2:1 was selected for final FL SMEDDS formulation.

FIGURE 3 Ternary phase diagrams of different selected systems dispersed in water at 25 °C. (Oil = lauroglycol FCC, Surfactant = Chremophor EL, Co-surfactant = Transcutol P) Ratio of surfactant to cosurfactant in (a) is 0.5:1, (b) is 1:1, (c) is 1.5:1 and (d) is 2:1. Dark area shows oil in water microemulsion region. 

Microemulsions resulting from dilution of FL SMEDDS with various dissolution media were robust to all dilutions and did not show any separation even after 24 h of storage. The mean globule size of FL SMEDDS after dilution with various dissolution media is given in Table IV. Optimized FL SMEDDS showed approximately similar mean globule size within range of 65-85 nm when diluted with various dissolution media of different pH. The time required for formation of microemulsions after dilution with various dissolution media was less than 4 min. The resulting microemulsions were translucent in appearance and they did not show any signs of phase separation and drug precipitation even after 24 h of the storage. Thus, the formulated composition was found to be stable.

TABLE IV Globule size and polydispersity index of FL SMEDDS at different pH conditions 

Dissolution Medium Water Buffer pH 1.2 Buffer pH 4.5 Buffer pH 6.8
Globule size (nm) a 65.34± 2.3 70.54 ± 8.8 68.45 ± 4.7 76.35 ± 9.2
Polydispersity index b 0.367± 0.078 0.213 ± 0.063 0.382 ± 0.092 0.213 ± 0.034

Ethyl cellulose was chosen as the coating polymer because of its weak mechanical strength and insolubility throughout the gastrointestinal tract. Though a not very flexible film is desired, the film formed must be strong enough to withstand the in-vivo GIT turbulences and remain intact for the period of “time lag”. Therefore, various grades of ethyl cellulose differing in their viscosities were screened. Figure 4 (a) showed the drug release profile of the different batches coated with various grades of ethyl cellulose. The release profile indicates that as the viscosity of the polymer increases stronger and more durable films are formed. The thickness of film is not uniform all over the capsules; rupture is occurred were film thickness is thin compared to other part of film. The grade with the lowest viscosity (Ethyl Cellulose N7) showed good mechanical strength and rupture after the desired time lag.

FIGURE 4 – (a) Effect of different grades of ethyl cellulose on time lag and in-vitro release profile (b) Effect of type of plasticizer on time lag (PEG 400: Polyethylene glycol 400, TEC: triethyl citrate, DEP: diethyl phthalate, DBP: dibutyl phthalate). 

Different plasticizers were used along with the film-forming polymer to produce good uniform film. Ethyl cellulose forms a tough however mechanically weak and brittle film and therefore plasticizers are added to increase film flexibility and to rupture after the desired time lag. Figure 4 (b) showed the effect of different types of plasticizer on time lag. Hydrophilic plasticizers such as PEG 400 gave a very small time lag (~0.33 h). This is due to the rapid dissolution of the plasticizer in the medium and formation of micro pores in the polymeric film coat through which the drug can diffuse out. As the lipophilicity of the plasticizer increased, an increase in time lag was observed. Films plasticized with dibutyl phthalate (DBP) gave desirable time lag (~6.0 h) and subsequently desired in-vitro drug release profile. Hence, DBP was chosen as the plasticizer to get the desired drug release.

Increase in the coat thickness also cause resistance to the water penetration and coat rupture. Figure 5 (a) showed that with increase in the percent coating weight gain i.e. with increase in coat thickness there was a corresponding increase in the time lag of the formulation indicating that this parameter could be used to modulate and achieve a desired time lag. The desired released profile was obtained by 10% weight gain of the polymer coat. pH independent drug release behaviour of the polymer was also studied by carrying out the dissolution in sequential buffer change. As shown in Figure 5 (b), drug release behaviour of the optimized formulation was found to be not affected by the pH of the medium. Thus, the developed formulation was showing pH independent release profile of FL owing to the use of ethyl cellulose as hydrophobic functional coating material.

FIGURE 5 – (a) Effect of percent coating weight gain of ethyl cellulose on time lag and in-vitro release profile (b) Dissolution of optimized formulation in sequential buffer change. 

CONCLUSIONS

The most significant issue to consider when formulating chronotherapeutics delivery is to release drugs after a defined delay period (lag period-interval of no drug release) after being taken by the patient. Here, we have successfully developed SMEDDS of Felodipine to increase the bioavailability and filled in hard gelatine capsules coated with pH independent polymer. Thus, time dependent release of drug from the formulation to a specific time of the day was successfully achieved when there is maximal clinical manifestation of the disease.

ACKNOWLEDGEMENTS

Authors are thankful to University Grant Commission (UGC), Government of India, for financial assistance and AICTE for providing facilities to perform the experimental work.

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Received: December 13, 2012; Accepted: November 02, 2013

* Correspondence: Khalid Akhter Ansari. Formulation Development Centre, Syngene International Ltd, 560099 - Biocon Park - Bangalore, India. E-mail: khalid.akhter@gmail.com

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