Tropical Journal of Pharmaceutical Research Pharmacotherapy Group, Faculty of Pharmacy, University of Benin, Benin City, Nigeria ISSN: 1596-5996 EISSN: 1596-9827 Vol. 9, Num. 3, 2010, pp. 293-299

Tropical Journal of Pharmaceutical Research, Vol. 9, No. 3, May-June, 2010, pp. 293-299

Research Article

Formulation of nimesulide floating microparticles using low-viscosity hydroxypropyl methylcellulose

Shujaat Ali Khan, Mahmood Ahmad, Ghulam Murtaza, Muhammad Naeem Aamir, Nisar-ur-Rehman, Rozina Kousar, Fatima Rasool, Mohammad Akhtar

Faculty of Pharmacy and Alternative Medicine, The Islamia University of Bahawalpur, Bahawalpur-63100, Pakistan

Correspondence Address:Ghulam Murtaza, Faculty of Pharmacy and Alternative Medicine, The Islamia University of Bahawalpur, Bahawalpur-63100, Pakistan, gmdogar356@gmail.com

Date of Submission: 11-Sep-2009
Date of Acceptance: 20-Apr-2010

Code Number: pr10036

Abstract

Keywords: Floating microparticles, Nimesulide, HPMC, Coacervation, Non-solvent addition, Sustained release

Introduction

Nimesulide (4-nitro-2-phenoxymethane-sulfo-nanilide) is a non-steroidal anti-inflammatory drug(NSAID) that is weakly acidic (pKa 6.5) and differs from other NSAIDs in that its chemical structure contains a sulfonanilide moiety as the acidic group ^[1] . It has good anti-inflammatory, analgesic and antipyretic activity, and is well tolerated by patients as demonstrated in clinical trials ^[2] . Nimesulide is the first marketed drug with a selective inhibition of prostaglandin synthesis via cyclo-oxygenase-2 (COX-2), which results in lower toxicity in the gastrointestinal mucosa and the kidney ^[3],[4] .

Microencapsulation is a common technique used in the production of sustained release dosage forms. Microcapsule-based drug delivery systems have received considerable attention in recent years. A number of methods have been devised to prepare microparticles of varying size, shape, as well as release and surface properties ^[5] .

Gastrointestinal transit time is one of the several physiological limitations that must be controlled in the development of per-oral sustained release dosage forms. Various attempts have been made to prolong the retention time of the dosage form in the stomach. One such method is the preparation of a device that remains buoyant in stomach contents due to a density that is lower than that of gastric fluids. On the other hand, a floating system made up of multiple units has relative merits compared to a single unit preparation ^[6] . Indeed, gastric emptying of a multiparticulate floating system would occur in a consistent manner with small individual variations. On each subsequent gastric emptying, sunken particles will spread out more uniformly over a large area of absorption sites, increasing the opportunity for drug release profile and absorption in a more or less predictable way. Moreover, since each dose consists of many subunits, the risk of dose dumping is reduced ^[7],[8] . The concept of floating microparticles can also be utilized to minimize the irritant effect of weakly acidic drugs on the stomach by avoiding direct contact with the mucosa and thus providing a means of making available low dosage for prolonged periods ^[6] .

The objective of the present study was to formulate a suitable gastroretentive floating microparticulate delivery system of a weakly acidic drug, nimesulide, using hydroxypropyl methylcellulose (HPMC) as the gel-forming polymer.

Experimental

Materials

Nimesulide BP was donated by Pharm-Evo Pharma (Pvt) Ltd, Karachi, Pakistan while HPMC (viscosity grade, 40 - 60 cps) was purchased from Sigma, USA. Dichloromethane, liquid paraffin and n-hexane, which were of analytical grade, were supplied by Merck Germany.

Preparation of microparticles

The microparticles were prepared by first dissolving nimesulide (1 g) and HPMC (1, 2 and 3 g) in dichloromethane (20 ml) at room temperature. Liquid paraffin (50 ml) was added slowly to the solution with constant stirring using a magnetic stirrer at a rate of 700 rpm for 2 h. The finely dispersed droplets of the polymer-drug were filtered and washed thrice with n-hexane and dried.

In vitro drug release studies

In vitro release of nimesulide from microparticles was evaluated in simulated gastric fluid (0.1M HCl, pH 1.2), distilled water (pH 6.5) and simulated intestinal fluid (phosphate buffer, pH 6.8) separately. An amount of the microparticles, equivalent to 100 mg of nimesulide was transferred to the dissolution medium (900 mL, 37 ^o C) in a USP XXII apparatus (basket method I, Pharma Test, Germany) operating at a speed of 100 rpm. Samples were withdrawn at intervals over a period of 10 h with an automated sample collector after filtering through a 10 μm Sinter filter and replaced immediately with an equal volume of fresh dissolution medium. The samples were analyzed for nimesulide using a UV-VIS spectrophotometer (Shimadzu UV-1601, Japan) at 404 nm ^[9] . The results were expressed as mean (± SD) of three tests.

Analysis of release data

The data obtained from the in vitro drug release studies were fitted into various release models, namely, zero order, first order, Higuchi square root, Hixson-Crowell cube root and Korsmeyer-Peppas ^[17] . Additionally, the similarity factor, ƒ2, was used to assess differences in dissolution profiles as in Eq 1 ^[18] .

ƒ₂ = 50 log {1 + 1/n ∑(R _t - T _t) ²}^{- 0.5}× 100 ............... (1)

Assessment of micromeritic properties

The microparticles were characterized for various micromeritic properties. Particle size was measured using an optical microscope (XSZ-150A, Ningbo, China) with the mean particle size calculated by measuring the size of 200 particles with the aid of a calibrated ocular micrometer. The tapping method was used to determine tapped density and compressibility index as in Eqs 2 and 3, respectively ^[10] .

Tapped density =M/V …………………. (2)

where M is the mass of the microparticles and V is the volume of the microparticles after tapping

Compressibility index (%) = (1- V/V_o) × 100 ….(3)

where V and Vo are the volumes of the sample after and before tapping, respectively. The true density of the particles was determined using the displacement method with benzene as the displacement liquid. Porosity (q , %) was calculated using Eq 4 ^[11] .

ε (%) = (1- P_p / P_t) ×100 ……………… .(4)

where P _t and P _p are the true density and tapped density, respectively. Angle of repose of the microparticles, which measures the resistance to particle flow, was determined by the fixed funnel method and calculated as in Eq 5 ^[12] .

θ = tan ^-1 h/r ………..………………… (5)

where r is the radius and h is the height of the microparticle heap. Hausnner′s ratio, another index of flowability, was calculated using Eq 6.

Hausner’s ratio = V/ V0 .…………….. (6)

where V is the volume before tapping and V₀ is the volume after tapping. Packing factor was calculated as the ratio of bulk density after tapping to bulk density before tapping, as indicated in Eq 7 ^[13] .

Packing factor (P_f ) =D/D₀…………… (7)

where D is the bulk density after tapping and D₀ is the bulk density before tapping.

Scanning electron microscopy

The microparticles were mounted directly onto the sample stub and coated with gold film (200 nm) and their surface characterized by scanning electron microscopy (Philips-XL-20, The Netherlands) under reduced pressure (0.133 Pa).

Wall thickness

The wall thickness (h) of the microparticles was computed using Eq 8 ^[14] .

h = r (1-p) d₁ / 3{pd₂ + (1-p) d₁} …………(8)

where r = arithmetic mean radius, d₁ = density of core material, d ₂ = density of coat material, and p = proportion of drug in microparticles

Buoyancy

Fifty milligrams of the floating microparticles were placed in simulated gastric fluid (pH 1.2, 100 ml) containing 0.02 w/v% Tween 20 and stirred at 100 rpm with a magnetic stirrer. After 8 h, the layer of buoyant microparticles was pipetted and separated by filtration. The sunken particles were also separated by filtration. Both sets of particles were dried in a desiccators over silica gel for 24 h to constant weight and the weight noted. Buoyancy was determined as in Eq 9 ^[15] .

Buoyancy (%) =Wf / (Wf + Ws) ×100 …. (9)

Where Wf and Ws are the weights of the floating and settled microparticles, respectively. All the determinations were made in triplicate.

Determination of drug entrapment efficiency, drug loading and yield

Accurately weighed 25 mg microparticles were suspended in 25 ml of methanol. After 24 h, the solution was filtered and the filtrate analysed for drug content spectrophotometrically at 404 nm. Drug entrapment efficiency (EE) was determined using Eq 10:

EE (%) = A/T x 100 ………..…………. (10)

where A = actual drug content and T =theoretical drug content. Yield was calculated as in Eq 11.

Yield (%) =P/(W_D+W_P) x 100 …...…… (11)

where P is the weight of the microparticles, and W _D andW_P are the weights of drug and polymer, respectively, used in forming the microparticles. Each determination was performed in triplicate ^[16] .

Compatibility test

Diffractograms of the drug, HPMC and floating microparticles were obtained using a Philips PW 1830 X-ray diffractometer. The radiation source was a copper (L = 1.54184 A) high-intensity x-ray tube operated at 35 KV and 15 mA. Fourier transform infrared spectroscopy (Shimadzu, FTIR-8400) was conducted on the materials to determine if there was any interaction between the drug and the polymer; they were scanned in the IR range of 500 to 4000 cm ^-1 by KBr method. The detector was purged carefully with clean dry helium gas to increase signal level and reduce moisture.

Statistical analysis

Pair-wise procedure, i.e., similarity factor (f ₂ ) was applied to the release data. One-way ANOVA for significance at P < 0.05 was conducted for the release profiles using SPSS version 12.0.

Results

Physicochemical properties of microparticles

The physicochemical properties of the microparticles are shown in [Figure - 1] and [Table - 1]. The SEM photograph [Figure - 1] show that the microparticles were spherical with a smooth surface and exhibited a range of sizes within each batch.

Yield was in the range 78.5 to 87.1 % while drug entrapment or loading was in the range 66.4 to 81.6 %. The microparticles floated for a prolonged time on the surface of the dissolution medium with a buoyancy of 63.4 to 67.7 % after 12 h and had a wall thickness of 15.6 - 17.7 μm.

Tapped density ranged from 0.229 to 0.309 g/cm ³ , while true density was between 0.165 and 0.241 g/cm ³ for all the formulations, the fairly wide range being due, probably, to the presence of fractions of low-density particles within the microparticles. Microparticle porosity was in the range of 68.0 - 74.4 while compressibility index ranged from 22.0 % to 28.0 %. All the formulations showed excellent flowability, judging by their angle of repose which was between 19.6 ± 0.5 and 23.7 ±0.6 ⁰ , thus indicating that the microparticles were non-aggregated. Their size ranged from 116.6 to 132.8 μm.

[Figure - 2] and [Table - 2] show the release data for the microparticles. The release rate of drug from formulation M1 was comparatively higher than that from M2 and M3 but this difference in drug release behaviour was non-significant (p > 0.05). The lower the concentration of the polymer (HPMC), the faster the release of drug from the microparticles. Moreover, the drug release characteristics from all formulations fitted best to Higuchi kinetic model as evident from its higher value of regression coefficient [Table - 2].

Data in parenthesis represent Korsemeyer-Peppas release exponent, n.

Drug-polymer compatibility

In order to determine the physical state of the drug in the microparticles, especially possible drug/polymer interaction, x-ray diffraction was conducted for the pure drug, the polymer and the microparticles. The results are shown in [Figure - 3]. The x-ray diffraction patterns indicate that the pure drug exhibited crystalline characteristics, while polymer diffractogram showed an amorphous pattern. The peaks are denser in the microparticle formulation due, probably, to re-crystallization of the drug on the surface of microparticles.

The FTIR spectra of the drug see [Figure - 3] indicate the presence of bands at 906 - 640 cm ^-1 (C-H aromatic), 1078 cm ^-1 (S=O), 1159 cm ^-1 (C-O-C ether linkage), 1077 cm ^-1 (CH ₃ C-H bending), 1516 and 1340 cm ^-1 (NO ₂ ) and 3286 cm ^-1 (N-H). The spectra of the microparticles also showed essentially identical peaks at the same bands, thus indicating that there was no chemical interaction between nimesulide and HPMC in the microparticles.

Discussion

Microencapsulation of nimesulide with HPMC produced microparticles with good flow characteristics. Entrapment efficiency and other physicochemical properties were similar to those previously reported for other microparticles ^[6] . Cumulative release of nimesulide decreased significantly with increasing HPMC concentration [Figure - 2]. However, f2 values of the dissolution profiles were between 50 and 70 which indicate similarity of the dissolution data for various formulations. Increase in polymer concentration from 1:1 to 1:3 (drug:polymer) also increased yield, entrapment efficiency, buoyancy, wall thickness and microparticle size ^[19],[20] . There was increase (p > 0.05) in particle size and wall thickness with increase in polymer concentration and this may be attributed to increased aggregation of the polymer particles as its concentration increased. With increasing polymer content, more particles of nimesulide would be coated leading to higher encapsulation efficiency ^[27],[28] . However, this increase was non-significant (p > 0.05).

On fitting the data into release models (zero-order, first-order, Higuchi, Hixson-Crowell and Korsmeyer-Peppas), the highest regression coefficient values were found for the Higuchi model, indicating that diffusion was the predominant mechanism of drug release. The data derived from the Hixson-Crowell model indicate a change in the surface area and diameter of the particles with progressive dissolution of the matrix as a function of time while the plot for the Korsmeyer-Peppas model showed good linearity. The release exponent, n, was in the order 0.45 < n < 0.89, which appears to indicate a coupling of diffusion and erosion mechanisms, i.e., the so-called anomalous diffusion, and this probably indicates that drug release was controlled by more than one process see [Table - 1]. Release data for formulation M1 in phosphate buffer (pH 6.8), 0.1M HCl (pH 1.2) and distilled water (pH 6.5) showed that 58.9, 35.8 and 55.0 % of nimesulide, respectively, were released after 10 h. This is due to the fact that acidic drugs ionize/dissolve more in a basic medium than in an acidic one.

Conclusion

Nimesulide microparticles of varying size and drug content can be obtained, using a coacervation non-solvent addition technique, by varying low-viscosity HPMC content. With the microparticles of nimesulide showing excellent floatability, good buoyancy and prolonged drug release (based mainly on diffusion-controlled mechanism) and absence of chemical interaction between drug and polymer, it can be stated that the floating microparticles constitute a potential candidate for multiple-unit delivery devices for intra-gastric drug absorption.

References

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