Upload
vinayak-s
View
216
Download
3
Embed Size (px)
Citation preview
ORIGINAL PAPER
Development of hollow/porous floating beads of metoprololfor pulsatile drug delivery
Sangmesh S. Taranalli • Panchaxari M. Dandagi •
Vinayak S. Mastiholimath
Received: 24 April 2013 / Accepted: 25 March 2014
� Springer International Publishing Switzerland 2014
Abstract The purpose of this work was to develop hol-
low calcium pectinate beads for floating pulsatile release of
metoprolol tartrate intended for chronopharmacotherapy.
Floating pulsatile concept was applied to increase the
gastric residence of the dosage form having lag phase
followed by a burst release. To overcome limitations of
various approaches for imparting buoyancy, hollow/porous
beads were prepared by simple process of acid-base reac-
tion during ionotropic cross-linking using low methoxy
pectin, xanthan gum, sodium carboxy methyl cellulose,
guar gum, locust bean, gellan gum and calcium chloride as
a cross-linking agent. Based on the preliminary studies
optimized polymers were selected for formulation design
with different polymers ratio concentrations. The obtained
floating beads were studied for entrapment efficiency,
buoyancy study, swelling index, surface morphology,
in vitro release, stability studies and in vivo floating study.
The floating beads obtained were porous, float up to
12–24 h. The radiological studies (X-rays) pointed out the
capability of the system to release drug in lower parts of
GIT after a programmed lag time for hypertension. The
floating beads provided expected two-phase release pattern
with initial lag time during floating in acidic medium fol-
lowed by rapid pulse release in phosphate buffer. From the
accelerated stability studies, it was observed that the for-
mulations are quite stable. All formulations followed first-
order release kinetics by diffusion mechanism. This
approach suggested the use of hollow calcium pectinate
microparticles as promising floating pulsatile drug delivery
system for site- and time-specific release of drugs acting as
per chronotherapy of diseases.
Keywords Hollow beads � Calcium pectinate beads �Floating pulsatile drug delivery � Metoprolol tartrate �Chronotherapy � Radiology
1 Introduction
A delivery system with a release profile that is character-
ized by a time period of no release (lag time) followed by a
rapid and complete drug release (pulse release) can be
called as an ideal pulsatile drug delivery system. Pulsatile
delivery system provides one or more rapid release pulses
at predetermined lag times or at specific sites resulting in
better absorption of the drug, and there by providing more
effective plasma concentration time profile (Venkatesh
2005). Natural biodegradable polysaccharides like pectin,
locust bean, guar gum, chitosan, sodium alginate and gellan
gum have been used in controlled drug delivery. Various
approaches to induce buoyancy in cross-linked beads have
been used (Whitehead et al. 2000; Iannuccelli et al. 1998;
Sriamornsak and Nunthanid 1999). The use of sodium
bicarbonate as buoyancy imparting agent to produce
floating beads is simplest among the various approaches
and has been attempted successfully by many workers
(Bussmer et al. 2003). Their floating property was based on
the evolution of CO2 when in contact with acidic envi-
ronment followed by the ability of polymer gel to entrap it,
which decreases their density below one. These beads have
been used to achieve prolonged gastric residence time, for
sustained release/stomach-specific drug delivery providing
S. S. Taranalli (&) � P. M. Dandagi
Department of Pharmaceutics, KLEU’s College of Pharmacy,
Belgaum 590010, Karnataka, India
e-mail: [email protected]
V. S. Mastiholimath
Department of Quality Assurance, KLEU’s College
of Pharmacy, Belgaum, India
Eur J Drug Metab Pharmacokinet
DOI 10.1007/s13318-014-0194-9
an opportunity for both local and systemic drug action
(Rajnikanth et al. 2007).
In cardiovascular disease, capillary resistance and vas-
cular reactivity are higher in the morning and decreases
latter in the day. Platelet agreeability is increased and
fibrinolytic activity decreased in the morning, leading to a
state of relative hypercoagulability of the blood. Therefore,
the frequencies of myocardial infarction (MI) and of sud-
den cardiac death are more prone from morning to noon.
Ambulatory blood pressure measurements show a signifi-
cant circadian variation to characterize blood pressure.
Increased heart rate, blood pressure, imbalanced autonomic
tone, and circulating level of catecholamines controlling
the cardiac arrhythmias show important circadian variation
and trigger the genesis of the circadian pattern of cardiac
arrhythmias. Atrial arrhythmias appear to exhibit circadian
pattern usually with a higher frequency in the daytime and
lower frequency in the night time with the abnormal foci
under the same long-term autonomic regulation as normal
pacemaker tissue. According to study, ventricular tach-
yarrhythmias show late morning peak in the patients with
MI sometime in the distant past morning peak and after-
noon peak in patients with recent MI. Both pharmacoki-
netics and pharmacodynamics of some oral nitrates,
calcium channel blocker and b-adrenoceptor antagonist
medications have been shown to be influenced by the cir-
cadian time of their administration (Mandal et al. 2010).
Metoprolol is a cardioselective b1-adrenergic blocking
agent used for acute MI, heart failure, angina pectoris and
mild to moderate hypertension. It may also be used for
supraventricular and tachyarrhythmias and prophylaxis for
migraine headaches. Metoprolol competes with adrenergic
neurotransmitters such as catecholamines for binding at
beta (1)-adrenergic receptors in the heart. Beta (1)-receptor
blockade results in a decrease in heart rate, cardiac output,
and blood pressure (Metoprolol tartrate (internet) 2012).
All beta blockers are nearly equally effective in decreasing
frequency and severity of attacks and in increasing exercise
tolerance in classical Angina, but cardioselective agents.
Long-term b-blocker therapy lowers risk of sudden cardiac
death among ischemic heart disease patients. In angina
pectoris, beta blockers are to be taken on a regular schedule
not on as and when required basis (Tripathi 2008).
It is moderately lipophilic drug belonging to class I of
BCS classification having high solubility and high perme-
ability. Since the half-life of metoprolol tartrate is 3–4 h,
two multiple doses are needed to maintain a constant
plasma concentration for a good therapeutic response and
improved patient compliance (Metoprolol tartrate (internet)
2012). Although it is well absorbed in the gastrointestinal
tract, its bioavailability is 40–60 % as a result of extensive
first pass metabolism (Metoprolol (internet) 2012). Thus,
there is a strong clinical need and market potential for a
dosage form that will deliver metoprolol tartrate in a
controlled manner to a patient needing this therapy, thereby
resulting in a better patient compliance.
Multi-particulate or multiple unit systems offer various
advantages over single-unit systems. These include no risk
of dose dumping, flexibility of blending units with different
release patterns, relative merits of bioavailability more
consistent blood levels, reproducible and avoid all or none
effect. The aim of the study was to design and characterize
hollow/porous floating beads of metoprolol tartrate for
pulsatile drug delivery for the treatment of hypertension.
2 Materials and method
2.1 Materials
Low methoxy pectin (LMP) was obtained as generous gift
sample from Krishna Pectins Pvt. Ltd., Jalgaon, Maha-
rashtra, India. Metoprolol tartrate was obtained as generous
gift sample from Astrazeneca Pharmaceuticals Pvt. Ltd.,
Bangalore (India). Xanthan gum, Sodium CMC, Guar gum
Locust bean, Gellan gum and Sodium bicarbonate from Hi-
media Laboratories Pvt. Ltd., Mumbai, and Calcium
Chloride from Loba Chem Pvt. Ltd., Mumbai. All other
chemicals used were of analytical grade.
2.2 Method
2.2.1 Formulation of metoprolol tartrate beads
2.2.1.1 Preliminary studies for selection of polymer com-
bination Four formulations were prepared using different
polymers as shown in Table 1.
Evaluation parameters such as drug entrapment effi-
ciency, buoyancy study of the beads and in vitro drug
release for the formulated beads were done and the
promising batch was selected on the basis of above
parameters for the further study.
2.2.1.2 Ionotropic gelation/bead formation A polymeric
solution was prepared by dissolving various amounts of
polymers in 15 ml of deionized water. Then, gas-forming
agent, such as sodium bicarbonate and metoprolol tartrate
(100 mg), was added into the solution (Table 2). The dis-
persion was sonicated for 30 min to break the lumps and to
remove air bubbles. The resultant dispersion was dropped
via a 21-gauge syringe needle into 3 % w/v calcium
chloride (CaCl2) solution containing 10 % (v/v) acetic
acid. The distance between the tip of the needle and the
surface of the CaCl2 medium was about 6 cm. The beads
formed were stirred at 150 ± 5 rpm using magnetic stirrer
for 15 min for curing. The beads were separated by
Eur J Drug Metab Pharmacokinet
filtration, washed three times with distilled water and
subsequently oven dried at 45 �C for 6 h (Dupuis et al.
2006).
2.2.2 Characterization of beads
2.2.2.1 Particle size analysis and surface morphol-
ogy 100 beads were analyzed for their size distribution by
optical microscopy. The mean diameter was determined by
measuring the number of divisions covered by beads using
ocular micrometer previously calibrated using stage
micrometer. The surface Morphology was analyzed with a
scanning electron microscope (JEOL JSM-6360 SEM)
operated at an acceleration voltage of 5 kV (Pornsak et al.
2005; Gadad et al. 2009).
2.2.2.2 Determination of drug entrapment effi-
ciency Accurately weighed quantities (50 mg) of beads
from each batch were placed in 100 ml phosphate buffer, pH
7.4 and mechanically agitated on shaker at 200 rpm for 24 h.
The resultant dispersions were filtered and analyzed spectro-
scopically at 224 nm. The percentage entrapment efficiency
was calculated using following equation (Claire et al. 2011).
Drug entrapment efficiency %
¼ Actual drug content in the beadsð=theoretical drug contentÞ � 100:
2.2.2.3 Bead porosity and bulk density The bead porosity
was assessed using mercury porosimetry (Autoscan 60
Porosimeter, Quantachrome software, USA). The pressure
was applied from 0 to 6,000 psi. The mercury intrusion
data were recorded and plotted against pressure. Standard
values for the contact angle and surface tension of mercury
were used for calculations. The bulk densities of the beads
were also measured using same mercury porosimeter
(Bulgarelli et al. 2002).
2.2.2.4 Buoyancy study Floating property of beads was
evaluated using USP XXIII type II dissolution test apparatus
(Electrolab TDT-06P, Mumbai, India) filled with 900 ml in
pH 1.2 containing 0.02 % w/v Tween 80, using paddle at a
rotation speed of 100 rpm. The temperature of medium was
maintained at 37 ± 2 �C. 100 beads of each batch were
placed in the media. Floating ability was observed visually
(Huimin et al. 2012; Mastiholimath et al. 2008).
2.2.2.5 Determination of swelling index The swelling
behavior of the beads was studied in pH 7.4 phosphate
buffer solution. Approximately 100 mg of beads was taken
in a dissolution basket and weighed; the baskets along with
the beads were immersed in 7.4 phosphate buffer solution.
The weight of the basket along with the beads was deter-
mined after 1 h, and then every hour. The swelling index
(SI) of each formulation was calculated using the following
equation (Sandolo et al. 2011; Patel et al. 2011):
%SI ¼ W2 �W1
W1
� 100
where, W1 is weight of the dry beads and basket and W2 is
weight of the swollen beads and basket.
2.2.2.6 In vitro drug release The dissolution study of
beads equivalent to 100 mg of metoprolol tartrate was
performed using a USP XXIII type 2 dissolution test
apparatus. The drug release study was performed in 900 ml
for 6 h in pH 1.2. Then the dissolution medium was
replaced with phosphate buffer of pH 6.8 for 3 h, the
average small intestinal transit time is about 3 h. After 9 h,
the dissolution medium was replaced with phosphate buffer
Table 1 Preliminary studies for selection of polymer combination
Batch
no.
Drug
(mg)
Low methoxy
pectin (mg)
Xanthan
gum (mg)
Sodium CMC
cellulose (mg)
Guar
gum (mg)
Locust
bean (mg)
Gellan
gum (mg)
Sodium
bicarbonate (mg)
FA 100 300 50 100 – – – 150
FB 100 300 50 – 100 – – 150
FC 100 300 50 – – 100 – 150
FD 100 300 50 – – – 100 150
Table 2 Formulation code for metoprolol tartrate floating beads
Batch
no.
Metoprolol
tartrate (mg)
Low methoxy
Pectin (mg)
Xanthan
gum (mg)
Locust
bean (mg)
Sodium
bicarbonate (mg)
Deionized
water (ml)
FCE 100 300 30 120 150 15
FCF 100 300 60 90 150 15
FCG 100 300 120 30 150 15
Eur J Drug Metab Pharmacokinet
of pH 7.4 maintained at 37.0 ± 0.5 �C at 100 rpm for 18 h.
Periodically 5 ml of sample was withdrawn and replaced
by dissolution media in order to maintain sink condition.
The withdrawn samples were filtered through a Wattman
filter paper 41 and the concentration of metoprolol tartrate
was measured spectrophotometrically at 221.5 and 224 nm
for acidic and basic media, respectively, after suitable
dilutions (Patel et al. 2011).
2.2.3 In vivo study
2.2.3.1 Radiology (X-rays) The optimized batch was
chosen for the preparation of the barium sulfate-loaded
beads. The barium sulfate beads were prepared as of
optimized batch but the drug was replaced with barium
sulfate (100 mg). Healthy rabbit weighing approximately
2.3 kg was used to assess in vivo floating behavior. Ethical
clearance for the handling of experimental animals was
obtained (CPCSEA). The animal was fasted for 12 h and
the first X-ray photographed to ensure the absence of radio
opaque material in the stomach. The rabbits were made to
swallow barium sulfate-loaded beads with 30 ml of water.
During the experiment, rabbits were not allowed to eat but
water was provided. At predetermined time intervals, the
radiograph of abdomen was taken using an X-ray machine
(Gangadharappa et al. 2011).
2.2.3.2 Stability study Stability study has become an
integral part of formulation development. It generates
information on which proposal for nature of drug or dosage
and their recommended storage conditions are based. The
accelerated stability study was conducted for selected for-
mulation as per the ICH guidelines.
Accelerated testing 40 ± 2 �C/75 ± 5 % RH for
6 months.
As per ICH guidelines, beads of promising formulation
were selected and subjected to accelerated stability study.
Weighed quantity of the samples was kept in glass vials,
sealed with rubber plugs and exposed to controlled tem-
perature (40 ± 2 �C) and relative humidity (75 ± 5 %) for
a period of 6 months in humidity control oven (Lab Con-
trol, Ajinkya IM 3500 Series, India).
2.2.3.3 Photo-stability study A light source that is
designed to produce an artificial daylight fluorescent lamp
combining visible and ultraviolet (UV) outputs, xenon, or
metal halide lamp is used. D65 is the internationally rec-
ognized standard for outdoor daylight as defined in ISO
10977 (1993). ID65 is the equivalent indoor indirect day-
light standard. For a light source emitting significant
radiation below 320 nm, an appropriate filter may be fitted
to eliminate such radiation. After 1, 2, 3 and 6 months, the
samples were taken out and analyzed for drug entrapment
efficiency, buoyancy study, and in vitro release (Gadad
et al. 2009; Amrutkar et al. 2012).
2.2.3.4 Release kinetics One of the most important and
challenging areas in the drug delivery field is to predict the
release of the active agent as a function of time using both
simple and sophisticated mathematical models. The impor-
tance of such models lies in their utility during both the
design stage of a pharmaceutical formulation and the
experimental verification of a release mechanism. In order to
identify a particular release mechanism, experimental data of
statistical significance are compared to a solution of the
theoretical model. To analyze the mechanism for the drug
release and drug release rate kinetics of the dosage form, the
data obtained was fitted into Zero order, First order, Higuchi
matrix and Korsmeyer-Peppas. In this study by comparing
the R2 values obtained, the best-fit model was selected.
Drug release kinetics can be analyzed by various
mathematical models, which are applied considering the
amounts of drug released from 0 to 24 h. The following
plots were made: Cumulative percentage drug release
versus time (zero-order kinetic model); log cumula-
tive percentage drug remaining versus time (first-order
kinetic model); cumulative percentage drug release versus
square root of time (Higuchi model); and log cumula-
tive percentage drug remaining versus log time (Kors-
meyer’s Peppas model) (Lin and Kawashima 1987).
3 Result and discussion
3.1 Pre-formulation study
3.1.1 Compatibility study
The FT-IR spectra of pure metoprolol tartrate and the
combination of metoprolol tartrate with the polymer show
similar characteristic functional peak. The similarity in the
peaks indicates the compatibility of metoprolol tartrate
with polymers as shown in Fig. 1.
3.1.2 Formulation of floating calcium pectinate beads
Based upon the results of preliminary study, FC formula-
tion was selected for further studies because it showed
highest entrapment efficiency of 70.89 %, produced float-
ing beads buoyancy for 24 h and highest in vitro drug
release of 96.04 %.
Three formulations (FCE, FCF and FCG) of metoprolol
tartrate beads were made. The formulations were prepared
by varying polymer ratio and keeping the concentration of
drug and other ingredients same as showed in table: the
method used to prepare the calcium pectinate beads by
Eur J Drug Metab Pharmacokinet
dripping method using 21-gauge needle into the 3 % cal-
cium chloride solution containing 10 % v/v acetic acid.
The beads were formed due to the cross-linking of the
pectin with divalent calcium ions of the calcium chloride
solution. The reaction between sodium bicarbonate and
acetic acid was occurred liberating carbon dioxide as gas
bubbles which are responsible for floating of beads.
3.1.3 Characterization of beads
3.1.3.1 Particle size analysis and surface morphol-
ogy The mean surface diameter of all three formulations
was between 1.134 ± 0.018 and 1.198 ± 0.008 (mm),
tabulated in Table 3; this indicates that size of beads
increased significantly with increase in viscosity there by
subsequent increase in interfacial tension, resulting in the
formation of larger particles.
Surface morphology of beads batch no FCF was
observed. It was shown that beads were spherical in
shape, with slightly rougher surface/shrinkage and dis-
crete as shown in Fig. 2. The surface topography reveals
that the beads were highly porous because of rapid
escape of the carbon dioxide during formulation. The
cross section of beads from batch FCF showed a hollow
core in the matrix, which may be because of the pre-
sence of gas generating agent. The thick matrix
Fig. 1 FTIR spectra
Table 3 Characterization of floating beads
Batch
code
Particle
size (mm)*
Drug entrapment
efficiency (%)*
Swelling
index (%)*
Bulk density
(g/cm3)*
Porosity
(%)
Floating ability
in pH 1.2 (h)
FCE 1.134 ± 0.02 68.44 ± 3.81 1.51 ± 0.15 1.35 ± 0.05 28.94 [12
FCF 1.176 ± 0.01 76.84 ± 6.37 1.95 ± 0.13 1.13 ± 0.19 32.73 [24
FCG 1.198 ± 0.01 72.72 ± 4.23 1.83 ± 0.13 0.87 ± 0.13 34.08 [24
* Values expressed are mean ± SD (n = 3)
Eur J Drug Metab Pharmacokinet
boundaries around the hollow core observed may be due
to the coalescence of the gas bubbles formed in the wet
beads.
3.1.3.2 Drug entrapment efficiency Drug entrapment in
the beads includes drug entrapped within the polymer
matrices. The values of total % entrapment efficiency of
the drug were in the range of 53.78–76.84 % for dried
beads as shown in Table 3.
The actual drug content and drug entrapment efficiency
was found to be more for the batch FCF with respect to
other batch; this may be due to greater extent of cross-
linking and thereby greater entrapment efficiency.
3.1.3.3 Bead porosity and bulk density The bulk density
of the beads (Batch no FCG) was less as compared with the
batch no FCE and FCF. As bulk density increases it was
observed that size and porosity decreases (Table 3).
3.1.3.4 Determination of buoyancy of beads Only beads
of batch no FD had a buoyancy lag time of 3 min. Batches
FA, FD and FCE produced floating beads remained floating
for more than 12 h and FC, FB, FCF and FCG for more
than 24 h. The floating property of hollow/porous beads
may be attributed to the low bulk density and the porosity
of the beads, implying that the beads will have the pro-
pensity to exhibit an excellent buoyancy effect in vivo.
Fig. 2 SEM photographs of
metoprolol tartrate formulation
beads
Eur J Drug Metab Pharmacokinet
Batches FA, FD and FCE floating beads remained floating
for \24 h. This may be attributed because these batches
could not maintain matrix integrity for more than 12 h.
3.1.3.5 Determination of swelling index The swelling
behavior of the polymer is also an important factor con-
trolling the release of the drugs from the bead systems. The
extent of swelling of the formulated beads showed that the
swelling was related to different polymer ratio with
swelling being more significant for beads with increased
gel formation this may be due greater extent of cross-
linking between the polymers. The SI was found to be in
the range of 1.51–1.95 % as shown in Table 3.
3.1.3.6 Drug release study The dissolution study of all
the formulations of metoprolol tartrate beads was carried
out in different media namely pH 1.2 and pH 6.8, 7.4
phosphate buffer. All these beads released 6.32–14.02 % of
the drug in acidic medium irrespective of time.
Batch FCE, FCF and FCG showed 14.02, 8.72 and
6.32 % drug release within 6 h in acidic medium, respec-
tively. There was a slow release for 6 h. After 6 h there
was burst release in phosphate buffer and the drug release
observed for about 18 h. The drug release profile in
phosphate buffer is shown in Fig. 3.
The porous beads showed excellent lag time in drug
release profile in acidic pH, this may be due to insolubility
of pectin. At acidic pH, calcium pectinate and locust bean
remained protonated into insoluble form with reduced
swelling. The second phase of pulsed release in pH 6.8 and
7.4 can be attributed to rapid swelling and gel relaxation of
calcium pectinate, locust bean at alkaline pH.
3.1.3.7 In vivo study The in vivo gastric residence of the
batch FCF was studied by radiological study (X-ray) of
radio-labeled beads using rabbit as animal model. In
stomach, the insoluble beads were acted as indigestible
food particle. Radiographic image 1–6 (Fig. 4) shows
X-ray scans taken on the rabbit during radiological study. It
can be interpreted from the images that the beads were
clumped together intact and remained floating for 8 h of
the study.
3.1.3.8 Stability study In view of potential utility of the
formulation, stability study was carried out on batch FCF
for 6 months according to ICH guidelines. Formulations
were subjected to drug entrapment, floating behavior and
in vitro release study after 30, 60, 90 and 180 days.
On comparing the optimized formulation with initial
data of % entrapment efficiency is 70.03 and cumulative %
drug release is 88.79. Result showed (Table 4) that there
were no significant changes observed in the appearance,
drug entrapment efficiency, buoyancy study and in vitro
release analysis of formulation. It confirms that formulation
FCF was stable at a temperature of 40 ± 2 �C/75 ± 5 %
and photo stable at the end of 180 days.
Fig. 3 In vitro release profile for formulations
Eur J Drug Metab Pharmacokinet
3.1.3.9 Drug release kinetics Based on regression coef-
ficient values (R2), all the formulations followed first-order
drug release kinetics. From Peppas model, it was found that
batch no FA, FB, FC, FCE, FCF and FCG showed anom-
alous transport kinetics, i.e., a combined mechanism of
pure diffusion and Case II transport and batch no FD
showed non-Fickian diffusion (Table 5).
4 Conclusion
The hollow beads containing metoprolol tartrate showed
excellent buoyancy in acidic environment of stomach.
The enhanced buoyancy of porous beads makes them
excellent candidate for intragastric floating drug delivery,
by slowing down the gastric emptying. The pulsatile drug
delivery was characterized by rapid and complete drug
release from the drug loaded porous beads due to the fast
disintegration in the basic medium after a lag time in
acidic environment. The release from porous beads was
due to faster entry of the gastrointestinal fluid through the
weak matrix of the bead in the buffer. Overall, the
buoyant beads provided a lag phase while showing gastro
Fig. 4 Radiographic images
taken on the rabbit during
radiological studies
Table 4 Stability study
Time
(days)
Drug entrapment
efficiency (%)*
Floating
duration
(h)
Percent cumulative
drug release at
the end of 24 h*
0 75.24 ± 6.33 [24 95.28 ± 0.81
30 74.55 ± 6.13 [24 95.54 ± 0.73
60 74.25 ± 6.06 [24 93.11 ± 1.48
90 73.71 ± 5.70 [24 91.83 ± 0.94
180 70.03 ± 5.40 [24 88.79 ± 0.90
* Values expressed are mean ± SD (n = 3)
Eur J Drug Metab Pharmacokinet
retention followed by a pulsatile drug release that would
be beneficial for hypertension.
Acknowledgments The authors are highly thankful to Dr. A. D.
Taranalli, Principal KLEU’s college of pharmacy, Belgaum for pro-
viding all the facilities required for the project. Authors wish to
thanks Low methoxy pectin (LMP), was obtained as generous gift
sample from Krishna Pectins Pvt. Ltd, Jalgaon (India). Metoprolol
tartrate was obtained as generous gift sample from Astrazeneca
Pharmaceuticals Pvt Ltd, Bangalore, Karnataka, India. Xanthan gum,
Sodium CMC, Guar gum, Locust bean, Gellan gum, Sodium bicar-
bonate from Hi-media Laboratories Pvt Ltd. Mumbai for providing
drug and polymers as a gift sample.
References
Amrutkar PP, Chaudhari PD, Patil SB (2012) Design and in vitro
evaluation of multiparticulate floating drug delivery system of
zolpidem tartarate. Colloids Surf B Biointerfaces 89:182–187
Bulgarelli E, Forni F, Bernaber MT (2002) Effect of matrix
composition and process condition on casein gelatin beads
floating properties. Int J Pharm 198:279–292
Bussmer T, Dashevsky A, Bodmeier R (2003) A pulsatile drug
delivery system based on rupturable-coated hard gelatin capsule.
J Control Release 93:331–339
Claire D, Ali A, Brice M, Yann P, Philippe C, Alf L, Odile C (2011)
Zinc-pectinate beads as an in vivo self-assembling system for
pulsatile drug delivery. Int J Pharm 414:28–34
Dupuis G, Chambin O, Genelot C, Champion D, Pourcelot Y (2006)
Colonic drug delivery: influence of cross-linking agent on pectin
beads properties and role of the shell capsule type. Drug Dev Ind
Pharm 32:847–855
Gadad AP, Patil MB, Naduvinamani SN, Mastiholimath VS, Dandagi
PM, Kulkarni AR (2009) Sodium alginate polymeric floating
beads for the delivery of cefpodoxime proxetil. J Appl Polym Sci
114:1921–1926
Gangadharappa HV, Biswas S, Getyala A, Vishal Gupta N, Pramod
Kumar TM (2011) Development, in vitro and in vivo evaluation
of novel floating hollow microspheres of Rosiglitazone Maleate.
Der Pharmacia Lettre 3(4):299–316
Huimin Y, Huijuan Y, Junyi Z, Junlin Y, Lifan Z (2012) Preparation
and evaluation of a novel gastric floating alginate/poloxamer
inner-porous beads using foam solution. Int J Pharm
4(22):211–219
Iannuccelli V, Coppi G, Bernabei MT, Cameroni R (1998) Air
compartment multiple-unit system for prolonged gastric resi-
dence. Int J Pharm 174:47–54
Lin SY, Kawashima Y (1987) Drug release from tablets containing
cellulose acetate phthalate as an additive or enteric coating
material. Pharma Res 4(1):70–74
Mandal AS, Biswas N, Karim KM, Guha A, Chatterjee S, Behera M
et al (2010) Drug delivery system based on chronobiology—a
review. J Control Release 147(3):314–325
Mastiholimath VS, Dandagi PM, Gadad AP, Mathews R, Kulkarni
AR (2008) In vitro and in vivo evaluation of ranitidine
hydrochloride ethyl cellulose floating microparticles. J Microen-
capsul 25(5):307–314
Metoprolol (internet) (2012) Available from http://en.wikipedia.org/
wiki/Metoprolol (updated 13 Mar 2012; cited 6 Mar 2012)
Metoprolol tartrate (internet) (2012) Available from http://www.
drugbank.ca/drugs/DB00264(APRD00208) (updated 14 Feb
2012; cited 6 Mar 2012)
Patel FM, Patel AN, Rathore KS (2011) Release of metformin
hydrochloride from ispaghula sodium alginate beads adhered
cock intestinal mucosa. Int J Cur Pharm Res 3(3):52–55
Pornsak S, Nartaya T, Satit P (2005) Emulsion gel beads of calcium
pectinate capable of floating on the gastric fluid: effect of some
additives, hardening agent or coating on release behavior of
metronidazole. Eur J Pharm Sci 24:363–373
Rajnikanth PS, Balasubramanium J, Mishra B (2007) Preparation and
in vitro characterization of Gellan based floating beads of
acetohydroxamic acid for eradication of H. pylori. Acta Pharm
57:413–427
Sandolo C, Pechine S, Le A, Hoys S, Janoir C, Coviello T et al (2011)
Encapsulation of Cwp84 into pectin beads for oral vaccination
against Clostridium difficile. Eur J Pharm Biopharm
79(3):566–573
Sriamornsak P, Nunthanid J (1999) Calcium Pectinate gel beads for
controlled release drug delivery: effect of formulation and
processing variables on drug release. J Microencapsul
16:303–313
Tripathi KD (2008) Essentials of medical pharmacology, 6th edn.
Jaypee Brother Medical Publishers (P) Ltd, New Delhi, p 528
Venkatesh G (2005) New tool for timed, pulsatile drug delivery.
Pharmaceutical formulation and quality. June–July 2005
Whitehead L, Collett JH, Fell JT (2000) Amoxycillin release from a
floating dosage form based on alginates. Int J Pharm 210:45–49
Table 5 Model fitting
Batch no. Zero order First order Higuchi model Korsmeyer-peppas model
R2 n R2 n R2 n R2 n
FA 0.7968 4.433 0.9034 -0.040 0.7771 22.24 0.7356 1.164
FB 0.8572 4.624 0.9492 -0.051 0.8124 22.87 0.8049 1.143
FC 0.8299 4.856 0.9462 -0.061 0.8010 24.24 0.7853 1.139
FD 0.7431 4.810 0.9065 -0.055 0.7777 24.99 0.7542 0.987
FCE 0.7902 4.580 0.8987 -0.048 0.8033 23.46 0.8072 0.968
FCF 0.7865 5.083 0.9372 -0.067 0.7707 25.56 0.7585 1.186
FCG 0.8430 4.341 0.9428 -0.039 0.7958 21.42 0.7396 1.200
R2 regression coefficient, n slope
Eur J Drug Metab Pharmacokinet