http://informahealthcare.com/drdISSN: 1071-7544 (print), 1521-0464 (electronic)
Drug Deliv, Early Online: 1–10! 2014 Informa Healthcare USA, Inc. DOI: 10.3109/10717544.2014.920430
RESEARCH ARTICLE
Perspectives of nanoemulsion assisted oral delivery of docetaxel forimproved chemotherapy of cancer
Prerna Verma1,2, Jaya Gopal Meher1, Shalini Asthana1, Vivek K. Pawar1, Mohini Chaurasia2, and Manish K. Chourasia1
1Pharmaceutics Division, CSIR-Central Drug Research Institute, Lucknow, India and 2Amity Institute of Pharmacy, Amity University, Lucknow, India
Abstract
Context: Nanoemulsions (NE) are one of the robust delivery tools for drugs due to their higherstability and efficacy.Objectives: The purpose of present investigation is to develop stable, effective and safe NE ofdocetaxel (DTX).Methods: Soybean oil, lecithin, Pluronic F68, PEG 4000 and ethanol were employed as excipientsand NEs were prepared by hot homogenization followed by ultra-sonication. NEs wereoptimized and investigated for different in vitro and in vivo parameters viz. droplet size, polydispersity index, charge; zeta potential, drug content and in vitro drug release, in vitrocytotoxicity, in vitro cell uptake and acute toxicity. Transmission electron microscopy wasperformed to study morphology and structure of NEs. Stability studies of the optimizedformulation were performed.Results: Droplet size, poly dispersity index, zeta potential, drug content and in vitro drugrelease were found to be 233.23 ± 4.3 nm, 0.24 ± 0.010, �43.66 ± 1.9 mV, 96.76 ± 1.5%,96.25 ± 2.1%, respectively. NE F11 exhibited higher cell uptake (2.83 times than control) andstrong cytotoxic activity against MCF-7 cancer cells (IC50; 13.55 ± 0.21mg/mL at 72 h) whereas notoxicity or necrosis was observed with liver and kidney tissues of mice at a dose of 20 mg/kg.Transmission electron microscopy ensured formation of poly-dispersed and spherical dropletsin nanometer range. NE F11 (values indicated above) was selected as the optimized formulationbased on the aforesaid parameters.Conclusion: Conclusively, stable, effective and safe NE was developed which might be used asan alternative DTX therapy.
Keywords
Acute toxicity, droplet size, MTT assay,soybean oil, zeta potential
History
Received 22 March 2014Revised 29 April 2014Accepted 29 April 2014
Introduction
Most of the anticancer/cytotoxic drugs are known to be
notorious as far as their pharmacokinetics (ADME) and
adverse drug effects are concerned (Undevia et al., 2005).
Taxoids (paclitaxel, docetaxel (DTX) etc.) are one of the
representative classes of cytotoxic drugs, which show various
undesirable side effects as well as low oral bioavailability
(510%) (Ganesh, 2007). The reasons for diminished bioavail-
ability is attributed to their low water solubility and high-
affinity for the P-glycoprotein (P-gp), which limit absorption
of the orally administered taxoids and mediates their direct
excretion into the gut lumen (Eytan & Kuchel, 1999; El-Readi
et al., 2010). Moreover cytochrome P450 (CYP 450) isoen-
zymes, abundantly found in the liver and gut wall also
contribute to high first-pass effect leading to poor
bioavailability (Spratlin & Sawyer, 2007). At such situation
the major challenges for scientists are to overwhelm interfer-
ence of biological barriers that confine the access of drugs to
target sites and also to develop drug delivery systems/drug
products with utmost therapeutic value. In this quest, one of
the simplest ways to resolve first-pass effect and bioavail-
ability issues may be parenteral route of administration, but it
results into patient incompliance, therapeutic complications,
high expenses, and poor quality of life. Alternatively, P-gp or
CYP 450 inhibitors such as cyclosporine may be employed to
minimize the metabolism/elimination of drug, but again these
are found to suppress body’s immune system and thus cause
severe health complications (Sweetman, 2007).
Aforementioned problems associated with taxoids create a
platform for the development of a novel drug delivery
system(s)/product(s), which may resolve the undesired effects
of taxoids. DTX is one of the effective anticancer drug
(preferably used for locally advanced or metastatic breast
cancer), commercially available as Taxotere� and Duopafei�.
These products contain high concentration of Tween-80 and
reported to show fluid retention, hypersensitivity, musculo-
skeletal toxicity, neurotoxicity as well as neutropenia
(Manjappa et al., 2013). Several research groups have
Address for correspondence: Manish K. Chourasia, Sr. Scientist,Pharmaceutics Division, CSIR-Central Drug Research Institute,Lucknow 226031, India. Tel:+91 522 2612411-18. Fax: +91 5222623405. Email: [email protected] Chaurasia, Amity Institute of Pharmacy, Amity University,Lucknow 226010, India. Tel: +91 522 2399418. Email:[email protected]
Dru
g D
eliv
ery
Dow
nloa
ded
from
info
rmah
ealth
care
.com
by
UB
der
LM
U M
uenc
hen
on 0
6/10
/14
For
pers
onal
use
onl
y.
reported different delivery systems of DTX ensuring better
therapeutic efficacy which include nanoparticles (Cho et al.,
2011), hydrogels (Bae et al., 2013), liposomes (Jinturkar
et al., 2012; Mishra et al., 2012), polymer-DTX conjugates
(Lee et al., 2009), micelles (Liu et al., 2008), solid oral
dispersions (Moes et al., 2011), micro needles and elastic
liposomes (Qiu et al., 2008) as well as solid self-nano
emulsifying delivery systems (Seo et al., 2013). Despite such
advancement in drug delivery, commercial/industrial viability
of these models are questionable, which might be accredited
to many issues especially stability and scale up of products.
Realizing the need for development of DTX in a
comparatively safe, stable and effective drug delivery
system, our research group started investigating a suitable
alternative and hypothesized that NE may serve as the robust
delivery system. A nanometric amphotericin B-encapsulated
chitosan nanocapsules using polymer deposition technique
mediated by NE template fabrication, which was a cost-
effective immune-adjuvant chemotherapeutic delivery system
is previously reported from our laboratory (Asthana et al.,
2013). NE, because of its nano size is believed to escape from
the recognition of P-gp and thus enhances the oral bioavail-
ability of taxoid, at the same time all complications of
parenteral administration also circumvent by this novel
approach (Dasgupta et al., 2013). Into the bargain, NEs
could shield integrated drug molecules from the gastric
degradation, gut wall metabolism and also prevent the first-
pass metabolism. NEs are comparatively stable bi-/multi-
phasic systems than liposomes, ethosomes or microspheres
with additional advantage of improved solubility as well as
absorption of poor bioavailable drugs (Gupta et al., 2005;
Chaurasia et al., 2008, Chourasia et al., 2011).
Based on our hypothesis and the features associated with
NEs, a NE delivery system for DTX (model drug representing
taxoids) has been proposed in the present research work. DTX
(C43H53NO14) is a semi-synthetic analogue of paclitaxel
having very poor water solubility (4.93 mg/mL) (Gao et al.,
2008; Yin et al., 2009). Because of low water solubility
dissolution is the rate limiting step in the absorption and
bioavailability of DTX. For the development of DTX NE,
soybean oil was employed as a solubilizer of drug, Pluronic
F68 and lecithin as surfactant, whereas ethanol and PEG 4000
were used as co-surfactant and stabilizer respectively. The
developed NEs were characterized for different in vitro and
in vivo parameters as well as subjected to stability studies.
The objective of this research work was to develop stable,
effective and safe NEs containing DTX by utilizing drug
delivery approach with broad aim to improve the chemother-
apy of cancer.
Materials and methods
Materials
Chemicals and biochemicals
Docetaxel was generously provided by Intas Pharma,
Ahmedabad, India as a gift sample. Poloxamer (Pluronic
F68), soya lecithin, Polyethylene glycol (PEG) 4000, soybean
oil, bovine serum albumin (BSA), MTT (3-[4, 5-dimethylthia-
zol-2-yl]-2, 5-diphenyltetrazolium bromide), DMEM and all
other chemicals, bio-chemicals and solvents were purchased
from Sigma-Aldrich, (St. Louis, MO). Ultrapure water
obtained by Millipore Milli-Q system (Bedford, MA) was
utilized throughout the experiments. Analytical reagent grade
chemicals and ingredients were used in the present studies as
received from the distributor/supplier without any modifica-
tion/alteration.
Laboratory animals and cell lines
MCF-7 cell lines procured from Microbial Type Culture
Collection and Gene Bank, Chandigarh, India were used for
in vitro cytotoxicity studies. Cell lines were maintained in
RPMI-1640 medium supplemented with 10% heat inactivated
fetal bovine serum, 100mg/mL streptomycin and 100m/mL
penicillin at 37 ± 2 �C in humidified atmosphere (5% CO2/air
mixture). Female Swiss mice weighing 30–35 g were obtained
from institutional animal house (CSIR-CDRI, Lucknow,
India) for in vivo acute toxicity studies. In vivo studies were
carried out with prior approval of the Animal
Ethics Committee of Central Drug Research Institute,
Lucknow. All animal experimentations were conducted
according to the guidelines of the Council for the Purpose
of Control and Supervision of Experiments on Animals
(CPCSEA), Ministry of Social Justice and Empowerment,
Government of India.
Methods
Preparation of NEs
NEs were prepared by a prototype hot homogenization
followed by ultra-sonication method (Sakulku et al., 2009).
Briefly, DTX was dissolved in soybean oil by sonication
(Vibra-Cell, Sonics) with moderate heating to get a clear
solution. The aqueous phase was prepared by mixing ethanol
and water, in which PEG 4000 was dispersed. Pluronic F68
and/or lecithin were dispersed in aqueous phase, which was
added drop wise to the oil phase under stirring
(25000 ± 200 rpm, Ultra-Turax T25, IKA, Germany) for
30 min in order to get a coarse emulsion. Afterwards, the
coarse emulsion was homogenized (Vibra-Cell, Sonics, USA)
to get the NE. Placebo NEs were prepared by the same
procedure omitting drug. The developed NEs were stored at
room temperature (22 ± 1 �C) until used for further
characterizations.
Optimization of NEs
The effect of formulation variables viz. type of surfactant, oil,
co-surfactant, and surfactant mixture (surfactant and
co-surfactant) ratio on NEs and their characteristics were
studied. Optimization of NEs was done with monitoring of
some selected parameters viz. droplet size, zeta potential and
drug content (Muller et al., 2012).
Characterization of NEs
NEs were characterized for various in vitro and in vivo
parameters viz. size, shape, surface morphology, charge (zeta
potential), drug content, in vitro drug release, in vitro cell
uptake, in vitro cytotoxic activity, in vivo acute toxicity and
stability studies.
2 P. Verma et al. Drug Deliv, Early Online: 1–10
Dru
g D
eliv
ery
Dow
nloa
ded
from
info
rmah
ealth
care
.com
by
UB
der
LM
U M
uenc
hen
on 0
6/10
/14
For
pers
onal
use
onl
y.
Droplet size and zeta potential
The mean droplet size and size distribution were measured by
photon correlation spectroscopy with a Zetasizer NanoZS
(Malvern, UK) at 22 ± 1 �C (Oh et al., 2011). DTX NE
samples were diluted to the appropriate concentration with
distilled water before measurement, filled in the cuvette and
measured for the mentioned parameters. The size distribution
of NEs droplets was represented by the polydispersity index
(PDI) values. Zeta potential was determined using electro-
phoretic mobility with laser-based multiple-angle particle
electrophoresis analyzer at 22 ± 1 �C (Zetasizer Nano-ZS,
Malvern, UK) (Oh et al., 2011).
Droplet shape and surface morphology
Transmission electron microscopy (TEM; Tecnai� G2 F20,
Eindhoven, Netharlands) was employed for the analysis of
shape and surface morphological characteristic of DTX NEs.
NE sample was prepared as a thin aqueous film held on a
300-mesh copper grid. A droplet of 2% (w/v) phosphotungstic
acid was used for negative staining and excess was drawn off.
Samples were dried and observed by TEM and images were
taken at a 200 kV acceleration voltage and recorded for
interpretation (He et al., 2013).
Drug content
High performance liquid chromatography (LC-10ATvp HPLC
instrument, Tokyo, Japan) with Lichrosphere reverse-phase
C18 column (250� 4 mm, 5 mm; Merck, Darmstadt,
Germany) was employed for the determination of quantity
of DTX in DTX NEs (Asthana et al., 2013). In brief,
accurately measured quantity of DTX NEs was dissolved in
0.5 mL dichloromethane (DCM) and mixed with 2 mL of
mobile phase (acetonitrile: deionized water; 65:35, v/v). The
above mixture was vortexed for 5 min, and DCM was
evaporated under a nitrogen stream until a clear solution
was obtained. The solution was analyzed by HPLC after
filtering through 0.45mm syringe filter. The flow rate of
mobile phase was set at 1.0 mL/min and column effluent was
detected with a UV detector at 230 nm. DTX was eluted
with mobile phase at 3.2 min. Linearity of response for
DTX quantization was verified in the concentration range
400–64 000 ng/mL with a correlation coefficient (R2) 0.998.
In vitro drug release
The in vitro drug release study was performed using dialysis
membrane diffusion method (Jiang et al., 2013). Accurately
the measured amount of DTX NE was filled in a dialysis bag
(cellulose membrane, MWCO: 12 KDa), sealed at both ends
and suspended in dissolution apparatus (DISSO 2000,
Labindia, India) containing 250 mL of phosphate buffer
saline (PBS; pH 7.4) with 0.1% w/v Tween 80 in order to
maintain sink conditions. Temperature of dissolution medium
was maintained at 37 ± 1 �C with moderate shaking at
100 ± 5 rpm. At predetermined time intervals, 1 mL of the
release medium was withdrawn and replaced with equal
volume of fresh pre-warmed medium. The withdrawn samples
were diluted and analyzed for the drug content by developed
HPLC method at 230 nm.
Stability studies
DTX NEs (F11) were stored in screw capped, amber colored
small glass bottles at 4 ± 1 and 22 ± 1�C temperature.
Samples were analyzed for droplet size and residual drug
content at time intervals of 10, 20, 30, 60 and 90 days (Kong
& Park, 2011).
In vitro cell uptake studies
A qualitative estimation was performed using fluorescence
activated cell sorting method (FACS) to depict the cell uptake
affinity of the developed NEs (Liu et al., 2011). MCF-7 cells
were seeded at a density of 2� 105 cells/well in a 6-well plate
and allowed to adhere over night with surface of the culture
plate. After 24 h, old media was exchanged with fresh media
containing FITC loaded NE and allowed incubation in a
controlled environment overnight. Subsequently, cells were
washed three times with PBS to remove any surface adhered
formulation. Washed cells were suspended in PBS and cell
assisted florescence was measured using flow cytometer (BD
Biosciences, FACS Aria, Germany) at an excitation wave-
length of 485 nm and an emission wavelength of 538 nm.
In vitro cytotoxicity studies
Cancer cell viability affected by DTX NEs and Taxotere
(marketed formulation) was evaluated using the 3-[4, 5-
dimethylthiazol-2yl]-2, 5-diphenyltetrazolium bromide
(MTT) assay (He et al., 2013). Briefly, 104 MCF-7 cells/
well were seeded in 100 mL DMEM, supplemented with 10%
FBS in each well of 96-well micro culture plates and
incubated for 24 h at 37 ± 1 �C in a CO2 incubator till 70%
confluence was reached. Cells were exposed to various
concentrations of DTX NEs, Taxotere and free drug (DTX) at
5, 10, 15, 20, 25, 30 mg/mL equivalent drug concentrations as
well as placebo NE for 24 and 72 h. At predetermined time,
the formulations were replaced with DMEM containing MTT
(500 mg/mL) and cells were incubated for additional 4 h. MTT
was aspirated off and dimethylsulfoxide (200mL) was added
to dissolve the formed crystals. Absorbance was measured at
570 nm by multi-well microplate reader (BIO-TEK, Model-
Power wave XS, Crailsheim, Germany). Cell death (%) was
expressed as the percentage of absorbance of transformed
MTT in cells incubated with formulations relative to that of
the untreated cells as control. The IC50 values were calculated
graphically (logarithmic scale) by plotting percent cell death
versus concentration.
In vivo acute toxicity studies
Female Swiss mice weighing 30–35 g were randomly grouped
(6 mice/group) into (1) DTX NEs treated, (2) free drug (DTX)
treated, (3) placebo NEs treated and (4) untreated control
group. Before administration, free drug (DTX), DTX NEs and
placebo NEs were re-suspended separately in purified water
to reach the desired concentration (20 mg/kg). Mice in all the
4 groups were orally administered with respective formula-
tions. Body weight and behavior of the animals were observed
and recorded throughout the acute toxicity studies. After
14 days animals were sacrificed and kidney and liver tissues
were isolated, fixed in 10% formalin. The tissues were
DOI: 10.3109/10717544.2014.920430 Nanoemulsion assisted oral delivery of docetaxel 3
Dru
g D
eliv
ery
Dow
nloa
ded
from
info
rmah
ealth
care
.com
by
UB
der
LM
U M
uenc
hen
on 0
6/10
/14
For
pers
onal
use
onl
y.
embedded in paraffin and sectioned as well as stained with
haematoxylin and eosin for histo-pathological analysis. The
sections were observed under an optical microscope (Eclipse
50i, Nikon, kawasaki, Kanagawa, Japan) and photomicro-
graphs of the sections, were recorded for comparison and
interpretation of acute toxicity (Tang et al., 2012).
Statistical analysis
Values of experimental results are expressed as mean ± SEM
(n¼ 3). One way ANOVA was employed to investigate any
significant difference in evaluation parameters (particle size,
PDI, zeta potential, in vitro drug release, in vitro cell uptake
and in vitro cytotoxicity evaluation) and student’s t test was
used to analyze any statistical difference in evaluation
parameters (particle size and drug content) during stability
studies, using GraphPad Prism 5 (Version 5.01) statistical
software.
Results and discussion
The objective of the present investigation was to develop NEs
of DTX which could ensure better therapeutic efficacy. NEs
were successfully developed and characterized for different
in vitro, in vivo parameters as well as subjected to stability
analysis. Developed NEs were optimized on the basis of
droplet size, zeta potential and drug content which were
influenced by the surfactant, co-surfactant and oil used in the
formulation development. The optimized NEs were evaluated
for cytotoxic potential using MCF-7 cancer cell lines and the
in vitro cell uptake as well as in vivo toxicity aspects were
also experimentally scrutinized.
Formulation and optimization of NEs
Pharmaceutical ingredients and their ratio used in the
formulation of NEs are depicted in Table 1. Five different
series of NEs (F1-F3, F4-F5, F6-F7, F8-F9 and F10-F11)
were formulated by varying the surfactants/co-surfactant/oil/
drug concentration. In the first two series the concentration of
soybean oil and ethanol was fixed whereas lecithin and
Pluronic F68 were varied. In the third and fourth series,
concentration of soybean oil and ethanol were altered but
lecithin and Pluronic F68 were kept constant. In the last
i.e. fifth series of NEs, the concentration of DTX was varied
keeping other ingredients unchanged as F1. The changes in
the ingredients/drug were not random, but guided by the
characterization parameters viz. droplet size, charge as well as
drug content. In the subsequent section (3.2 characterizations
of NEs) the optimization of NEs as directed by the aforesaid
parameters is discussed ins and outs.
Characterization of NEs
Parameters influencing thermodynamic activity viz. droplet
size, PDI and zeta potential are very much crucial in the
formulation of NEs (Muller et al., 2012). The results of these
characterization parameters are shown in Table 2. Among the
above said parameters, droplet size of the NEs is central
protagonist, as it regulates the rate and extent of drug release
as well as absorption. Drug can diffuse faster from smaller
droplets into the aqueous phase, thereby increasing the drug
dissolution. Moreover, smaller droplet provides larger surface
area for drug absorption. Reduction in droplet size and PDI
improves bio-availability of emulsion as compared to a coarse
emulsion (Asthana et al., 2013).
For the qualitative selection of surfactant and
co-surfactant, NEs were prepared, in which one of the
ingredients was omitted and other ingredients were kept
constant. As discussed in the formulation and optimization
(section 3.1), in formulation F1, the surfactants lecithin:
Pluronic F68 (1:1) and co-surfactant – PEG 4000 were taken
in equal amount. In F2, Pluronic F68 was excluded and other
contents were kept constant as in F1 whereas in F3, PEG-400
has been skipped keeping rest of the excipients unaltered as in
F1. Between these three NEs only F1 (lecithin: Pluronic F68:
PEG in 1:1:1; Table 1) passed the stability test and was of
smallest size (252.93 ± 7.4 nm; Table 2). There was signifi-
cant difference (p50.05) in the particle size, PDI, and zeta
potential of these formulations. Based on the outcomes,
lecithin, Pluronic F68 and PEG 4000 were included for
further optimization study in next series of NEs. NEs without
Pluronic (F2) was degraded few minutes after preparation,
Table 1. Composition of the NE formulations.
Formulationcodea
Soya beanoil (mL)
Egg lecithin(mg)
PluronicF68 (mg)
PEG 4000(mg)
Ethanol(mL)
Docetaxel(mg)
Water(mL)
First series Quantity sufficient (up to 10 mL)F1 2 100 100 100 3 0.5F2 2 100 – 100 3 0.5F3 2 100 100 – 3 0.5
Second seriesF4 2 50 50 100 3 0.5F5 2 100 100 50 3 0.5
Third seriesF6 1 100 100 50 3 0.5F7 3 100 100 50 3 0.5
Fourth seriesF8 2 100 100 50 2 0.5F9 2 100 100 50 4 0.5
Fifth seriesF10 2 100 100 100 3 1F11 2 100 100 100 3 10
aplacebo NE for each series were prepared.
4 P. Verma et al. Drug Deliv, Early Online: 1–10
Dru
g D
eliv
ery
Dow
nloa
ded
from
info
rmah
ealth
care
.com
by
UB
der
LM
U M
uenc
hen
on 0
6/10
/14
For
pers
onal
use
onl
y.
which might be attributed to the inadequate balance of
surfactant-PEG combination in NE. On the contrary, F3 NE,
which was devoid of PEG was prepared, however the
formulation was appeared to be unstable upon storage. Any
bi/multi-phasic system requires a specific hydrophilic lipo-
philic balance (HLB) in order to attain stability for a definite
period of time and a combination of surfactants in specific
ratio could achieve stability by reducing the interfacial
tension of immiscible phages (Meher et al., 2013; Yadav
et al., 2013). In the present formulation, a combination of
lecithin, Pluronic and PEG in the same ratio was indeed
required to develop a stable NE containing soybean oil and
DTX. Hosny et al. and Brusewitz et al. have employed PEG
and Poloxamer in the development of nanoemulsion and
reported these to be effective in maintaining the stability of
the nanoemulsions (Brusewitz et al., 2007; Hosny & Banjar,
2013).
Furthermore, for the quantitative optimization of the
surfactant and co-surfactant ratio, two NE formulations
(F4 and F5) were prepared, where F5 (droplet size;
264.50 ± 4.3 nm, PDI; 0.25 ± 0.005; Table 2) was found to
be superlative between these formulations. Observation of
particle size and PDI indicated that higher concentration of
PEG was not in favor of stable NE, rather less i.e. half
concentration of PEG and equal ratio of surfactant (lecithin
and Pluronic, Table 1) were suitable for the development of a
stable NE. This behavior of NEs was attributed to the
thermodynamic commotion of bi/multi-phasic system and
surfactant-co-surfactant ratio (Dasgupta et al., 2013). PEG
4000 is one of the commonly used excipients of generally
recognized as safe (GRAS) category which has got wide
application as co-surfactant, solubilizer, co-solvent as well as
drug-targeting agent like chitosan, PLGA and Azo polymers
etc. (Jain et al., 2005; Cheng et al., 2007). In the current
formulation PEG exhibited promising activity in stabilization
of emulsion.
In next series (3rd series) of formulations, concentration of
soybean oil and stability of NEs were examined. Soybean oil
is an edible oil and has been used in the preparation of
pharmaceutical formulations as solubilizer of drug molecules
(Bilbao-Sainz et al., 2010; He et al., 2011). In the present
study it was employed as the solubilizer of DTX.
In formulation F6 and F7, the concentration of oil was
1 and 3 mL, respectively (Table 1). Apart from the stability,
drug content was another parameter which was optimized
for these formulations. Results of these parameters are
exhibited in Table 2. Between F5, F6 and F7 NEs, F5 was
found to display higher content of the drug (82.30 ± 1.2%).
NE F6 showed lower drug content (75.38 ± 1.8%) as
compared to F5 but it could pass the stability evaluation.
On the other hand F7 was degraded out after few hours of
preparation, which was assumed due to higher concentration
of soybean oil (3 mL) leading to imbalance in HLB require-
ment of NE. Based on these results, NE F5 was further
continued in the optimization process in order to get the best
formulation.
The next excipient to be optimized was ethanol, which was
playing the role of a co-surfactant. In the 4th series of NE
formulation, F8 and F9 were prepared containing 2 and 4 mL
of ethanol, respectively. Both of these NEs were degraded in
the stability evaluation. The role of co-surfactant is to impart
either rigidity or flexibility to the tight layer of surfactant-
co-surfactant mixture surrounding the oil droplets in the NEs
(Peng et al., 2010). As the HLB requirement of a particular oil
(mixture of oils) is very much specific, any fluctuation in the
same may disrupt the thermodynamic stability causing
degradation of NEs (Hosny & Banjar, 2013). Here, in this
case the change in concentration of ethanol caused a change
in the required HLB by increasing the hydrophilicity and led
to destabilization of F8 and F9.
So far, the NEs F1, F4, F5 and F6 could clear the stability
tests showing thermodynamic steadiness. There was signifi-
cant difference (P50.05) in thermodynamic parameters
(particle size, PDI and zeta potential) and in vitro drug
release of the above NEs. Among these NEs, F5 and F6
demonstrated excellent results as far as thermodynamic
parameters were concerned. But as and when, the other
parameters viz. drug content and in vitro drug release were
taken into consideration, F1 dominated both F5 and F6
(Table 2). Based on the above discussion, F1 was selected as
the optimized NE and further, concentration of drug was
attempted to be optimized.
Table 2. Physicochemical parameters of the DTX NEs.
Formulation code Particle size (nm) Zeta potential (mV) PDI Stability status Drug Content (%) Drug Releasea (%)
First seriesF1 252.93 ± 7.4 �46.16 ± 2.2 0.34 ± 0.019 Pass 97.53 ± 0.9 94.64 ± 1.3F2 ND ND ND Fail ND NDF3 277.30 ± 5.5 �44.86 ± 2.0 0.34 ± 0.009 Fail ND ND
Second seriesF4 286.66 ± 3.8 �35.90 ± 2.5 0.36 ± 0.008 Pass 80.40 ± 1.3 71.73 ± 3.0F5 264.50 ± 4.3 �35.13 ± 1.8 0.25 ± 0.005 Pass 82.30 ± 1.2 81.81 ± 1.5
Third seriesF6 228.56 ± 4.2 �41.11 ± 0.9 0.16 ± 0.008 Pass 75.38 ± 1.8 59.68 ± 5.2F7 229.03 ± 5.6 �45.13 ± 1.6 0.20 ± 0.009 Fail 71.96 ± 1.1 ND
Fourth seriesF8 275.40 ± 5.0 �54.83 ± 1.8 0.15 ± 0.009 Fail 41.46 ± 2.4 NDF9 385.90 ± 8.1 �53.73 ± 1.3 0.40 ± 0.006 Fail 45.51 ± 1.7 ND
Fifth seriesF10 241.50 ± 3.9 �45.00 ± 1.5 0.28 ± 0.006 Pass 96.57 ± 0.9 94.46 ± 2.4F11 233.23 ± 4.3 �43.66 ± 1.9 0.24 ± 0.010 Pass 96.76 ± 1.5 96.25 ± 2.1
Mean ± SEM (n¼ 3), PDI; Poly dispersity index; ain vitro drug release at 12 h, ND; not determined.
DOI: 10.3109/10717544.2014.920430 Nanoemulsion assisted oral delivery of docetaxel 5
Dru
g D
eliv
ery
Dow
nloa
ded
from
info
rmah
ealth
care
.com
by
UB
der
LM
U M
uenc
hen
on 0
6/10
/14
For
pers
onal
use
onl
y.
In the 5th series of NE formulations, F10 and F11 were
prepared where concentration of drug was 1.0 and 10.0 mg/
mL respectively. F11 exhibited smaller droplet size
(233.23 ± 4.3 nm), lower PDI (0.24 ± 0.010) and higher zeta
potential (�43.66 ± 1.9 mV) in comparison to F10 (Table 2).
Although there were no significant difference in the thermo-
dynamic profile of F11 and F10, the higher accommodation
of DTX suggested F11 NEs to be the optimized formulation.
The percent drug release from F11 formulation was found to
be 96.25 ± 2.1% and drug content was determined to be
96.76 ± 1.5%. The drug release mechanism was found to be
zero order and non-fickian diffusion controlled. The drug
release kinetics data of F1, F4, F5, F6, F10 and F11 NEs
[those passed stability test (Table 2)] is presented in Table 3.
Finally, optimized NE F11 was characterized for shape and
surface morphology, in vitro cytotoxic potential, cell uptake
in animal cell lines and in vivo acute toxicity studies in mice.
The NE (F11) appeared bright and the surrounding was dark
in TEM as it was clear from the image (Figure 1).
The droplets were clearly visible as a poly-dispersed system
of emulsified soybean oil (Figure 1A). Some equally
distributed droplet sizes were measured using TEM, as it
was capable of point to point resolution. Figure 1(B) exhibits
the magnified view with droplet size. The droplet size is in
agreement with the results obtained from droplet size analysis
(Table 2). TEM analysis ensured the development of a
polydisperse NE.
Stability of NEs
Stability of a product during its self-life is an important aspect
in the successful development of dosage form (Singh et al.,
2013). Hence, a well-designed stability-testing plan is essen-
tial for the development of NE. NEs were stored at two
different storage conditions i.e. 4 ± 1 and 22 ± 1 �C and were
subjected to stability studies. Droplet size and residual drug
content upon aging were selected as the evaluation criteria for
the stability analysis. Mean droplet size of NEs was found to
increase on storage, which could be due to coalescence of oil
droplets over time. Figure 2(A and B) demonstrate the pattern
of increasing NE droplet size upon storage at 4 ± 1 �C and
Figure 2. Plots showing effect of storage at (A) 4 ± 1 �C and (B) 22 ± 1 �C on particle size and drug content of F11 NE.
Figure 1. TEM photomicrograph of DXT NEs (A) broad view (B) magnified view.
Table 3. Tumor cells inhibition activity of NE and Taxotere after 24 and72 h incubation with MCF cells in 96-well plate.
IC50 (mg/mL)a DTX NE (F11) Taxotere Free Drug (DTX)
After 24 h incubation 23.19 ± 0.12 17.38 ± 0.65 18.88 ± 0.38After 72 h incubationb 13.55 ± 0.21 16.56 ± 0.34 17.11 ± 0.16
Results represented in terms of IC50; calculated from percent cell deathagainst various equivalent concentration of DTX represented viadeveloped NE and marketed formulation.
aMean ± S.E.M. (n¼ 3).bSignificant difference (p50.05) between DTX NE versus Taxotere and
DTX NE versus free drug (DTX).
6 P. Verma et al. Drug Deliv, Early Online: 1–10
Dru
g D
eliv
ery
Dow
nloa
ded
from
info
rmah
ealth
care
.com
by
UB
der
LM
U M
uenc
hen
on 0
6/10
/14
For
pers
onal
use
onl
y.
22 ± 1 �C, respectively. There was a significant difference
(p50.05) in the mean droplet size of NEs (F11) at these two
different storage conditions. Such behavior leading to
thermodynamic instability was observed to be least with
NEs stored at 22 ± 1 �C, which indicated that coalescence
could be controlled by storage of formulation at this
temperature. The NEs stored at 4 ± 1 �C exhibited higher
increase in droplet size (coalescence) which might be
attributed to the fact that at low temperature, NE droplets
tend to aggregate/coalesce (Rahn-Chique et al., 2012). Jiang
et al., have reported an increase in particle size up to 100 nm
at room temperature in a three months stability study of
nanoemulsion but they did not find any variation in the
entrapment efficiency (Jiang et al., 2013). Percent of residual
drug remaining in NEs over storage was investigated by
determining the drug content at different time intervals as
described in the section 2.2.3.5. In both the storage conditions
a decrease in drug content was detected, however no
significant difference (p50.05) was found in the residual
drug content on aging at these two different storage condi-
tions. Figures 2(A) and (B) exhibit the residual drug content
at 4 ± 1 �C and 22 ± 1 �C respectively. It was comprehended
that after 90 days of storage, NEs stored at 4 ± 1 �C illustrated
86.93 ± 2.13% drug whereas 91.1 ± 0.96% was found with
NEs stored at 22 ± 1 �C. Based on the results obtained from
stability analysis, NE F11 stored at 22 ± 1 �C was found to be
comparatively stable and further subjected to in vitro cell
uptake, cytotoxicity and acute toxicity studies.
Cell uptake and cytotoxicity
The qualitative NE ingestion capability via MCF-7 cells was
evaluated using FACS. Results demonstrated a 2.83 times
higher mean florescence intensity of FITC loaded NE in
comparison to control cells. FACS histogram and mean
florescence intensity of control NE are represented in
Figure 3. Higher mean florescence intensity signifies higher
internalization of the fluorescence tagged moieties. The
internalization of the NEs would be processed through core
triglyceride (soybean oil) which undergoes a partially solu-
bilization upon contact with cellular phospholipid layer. Acyl
chains of triglyceride cause a partial penetration into the
hydrophobic domain of the surface phospholipid monolayers
resulting in separation of surface head group as to engage
Figure 3. Cell uptake by flow cytometer (A) FACS histogram showing uptake of NE in MCF-7 cells. (B) Mean florescence intensity of control andNE; *a significant difference was noticed at level p50.01.
Figure 4. Cytotoxic effect of developed and marketed formulation in terms of percent cell death. Cytotoxic potential after (A) 24 h and (B) 72 hincubation of DTX NE, Taxotere, free drug (DTX) and placebo NE with MCF cells.
DOI: 10.3109/10717544.2014.920430 Nanoemulsion assisted oral delivery of docetaxel 7
Dru
g D
eliv
ery
Dow
nloa
ded
from
info
rmah
ealth
care
.com
by
UB
der
LM
U M
uenc
hen
on 0
6/10
/14
For
pers
onal
use
onl
y.
Figure 5. Acute toxicity in animals. (A) Percent body weight change in mice after treatment with DTX NEs, placebo NE, Taxotere and free drug(DTX). (B) Representative photographs showing histopathology of liver and kidney tissues of mice after 14 days of treatment (dose 20 mg/kg) DXTNEs treated (a) liver, (b) kidney, free drug (DXT) treated (c) liver, (d) kidney, placebo NE treated (e) liver, (f) kidney.
8 P. Verma et al. Drug Deliv, Early Online: 1–10
Dru
g D
eliv
ery
Dow
nloa
ded
from
info
rmah
ealth
care
.com
by
UB
der
LM
U M
uenc
hen
on 0
6/10
/14
For
pers
onal
use
onl
y.
space for apoprotein binding (Saito et al., 2001; Tanaka et al.,
2003).
In order to confirm the cytotoxic potential of the NEs MTT
assay was performed employing MCF-7 cancer cell line.
A comparative cytotoxic effects of DTX NEs (F11), DTX and
Taxotere at 5, 10, 15, 20, 25, 30 mg/mL equivalent drug
concentrations as well as placebo NE were evaluated.
Figure 4(A and B) illustrate the percent cell death of MCF-
7 cells following incubation for 24 and 72 h, respectively.
There was significant difference (p50.05) in the percent cell
death of placebo NE, DTX NE (F11), Taxotere and free drug
(DTX). Experimental findings clearly suggested an aug-
mented reduction in viability of MCF-7 cells with increase in
drug concentration. Cytotoxicity of DTX NE was found to be
increased with rise in drug concentration but after the initial
incubation period (24 h) it was found to be less than both free
DTX and Taxotere. Similarly after 72 h of incubation
cytotoxicity of DTX NE was observed to be increasing but
higher cytotoxicity was noticed with DTX NE in comparison
to the free DTX and Taxotere. Such behavior of DTX NE
might be attributed to the sustained release of DTX from NE,
which is in agreement with the drug release kinetics of DTX
NEs (Table 3). The IC50 values further support the results that
DTX NE exhibited IC50 13.55 ± 0.21mg/mL, whereas
Taxotere and free drug (DTX) showed IC50 16.56 ± 0.34
and 17.11 ± 0.16mg/mL respectively. These results suggested
stronger cytotoxic activity of DTX NE in comparison to both
marketed formulation Taxotere and free drug (DTX), which in
turn indicate less drug is required for cytotoxic action in
NE formulations. Current findings are in agreement with
previously reported NEs, liposomes and nanoparticles,
advocating higher cytotoxic effect of these delivery systems
than the conventional systems (Dıaz et al., 2006; Choudhury
et al., 2014).
Acute toxicity
Many authors have demonstrated acute toxicity of nano-
particulate formulations. Such toxicity is due to the accumu-
lation of nanoparticles in some specific tissues (Beer et al.,
2012; Hu et al., 2012). In order to verify the toxicity potential
of DTX NE (F11), it was exposed to in vivo environment in
mice. The behavior of all the animals was found normal
throughout the study however, a significant variation
(p50.05) was observed in the body weights of the animals
treated with free drug (DTX) and DTX NE. Figure 5 displays
the percent body weight change in mice after treatment with
DTX NEs, placebo NE, Taxotere and free drug (DTX). Based
on the findings of histo-pathological studies, no particular
toxicity and/or necrosis were observed in liver and kidney
tissues with single dose of DTX NEs (Figure 5a and b), which
makes ground to claim that developed NE can be safely used
in vivo at concentration up to 20 mg/kg body weight. On the
contrary examination of liver tissues in free drug (DTX)
treated group revealed focal lesions surrounding a cluster of
necrotic hepatocytes, isolated foci of necrotic hepatocytes and
hepatocytes in the centrilobular zone showing degenerative
features (Figure 5c). Moreover, histo-pathological analysis of
kidney tissue treated with free drug (DTX) showed patchy
tubular epithelial necrosis that varied in extent from focal to
extensive (Figure 5d). The untreated group exhibited no sign
of any of the above mentioned abnormalities either in liver
(Figure 5e) or kidney (Figure 5f). The excipients used in NE
formulations are of GRAS category and hence the toxicity
seen in the free drug treated group is due to the DTX.
Comparatively lower toxicity of NEs is also reported by
several authors which is attributed to controlled exposition of
drug to tissues (Borhade et al., 2012; Asthana et al., 2013).
Conclusion
Stable (up to three months) NEs containing DTX (10 mg) was
successfully formulated with lecithin, Pluronic and PEG in
equal ratio (1:1:1) in combination with soybean oil (2 mL) and
ethanol (3 mL). In vitro cytotoxicity evaluation in MCF-7
cancer cell lines ensured the selective uptake of DTX NEs
to cells and exhibited promising cytotoxicity (IC50
13.55 ± 0.21 mg/mL) corroborating it to be effective. In vivo
acute tissue toxicity in mice demonstrated not any specific
toxicity and/or necrosis in the liver and kidney tissues with
single dose of DTX NEs (520 mg/kg), supporting it to be safe
for use.
In conclusion a stable, effective and safe NE was
formulated as well as characterized, however the clinical
investigations and scale up issues remain as the future scope
of present investigation.
Acknowledgements
Authors are thankful to SAIF, CSIR-Central Drug Research
Institute, Lucknow for providing facilities to perform cell
uptake using FACS. Authors extend their sincere thanks to
CSIR for granting financial assistance (network project
CSC0302) to the present investigation. Intas Pharma,
Ahmedabad, India is duly acknowledged for providing
docetaxel drug as gift sample.
Declaration of interest
All authors involved in the present research work declare no
conflict of interest. CSIR-CDRI Communication No.: 8677.
References
Asthana S, Jaiswal AK, Gupta PK, et al. (2013). Immunoadjuvantchemotherapy of visceral leishmaniasis in hamsters using amphoteri-cin B-encapsulated nanoemulsion template-based chitosan nanocap-sules. Antimicrob Agents Chemother 57:1714–22.
Bae WK, Park MS, Lee JH, et al. (2013). Docetaxel-loaded thermo-responsive conjugated linoleic acid-incorporated poloxamer hydrogelfor the suppression of peritoneal metastasis of gastric cancer.Biomaterials 34:1433–41.
Beer C, Foldbjerg R, Hayashi Y, et al. (2012). Toxicity of silvernanoparticles-nanoparticle or silver ion? Toxicol Lett 208:286–92.
Bilbao-Sainz C, Avena-Bustillos RJ, Wood DF, et al. (2010).Nanoemulsions prepared by a low-energy emulsification methodapplied to edible films. J Agric Food Chem 58:11932–8.
Borhade V, Pathak S, Sharma S, Patravale V. (2012). Clotrimazolenanoemulsion for malaria chemotherapy. Part II: Stability assessment,in vivo pharmacodynamic evaluations and toxicological studies.Int J Pharm 431:149–60.
Brusewitz C, Schendler A, Funke A, et al. (2007). Novel poloxamer-based nanoemulsions to enhance the intestinal absorption of activecompounds. Int J Pharm 329:173–81.
Chaurasia M, Chourasia M, Jain NK, et al. (2008). Methotrexate bearingcalcium pectinate microspheres: a platform to achieve colon-specificdrug release. Curr Drug Deliv 5:215–19.
DOI: 10.3109/10717544.2014.920430 Nanoemulsion assisted oral delivery of docetaxel 9
Dru
g D
eliv
ery
Dow
nloa
ded
from
info
rmah
ealth
care
.com
by
UB
der
LM
U M
uenc
hen
on 0
6/10
/14
For
pers
onal
use
onl
y.
Cheng J Teply BA, Sherifi I, et al. (2007). Formulation of functionalizedPLGA–PEG nanoparticles for in vivo targeted drug delivery.Biomaterials 28:869–76.
Cho H-J, Yoon HY, Koo H, et al. (2011). Self-assembled nanoparticlesbased on hyaluronic acid-ceramide (HA-CE) and Pluronic� for tumor-targeted delivery of docetaxel. Biomaterials 32:7181–90.
Choudhury H, Gorain B, Karmakar S, et al. (2014). Improvement ofcellular uptake, in vitro antitumor activity and sustained releaseprofile with increased bioavailability from a nanoemulsion platform.Int J Pharma 460:131–43.
Chourasia MK, Kang L, Chan SY. (2011). Nanosized ethosomes bearingketoprofen for improved transdermal delivery. Results Pharma Sci1:60–67.
Dasgupta S, Dey S, Choudhury S, Mazumder B. (2013). Topical deliveryof aceclofenac as nanoemulsion comprising excipients having opti-mum emulsification capabilities: preparation, characterization andin vivo evaluation. Expert Opin Drug Deliv 10:411–20.
Dıaz C, Vargas E, Gatjens-Boniche O. (2006). Cytotoxic effect inducedby retinoic acid loaded into galactosyl-sphingosine containing lipo-somes on human hepatoma cell lines. Int J Pharm 325:108–15.
El-Readi MZ, Hamdan D, Farrag N, et al. (2010). Inhibition ofP-glycoprotein activity by limonin and other secondary metabolitesfrom Citrus species in human colon and leukaemia cell lines. Eur JPharmacol 626:139–45.
Eytan GD, Kuchel PW. (1999). Mechanism of action of p-glycoprotein inrelation to passive membrane permeation. In: Kwang WJ (ed.)International review of cytology. Academic Press. 175–250.
Ganesh T. (2007). Improved biochemical strategies for targeted deliveryof taxoids. Bioorg Med Chem Lett 15:3597–623.
Gao K, Sun J, Liu K, et al. (2008). Preparation and characterization of asubmicron lipid emulsion of docetaxel: submicron lipid emulsion ofdocetaxel. Drug Dev Ind Pharm 34:1227–37.
Gupta Y, Soni V, Chourasia M, et al. (2005). Targeted drug deliveryto the brain via transferrin coupled liposomes. Drug Deliv Tech 5:66–71.
He W, Lu Y, Qi J, et al. (2013). Nanoemulsion-templated shell-crosslinked nanocapsules as drug delivery systems. Int J Pharma 445:69–78.
He W, Tan Y, Tian Z, et al. (2011). Food protein-stabilizednanoemulsions as potential delivery systems for poorly water-solubledrugs: preparation, in vitro characterization, and pharmacokinetics inrats. Int J Nanomedicine 6:521–33.
Hosny KM, Banjar ZM. (2013). The formulation of a nasal nanoemul-sion zaleplon in situ gel for the treatment of insomnia. Expert OpinDrug Deliv 10:1033–41.
Hu X, Tulsieram KL, Zhou Q, et al. (2012). Polymeric nanoparticle–aptamer bioconjugates can diminish the toxicity of mercury in vivo.Toxicol Lett 208:69–74.
Jain S, Chourasia M, Dengre R. (2005). Azo polymers for colon targeteddrug delivery. Indian J Pharma Sci 67:43–50.
Jiang SP, He SN, Li YL, et al. (2013). Preparation and characteristicsof lipid nanoemulsion formulations loaded with doxorubicin.Int J Nanomedicine 8:3141–50.
Jinturkar KA, Anish C, Kumar MK, et al. (2012). Liposomal formula-tions of etoposide and docetaxel for p53 mediated enhanced cytotox-icity in lung cancer cell lines. Biomaterials 33:2492–507.
Kong M, Park HJ. (2011). Stability investigation of hyaluronic acidbased nanoemulsion and its potential as transdermal carrier. CarbohydPolym 83:1303–10.
Lee E, Kim H, Lee I-H, Jon S. (2009). In vivo antitumor effects ofchitosan-conjugated docetaxel after oral administration. J ControlledRelease 140:79–85.
Liu B, Yang M, Li R, et al. (2008). The antitumor effect of noveldocetaxel-loaded thermosensitive micelles. Eur J Pharm Biopharm 69:527–34.
Liu D, Liu Z, Wang L, et al. (2011). Nanostructured lipid carriers asnovel carrier for parenteral delivery of docetaxel. Colloids Surf BBiointerface 85:262–9.
Manjappa AS, Goel PN, Vekataraju MP, et al. (2013). Is an alternativedrug delivery system needed for docetaxel? The role of controllingepimerization in formulations and beyond. Pharm Res 30:2675–93.
Meher JG, Yadav NP, Sahu JJ, Sinha P. (2013). Determination ofrequired hydrophilic-lipophilic balance of citronella oil and develop-ment of stable cream formulation. Drug Dev Ind Pharm 39:1540–6.
Mishra N, Yadav NP, Meher JG, Sinha P. (2012). Phyto–vesicles: conduitbetween conventional and novel drug delivery system. Asian Pac JTrop Biomed 2:S1728–34.
Moes JJ, Koolen SLW, Huitema ADR, et al. (2011). Pharmaceuticaldevelopment and preliminary clinical testing of an oral soliddispersion formulation of docetaxel (ModraDoc001). Int J Pharma420:244–50.
Muller RH, Harden D, Keck CM. (2012). Development of industriallyfeasible concentrated 30% and 40% nanoemulsions for intravenousdrug delivery. Drug Dev Ind Pharm 38:420–30.
Oh DH, Balakrishnan P, Oh Y-K, et al. (2011). Effect of processparameters on nanoemulsion droplet size and distribution in SPGmembrane emulsification. Int J Pharma 404:191–7.
Peng L-C, Liu C-H, Kwan C-C, Huang K-F. (2010). Optimization ofwater-in-oil nanoemulsions by mixed surfactants. Colloids Surf APhysicochem Eng Asp 370:136–42.
Qiu Y, Gao Y, Hu K, Li F. (2008). Enhancement of skin permeation ofdocetaxel: A novel approach combining microneedle and elasticliposomes. J Controlled Release 129:144–50.
Rahn-Chique K, Puertas AM, Romero-Cano MS, et al. (2012).Nanoemulsion stability: Experimental evaluation of the flocculationrate from turbidity measurements. Adv Colloid Interface Sci 178:1–20.
Saito H, Tanaka M, Okamura E, et al. (2001). Interactions ofphosphatidylcholine surface monolayers with triglyceride cores andenhanced apoa-1 binding in lipid emulsions. Langmuir 17:2528–32.
Sakulku U, Nuchuchua O, Uawongyart N, et al. (2009). Characterizationand mosquito repellent activity of citronella oil nanoemulsion.Int J Pharma 372:105–11.
Seo YG, Kim DH, Ramasamy T, et al. (2013). Development ofdocetaxel-loaded solid self-nanoemulsifying drug delivery system(SNEDDS) for enhanced chemotherapeutic effect. Int J Pharma 452:412–20.
Singh S, Junwal M, Modhe G, et al. (2013). Forced degradation studiesto assess the stability of drugs and products. Trends Anal Chem 49:71–88.
Spratlin J, Sawyer MB. (2007). Pharmacogenetics of paclitaxel metab-olism. Crit Rev Oncol Hematol 61:222–9.
Sweetman S. (2007). Martindale: the complete drug reference. London:The Pharmaceutical Press.
Tanaka M, Saito H, Arimoto I, et al. (2003). Evidence for interpene-tration of core triglycerides into surface phospholipid monolayers inlipid emulsions. Langmuir 19:5192–6.
Tang SY, Sivakumar M, Ng AM-H, Shridharan P. (2012). Anti-inflammatory and analgesic activity of novel oral aspirin-loadednanoemulsion and nano multiple emulsion formulations generatedusing ultrasound cavitation. Int J Pharma 430:299–306.
Undevia SD, Gomez-Abuin G, Ratain MJ. (2005). Pharmacokineticvariability of anticancer agents. Nat Rev Cancer 5:447–58.
Yadav NP, Meher JG, Pandey N, et al. (2013). Enrichment,Development, and Assessment of Indian Basil Oil Based AntisepticCream Formulation Utilizing Hydrophilic-Lipophilic BalanceApproach, Biomed Res Int 2013: 410686, doi:10.1155/2013/410686.
Yin Y-M, Cui F-D, Mu C-F, et al. (2009). Docetaxel microemulsion forenhanced oral bioavailability: preparation and in vitro and in vivoevaluation. J Controlled Release 140:86–94.
10 P. Verma et al. Drug Deliv, Early Online: 1–10
Dru
g D
eliv
ery
Dow
nloa
ded
from
info
rmah
ealth
care
.com
by
UB
der
LM
U M
uenc
hen
on 0
6/10
/14
For
pers
onal
use
onl
y.