Int J App Pharm, Vol 11, Issue 5, 2019, 188-193Original Article


DERMAL DELIVERY OF DOCETAXEL LOADED NANO LIQUID CRYSTALS FOR THE TREATMENT OF SKIN CANCER

ARTI MAJUMDAR1,2, NIDHI DUBEY1, NITIN DUBEY3

1School of Pharmacy, Devi Ahilya Vishwavidyalaya, Indore, India, 2Smriti College of Pharmaceutical Education, Indore, India, 3College of Pharmacy, IPS Academy, Indore, India
Email: artijmajumdar10@gmail.com

Received: 19 Jun 2019, Revised and Accepted: 25 Jul 2019

ABSTRACT

Objective: The aim of the present study is to develop docetaxel-loaded nano liquid crystals (NLCs) to enhanced and effective delivery of the drug to the skin cancer.

Methods: NLCs bearing docetaxel were prepared by an emulsification solvent diffusion method. The formulated NLCs were characterized for average particle size, polydispersity index (PDI) Zeta potential, entrapment efficiency and in vitro drug release study. The prepared formulations were studied for it's in vitro cell line and cell uptake study.

Results: It was revealed that the average size of NLCs was found 178.3±5.07, PDI was 0.189, percent entrapment efficiency was found 71.3±2.49 and Zeta potential was found-17.3±2.4. In vitro release determined by Franz diffusion cell was found 61.6±3.2% after 72 hr. 3-(4,5-Dimethylthiazol-2-yl)-2,5-diphenyltetrazolium bromide (MTT) assay shows that Docetaxel loaded NLCs were giving more cytotoxicity as compared to the plain drug. The cell uptake study was found enhanced uptake of fluorescein isothiocyanate (FITC) loaded NLCs in comparison to plain FITC. Docetaxel and docetaxel-loaded NLCs showed 28.3±0.3 and 39.3±1.3 growth inhibition respectively after 48h upon incubation at 0.5 µg/ml concentration (p<0.05).

Conclusion: The result of the studies was concluded that NLCs can be used as impending drug delivery system which may enhance the drug uptake and maintain the drug level for longer period of time and it is potential carrier system which can be used for the treatment of skin diseases like cancer.

Keywords: Docetaxel, NLCs, Cytotoxicity, Skin cancer, Cell uptake

© 2019 The Authors. Published by Innovare Academic Sciences Pvt Ltd. This is an open-access article under the CC BY license (http://creativecommons.org/licenses/by/4.0/)
DOI: http://dx.doi.org/10.22159/ijap.2019v11i5.34621

INTRODUCTION

Melanoma, squamous cell carcinoma, and basal cell carcinoma are different types of skin cancer that are most commonly origin by extensive contact to sunlight and it is recognized by unwarranted propagation of these type of cells which generally results in damage of keratinocytes. Excessive UV exposure suppresses the expression of p53 suppressor gene, which plays a key role in the removal of sunburn cells and avoidance of basal cells transformation. Docetaxel used to treat a number of breast cancer, head and neck cancer, stomach cancer, prostate cancer, and non-small-cell lung cancer. It is the taxane family of medications. It works by disrupting the normal function of microtubules and thereby stopping cell division [1]. It may be used by itself or along with other chemotherapy medication. Common side effects include hair loss, low blood cell counts, numbness, and irregular breathing and muscle pains. Unwanted drug distributions or chemotherapeutic failure is the major reason behind these side effects and it is necessary to design a suitable drug delivery system and select a route of administration which overcomes above side effect by preventing the unwanted distribution of drug [2, 3]. A need for the simple, safe and stable formulation is necessary. Nano Liquid Crystals (NLCs) are a novel drug delivery systems have properties and advantages like NLCs and lipid NLCs [5]. NLCs are non-toxic and can be prepared without the use of toxic materials [6]. They are capable to protect the drug molecules against degradation and provide sustained release pattern [7, 8]. The topical administration of Docetaxel-loaded NLCs for skin cancer can be minimizing the side effects of Docetaxel and increase therapeutic effectiveness [3]. The nanosize of NLCs promotes drug absorption through the stratum corneum, it is the outermost barrier of epidermis that able to retard the drug penetration into the skin [9]. Aim of this study was to investigate and assess the potential of Docetaxel-loaded NLCs for the treatment of skin cancer using skin cancer cell line [2, 10, 11].

MATERIALS AND METHODS

Materials

Docetaxel was obtained as a gift sample from Sun Pharma Pvt Ltd. Ahmadabad, India. Stearic acid was purchased from Himedia, Mumbai, India. Oleic acid was purchased from Loba Chemical, Mumbai, India. Tristearin, cholesterol, and soya PC were purchased from Sigma Aldrich, USA. Other chemicals and solvents were used of analytical reagent grade.

Preparation of docetaxel loaded NLCS

The docetaxel-loaded NLCs were prepared solvent diffusion melt dispersion techniques according to Selvamuthukumar et al., 2012 [12]. The lipid, stearic acid (3.0%w/v), oleic acid (0.5% w/v), tristearin (1.0%w/v), cholesterol (0.75%) and soya phosphatidylcholine (1.5%w/v) were dissolved in 10 ml of ethanol: acetone solvent system in a 250 ml of beaker. Drug (docetaxel 20%w/w of lipid) was added to above mixture. The mixture was melted 70 °C to get a clear lipid phase. In a separate beaker, 60 ml of double-distilled water containing tween 80 was stirred under magnetic stirrer and then heated at 70 °C with heating mental. The aqueous phase was maintained at 70ᵒC and kept under the high-speed homogenizer (IKA T 25 digital ULTRA-TURRAX®, Germany) at 10000 rpm to make microemulsion. The oil phase containing drug was added dropwise to the aqueous phase using preheated (at 70 °C) hypodermic syringe. After 30 min of stirring, heating was stopped. Then 20 ml of cold water was added dropwise to reduce the temperature of the dispersion. The dispersion was continuously stirred for 2 hr to the removal of ethanol and acetone from the NLCs. After stirring the prepared formulation was lyophilized using Labconco freeze dryer (Labconco, Cascade Freezone Plus 4.5 L Benchtop Freeze dryer, USA) and stored at 2-8 °C until further used for characterization.

Preparation of gel base

Carbopol 934 (1-3%w/v) was accurately weighed and dispersed into double distilled water (80 ml) in a beaker. This solution was stirred continuously at 800 rpm for 1 hour and then 10 ml of propylene glycol was added to this solution. The obtained slightly acidic solution was neutralized by dropwise addition of 0.05 N sodium hydroxide solutions, and again mixing was continued until gel becomes transparent. The volume of the gel was adjusted to 100 ml and then sonicated for 10 min on bath sonicator to remove air bubbles. Final pH of the gel base was adjusted to 6.5 [13]. The gel was also prepared with the plain drug by adding 10 mg of drug and dispersed properly by following the same procedure given above. The same procedure was used to formulate nanocarriers containing gel in which previously prepared NLCs were added in place of plain drug. The NLCs preparation corresponding to 6.0 % w/w (6.0 mg of drug in 100 mg of gel) of the drug was incorporated into the gel base to get the desired concentration of drug in a gel base.

Characterizations of docetaxel-loaded NLCS

Determination of particle size, PDI and surface charge

Mean particle size distribution of Docetaxel-NLCs formulations and polydispersity index (PDI) of the NLCs were determined by photon correlation spectroscopy using a Zetasizer DTS, version 4.10 (Malvern Instrument, UK). Before analysis, the formulations were diluted with 1:9 v/v with deionized water. The particles size and PDI were represented by the average diameter of the Gaussian distribution function in the logarithmic axis mode. Surface charge measurement of the NLCs was based on the zeta potential (ε) that was calculated according to Helmholtz–Smoluchowsky from their electrophoretic mobility. Zeta potential was determined by a Zetasizer (Zetasizer Nano ZS, Malvern Instruments, UK) with a field strength of 20 V/cm on a large bore measures cell. Before analysis, samples were diluted with 0.9 % NaCl to adjust the conductivity of 50 μS/cm [14]. Particle size, size distribution, and zeta potential the prepared formulation was performed at the SAIL, School of Pharmaceutical Sciences, Rajiv Gandhi Proudyogiki Viswavidyalaya, Bhopal (MP), India.

Shape and surface morphology

The shape and surface morphology were examined by Transmission electron microscopy and scanning electron microscopy (SEM). For the SEM analysis, the prepared NLCs were sprinkling on a double adhesive tape which was stuck on an aluminum stub. The stubs were then coated with a gold layer about 300 Å of thickness using a sputter coater. The photomicrographs of prepared NLCs were taken with SEM (FESEM, GeminiO, Giess, Netherlands).

The shape of the NLCs was determined by Transmission Electron Microscopy (TEM; Philips CM12 Electron Microscope, Eindhoven, Netherlands). For the TEM, the samples were prepared by taking one drop NLCs dispersion and a copper grid was placed on it. After 60 seconds the grid was removed and excess of liquid was soaked with filter paper. Then the grid was negatively stained with 2.0 % phosphotungstic acid solution at a 20 kV acceleration voltage. The TEM images of prepared NLCs were taken which was shown in fig. 2(a) and 2(b). Analysis of sample on SEM and TEM was carried out at IISER, Bhopal, India [14-16].

Determination of entrapment efficiency (EE)

The entrapment efficiency of prepared NLCs was determined according to Gupta et al., (2007) [14]. The lyophilized formulation equivalent to 10 mg of drug was taken and dissolved in 50 ml of a beaker containing 10 ml of ethanol. The solution was then centrifuged at 10000 rpm for 10 min. The 1.0 ml of the supernatant solution was withdrawal with the help of micropipette and transfer into a 10 ml of volumetric flask. The volume was made upto 10 ml with ethanol and analyze spectroscopically for drug content using Simadzu 1700 UV-spectrophotometer and it was calculated according to the formula given below.

Characterization of NLCS containing gel

Measurement of viscosity

Viscosity measurements of prepared topical NLCs based gel were measured by Brookfield viscometer using spindle no. 63 with the optimum speed of 10rpm; viscosity was found to be 3776cps.

Drug content

Accurately weighed equivalent to 100 mg of topical NLCs gel was taken in a beaker and added 20 ml of 0.01N HCl. This solution was mixed thoroughly and filtered using Whatman filter paper no.1. Then 1.0 ml of filtered solution was taken in 10 ml capacity of volumetric flask and volume was made up to 10 ml with 0.01 N HCL [16]. This solution was analyzed using UV-Spectroscope at λmax 251 nm. Drug content of NLCs based gel is shown in table 1.

Extrudability study

Extrudability was based upon the quantity of the gel extruded from the collapsible tube on the application of a certain load. More the quantity of gel extruded shows better extrudability. It was determined by applying the weight on the gel-filled collapsible tube and recorded the weight on which gel was extruded from the tube. Extrudability of gel required 170 grams of weight to extrude a 0.6 cm ribbon of gel in 6 seconds [13].

Spreadability

Spreadability of the formulation is necessary to provide sufficient dose available to absorb from the skin to get a good therapeutic response. It was determined by the method reported by Khan et al., (2013) [15]. An apparatus in which a slide fixed on a wooden block and the upper slide has movable and one end of movable slide tied with weight pan. To determine spreadability, placing 2-5 g of gel between two slides and gradually weight was increased by adding it on the weight pan and time required by the top plate to cover a distance of 10 cm upon adding 80g of weight was noted. Good spreadability show lesser time to spread [13, 15]

In vitro drug diffusion study

The in vitro diffusion study is carried by using Franz Diffusion Cell. Egg membrane is taken as a semi-permeable membrane for diffusion. The Franz diffusion cell has a receptor compartment with an effective volume of approximately 60 ml and an effective surface area of permeation 3.14sq. cms. The egg membrane is mounted between the donor and the receptor compartment. A two cm2size patch taken and weighed then placed on one side of the membrane facing the donor compartment. The receptor medium is phosphate buffer pH 7.4. The receptor compartment is surrounded by a water jacket so as to maintain the temperature at 32±0.5 °C. Heat is provided using a thermostatic hot plate with a magnetic stirrer. The receptor fluid is stirred by Teflon coated magnetic bead which is placed in the diffusion cell [5]. During each sampling interval, samples are withdrawn and replaced by equal volumes of fresh receptor fluid on each sampling. The samples withdrawn are analyzed spectrophotometrically at a wavelength of the drug (fig. 2)

Stability studies

Stability study was carried out for drug-loaded NLCs at two different temperatures i.e. refrigeration temperature (4.0±0. 2 °C) and at room temperature (25-28±2 °C) for 3 w. The formulation subjected to stability study was stored in borosilicate container to avoid any interaction between the formulation and glass of container. The formulations were analyzed for any physical changes and drug content (table 2) [16].

Cell culture and mtt assay

Cell cytotoxicity assay (MTT assay) for the optimized formulation was performed using B16F10 skin cancer (melanoma) cells lines from Advanced Centre for Treatment, Research and Education in Cancer (ACTREC), Tata Memorial Hospital (TMH), Mumbai, Cancer cells were cultured in RPMI 1640 medium and added 10% of FBS, and 100 g/ml of streptomycin at 37 °C into CO2 incubator. After reaching 70% convergence cells were seeded in a 96 well microplate with 1000 µl of growth medium. The prepared samples of the plain drug and optimized formulation of NLCs were added in the 96 well plates in order to increase the concentration of Docetaxel then cells were incubating for 24 hr. After incubation, 200 µl of fresh media containing 20 µl of MTT solution was added and then incubated it for 4 hr at 37 °C. After incubation, media was replaced with 200 µl of DMSO to dissolve Formazan crystals. The 96 well plate was analyze using microplate reader by taking absorbance at 570 nm [5].

Cell uptake assay

Preparation of fluorescein isothiocyanate loaded NLCs

NLCs formulation containing fluorescent label (with fluorescein isothiocyanate (FITC)) were prepared to add 0.04 % of FITC in place of the drug to the lipid. The fluorescent NLCs were prepared according to the method used for the preparation of docetaxel-loaded NLCs [6, 7].

Fluorescence microscopy

Qualitative Cellular uptake of conjugates was determined with the following procedure. Briefly, the optimized formulation was previously labeled with fluorescein isothiocyanate (FITC) solution. 2.5 x 105 cells/well were seeded in a six-well plate and incubated for 24 h at 37 °C with 5% CO2, and then the medium in each well was replaced with 2 ml of medium containing labeled formulation and plain FITC. The fluorescence due to the uptake of the fluorescent-labeled formulation was analyzed under an inverted fluorescent microscope (Labomed, Germany) after 4, 12, 24, and 48 h [5].

RESULTS AND DISCUSSION

Prepared formulations of NLCs were optimized on the basis of particle size, shape, surface charge, and entrapment efficiency. The particle size of NLCs determined by the light scattering method (Malvern Zetasizer, ZEM 5002, and UK) and found that the average particle size of optimized formulation was 178.37±5.07 nm. The PDI was found 0.189 and Zeta potential was-17.3±2.4 (table 1) [14, 16, 17]. It was observed that the particles size of NLCs was increase with increasing the concentration of stearic acid and similarly particle size was decease with increasing the concentration of tween 80, stirring speed and increasing the sonication time. The size reduction may be due to surfactant action of surfactant, mechanical force and sonication wave force was responsible respectively for reducing the size of particles [18]. There was no significant difference in average particle size was observed with increasing the drug concentration. But in increasing the sonication time the size particle was decreasing from 218.42±6.09 to 145.29±7.80 after 90 sec of sonication. The low PDI value represents the uniformity of formulation in which there is no major difference in the size of particles. The PDI of optimized formulation was found at 0.189. PDI of the formulation was varied with increasing or decreasing the concentration ratio of lipid and surfactant and sonication time [16]. It was observed that when the lipid ratio in formulations was decreased and surfactant concentration was increased then the PDI was found decrease. When, sonication time increase from 30 to 90 second, then PDI was 0.309, 0.189 and 0.487, respectively for different NLCs formulations. It was observed that on 90 second of sonication time the PDI was increased and it was due to the high mechanical forced of sonication waves which were resultant in heat generation which leads to agglomerates or denaturing the lipid molecules after breaking the particles [19-22].

Table 1: Characterization of optimized formulation of NLCs

Characterization Average vesicle size (nm) % Entrapment efficiency PDI Zeta potential (mV)
Doce-NLCs 178.3±5.07 71.3±2.49 0.189 -17.3±2.4

Value represent as mean±SD (n=6)

The shape and surface morphology of prepared NLCs was determined by using TEM and SEM. The photomicrograph was taken which shown in fig. 1 and was found that they were spherical in shape with smooth in the surface. The % Entrapment efficiency of optimized NLCs formulation was found 71.03±2.49% [16].

Fig. 1: SEM (a) and TEM (b) photomicrograph of optimized NLCs formulation at 1000KX

It was observed that the percent drug entrapment was decreasing with increasing the concentration of surfactant and on increasing the time of sonication. It is due to the extract out the drug from particles on increasing the mechanical force by sonication and size reduction of size NLCs on increasing the concentration of surfactant due to their surfactant action [16, 23-26]. Stability study data was revealed that the optimized formulation stable after 3 mo of storage at 4ᵒC while at 25-28±2 °C, the formulation was found unstable. Stability of formulation was observed on the basis of % drug remain, average particles size and physical appearance. The average particle size of NLCs was found 178.37±5.07, 179.32±2.49 and 186.84±5.84 nm after 1, 2 and 3 mo of storage at 4.0±0.2 °C while at 25-28±2 °C the average particle size was found 192.56±3.43, 238.54±4.87 and 583.54±6.99 nm after 1, 2 and 3 mo of storage. Drug remaining in NLCs formulation was 48.62±1.39, 35.29±1.08 and 23.83±2.11 % after 1, 2 and 3 mo of storage at 25-28±2 °C while there were no significant changes in % drug remains and physical appearance in NLCs formulation was observed after 3 mo of storage at 4ᵒC. (table 2).

Table 2: Stability study of optimized formulation of NLCs

Characteristic Time (mo)
1 mo 2 mo 3 mo
Temperature 4.0±0. 2 °C 25-28±2 °C 4.0±0. 2 °C 25-28±2 °C 4.0±0. 2 °C 25-28±2 °C
Average particle size (nm) 178.3±5.07 192.5±3.43 179.32±2.49 238.5±4.87 186.8±5.84 583.5±6.99
% EE 67.3±2.52 48.6±1.39 62.3±2.52 35.2±1.08 52.3±2.52 23.8±2.11
Physical Appearance Normal High turbid Normal High turbid and agglomeration Normal High turbid and agglomeration

Value represents as mean±SD (n=6)

Prepared gel was evaluated for viscosity, % entrapment, extrudability, spreadability, and drug release study. It was found that viscosity of prepared gel was 178.37±5.07 cps, % Entrapment efficiency was 71.03±2.49%, Extrudability was 170 g and Spreadability (g. cm/sec) was found that 5.16 (g. cm/sec) respectively (table 2).

Table 3: Characterization of gel-based formulation of NLCs

Characterization Viscosity (cps) % Entrapment efficiency Release after 72 h Extrudability (g) Spreadability (g. cm/sec)

Optimized formulation

(DOCE-NLCs)

 3776 71.03±2.49 61.6±3.2 170 5.16

Value represents as mean±SD (n=6)

In vitro drug release from NLCs was carried out using Frenze diffusion cell method and found 61.6±3.2% in 72 hr. In the first 30 min, it was 12.45±0.9% drug release which slightly high. It was due to the release of free drug present in the bag after leaching from NLCs [27-29]. Drug release from NLCs formulation was found in a very sustained and controlled manner and follow Higuchi and Korsmeyer Peppas release kinetic. Drug release in 24 hr was 41.36±1.8 and 52.06±2.6 in 48 hr (fig. 2).

In vitro cell line study data shown that Docetaxel loaded NLCs was entered by the cancer cells and retard the growth by killing them in very low concentrations [6]. In vitro cytotoxicity using B16F10 was evaluated for plain docetaxel and docetaxel-loaded NLCs formulations in the concentration range of 0.05-0.5 µM of docetaxel. However, docetaxel and docetaxel-loaded NLCs showed 28.3±0.3 and 39.3±1.3 growth inhibition respectively after 48h upon incubation at 0.5 µg/ml concentration (fig. 7.2). This was due to the high penetration of docetaxel-loaded NLCs into cancer cells. The value of IC50 for docetaxel and docetaxel-loaded NLCs was found to be 0.2 µg/ml and 0.1µg/ml following 24 hr and 48 hr incubation, respectively which was more than 5-fold lower as compared to free docetaxel (fig. 3).

Fig. 2: In vitro drug release of gel-based NLCs, the value represents as mean±SD (n=6)

Qualitative (Fluorescence) uptake study of FITC and FITC loaded NLCs was performed to assess the capability of NLCs to penetrate skin cancer cell lines. Similar to the results of the percent cell growth inhibition assay, uptake studies also displayed higher uptake of NLCs in comparison to plain FITC (fig. 4). Uptake of FITC loaded NLCs by cancer cells showed an enhanced uptake of the fluorescent marker after 4 hr of incubation. A slight uptake was observed with the cell treated with free FITC [6-8].

Fig. 3: In vitro cytotoxicity of DOCE and DOCE-NLCs formulations (Percent Cell Growth Inhibition Assay) on skin cancer cell line, the value represents as mean±SD (n=6)

Fig. 4: Cell uptake (fluorescence microscopy) image of the plain drug (A-D) and Docetaxel loaded NLCs (E-H) after 4, 12, 24 and 28 h of incubation respectively

Statistical analysis

Data are expressed as the mean±SD and statistical analysis was carried out using one-way ANOVA test using the Graph Pad PRISM software. A value of P<0.005 was measured, which was statistically significant [16, 29].

CONCLUSION

We have demonstrated that NLCs are promising colloidal Nanosystems for dermal delivery of Docetaxel through the in vitro and in vivo studies. NLCs suspension enhances Docetaxel permeability and picks it up to cancer cells and decreases cell viability at different concentration. According to cell uptake study, a substantial improvement in the restriction of cancer cell was found. Further studies are necessary for the determination of long-term Docetaxel-NLCs stability and the lack of cytotoxicity on the various untargeted organs to exploit this carrier can be used for the treatment of skin cancer.

ACKNOWLEDGMENT

Authors want to acknowledge Sun Pharma. Pvt Ltd for providing the gift sample of Docetaxel. We are sincerely grateful to Dr. Ahmad Yari Khosroshahi for providing the necessary structure for the successful accomplishment of this research. One of the authors wants to acknowledge IISER Bhopal to provide electron microscopy facility. Authors also want to acknowledge Anti-Cancer Drug Screening Facility (ACDSF), ACTREC, Tata Memorial Centre Kharghar, Navi Mumbai to perform cell line study. Authors want to acknowledge Department of Pharmaceutics, Ravishankar College of Pharmacy, Bhopal for providing freeze drying facility.

DISCLOSURE STATEMENTS

The authors report no declarations of interest

AUTHORS CONTRIBUTIONS

All the author have contributed equally

CONFLICT OF INTERESTS

Declaration for confirming the absence of any conflict of interest. We, the undersigned, Mrs. Arti Majumdar, Principle Investigator, and Dr. Nidhi Dubey and Dr. Nitin Dubey Co-Investigator of research article entitled “Dermal Delivery of Docetaxel Loaded Nano Liquid Crystals for the Treatment of Skin Cancer” submitting the article. We confirm that we do not have any conflict of interest in connection to the proposed research project and we have not granted, sought, attempted to obtain or accept any advantage, financial or in-kind, either directly or indirectly, as an incentive or reward relating to the award.

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