Polysorbate 80 Coated Solid Lipid Nanoparticles for the Delivery of Temozolomide Into the Brain

Pawan Yadav1, Goutam Rath1, Gazal Sharma1, Ranjit Singh2, Amit Kumar Goyal1, *
1 Department of Pharmaceutics, ISF College of Pharmacy, Moga, Punjab, India
2 Adarsh Vijendra Institute of Pharmaceutical Sciences, Shobhit University, Gangoh, Sahranpur-247341 UP, India

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© 2018 Yadav et al.

open-access license: This is an open access article distributed under the terms of the Creative Commons Attribution 4.0 International Public License (CC-BY 4.0), a copy of which is available at: (https://creativecommons.org/licenses/by/4.0/legalcode). This license permits unrestricted use, distribution, and reproduction in any medium, provided the original author and source are credited.

* Address correspondence to this author at the Department of Pharmaceutics, ISF College of Pharmacy, Moga, Punjab, India; Mobile: 9888206383; E-mails: amitkumargoyal1979@gmail.com; goyalddrl@gmail.com



Anti-angiogenic therapy can produce transient regression in tumor in case of Glioblastoma (GBM); however, no prolongation of patient survival rate had so far been achieved.


To address this problem, an effort was made to design and characterize a temozolomide loaded nanosystem for targeting the tumor vasculature in the brain using polymeric nanoparticles. It included the formation of Temozolomide (TMZ) loaded Solid-Lipid Nanoparticles (SLNs) and their conjugation with polysorbate-80 (P-80) which enhanced the penetration of drug to blood-brain barrier resulting in the enhancement of pro-apoptotic activity.


Conjugating nanoparticles with a tumor-penetrating polymer (P-80) further enhanced the therapeutic efficacy of the drug.


The animal studies indicated the enhanced potential of the developed system in the effective treatment of glioblastoma.

Keywords: Brain targeting, Blood-brain barrier, Temozolomide, Solid lipid nanoparticles, Glioblastoma multiform, Polysorbate 80.


Brain cancer is one of the prominent dreadful diseases among other CNS related disorders. Although various treatment strategies including surgery, chemotherapy have been available to control the progression of diseases, but still mortality rate against brain cancer is very high [1, 2]. This may be attributed to the development of resistance against existing treatment strategies [3]. There is an unmet need to provide better strategies especially to blood-brain barriers that provide enough quantity of drugs to the site of action. It is very difficult to improve the availability of drugs to the brain compartment by passing blood-brain barriers [4-8].

Many novel drug delivery systems have been designed to improve the bioavailability of drug to brains including nanoparticles, micellar systems, microemulsion, solid lipid nanoparticles, liposomes, niosomes etc. [9-12]. Among them, nanoparticles based delivery of drugs to the brain has shown significant potential. Nanometric size of these particulate carriers not only improves the permeation and availability of drugs to the brain, but also provides a large surface area, improves solubility and ability to encapsulate both hydrophilic and lipophilic drugs. Further, it is also possible to regulate the release of drugs for a prolonged period of time [13, 14]. Furthermore, several studies have reported that the presence of surface active agents, permeabilizers, solubilizers cationic and anionic agents at the surface of nanoparticles provides better stability of carrier systems in blood and better brain uptake. Many drugs have been delivered using these strategies that include paclitaxel, doxorubicin, docetaxel, dalargin, methotrexate, kytorphin, loperamide, tubocurarine, MRZ2/576 etc. [15-23].

Temozolomide, a prodrug, is a nonfunctional alkylating agent that readily crosses the blood-brain barrier. It is derived from a series of modified imidazotetrazinones. It is chemically related to dacarbazine and is the 3-methyl derivative of the experimental anticancer drug mitozolomide [24, 25]. Unlike dacarbazine, temozolomide does not require hepatic metabolism to the intermediate species methyltriazen-1-yl imidazole- 4-carboxamide (MTIC). Chemical stability studies have shown that temozolomide spontaneously hydrolyzes to MTIC above pH 7 [22]. Many studies have demonstrated the chemotherapeutic potential of this drug in various tumor models [26-28]. Further, temozolomide not only demonstrated broad-spectrum anti-cancer activity, but also provided better pharmacokinetic profile including better penetration in the brain with relative low toxicity compared with its parent compound mitozolomide [29-37]. In the present studies, surfactant coated lipid nanoparticles were explored for the delivery of temozolomide. Further, its pharmacokinetics was also compared with an uncoated lipidic nanoparticulate formulation for providing better availability of drugs to the brain compartments.


2.1. Materials and Instruments

Temozolomide was obtained as a gift sample from Cipla Pharmaceuticals Banglore. Tripalmitin, soya lecithin and polysorbate 80 (Tween 80) were purchased from Sigma Pvt. Ltd. New Delhi. All other materials and reagents used in the study were of analytical/HPLC grade. Several instruments have been used during the development of solid lipid nanoparticles including double beam UV spectrophotometer, digital balance, incubator cum shaker, particle size and zeta-potential analyzer, scanning electron microscope, transmission electron microscope, HPLC etc.

2.2. Development of Solid Lipid Nanoparticles

Solid lipid nanoparticles were prepared by partially modified hot homogenization method [31]. Initially, temozolomide (3mg) and tripalmitin (30mg) were dissolved in a mixture of ethyl acetate and methanol (1:1), subsequently resultant solution was placed under rotatory evaporator for complete removal of organic solvent under inert atmospheric condition. Resultant dried drug-lipid mixture was further melted at 50oC ± 5oC for 15 min. Thereafter, 40 ml of a hot aqueous solution of Poloxamer 188 was further homogenized with molten lipid phase at 4000 rpm at 50oC ± 5oC temperature condition. Emulsified homogenized lipid formulation was further subjected under sonication using a probe sonicator at 50W for 20 min. The obtained nanoemulsions were cooled at 6oC to affect re-crystallization for the formation of solid lipid nanoparticles.

2.3. Coating of Surfactant on Solid Lipid Nanoparticles

Surfactant coated solid lipid nanoparticles were prepared by using polysorbate 80 (Tween® 80). 1% (w/v) solution of polysorbate 80 was admix nanoparticle suspension for surface coating of nanoparticles under magnetic stirring for 30 min. Resultant coated nanoparticles were centrifuged, re-dispersed and were stored under refrigerated condition for further characterization [32].

2.4. Size, Shape and Zeta Potential Determination

Size and zeta potential of developed nanoparticles were determined by zetasizer (DeslananoTMC, instrument, Beckman Coulter, USA). Similarly, SEM and TEM techniques were also used to determine the size and shape of developed nanoparticles.

2.5. Entrapment Efficiency

Entrapment efficiency of developed different SLN formulations was analyzed as reported by Venkateswarlu and Manjunath, with minor modifications [33]. After the development of solid lipid nanoparticles, resultant dispersion was taken in centrifuge tube and centrifuged until the separation of solid lipid nanoparticles from dispersion. Finally, the amount of unentrapped drug was measured in the supernatant. The percent EE was calculated using the following formula.

% Entrapment Efficiency =

2.6. In Vitro Drug Release Studies

In vitro drug release kinetics of developed formulation was performed by diffusion method. Drug-loaded SLNs and TMZ-SLNs suspensions were filled in dialysis tubes (12,000 molecular weight cutoff) and tagged tightly with the tube and subsequently, formulation filled dialysis tube was placed into a beaker containing 200 ml phosphate-buffered saline (pH 6.8) under a magnetic stirrer at 37oC. During the in-vitro release studies, 0.5 ml of the sample was collected at a predefined time interval and the same amount of fresh medium was added. All the collected samples were further diluted appropriately and analyzed by UV spectrometry.

2.7. Cell Viability Assay

The toxicity of developed formulation was determined by MTT assay as reported previously [34]. 96 wells microtiters plates were used to grow cells at 2x104 cells/ 200µl growth medium /well. Finally, cells were incubated with fresh growth medium containing different formulations in the concentration range of 2 -14µg/ml. Later, growth medium was aspirated and washed with 200µl PBS (1M, pH 6.8). Afterward, MTT reagent (0.8 mg/ml) was added in each well and incubated for 5 h. Later, the supernatants were discarded and DMSO was added in each well and again incubated at 37ºC for 1 hour, and finally, absorbance was recorded using ELISA reader. An OD value of control cells (unexposed cells) was taken as 100% viability.

2.8. Pharmacokinetics and Tissue Distribution

Six healthy mice (provided by IIM Jammu, body weight 20±1.0/kg, three females and three males) were taken for biological studies. The mice fasted overnight with free access to water. The different formulations were injected intravenously (10 mg/kg body weight) and blood samples from different groups were added in heparinized tubes at predefined time intervals of 0, 0.25, 0.5, 1, 2, 4, 6, 8, 12, 24, 36 and 48 hr and centrifuged at 2000 rpm for 15 min. Further, plasma were collected after centrifugation at 2000 rpm for 15 min and stored at -20oC until use. Availability of drug within brain has also been determined after scarifying mice. Brain and its tissue were dissected and further processed as discussed previously. Collected plasma and biological samples were further processed and used for determination of drug content at a different time interval via HPLC analysis.


Temozolomide is the newly approved drug by the FDA for the treatment of malignant glioma. The present study explores the targeting potential of an anticancer drug (temozolomide) via delivery through lipidic nanoparticles. The developed system would be able to avoid the RES system of the mononuclear in the brain using ear phagocytes systems. Temozolomide loaded solid lipid nanoparticles were prepared by hot melt homogenization method in conjunction with sonication.

Solubility of the drug was determined in various solvents at room temperature. Temozolomide was found to be freely soluble in methanol, chloroform, slightly soluble in ethanol, acetone and insoluble in water. These observations showed that the drug is highly lipophilic in nature. Melting range of the drug was found to be 210-213oC, which is in agreement with the reported values. The methanolic solution of temozolomide exhibited absorbance maxima at 328nm which is concordant with I.P. standards. The IR spectrum of drug samples was found to be in concordance with the reference spectrum given in IP 2010 as the observed peaks were very close to standard peaks. All these observations confirmed the identity of temozolomide. The standard curves of temozolomide (triplicate) were prepared in methanol and PBS (pH 6.8). The absorbance data obtained was subjected to linear regression. The correlation coefficient was found to be 0.998, indicating good linearity.

During the preparation of solid lipid nanoparticles, formulations were optimized by using different lipid ratio subjected to drug entrapment efficiency and particle size analysis. Increasing the methanol: ethyl acetate ratio, the size of SLNs’ was noted to be decreased viz. 163.3±3.2nm (D1), 162.3±3.6nm (D2), 146.7±3.9nm (D3), 151.8±4.3nm (D4). It was noted that on increasing the amount of soya lecithin, entrapment efficiency decreased, 71.46±1.4% (C1), 70.56±1.3% (C2), 70.93±1.5% (C3), 69.80±1.3% (C4). The potential drop was also observed on increasing homogenization time, 28.4±2.3 (A1), -34.7±2.3 (A2), -33.08±3.1 (A3), -40.09±2.1 (A4). D3 formulation was found to be optimum out of sixteen developed formulations, having size 146.7±3.9nm, PDI 0.314±0.003, zeta potential -38.27±2.4mV, mobility -2.984±0.01e-004cm2/Vs, entrapment efficiency 72.90±1.3% Table 1.

Table 1. Various attributes of optimized formulation D3.
S.NO Parameter Value
1 Size 146.7±3.9nm
2 PDI 0.314±0.003
3 Zeta potential -38.27±2.4mV
4 Mobility -2.984±0.01e-004cm2/Vs
5 Entrapment efficiency 72.90±1.3%
(mean ±S.D; n=3)

The shape of the SLNs was examined using SEM & TEM. SEM & TEM studies of all the solid lipid nanoparticles were performed. The images revealed that the SLNs were spherical in shape and homogeneously distributed (Figs. 1 and 2).

Fig. (1). Scanning electron microscopy of solid lipid nanoparticles.

Fig. (2). Transmission electron microscopy of solid lipid nanoparticles.

In vitro drug release of different formulations was evaluated by diffusion method in phosphate-buffered saline (pH 6.8) at 37°C until the complete release of drugs from the formulations. P-80 coated SLNs exhibited 82.46 ± 1.43% drug release and followed first order kinetics. The P-80 coated TMZ SLNs showed slower drug release as compared to TMZ SLNs. The drug release studies are shown in (Fig. 3).

Fig. (3). In-vitro drug release studies of the P-80 coated temozolomide loaded solid lipid nanoparticles and plain temozolomide loaded solid lipid nanoparticles.

The comparative cytotoxicity studies of different coated and uncoated SLNs’ formulations were carried out using MTT assay. Percentage cell viability of formulation in U373MG glioblastoma cancer cell lines was evaluated. Fig. (4) presents the IC50 value for different formulations. The IC50 value was found to be 8µg/ml with polysorbate 80 (P-80) coated solid lipid nanoparticles. The percent (%) drug release from the P-80 coated solid lipid nanoparticles was a bit lesser than the uncoated SLN which may be attributed to the P-80 coating over the solid lipid nanoparticles.

Fig. (4). Percent cell viability of P-80 coated Temozolomide loaded solid lipid nanoparticles in U373MG glioblastoma cancer cell lines using MTT assay.

Various pharmacokinetic parameters such as MRT (h), AUC (h ng ml-1), C max (ng ml−1), CL (mg kg−1/h ng ml−1) were calculated and compared with the free drug Table 2. In plasma, the AUC and MRT were increased for P-80 coated TMZ SLNs’ as compared to other formulations. The concentration of temozolomide in the brain was significantly increased in case of P-80-TMZ SLNs as compared to TMZ solution & TMZ SLNs’ (26.19±0.11, 6.43±0.21 & 15.07±0.21% respectively). The results showed that polysorbate 80 coated SLNs exhibited better delivery of the drug in the brain compared to other formulations.

Table 2. Various pharmacokinetic parameters of different formulations.
S.No. Parameter TMZ Solution TMZ SLNs’ P-80 coated SLNs’
1 MRT (h) 3.78±0.03 45.32±0.82 57.89±0.45
2 AUC (h ng ml-1) 807.63±2.4 7305.67±4.2 9605.84±3.7
3 C max (ng ml−1) 376.2±3.5 200.1±3.9 157.66±2.4
4 CL (mg kg−1/h ng ml−1) 0.0124±0.0001 0.0014±0.0001 0.0006±0.0001
(mean ±S.D; n=3)

Several studies have also supported that surfactant coated nanoparticles are an important tool to increase the uptake of drugs into the brain. This may be attributed to the interaction of surface active agents with the endothelial microvasculature of the brain. In addition to this, the presence of surfactant may help loose the tight junction of the BBB. This may lead to better uptake of surfactant coated nanoparticulate formulation.


The blood-brain barrier is the highly selective tight junction defence system to prevent the passage of unwanted harmful substances [13]. This phenomenon of BBB is a major limiting factor of the absorption of drugs within the brain tissue. Several approaches have been developed to increase the permeability of drugs across the brain especially nanotechnology [37]. Furthermore, the presence of surfactant over nanoparticles has also demonstrated increased uptake of the drugs. Polysorbate 80 coated solid lipid nanoparticles have shown significantly better uptake of drugs compared with other formulation. Pharmacokinetic parameters like increased values of AUC and MRT have highlighted the important of surfactant coating over nanoparticle surface. The concentration of drug in the brain was significantly higher in case of polysorbate-80 coated nanoparticles as compared to TMZ solution & simple TMZ SLNs. The results proved the potential of coated nanoparticles in enhancing the delivery of a drug across the brain.


The polysorbate-80 coated SLNs are multipurpose nanoparticulate systems able to deliver both hydrophilic and lipophilic drugs and also avoiding RES uptake to lesser uptake of the drug to other organs. The developed formulations may also reduce the total dose required for the therapy with a concurrent reduction in dose-related toxicity. However, further studies are required to endorse their potential as an effective drug delivery system.


All experimental procedures and protocols used in this investigation were reviewed and approved by the Institutional Animal Ethics Committee (IAEC), I.S.F. College of Pharmacy, Moga, Punjab, India.


No humans were used in the experiments. All the reported experiments involving animals used in the study were in accordance with the guidelines of the council for the purpose of control and supervision of experiments on animals (CPCSEA).


Not applicable.


The authors declare no conflict of interest, financial or otherwise.


The authors are thankful to Chairman, ISF College of Pharmacy, Moga Punjab, India, for providing necessary facilities to carry out this work.


[1] Tamai I, Tsuji A. Drug delivery through the blood brain barrier. Adv Drug Deliv Rev 1996; 19(3): 401-24.
[2] Misra A, Ganesh S, Shahiwala A, Shah SP. Drug delivery to the central nervous system: A review. J Pharm Pharm Sci 2003; 6(2): 252-73.
[3] Vyas SP, Khar RK. Targeted & controlled drug delivery novel carrier systems 2011; 249-79.
[4] Pardridge WM. Drug and gene targeting to the brain via blood-brain barrier receptor-mediated transport systems. Int Congr Ser 2005; 1277: 49-62.
[5] Brightman M. Ultrastructure of the brain endothelium.Physiology and pharmacology of the blood-brain barrier handbook of experimental pharmcology 1992; 1-22.
[6] Begley DJ. The blood-brain barrier: Principles for targeting peptides and drugs to the central nervous system. J Pharm Pharmacol 1996; 48(2): 136-46.
[7] Davson H, Segal M. Physiology of the CSF and blood-brain barrier 1996.
[8] Wolburg H, Lippoldt A. Tight junctions of the blood-brain barrier: Development, composition and regulation. Vascul Pharmacol 2002; 38(6): 323-37.
[9] Bodor N, Prokai L, Wu WM, et al. A strategy for delivering peptides into the central nervous system by sequential metabolism. Science 1992; 257(5077): 1698-700.
[10] Devineni D, Klein-Szanto A, Gallo JM. Tissue distribution of methotrexate following administration as a solution and as a magnetic microsphere conjugate in rats bearing brain tumors. J Neurooncol 1995; 24(2): 143-52.
[11] Huwyler J, Wu D, Pardridge WM. Brain drug delivery of small molecules using immunoliposomes. Proc Natl Acad Sci USA 1996; 93(24): 14164-9.
[12] Kreuter J. Nanoparticulate systems for brain delivery of drugs. Adv Drug Deliv Rev 2001; 47(1): 65-81.
[13] Garcia-Garcia E, Andrieux K, Gil S, Couvreur P. Colloidal carriers and Blood-Brain Barrier (BBB) translocation: A way to deliver drugs to the brain? Int J Pharm 2005; 298(2): 274-92.
[14] Vinogradov SV, Bronich TK, Kabanov AV. Nanosized cationic hydrogels for drug delivery: Preparation, properties and interactions with cells. Adv Drug Deliv Rev 2002; 54(1): 135-47.
[15] Kreuter J, Alyautdin RN, Kharkevich DA, Ivanov AA. Passage of peptides through the blood-brain barrier with colloidal polymer particles (nanoparticles). Brain Res 1995; 674(1): 171-4.
[16] Schroeder U, Sommerfeld P, Ulrich S, Sabel BA. Nanoparticle technology for delivery of drugs across the blood-brain barrier. J Pharm Sci 1998; 87(11): 1305-7.
[17] Alyautdin RN, Petrov VE, Langer K, Berthold A, Kharkevich DA, Kreuter J. Delivery of loperamide across the blood-brain barrier with polysorbate 80-coated polybutylcyanoacrylate nanoparticles. Pharm Res 1997; 14(3): 325-8.
[18] Alyautdin RN, Tezikov EB, Ramge P, Kharkevich DA, Begley DJ, Kreuter J. Significant entry of tubocurarine into the brain of rats by adsorption to polysorbate 80-coated polybutylcyanoacrylate nanoparticles: An in situ brain perfusion study. J Microencapsul 1998; 15(1): 67-74.
[19] Friese A, Seiller E, Quack G, Lorenz B, Kreuter J. Increase of the duration of the anticonvulsive activity of a novel NMDA receptor antagonist using poly(butylcyanoacrylate) nanoparticles as a parenteral controlled release system. Eur J Pharm Biopharm 2000; 49(2): 103-9.
[20] Gulyaev AE, Gelperina SE, Skidan IN, Antropov AS, Kivman GY, Kreuter J. Significant transport of doxorubicin into the brain with polysorbate 80-coated nanoparticles. Pharm Res 1999; 16(10): 1564-9.
[21] Göppert TM, Müller RH. Polysorbate-stabilized solid lipid nanoparticles as colloidal carriers for intravenous targeting of drugs to the brain: Comparison of plasma protein adsorption patterns. J Drug Target 2005; 13(3): 179-87.
[22] Fundarò A, Cavalli R, Bargoni A, Vighetto D, Zara GP, Gasco MR. Non-stealth and stealth Solid Lipid Nanoparticles (SLN) carrying doxorubicin: Pharmacokinetics and tissue distribution after i.v. administration to rats. Pharmacol Res 2000; 42(4): 337-43.
[23] Neves AR, Queiroz JF, Weksler B, Romero IA, Couraud PO, Reis S. Solid lipid nanoparticles as a vehicle for brain-targeted drug delivery: Two new strategies of functionalization with apolipoprotein E. Nanotechnology 2015; 26(49): 495103.
[24] Stevens MFG, Hickman JA, Stone R, et al. Antitumor imidazotetrazines. 1. Synthesis and chemistry of 8-carbamoyl-3-(2-chloroethyl)imidazo[5,1-d]-1,2,3,5-tetrazin-4(3 H)-one, a novel broad-spectrum antitumor agent. J Med Chem 1984; 27(2): 196-201.
[25] Denny BJ, Wheelhouse RT, Stevens MFG, Tsang LL, Slack JA. NMR and molecular modeling investigation of the mechanism of activation of the antitumor drug temozolomide and its interaction with DNA. Biochemistry 1994; 33(31): 9045-51.
[26] Avgeropoulos NG, Batchelor TT. New treatment strategies for malignant gliomas. Oncologist 1999; 4(3): 209-24.
[27] Stevens MFG, Hickman JA, Langdon SP, et al. Antitumor activity and pharmacokinetics in mice of 8-carbamoyl-3-methylimidazo[ 5,1-d]-1,2,3,5-tetrazin-4(3H)-one (CCRG 81045: M & B398310). Cancer Res 1987; 47(22): 5846-52.
[28] Plowman J, Waud WR, Koutsoukos AD, Rubinstein LV, Moore TD, Grever MR. Preclinical antitumor activity of temozolomide in mice: Efficacy against human brain tumor xenografts and synergism with 1,3-bis(2-chloroethyl)-1-nitrosourea. Cancer Res 1994; 54(14): 3793-9.
[29] Wedge SR, Porteous JK, Newlands ES. Effect of single and multiple administration of an O6-benzylguanine/temozolomide combination: An evaluation in a human melanoma xenograft model. Cancer Chemother Pharmacol 1997; 40(3): 266-72.
[30] Patel M, McCully C, Godwin K, Balis FM. Plasma and cerebrospinal fluid pharmacokinetics of intravenous temozolomide in non-human primates. J Neurooncol 2003; 61(3): 203-7.
[31] Mehnert W, Mäder K. Solid lipid nanoparticles: Production, characterization and applications. Adv Drug Deliv Rev 2001; 47(2-3): 165-96.
[32] Kreuter J, Ramge P, Petrov V, et al. Direct evidence that polysorbate-80-coated poly(butylcyanoacrylate) nanoparticles deliver drugs to the CNS via specific mechanisms requiring prior binding of drug to the nanoparticles. Pharm Res 2003; 20(3): 409-16.
[33] Venkateswarlu V, Manjunath K. Preparation, characterization and in vitro release kinetics of clozapine solid lipid nanoparticles. J Control Release 2004; 95(3): 627-38.
[34] Calderón-Colón X, Raimondi G, Benkoski JJ, Patrone JB. Solid Lipid Nanoparticles (SLNs) for intracellular targeting applications. J Vis Exp 2015; (105): 53102.
[35] Grislain L, Couvreur P, Lenaerts M, Roland M, Deprezdecampeneere D, Speiser P. Pharmacokinetics and distribution of a biodegradable drug-carrier. Int J Pharm 1983; 15(3): 335-45.
[36] Douglas SJ, Illum L, Davis SS, Kreuter J. Particle size and size distribution of poly(butyl-2-cyanoacrylate) nanoparticles. J Col Interf Sci 1984; 101(1): 149-58.
[37] de Boer AG, Gaillard PJ. Strategies to improve drug delivery across the blood-brain barrier. Clin Pharmacokinet 2007; 46(7): 553-76.