Paclitaxel-clusters coated with hyaluronan as selective tumor-targeted nanovectors
Introduction
Paclitaxel (PTX), a microtubules stabilizer that causes mitotic arrest, has shown broad–spectrum activity in many solid tumors including ovarian, breast, AIDS-related Kaposi’s sarcoma, lung, head and neck and bladder [1], [2]. The FDA-approved formulation of PTX-Cre (Taxol®), requires dissolving the paclitaxel in Cremophor® EL (polyoxyethylated castor oil) and ethanol (CrEL) [3]. However, the use of Taxol® requires premedication with corticosteroids and antihistamines to reduce risks of hypersensitivity reaction [4], [5], [6], [7]. It can also cause neutropenia [8], and prolonged, peripheral neuropathy, which may be associated with axonal degradation [6], [7]. In addition to serious toxicities, CrEL may negatively impact efficacy by limiting tumor penetration through the formation of large polar micelles, which can lead to nonlinear pharmacokinetics and decreased unbound drug fraction [6], [8].
Among carriers for paclitaxel made from biological materials, liposomes have been well-studied as carriers for PTX, although drug loading into liposomes is relatively low (≤10% (w/w)) [9], [10], [11], [12], [13], [14]. Recently, a new formulation was approved by the FDA, albumin-bound PTX (nab™-PTX; Abraxane®) forming nanoparticles (∼135 nm in diameter). This formulation, consisting of unmodified PTX and human albumin, is CrEL-free. By eliminating CrEL from its formulation, nab-PTX reduces risks of hypersensitivity reactions, does not require premedication, and can be given over a shorter period without special intravenous tubing [15]. However, it is reported to have low PTX loading yield, similar to liposomes and minimal improvement in efficacy [16]. Both liposomes and nab™-PTX are non-targeted drug carriers that utilize the enhanced permeability and retention effect (EPR) [17], [18] to accumulate at close proximity to the tumors.
The frequent overexpression of the hyaluronan (HA) receptors CD44 and CD168 (RHAMM) on many types of tumors opens new avenues for targeting by the naturally-occurring high-molecular weight HA [19], [20], [21], [22]. HA, a naturally-occurring glycosaminoglycan, is one of the major components of the extracellular matrix (ECM). It is found in many tissues such as skin, joint tissue (in synovial fluid) and eyes [23], [24]. HA is known as a bioadhesive compound capable of binding with high affinity to both cell surface and intracellular receptors, to ECM components and to itself [25], [26]. In cancer cells, binding of HA to its receptors is involved in tumor growth and spreading. CD44 regulates cancer cells proliferation and metastatic processes [27], [28]. In addition, disruption of HA–CD44 binding was shown to reduce tumor progression [29], [30], [31]. Administration of exogenous HA resulted in arrest of tumor spreading [31]. HA is a non-toxic and non-immunogenic compound, already approved for use in eye surgery, joint therapy and wound healing [32]. Coating small unilamellar liposomes with HA stabilizes these particles in a cycle of lyophilization and rehydration [33], provides selective targeting to tumors expressing the HA receptors [19], [20], [34], and presents a scaffold for conjugation of other ligands to the surface for further improving the selectivity to cell surface receptors [35].
Here, we report on tumor-targeted nanoparticles, constructed of PTX-phosphatidylethanolamine (PE) clusters covalently coated with HA. The terms used for the particles themselves (i.e., drug-free) and when loaded with PTX are GAGs and PTX-GAGs, respectively [36]. In contrast to other phospholipids such as phosphatidylcholine (PC) or phosphatidylserine (PS) that form lipid bilayers closed into circular particle like liposomes, PE by itself does not form a liposome, but other lamellar shapes. The variety of shapes depends on several factors such as the lipid side chains, concentration, temperature, pressure, hydration level, pH, and salt concentration [37], [38], [39], [40], [41], [42]. For the present task we selected dilauroyl-PE (DLPE). The saturated chains are more stable than unsaturated chains that tend to oxidize into toxic peroxi-lipids. Being relatively-short, the DL chains impart additional advantages: (i) relatively low gel-liquid crystalline transition temperature (Tm = 43 °C) [43], indicating homogenous particle suspensions may be achieved without the need for overheating that may harm incorporated drugs, and (ii) higher affinity, compared to longer chains, to PTX [14], [44].
Herein, we report studies at the molecular, cellular and whole animal levels of organization. The molecular studies included preparation, physicochemical, thermal analyses and ultrastructure characterization of the PTX-GAG particles. The in vitro studies in cancer cells included GAGs-cell binding and internalization, as well the cytotoxicity of PTX-GAGs. Biological effects of the PTX-GAG particles, studied in BALB/c mice, included evaluations of liver enzyme release and inductions of cytokines and of interferon response. PTX-GAGs retention in circulation, biodistribution, weight changes and efficacy were studied in BALB/c mice bearing a solid s.c. tumor (CT-26). Control systems were usually saline, drug-free GAGs and Taxol, and the addition of Abraxane® for the in vivo efficacy studies.
Section snippets
Cell lines
Cell monolayers (all were purchased from American Type Culture Collection (ATCC)) were grown in 100×20 mm dishes (culture plates and dishes were from Corning, Corning Glass works, Corning, New York, USA). The CT-26 and D122 cells were cultured in RPMI 1640 medium at 37 °C in 5% CO2 supplemented with 10% fetal calf serum (FCS), Penicillin (10,000 units/ml), Streptomycin (10 mg/ml) and l-Glutamine (200 mm). The PANC-1 cells were similarly cultured except the medium was DMEM. Cells were free of
Structural and physicochemical characterization of drug-free and PTX-loaded particles
The steps in forming the PTX-GAG particles are illustrated in Fig. 1A (drug-free GAGs are prepared quite similarly, except the omission of drug). As described under methods and demonstrated in Fig. 1A, GAGs are composed of the lipid molecules that self-assemble into particulate clusters (with/without PTX), that are then covalently coated with high-molecular weight HA at a lipid:HA ratio of 10:1 (w/w). HA is the main component of the particle’s surface and its interior contains both the lipid
Conclusions
We devised a strategy that utilized taxanes’ affinity to lipids, to self-assemble into nanoparticle-like clusters and then, by covalently binding them to HA, we further exploited the interaction between the HA-coated particles and CD44 on tumor cells. PTX was chosen as a proof-of-principle and was formulated in the GAGs (PTX-GAGs). We found this system to be superior to the FDA-approved formulations in improved efficacy (even at 4-fold lower doses), and in reduced unwanted adverse effects.
Acknowledgements
We declare no conflict of interests. This work was supported by grants from the Alon Foundation, the Marie Curie IRG-FP7 of the European Union, and the Lewis family-trust for cancer research to Dan Peer.
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IR and DP contributed equally to this study.
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Present address: Department of Biomedical Engineering, Technion, Israel
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Former affiliation: Immune Disease Institute, Harvard Medical School, Boston 02115, Massachusetts, USA