Codelivery of zoledronic acid and doublestranded RNA from core-shell nanoparticles.

BACKGROUND: Zoledronic acid, an inhibitor of osteoclast-mediated bone resorption, has been shown to have both direct and indirect antitumor activity. However, its use in extraskeletal malignancy is limited due to rapid uptake and accumulation within bone. Polyinosinic acid-polycytidylic acid [poly (I:C)] is a synthetic double-stranded RNA with direct antitumor cytotoxicity if it can be delivered to tumor cells intracellularly.
METHODS: Cationic lipid-coated calcium phosphate nanoparticles (LCP) were developed to enable intracellular codelivery of zoledronic acid and poly (I:C). LCP codelivering zoledronic acid and poly (I:C) were prepared using an ethanol injection method. Briefly, the ethanol solution of lipids was rapidly injected into newly formed calcium phosphate crystals containing poly (I:C) and zoledronic acid, and the mixture was then sonicated briefly to form LCP. The LCP were fully characterized for mean diameter size and zeta potential, efficiency in loading zoledronic acid, cytotoxic effect in a B16BL6 melanoma cell line in vitro, and antitumor effect in B16BL6 melanoma-bearing mice.
RESULTS: LCP with a mean diameter around 200 nm and a narrow size distribution (polydispersity index 0.17) and high zoledronic acid encapsulation efficiency (94%) were achieved. LCP loaded with zoledronic acid and poly (I:C) had significantly greater antitumor activity than the free drugs in the B16BL6 melanoma cell line (P < 0.05). Furthermore, codelivery of zoledronic acid and poly (I:C) by LCP had higher cytotoxicity than delivering poly (I:C) alone by LCP (P < 0.05), indicating a synergism between zoledronic acid and poly (I:C). Finally, the antitumor study in melanoma-bearing mice also demonstrated synergism between zoledronic acid and poly (I:C) codelivered by LCP.
CONCLUSION: Cationic lipid-coated calcium phosphate nanoparticles constructed for codelivery of zoledronic acid and double-stranded RNA poly (I:C) had better antitumor activity both in vitro and in vivo. Future preclinical development of LCP encapsulating zoledronic acid and poly (I:C) for the treatment of human cancer is under way.

Introduction

Zoledronic acid and other n>an class="Chemical">nitrogen-containing bisphosphonates are potent inhibitors of osteoclast proliferation, and are used to treat osteoporosis and cancer-related bone metastases.1 Moreover, preclinical studies have demonstrated the antitumor effects of zoledronic acid in various nonskeletal tumor models, including breast cancer, myeloma, and others, suggesting that zoledronic acid has direct tumor inhibitory activity.2 Zoledronic acid can directly induce apoptosis in tumor cells, and inhibit tumor cell growth and angiogenesis.3–6 For example, zoledronic acid directly suppresses cell proliferation and induces apoptosis in highly tumorigenic prostate and breast cancers.7 The anticancer activity of zoledronic acid has also been seen in the induction of γδ T-cell activation needed to initiate both the innate and the adaptive immune responses.8,9

However, zoledronic acid n>an class="Chemical">is rapidly eliminated after intravenous injection due to preferential uptake and accumulation within bone, which results in ineffective concentrations of zoledronic acid in nonskeletal cancer tissues.10 In addition, accumulation of zoledronic acid in bone would pose a serious health risk.11 These problems could be solved by a nanoparticle drug delivery system shielding the zoledronic acid from directly binding to bone whilst in the circulation.12–16 The enhanced permeation and retention effect of the nanoparticle drug delivery system can also improve accumulation of zoledronic acid in solid tumors.17,18

Synthetin>an class="Chemical">c double-stranded RNA polyinosinic-polycytidylic acid [poly (I:C)], a ligand for endosomal receptor TLR3,19 can induce expression of inflammatory cytokines and type I interferon via the NF-κB, mitogen-activated protein kinase, and interferon regulatory factor 3 pathways, so enhancing the antitumor immune response.11,20,21 Furthermore, poly (I:C) can be a ligand for cytoplasmic melanoma differentiation-associated gene 5.22 In human melanoma, transfection of poly (I:C) into the cytoplasm can induce autophagy-mediated apoptosis via the melanoma differentiation-associated gene 5-mediated signaling pathway.21,23,24 Thus, delivering poly (I:C) to solid tumor tissue can induce tumor apoptosis directly if delivery to the cytoplasm can be achieved.

Compn>lexes n>an class="Chemical">containing nucleic acid and calcium phosphate precipitates have been used in gene transfection studies for many years.25 They can be taken up easily by cells through endocytosis and subsequently dissolved in endosomes.26 Also, calcium phosphate has low toxicity and good biocompatibility because it is the inorganic component of hard biological tissues, ie, bones and teeth.27 Therefore, it has the potential to be a good carrier system for drug delivery, especially for nucleic acid-based therapeutics. However, large aggregates are easily formed as a result of rapid crystal growth, so use of these complexes is limited to in vitro gene transfection.28 The key issue when fabricating calcium phosphate nanoparticles is to halt continuous growth of crystals. Synthesis of calcium phosphate nanoparticles can be done by various methods, including wet precipitation,29 solid state reaction,30 flame spray pyrolysis,31 and hydrothermal,32 spray-drying,33 micelle-mediated,34 reverse micelle-mediated,35,36 and double emulsion-mediated synthesis.37 These calcium phosphate nanoparticle fabrication methods usually involve multiple steps, which are not easily scaled up in the pharmaceutical manufacturing process.

In thn>an class="Chemical">is study, we devised a simple method of wet precipitation combined with cationic lipid surface coating for fabrication of calcium phosphate nanoparticles and codelivery of zoledronic acid and poly (I:C). Being a polyanion, poly (I:C) is not only a therapeutic agent, but has a unique role in the process of fabricating calcium phosphate nanoparticles. In this study, binding poly (I:C) prevented continuous growth of calcium phosphate crystals and imparted a negative charge to the surface of calcium phosphate crystals for subsequent cationic lipid coating. We also tested whether codelivery of zoledronic acid and poly (I:C) has a synergistic inhibitory effect on growth of the mouse melanoma both in vitro and in vivo.

Materials and methods

Materials

DOTAP (n>an class="Chemical">1,2-dioleoyl-3-trimethylammonium-propane) was purchased from Avanti Polar Lipids Inc (Alabaster, AL). Poly (I:C) was sourced from EMD Chemicals (San Diego, CA). Zoledronic acid was obtained from Alexis Corporation (San Diego, CA). Cholesterol and tetrabutylammonium hydrogen sulfate were purchased from JT Baker (Phillipsburg, NJ). Calcium nitrate, phosphate salt, and all other reagents were purchased from VWR International (West Chester, PA). Fetal bovine serum, Dulbecco’s Modified Eagle’s Medium, and other reagents needed for cell culture were purchased from Mediatech (Manassas, VA). A mouse melanoma cell line (B16BL6) was obtained from the National Cancer Institute (Frederick, MD).

Preparation of lipid-coated calcium phosphate nanoparticles

Calcium phosphate nanopn>artn>an class="Chemical">icles were prepared by a wet precipitation method (Figure 1).28,38 Briefly 500 μL of aqueous solution of calcium chloride (6.25 mM) was mixed with 500 μL of aqueous solution of diammonium hydrogen phosphate (3.74 mM). The pH of both solutions was preadjusted to 9.0 with 0.1 M NaOH.39 Mixing was accomplished by rapidly injecting both solutions using a 1 mL insulin syringe into a 1.5 mL tube into which 15 μL of poly (I:C) aqueous solution (5 μg/μL or higher concentrations in some experiments) was added before injection. The suspension was then mixed well by vortex for 10 seconds. Finally, 7.5 μL of zoledronic acid 10 mg/mL was added to the calcium phosphate-poly (I:C) complex to form a calcium phosphate-poly (I:C)-zoledronic acid core.

Figure 1

Fabrication of lipid-coated calcium phosphate nanoparticles.

Abbreviations: CaP, calcium phosphate; LCP, lipid-coated calcium phosphate nanoparticles; poly (I:C), polyinosinic acid-polycytidylic acid.

The lipid mixture, composed of DOTAP-cholesterol (1:1 mol/mol), was dissolved in absolute ethanol and coated onto the surface of the calcium phosphate-poly (I:C)- zoledronic acid complex. Briefly, 80 μL of the lipid mixture in 25 mg/mL ethanol solution was rapidly injected into the calcium phosphate-poly (I:C)-zoledronic acid core, and the mixture was then sonicated for 2 minutes in a bath sonicator to form lipid-coated nanoparticles consisting of a lipid shell and calcium phosphate-poly (I:C)-zoledronic acid core. The nanoparticles formed were extensively dialyzed against pH 8.0 Tris-HCl buffer to remove residual ethanol.

Preparation of cationic liposomes

DOTAP cationic liposomes were prepared using the ethanol injection method.40 Briefly, 80 μL of lipid ethanol solution (DOTAP to cholesterol, 1:1, 25 mg/mL) was rapidly injected into a 1.5 mL tube containing 1.0 mL of filtered sterilized water, and the suspension was then sonicated in a bath sonicator for 2 minutes to form liposomes. The cationic liposomes formed were extensively dialyzed against water to remove the residual ethanol.

Preparation of nanoparticles

Because n>an class="Chemical">poly (I:C) has a unique role in stabilizing LCP, LCP containing various amounts of poly (I:C) (25, 75, 150, 300 μg/mL, respectively) was prepared to investigate the effect of amount of poly ( I:C) on nanoparticle size. The mean diameters of the calcium phosphate nanoparticles, cationic liposomes, and LCP were compared between the three formulations. LCP containing various amounts of zoledronic acid (25, 50, and 75 μg/mL) and a fixed amount of poly (I:C) (75 μg/mL) were prepared using the method described above and evaluated for particle size and cytotoxicity in a B16BL6 melanoma cell line.

Particle size and zeta potential of calcium phosphate nanoparticles, cationic liposomes, and LCP

Mean diameter and n>an class="Chemical">polydispersity index were used to characterize the size distribution of the nanoparticles. The particle size and zeta potential of the different formulations were determined at room temperature using a particle sizer (Nicomp Model 380/ZLS, Particle Sizing Systems, Santa Barbara, CA). Each sample was diluted 20-fold with 0.22 μL of filtered water before measurement. All values were calculated as the mean of the three separate batches.

Quantitative analysis and calculation of zoledronic acid encapsulation efficiency in LCP

Quantitative analysis of zoledronic acid was performed by reverse-phase high-performance liquid chromatography on a Luna C18(2) column (3 μm, 150*4.6 mm) using a mobile phase composed of 5:95 methanol to phosphate buffer (8 mM, pH 7.4), 3 mM tetrabutylammonium hydrogen sulfate, and 2.3 μg/mL ethylenediamine tetra-acetic acid at a flow rate of 0.6 mL per minute at room temperature, with ultraviolet detection at 215 nm.41 Briefly, 1 mL of liposomes or nanoparticles was centrifuged through a centrifugal device with a molecular cutoff of 100,000 (Nanosep, Pall Life Sciences, Menlo Park, CA) at 12,000 rpm for 20 minutes. The supernatants containing free zoledronic acid were then carefully collected, and the zoledronic acid concentration was determined by high-performance liquid chromatography.42 The zoledronic acid encapsulation efficiency was calculated by the following equation:

Stability study

To determine the stability of LCP under storage conditions, LCP was freshly prepared and then stored at 4°C in 10 mM pH 8.0 Tris-HCl buffer, and the particle size and zoledronic acid encapsulation efficiency were then monitored during 30 days of storage.

Cell viability assay

In vitro cytotoxicity was determined by MTT assay, as described previously.43 The B16BL6 cells were grown in Dulbecco’s Modified Eagle’s medium supplemented with 10% fetal bovine serum, 100 U/mL penicillin, and 100 μg/mL streptomycin at 37°C in a humidified atmosphere containing 5% CO2. The B16BL6 cells were seeded in 96-well plates at 8 × 103 cells/well in 100 μL of medium. After 16 hours, the cells were treated with the different formulations diluted in Dulbecco’s Modified Eagle’s medium to provide the same mass concentration (μg/mL) of poly (I:C), zoledronic acid, or their combination, and incubated for 48 hours prior to MTT assay. Briefly, MTT reagent was added to the culture medium at a final concentration of 0.5 mg/mL and the cells were incubated at 37°C for an additional 4 hours. Finally, the medium was removed, the cells with dye compounds were dissolved in dimethylsulfoxide, and adsorption was measured at 544 nm using a microplate reader (Fluostar, BMG LabTech GmbH, Ortenberg, Germany). Viability was expressed as a percentage of the untreated control cells (100% viability).

Animal study

Female 8-week-old Charles River C57BL/6 mice were used to evaluate the in vivo efficacy of the different formulations. The animal experiments complied with the rules set down in the National Institutes of Health Guide for the Care and Use of Laboratory Animals and the Institutional Animal Care and Use Committee. B16BL6 mouse melanoma cells were used as the tumor development model. B16BL6 cells (5 × 105) were inoculated subcutaneously into the mice to induce tumor formation and growth. After 5 days, when the tumor volume had reached approximately 50 mm3, mice were randomly divided into four groups (n = 6) to receive phosphate-buffered solution (control), free zoledronic acid, LCP-poly (I:C), or LCP-poly (I:C)-zoledronic acid, and received four peritumoral injections on days 0, 2, 4, and 6 after tumor formation at a dose of 4.5 μg per mouse. The doses of 4.5 μg per mouse were calculated as free zoledronic acid or poly I:C or their 1:1 combination in the three treatment groups mentioned above. Following treatment, the animals were monitored regularly for body weight, tumor growth, and survival. Tumor volumes were assessed by measuring two perpendicular diameters with digital calipers and using the formula (L*W2)/2, where L is the longest diameter and W is perpendicular to L.42 Results are expressed as the mean tumor volume ± standard deviation for six mice.

Statistical analysis

The Student’s t-test was used to identify significant differences between groups. P < 0.05 was considered to be statistically significant.

Results and discussion

Nanoparticle preparation and characterization

As shown in Fn>an class="Chemical">igure 2A, the diameter of LCP without poly (I:C) prepared by the newly formed calcium phosphate crystals and DOTAP was about 8.3 μm, suggesting no affinity between calcium phosphate crystals and DOTAP. Therefore, the surface of the calcium phosphate crystal needed to be functionalized by negative charges for further coating with cationic liposomes. Poly (I:C), a negatively charged synthetic nucleic acid, was chosen to functionalize the surface of calcium phosphate because of its high affinity for calcium phosphate and therapeutic effects. We then investigated the effect of poly (I:C) on the particle size of LCP. The particle size was still large with the addition of poly (I:C) 25 μg/mL (Figure 2A). However, the diameter of LCP was dramatically decreased to the size range of nanoparticles (around 200 nm) by addition of poly (I:C) 75 μg/mL to the preparation. There was no significant difference in particle size between the three poly (I:C) concentrations used (75, 150, 300 μg/mL), indicating that 75 μg/mL of poly (I:C) was enough to prevent continuous growth of calcium phosphate crystals. Meanwhile, under such conditions, the charge (+/−) to N/P ratio (for DOTAP and poly (I:C), respectively), was 4:1, and this ratio was appropriate for DOTAP coating to achieve colloidal stability of LCP. It was confirmed that all the poly (I:C) was associated with LCP, with an N/P ratio of 4:1 by agarose gel retardation assay (data not shown). The agarose gel retardation assay also indicated that increasing poly (I:C) to >150 μg/mL in the preparation resulted in gradual accumulation of free poly (I:C) in the formulation (data not shown), so an N/P ratio of 4:1 was used for subsequent experiments.

Figure 2

(A) Effect of poly (I:C) on particle size of LCP without zoledronic acid. (B) Effect of ratio of poly (I:C) to zoledronic acid on particle size of LCP.

Abbreviations: LCP, lipid-coated calcium phosphate nanoparticles; poly (I:C), polyinosinic acid-polycytidylic acid; zol, zoledronic acid.

In order to n>an class="Chemical">codeliver poly (I:C) and zoledronic acid, different weight ratios of poly (I:C) to zoledronic acid with a fixed 75 μg/mL amount of poly (I:C) were used in the fabrication of LCP, and their sizes were compared (Figure 2B). There were no obvious increases in LCP particle size when the weight ratios were varied from 3:1 to 3:3 [poly (I:C) to zoledronic acid], but the size increased to around 300 nm at a ratio of 3:6. Because zoledronic acid has high affinity for calcium phosphate,12 it will compete with poly (I:C) binding to calcium phosphate, leading to compromise of the stabilization effects of poly (I:C).

Four different delivery systems were prepared and characterized, and the results were summarized in Table 1, which shows that LCP is capable of delivery of poly (I:C) alone. The size of LCP-poly (I:C) is around 180 nm. The lipoplex formed by mixing of cationic liposomes, poly (I:C), and zoledronic acid, had the smallest particle size of 138 nm but the broadest size distribution (polydispersity index 0.33) of all the formulations tested. It appeared that only 42% of the total amount of zoledronic acid was associated with the lipoplex. This is probably due to the rapid diffusion of zoledronic acid from the lipoplex because the molecular weight of zoledronic acid is less than 300 Da. The LCP-poly (I:C)- zoledronic acid, formed by a calcium phosphate core and DOTAP coating, had higher zoledronic acid encapsulation efficiency (94%) and a relatively small size (205 nm). Being one of the bisphosphonates, zoledronic acid anions are suitable for coordinating calcium cations in the calcium phosphate phase through bidentate chelation.44 The high affinity between calcium phosphate and zoledronic acid decreased the diffusion of zoledronic acid from LCP. The lipid coating added another diffusion barrier to zoledronic acid, leading to overall high encapsulation efficiency. Interestingly, without a lipid coating, the freshly prepared intermediate core formed by calcium phosphate, poly (I:C), and zoledronic acid had a negative charge (−10 mV) and a high loading efficiency for zoledronic acid (90%), suggesting that the major contribution to the high encapsulation efficiency of zoledronic acid in LCP was the high affinity between zoledronic acid and calcium phosphate. The size distribution of LCP-poly (I:C)-zoledronic acid is shown in Figure 3.

Table 1

Diameter, polydispersity index, zeta potential, and encapsulation efficiency of different nanoparticles

	Diameter (nm)1	Polydispersity index	Zeta potential (mV)	Encapsulation efficiency (% zoledronic acid)
LCP-poly (I:C)	184 ± 25	0.22 ± 0.02	43.2 ± 5.3	N/A
Lipoplex-poly (I:C)-zoledronic acid2	138 ± 40	0.33 ± 0.30	44.2 ± 6.3	42 ± 5.7
CaP-poly (I:C)-zoledronic acid2	359 ± 15	0.12 ± 0.10	−10.1 ± 2.5	90 ± 2.4
LCP-poly (I:C)-zoledronic acid2	205 ± 20	0.17 ± 0.04	21.7 ± 4.2	94 ± 1.3

Notes: Data are presented as the mean ± standard deviation; poly (I:C)-zoledronic acid = 1:1 (weight ratio).

Abbreviations: CaP, calcium phosphate; LCP, lipid-coated calcium phosphate nanoparticles; poly (I:C), polyinosinic acid-polycytidylic acid.

Figure 3

Size distribution of LCP-poly (I:C)-zoledronic acid.

Abbreviations: LCP, lipid-coated calcium phosphate nanoparticles; poly (I:C), polyinosinic acid-polycytidylic acid.

We then studied the stabn>an class="Chemical">ility of LCP in pH 8.0 Tris- HCl buffer stored at 4°C for 30 days. Although the calcium phosphate-poly (I:C)-zoledronic acid complex had a relatively small size of 360 nm when freshly prepared, its size gradually increased to more than 1 μm after 24 hours (Figure 4). However, LCP-poly (I:C)-zoledronic acid demonstrated good colloidal stability. Figure 4 shows that the particle size of LCP-poly (I:C)-zoledronic acid remained unchanged over 30 days. Therefore, the cationic DOTAP coating on the LCP nanoparticle contributed to its good colloidal stability. The cationic liposome drug delivery system has been widely studied for gene transfection, vaccine delivery, and antitumor targeting. LCP may have some characteristics similar to those of a cationic liposome, such as good colloidal stability. However, more experiments are required for a better understanding of the difference between these two drug delivery systems.

Figure 4

Change of particle size of LCP-poly (I:C)-zoledronic acid and CaP-poly (I:C)-zoledronic acid at 4°C within 30 days.

Abbreviations: CaP, calcium phosphate; LCP, lipid-coated calcium phosphate nanoparticles; poly (I:C), polyinosinic acid-polycytidylic acid; ZOL, zoledronic acid.

Codelivery of poly (I:C) and zoledronic acid had superior cytotoxicity in melanoma cells

It has been repn>orted that n>an class="Chemical">poly (I:C) induces direct apoptotic cytotoxicity in cancer cells, including melanoma,45 lung cancer,46 and breast cancer,45,47 if poly (I:C) can be delivered into the cytoplasm.48 Therefore, we formulated poly (I:C) using calcium phosphate nanoparticles, a DOTAP lipoplex, and LCP, and compared their cytotoxicity in B16BL6 mouse melanoma cells. As shown in Figure 5, at the same poly (I:C) concentration of 0.5 μg/mL, LCP-poly (I:C) showed the highest cytotoxicity to B16BL6 cells, followed by the poly (I:C)-lipoplex, and finally poly (I:C)-calcium phosphate nanoparticles. Cell viability was 47.1%, 61.2%, and 86.3%, respectively. Blank calcium phosphate nanoparticles, DOTAP liposomes, or their combination had no cytotoxic effect on B16BL6 cells (data not shown). The enhanced cytotoxic effect of LCP could be explained by delivery of more poly (I:C) into the cytoplasm by LCP. It has been reported that the calcium phosphate core in LCP is unstable in an acidic endosomal environment, so its decomposition to free calcium and phosphate ions in the endosome will increase osmotic pressure and cause swelling and rupture of the endosomes, and release of their contents into the cytosol.26,49,50 However, without DOTAP, the negatively charged calcium phosphate-poly (I:C) nanoparticles are not easily taken up by melanoma cells, leading to a compromised cytotoxic effect.48

Figure 5

In vitro cytotoxicity of free poly (I:C), CaP-poly (I:C), Lipoplex-poly (I:C), and LCP-poly (I:C) in a B16BL6 cell line, with a poly (I:C) concentration of 0.5 μg/mL.

Notes: *P < 0.05, compared with free poly (I:C); **P < 0.05, compared with lipoplex-poly (I:C).

Abbreviations: CaP, calcium phosphate; LCP, lipid-coated calcium phosphate nanoparticles; poly (I:C), polyinosinic acid-polycytidylic acid.

Next, the cytotoxicity of n>an class="Chemical">LCP codelivering poly (I:C) and zoledronic acid was tested in B16BL6 cells. Like free poly (I:C), free zoledronic acid at a concentration of 0.5 μg/mL had no cytotoxic effect in B16BL6 cells. We then prepared LCP codelivering poly (I:C) and zoledronic acid in different ratios, but the combined concentration of both drugs (poly (I:C) + zoledronic acid) in LCP was kept constant (0.5 μg/mL) in the subsequent MTT assay. The results demonstrated that the drug combination was more potent in its ability to generate cytotoxicity in melanoma cells than were the individual drugs used alone (Figure 6). As shown in Figure 6, the cell viabilities after treatment with free zoledronic acid and LCP-poly (I:C) were 91.8% and 49.0%, respectively. Codelivery of poly (I:C) and zoledronic acid (1:1) by LCP showed enhanced cell cytotoxicity, with a cell viability of 14.4%. Interestingly, the greater the amount of zoledronic acid in the LCP-poly (I:C)-zoledronic acid complex, the greater the potency of the cytotoxicity to B16BL6 cells, although the combined concentration of the two drugs was the same. However, from previous formulation studies, zoledronic acid could not be increased to more than 50%, because more zoledronic acid led to instability of LCP during the fabrication process.

Figure 6

In vitro cytotoxicity of LCP-poly (I:C)-zoledronic acid in B16BL6 cell line with different weight ratios of poly (I:C) to zoledronic acid.

Notes: The concentration of total drugs (poly (I:C) + zoledronic acid) was 0.5 μg/mL. *P < 0.05, compared with the ratio of 3/0; **P < 0.01, compared with the ratio of 3:0.

Abbreviations: LCP, lipid-coated calcium phosphate nanoparticles; poly (I:C), polyinosinic acid-polycytidylic acid; ZOL, zoledronic acid.

Tumor inhibition by codelivering poly (I:C) and zoledronic acid in melanoma-bearing mice

Based on the superior n>an class="Disease">cytotoxicity of LCP codelivering poly (I:C) and zoledronic acid in the B16BL6 melanoma cell line, we investigated its antitumor activity in B16BL6 tumor-bearing mice. The tumors were allowed to grow subcutaneously for 5 days, and the tumor-bearing mice were then treated with phosphate-buffered solution (control), free zoledronic acid, LCP-poly (I:C), or LCP-poly (I:C)-zoledronic acid by peritumoral injection on days 0, 2, 4, and 6. As shown in Figure 7, the control mice had the largest tumors at day 11. Mice treated with LCP-poly (I:C)-zoledronic acid showed significant tumor growth inhibition compared with the other groups (P < 0.05). Mice treated with LCP-poly (I:C) also showed slight tumor growth inhibition.

Figure 7

Tumor growth inhibition by poly (I:C) and zoledronic acid codelivered by LCP in melanoma-bearing mice.

Notes: *P < 0.05 compared with PBS; **P < 0.01 compared with PBS.

Abbreviations: LCP, lipid-coated calcium phosphate nanoparticles; poly (I:C), polyinosinic acid-polycytidylic acid; ZOL, zoledronic acid; PBS, phosphate-buffered solution.

Poly (I:C) has n>an class="Gene">multiple actions in the inhibition of tumor growth, including direct apoptosis effects on tumor cells and modulation of the immune system.51–55 One of the side effects of poly (I:C) is induction of toxic cytokines, so its use in cancer is limited.56–58 In our study, by encapsulating zoledronic acid and poly (I:C) in LCP, the effective doses of both poly (I:C) and zoledronic acid could be decreased, so this formulation may have less toxic effects. The current peritumoral injection of LCP-poly (I:C)-zoledronic acid in melanoma-bearing mice confirmed the in vivo efficacy of codelivery of poly (I:C) and zoledronic acid by LCP. However, further development of LCP by surface PEGylation and targeting ligands is required for intravenous injection, and is suitable for treatment of other type of tumors.

Conclusion

LCP were developn>ed for sn>an class="Chemical">imultaneous delivery of zoledronic acid and poly (I:C). Lipid-coated nanoparticles including a calcium phosphate core and lipid shell had a narrow particle size distribution and high loading efficiency for poly (I:C) and zoledronic acid, with good stability. In addition, codelivery of zoledronic acid and poly (I:C) offered superior antitumor activity in both in vitro and in vivo studies. These results suggest a potential for future preclinical development of zoledronic acid and poly (I:C)-encapsulating LCP for the treatment of human cancer.