Development of Drug Loaded Nanoparticles Binding to Hydroxyapatite Based on a Bisphosphonate Modified Nonionic Surfactant

Zhang, Jiabin; Liu, Xinrong; Deng, Tongming; Yao, Peng; Song, Heliang; Zhou, Shaobing; Yan, Weili

doi:https://doi.org/10.1155/2015/393968

Journal of Nanomaterials

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Abstract Introduction Methods Results and Discussion Conclusions References Copyright Related Articles

Research Article | Open Access

Volume 2015 | Article ID 393968 | https://doi.org/10.1155/2015/393968

Development of Drug Loaded Nanoparticles Binding to Hydroxyapatite Based on a Bisphosphonate Modified Nonionic Surfactant

Jiabin Zhang,¹Xinrong Liu,¹Tongming Deng,¹Peng Yao,¹Heliang Song,¹Shaobing Zhou,²and Weili Yan¹

Academic Editor: Xuping Sun

Received12 Jan 2015

Accepted16 Mar 2015

Published05 Apr 2015

Abstract

This study aimed at development of drug loaded nanoparticles which could bind to hydroxyapatite (HA) to construct drug or growth factor releasing bone graft substitutes. To this end, the terminal hydroxyl group of a nonionic surfactant Brij 78 (polyoxyethylene (20) stearyl ether) was first modified with pamidronate (Pa). Using Pa-Brij 78 as both a surfactant and an affinity ligand to HA, three different Pa surface functionalized nanoparticles were prepared, named as solid lipid nanoparticles (Pa-SNPs), nanoemulsions (Pa-NEMs), and PLGA nanoparticles (Pa-PNPs). A model drug curcumin was successfully encapsulated in the three nanoparticles. The sizes of Pa-NEM and Pa-PNP were around 150 nm and the size of Pa-SNP was around 90 nm with polydispersity indexes (PDIs) less than 0.20. Drug encapsulation efficiencies of the three nanoparticles were all greater than 85%. Furthermore, the order of binding affinity of the nanoparticles to HA was . After lyophilization, the sizes of the three nanoparticles were increased about 0.5–2.0-fold but their binding affinities to HA were almost the same as the fresh prepared nanoparticles. In conclusion, a Pa-modified Brij 78 was synthesized and used for fabrication of a series of drug loaded nanoparticles to construct drug-eluting HA-based bone graft substitutes.

1. Introduction

Hydroxyapatite (HA), a mineral form of calcium apatite with the formula Ca₅(PO₄)₃(OH), is the major inorganic component of bone and teeth in mammals [1]. Because the crystalline phase of natural bone is similar to HA, HA ceramics have been widely used as a substitute in bone grafts. The porosity of HA in the range of 100–200 μm in diameter enables mesenchymal cell migration, adhesion, proliferation, and differentiation into osteoblasts and the structure is also the basis of osteoconductive characteristics of HA. The unique physical property of HA allows the growth of neovasculature and infiltration of osteogenic precursor cells during the bone growth process. However, a graft material that is only osteoconductive cannot transfer inductive simulative signals but rather acts only as a scaffold that supports the bone growth [2], so ideally exogenous bioactive small molecules or growth factors should be incorporated into the graft substitute. Furthermore, musculoskeletal diseases and disorders often require drug treatment at the specific sites of surgery or defect [3]. In bone tissue engineering and treatment, the drugs could be not only traditional drugs such as antibiotic, anticancer, anti-inflammatory, but also biological agents, such as proteins and nucleic acids, which produce exogenous osteoinductive signals [4]. Thus, it is an urgent need to design drug and/or growth factor releasing HA for the bone grafts and repair.

There are several approaches to incorporate drugs or growth factors into HA. For example, the growth factors can be chemically modified to have the binding affinity to HA [5] and the small molecule drugs can be physically absorbed onto the surface of calcium phosphate based biomaterials [6]. These approaches rely on the fixed and limited surface of HA. Moreover, the incorporation of drugs into HA requires the specific chemical or physical properties of the drugs, so it is impossible to utilize a universal method to fabricate drug loaded and releasing HA. Furthermore, the highly hydrophobic drugs are difficult to be incorporated into HA crystal.

Drugs or growth factors releasing from bone graft substitutes should be in a controlled and sustained manner [7–11], and this can be achieved by nanoparticles (NPs) drug delivery system. Thus, the combination of drug loaded NPs with HA is a promising approach to prepare drug-eluting HA and keep both advantages of NPs and HA. First, the binding affinity between NPs and HA is majorly determined by their surface properties but is independent of the chemical or physical properties of drugs inside of NP, so theoretically the complex (NP-HA) formed by NPs and HA can incorporate drugs with a broad range of physical and chemical characteristics. Second, the NP system could virtually overcome the limitation of the HA surface to increase the drug loading efficiency of HA. Third, the matrix of NPs provides a diffusion barrier for the release of drugs and growth factors and the researchers are able to adjust the rate of the release by rational design of the components of the matrix of the NPs.

The structure of bisphosphonates (BP) presents two phosphonate groups sharing a common carbon atom (P-C-P), which are believed to be responsible for its high affinity to bone and HA. BP was utilized for the modification of the surfaces of micelles, liposomes, and NPs in the literature for bone targeting [12–15]. For example, the BP modified cholesterol, DSPE-PEG2000, and BPA have been used to prepare liposomes and micelles targeting bone [16]. Furthermore, de Miguel et al. synthesized PBLG-b-PEG-BP to prepare bone targeted NPs and achieved good results [13]. Thamake et al. prepared PLGA NPs and then coated BP on the surface of NPs resulting in satisfying bone targeting effects [15]. Theoretically, all those BP decorated bone targeted NPs could also be used for fabrication of drug releasing HA bone grafts substitutes. However, it is favorable to design a universal surfactant compound for fabrication of multiple types of NPs to satisfy the requirements of bone tissue engineering and treatment.

To this end, we synthesized a BP (e.g., pamidronate, Figure 1(a)) modified nonionic surfactant Brij 78 (Pa-Brij 78). Using Pa-Brij 78, three different Pa surface functionalized NPs (Pa-NPs) were then prepared successfully including E-wax based solid lipid NPs (Pa-SNPs), glycerol trioctanoate based nanoemulsions (Pa-NEMs), and PLGA based biodegradable NPs (Pa-PNPs) [11–15]. We then studied the interactions between the Pa-NPs and HA and the properties of the NP-HA complex.

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2. Material and Methods

2.1. Materials

Brij 78, 4-toluene sulfonyl chloride, triethylamine, pamidronate disodium, sodium bicarbonate, TPGS, glycerol trioctanoate, PLGA, and curcumin were purchased from Sigma (St. Louis, MO). E-wax was provided by Spectrum (New Brunswick, NJ). Hydroxyapatite was provided by Sinopharm Group (Shanghai, China).

2.2. Synthesis of Ts-Brij 78

Brij 78 (1.15 g, 1 mmol) was first dissolved in 15 mL dichloromethane (DCM) and incubated at 0°C and 4-methyl-benzenesulfonyl chloride (380 mg, 2 mmol) and triethylamine (303 mg, 3 mmol) premixed in 5 mL DCM were added to the Brij 78 solution dropwise. The mixture was stirred for 18 h at room temperature, followed by rotary evaporation under reduced pressure, and the precipitate was redissolved in 65 mL ethanol acidified with 250 μL 1 M HCl. The solution was kept overnight at −20°C and then the formed precipitate was centrifuged at 5000 g at −10°C. The solid Ts-Brij 78 was stored at −20°C.

2.3. Synthesis of Pa-Brij 78

Ts-Brij 78 (1.3 g, 1 mmol), pamidronate disodium (370 mg, 1 mmol), and sodium bicarbonate (420 mg, 5 mmol) were dissolved in 20 mL water. The mixture was refluxed for 24 h, after which the solution was evaporated under reduced pressure and the precipitate was redissolved in 30 mL ethanol. The solution was filtered, the residue was discarded, and the filtrate was rotary evaporated under reduced pressure; then the precipitate was washed by petroleum ether three times and the solid was dried under vacuum. The solid Pa-Brij 78 was stored at room temperature.

2.4. Determination of Critical Micelle Concentration (CMC) of Pa-Brij 78

The electrical conductivity method was widely used to estimate the degree of ionization of ionic micelles and was used in determining the CMC of ionic surfactant [17]. To determine the CMC of Pa-Brij 78, different concentrations of Pa-Brij 78 aqueous solutions (0.1–3.9 mM) were prepared and their molar conductivities were measured at 25°C by a software of a particle size analyzer (Zetasizer Nano-ZS, Malvern Instruments Ltd, Malvern, UK). The graph of molar conductivities versus concentrations was plotted on which the turning point is the CMC of Pa-Brij 78.

2.5. Preparation of Curcumin Loaded NPs Using Pa-Brij 78

2.5.1. Curcumin Loaded Solid Lipid NPs

The method of preparation of E-wax based solid lipid NPs was based on previous reports [18, 19] with slight modification. Briefly, 4 mg of E-wax, 7 mg of Pa-Brij 78, or the mixture of Brij 78 and Pa-Brij 78 and 0.4 mg of a model drug curcumin were mixed in a glass vial and then heated at 65°C and then 200 μL 65°C distilled water was added to the vial. The mixture was stirred for 10 min at 65°C to form a slurry-like mixture. Then, 1.8 mL distilled water at 65°C was added to the vial heated at 65°C; the mixture was continued stirring at 65°C for 40 min to form a warm clear oil-in-water microemulsion. NPs were obtained by cooling the vials to room temperature while stirring. The size and PDI of the NPs were measured by a particle size analyzer (Zeta sizer Nano-ZS, Malvern Instruments Ltd, Malvern, UK).

2.5.2. Curcumin Loaded Nanoemulsion

The method of preparation was adapted from previous work [18] with slight modification. Briefly, 2 mg of glycerol trioctanoate as the oil phase, 3.5 mg of Pa-Brij 78, or the mixture of Brij 78 and Pa-Brij 78 in some experiments as surfactants, 1.2 mg of TPGS as a cosurfactant, and 0.6 mg of curcumin as a model drug were added and then heated to 55°C followed by addition of distilled water (200 μL, 55°C) at 55°C. The mixture was stirred thoroughly for 10 min at 55°C to form a slurry-like mixture. Then, 1.8 mL 55°C distilled water was added to the vial at 55°C and the mixture was stirred at 55°C for at least 40 min to form a warm clear oil-in-water microemulsions. Nanoemulsions were obtained by cooling the vials to room temperature while stirring. The size and PDI of the NPs were measured by a particle size analyzer.

2.5.3. Curcumin Loaded PLGA NPs

The method of preparation was adapted from previous work [16, 17] with slight modification. Briefly, PLGA (20 mg) and 2 mg of curcumin were dissolved in 1 mL DCM, and then the organic solution was poured into 4 mL 0.3% Pa-Brij 78 aqueous solution. The mixture was stirred vigorously for 5 min and then poured into the high pressure homogenizer (Model number JN-02C by Junbio, Guangzhou, China) with the pressure of 1500 bars at 4°C for 5 consecutive cycles to form a microemulsion. The DCM was removed from the microemulsion under reduced pressure to form the curcumin loaded PLGA NPs. The size and PDI of the NPs were measured by a particle size analyzer.

2.6. Curcumin Encapsulation in NPs

The method of determination of the entrapment efficiency of curcumin in the NPs was adapted from literature [10] with slight modification. Briefly, ultrafiltration centrifuge tubes (30 kD MWCO from VWR) were used to separate free curcumin from the NPs. The concentration of curcumin in the filtrate after centrifugation was measured by a fluorescence method (excitation wavelength, 420 nm; emission wavelength, 470 nm). A standard curve was plotted using a set of standard concentrations of curcumin dissolved in ethanol. The amount of encapsulated curcumin and the encapsulation efficiency were calculated by the following equation:

2.7. Scanning Electron Microscopy (SEM)

Prior to the examination, the samples were deposited on a brass stub using a double-sided tape and stored at −20°C and then the samples were freeze-dried for 12 h. The samples were gold-coated for 200 s by a sputter coater. The morphologies of nanoparticles were examined using a Scanning Electron Microscope (JEOL JSM-7001F, Japan) operated at an accelerating voltage of 15 kV.

2.8. Binding Ratio of NPs or Pa-NPs to HA

First, the concentration of each NP was diluted to 1.0 mg/mL of matrix used. One mL of each of the curcumin loaded NPs (SNP, Pa-SNP, NEM, Pa-NEM, PNP, and Pa-PNP) and 5–200 mg dry powder of HA were mixed in 1.5 mL centrifuge tubes. The NPs and HA were incubated with gentle shaking for 5 min on the oscillator and then briefly centrifuged to separate unbound NPs from the complex of HA/Pa-NPs. The NPs in the supernatant were quantified by measurement of curcumin concentration by a fluorescence method mentioned in Section 2.6. For the binding kinetics study, 1 mL of each of the NPs described previously and 60 mg HA were added to 1.5 mL centrifuge tubes and then incubated with gentle shaking for different time on the oscillator and centrifuged for separation of unbound NPs from HA; the unbound NPs in the supernatant were quantified by measurement of curcumin concentration by a fluorescence method mentioned in Section 2.6.

The NPs were also labeled by coumarin (10% weight of curcumin) for fluorescence images. The phase contrast and fluorescence images were captured by an Olympus IX71 fluorescence microscope.

2.9. Specific Binding of Pa-NPs to HA

To study specificity of Pa-NPs binding to HA, the HA/Pa-NPs complex was constructed with the method mentioned in Section 2.7. The pamidronate disodium aqueous solution (10 mM or 50 mM) was then added to the complex of HA/Pa-NP followed by gentle shaking at 37°C for 2 h for competition. After centrifugation, the unbound NPs in the supernatant were quantified by measurement of curcumin concentration by a fluorescence method mentioned in Section 2.6.

2.10. Binding of Pa-NPs to HA with the Existence of Free Calcium Chloride

One mL of each Pa-NPs and 60 mg HA were added to a centrifuge tube with or without the existence of 2.5 or 5 mM calcium chloride. The centrifuge tube was incubated at 37°C with gentle shaking for 5 min on the oscillator and then centrifuged for separation of unbound NPs from the complex of HA/Pa-NPs. The amount of unbound NPs in the supernatant was quantified by measurement of curcumin concentration by a fluorescence method mentioned in Section 2.6.

2.11. Stability of the Complex of HA/Pa-NPs in Calcium Chloride Solution

The HA/Pa-NPs complex was prepared by the method mentioned in Section 2.7. The calcium chloride solution (final concentration equal to 2.5 mM or 5.0 mM) was then added to the complex of HA/Pa-NP followed by gentle shaking at 37°C for 2 h. After centrifugation, the amount of NPs in the supernatant was quantified by measurement of curcumin concentration by fluorescence method mentioned in Section 2.6.

2.12. The Freeze-Drying of NPs

Pa-NPs suspension was mixed with equal volume of lyoprotecting solution (20% sucrose solution). Then the Pa-NPs were freeze-dried by a standard protocol. The freeze-dried samples were stored in −80°C for a month and reconstructed in PBS buffer to obtain recovered Pa-NPs suspensions. The recovered Pa-NPs were first analyzed by size distribution and PDI and then were tested for binding affinity to HA and the results were compared with fresh prepared Pa-NPs.

3. Results and Discussion

3.1. Synthesis and Characterization of Pa-Brij 78

Brij 78 contains a hydrophilic PEG chain, so the hydroxyl end group of PEG was first activated by TsCl to form Ts-Brij 78. The Pa-Brij 78 was then successfully conjugated by reaction of amine group of Pa to the Ts-Brij 78, with the existence of sodium bicarbonate to keep the reaction under basic condition (Figure 1(a)). The overall yield achieved about 80%. The structure of Pa-Brij 78 was confirmed by ¹H-NMR (the solvent was D₂O). The signals (7.73–7.39, m, 1H, 2.43, s, 2H, and 1.61, s, 2H) indicated the existence of a –NH–CH₂–CH₂– in this compound (Figure 1(b)). The CMC of Pa-Brij 78 was around 1.9–2.1 mM at 25°C measured by the method of molar conductivity.

3.2. Preparation and Characterization of PA Functionalized NPs

Three types of Pa functionalized NPs (Pa-NPs) were successfully prepared. The size and surface charge of the NPs were analyzed by light scattering. The average particle sizes of the NPs were 83.9 nm for Pa-SNPs (Figure 2(a)), 168.4 nm for Pa-NEMs (Figure 2(b)), and 156.7 nm for Pa-PNPs (Figure 2(c)). The data of zeta potential indicated the negative charge on the surface of Pa-NPs. The SEM images clearly showed the sphere shape of Pa-NPs (Figures 3(a), 3(b), and 3(c)). The sizes, PDI, and zeta potential of the Pa-NPs were summarized in Table 1.

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After storage for 7 days at 4°C, the colloidal suspensions of Pa-NPs kept the same appearance without precipitation or cloudiness. The PDIs and particle sizes of the Pa-NPs were monitored for 7 days and the data indicated only a small increase of the sizes (<20%) during the 7-day storage (Figure 4). Furthermore, the PDIs of the Pa-NPs were all less than 0.25 during the 7-day storage suggesting the monodispersity of the particles. The good stability of the Pa-NPs probably was due to hydrophilic PEG shielding and a negative surface charge. The lipid based SNPs and NEMs were widely used for delivery of hydrophobic drugs to increase their solubility and bioavailability and the biodegradable PLGA based PNPs have the potential for delivery of hydrophilic drugs and protein or peptide based growth factors. Thus, Pa-Brij 78 has the capability to fabricate a series of Pa-NPs which can encapsulate therapeutic agents with a broad range of chemical or physical properties.

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3.3. HA Binds to Curcumin Loaded Pa-NPs to Form Drug Loaded HA/Pa-NPs Complex

After the conditions of fabrication of Pa-NPs were optimized, a model drug curcumin was encapsulated in Pa-NPs. Table 2 showed that all the Pa-NPs could achieve more than 85.0% drug loading efficiency and that the drug encapsulation efficiency of the Pa-NPs was in the range of 10–30%. The drug to carrier ratio of Pa-NEM was greater than 30% because the hydrophobic drug curcumin might dissolve well in the liquid oil phase of emulsion to enhance the drug loading efficiency.

Then we continued to explore the conditions to build the drug loaded HA/Pa-NPs complex. First, the fixed amount of Pa-SNPs was used in the binding study. From Figure 5(a), the HA binding ratio was gradually increased as the amount of HA increased. The maximum HA binding ratio of Pa-SNPs around 45% was achieved. Under the same condition, SNPs without Pa modification only had minimum interaction with HA, suggesting the essential role of Pa in the binding. Similarly, the maximum HA binding ratio of Pa-NEM was about 55% (Figure 5(b)). Interestingly, the PNPs without surface Pa had a nonspecific interaction with HA to induce weak binding between PNPs and HA. Nevertheless, the maximum HA binding ratio of Pa-PNPs was around 70% (Figure 5(c)). The results indicated that although Pa on the surface of the NPs played an essential role in the binding between HA and NPs, the NPs themselves could also have impact on binding affinity.

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We also explored the optimum incubation time for HA binding to the three Pa-NPs. The results indicated the binding was rather fast and maximum binding could be achieved at 15 min (data not shown) for all three Pa-NPs.

The results demonstrated that HA binding to Pa-SNPs or Pa-NEMs gradually increased as the ratio of Pa-Brij 78 in the total surfactant increased from 0% to 100%, suggesting the high density of Pa required for the binding. However, the HA binding to Pa-PNPs achieved maximum as Pa-Brij 78 increased to 20% of the total surfactant. Further increasing the ratio of Pa-Brij 78 did not change the binding (Figure 6).

The interaction between Pa-NPs and HA to form HA/Pa-NPs complex was confirmed by fluorescence microscopy. As shown in Figure 7, HA with fluorescence labeled NPs without surface Pa displayed no or very weak green fluorescence suggesting weak interaction between the NPs and HA. However, each of the Pa-NPs exhibited stronger binding affinity to HA than its parental NPs without Pa. The images in Figure 7 also confirmed that the binding affinity of Pa-PNPs to HA was the highest among all three Pa-NPs.

Lyophilization can keep long-term stability of bioactive and thermosensitive drugs, such as antibiotics and growth factors. After lyophilization and storage in −80°C for a month, the size of recovered Pa-SNPs increased to around 280 nm and the sizes of the other two NPs increased to 200–250 nm (Figure 8(a)). The further optimization of the lyophilization protocol is still ongoing in the lab to obtain satisfying physical stability of NPs. Although the sizes of Pa-NPs increased significantly after the process of freeze-drying, the binding affinities of the three Pa-NPs did not change compared to the fresh prepared Pa-NPs (Figure 8(b)).

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3.4. Characterization of Complex of HA/Pa-NPs

3.4.1. Specific Interaction between Pa-NPs and HA

To study the specific interaction between Pa-NPs and HA, the free Pa was incubated together with the Pa-NPs and HA to test if free Pa can interfere with the interaction between Pa-NPs and HA. The results showed that the 10 mM Pa decreased around 30% of Pa-NPs bound to HA and 50 mM PA decreased around 65% of Pa-NPs bound to HA (Figure 9). The results of Pa concentration dependent competition demonstrated that the binding between Pa-NPs and HA was through the specific interaction between the Pa on the surface of NPs and HA and was independent of the matrix of the NPs. This advantage allows the researchers to choose the appropriate matrix of NPs to encapsulate the drugs of choice. For example, PLGA might be a good candidate for protein based growth factor delivery; the lipid based SNP and NEM could encapsulate hydrophobic drugs. By incorporation of Pa-Brij 78, the three different NPs loaded with different drugs can be incorporated into HA bone graft substitutes. Furthermore, the mixture of the three types of Pa-NPs delivering multiple agents can be loaded simultaneously to HA to form multi-drugs-eluting bone graft materials.

3.4.2. Interference of Free Calcium Ion to the Binding between Pa-NPs and HA

The drug loaded HA/Pa-NPs complex was designed as drug-eluting bone graft biomaterials for in vivo use. The affinity mechanism between the Pa-NP and HA is based on the Pa binding to calcium on the surface of HA, so the free calcium in the body fluid may destroy or decrease the integrity of HA/Pa-NPs. Therefore, we first used the blood concentration of calcium to study its effects on the stability of prepared HA/Pa-NPs. The results showed that the 2.5 mM calcium chloride (equal to normal Ca concentration in serum) did not break down the HA/Pa-NPs, suggesting the complex can tolerate the free calcium in the body fluid. However, if the concentration of calcium was increased to 5.0 mM, the majority of the NPs would have been released from the complex (Figure 10(a)).

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Because HA crystal is a mimic of natural bone, the study of in vitro Pa-NPs targeting HA with the existence of Ca²⁺ can preliminarily test if Pa-NPs are suitable for targeted delivery of drugs to bones. The results demonstrated that Pa-SNPs and Pa-NEMs lost their affinity to HA with the Ca²⁺ concentration in serum (2.5 mM), so these Pa-NPs are not suitable for bone targeting through i.v. administration. However, the Pa-PNPs still interacted with HA with the existence of 2.5 mM calcium chloride, suggesting that Pa-PNPs have the potential to deliver therapeutic agents for treatment of bone diseases and tumor bone metastasis (Figure 10(b)).

4. Conclusions

In conclusion, a Pa-modified Brij 78 was synthesized and the new compound Pa-Brij 78 was used as both surfactants and a target ligand for fabrication of a series of drug loaded Pa-NPs which could interact with HA. The complex of HA/Pa-NPs has potential to construct drug or growth factor eluting HA-based bone graft substitute.

Conflict of Interests

The authors declare that there is no conflict of interests regarding the publication of this paper.

Acknowledgment

This work was supported by Construction Program for Innovative Research Team of University in Sichuan Province (14TD0050).

References

L. L. Hench, “Bioceramics—from concept to clinic,” Journal of the American Ceramic Society, vol. 74, pp. 1487–1510, 1991.
View at: Google Scholar
S. Itoh, S. Nakamura, M. Nakamura, K. Shinomiya, and K. Yamashita, “Enhanced bone ingrowth into hydroxyapatite with interconnected pores by Electrical Polarization,” Biomaterials, vol. 27, no. 32, pp. 5572–5579, 2006.
View at: Publisher Site | Google Scholar
P. Wu and D. W. Grainger, “Drug/device combinations for local drug therapies and infection prophylaxis,” Biomaterials, vol. 27, no. 11, pp. 2450–2467, 2006.
View at: Publisher Site | Google Scholar
M. Brown, Y. Zou, R. Peyyala, T. Dziubla, and D. Puleo, “Temporal separation in the release of bioactive molecules from a moldable calcium sulfate bone graft substitute,” Current Drug Delivery, vol. 11, no. 5, pp. 605–612, 2014.
View at: Publisher Site | Google Scholar
S. P. Becerra, L. A. Perez-Mediavilla, J. E. Weldon et al., “Pigment epithelium-derived factor binds to hyaluronan: mapping of a hyaluronan binding site,” The Journal of Biological Chemistry, vol. 283, no. 48, pp. 33310–33320, 2008.
View at: Publisher Site | Google Scholar
F.-H. Lin, G.-C. Dong, K.-S. Chen, G. J. Jiang, C.-W. Huang, and J.-S. Sun, “Immobilization of Chinese herbal medicine onto the surface-modified calcium hydrogenphosphate,” Biomaterials, vol. 24, no. 13, pp. 2413–2422, 2003.
View at: Publisher Site | Google Scholar
S. E. Bae, J. Choi, Y. K. Joung, K. Park, and D. K. Han, “Controlled release of bone morphogenetic protein (BMP)-2 from nanocomplex incorporated on hydroxyapatite-formed titanium surface,” Journal of Controlled Release, vol. 160, no. 3, pp. 676–684, 2012.
View at: Publisher Site | Google Scholar
J. Balzeau, M. Pinier, R. Berges, P. Saulnier, J.-P. Benoit, and J. Eyer, “The effect of functionalizing lipid nanocapsules with NFL-TBS.40-63 peptide on their uptake by glioblastoma cells,” Biomaterials, vol. 34, no. 13, pp. 3381–3389, 2013.
View at: Publisher Site | Google Scholar
M. P. Siqueira-Moura, F. L. Primo, E. M. Espreafico, and A. C. Tedesco, “Development, characterization, and photocytotoxicity assessment on human melanoma of chloroaluminum phthalocyanine nanocapsules,” Materials Science and Engineering C: Materials for Biological Applications, vol. 33, no. 3, pp. 1744–1752, 2013.
View at: Publisher Site | Google Scholar
A. Yadav, V. Lomash, M. Samim, and S. J. S. Flora, “Curcumin encapsulated in chitosan nanoparticles: a novel strategy for the treatment of arsenic toxicity,” Chemico-Biological Interactions, vol. 199, no. 1, pp. 49–61, 2012.
View at: Publisher Site | Google Scholar
W. Yan and L. Huang, “Recent advances in liposome-based nanoparticles for antigen delivery,” Polymer Reviews, vol. 47, no. 3, pp. 329–344, 2007.
View at: Publisher Site | Google Scholar
K. R. Chaudhari, A. Kumar, V. K. M. Khandelwal et al., “Bone metastasis targeting: a novel approach to reach bone using Zoledronate anchored PLGA nanoparticle as carrier system loaded with Docetaxel,” Journal of Controlled Release, vol. 158, no. 3, pp. 470–478, 2012.
View at: Publisher Site | Google Scholar
L. de Miguel, M. Noiray, G. Surpateanu, B. I. Iorga, and G. Ponchel, “Poly(gamma-benzyl-L-glutamate)-PEG-alendronate multivalent nanoparticles for bone targeting,” International Journal of Pharmaceutics, vol. 460, no. 1-2, pp. 73–82, 2014.
View at: Publisher Site | Google Scholar
V. Hengst, C. Oussoren, T. Kissel, and G. Storm, “Bone targeting potential of bisphosphonate-targeted liposomes: preparation, characterization and hydroxyapatite binding in vitro,” International Journal of Pharmaceutics, vol. 331, no. 2, pp. 224–227, 2007.
View at: Publisher Site | Google Scholar
S. I. Thamake, S. L. Raut, Z. Gryczynski, A. P. Ranjan, and J. K. Vishwanatha, “Alendronate coated poly-lactic-co-glycolic acid (PLGA) nanoparticles for active targeting of metastatic breast cancer,” Biomaterials, vol. 33, no. 29, pp. 7164–7173, 2012.
View at: Publisher Site | Google Scholar
Y. Dong and S.-S. Feng, “Poly(D,L-lactide-co-glycolide) (PLGA) nanoparticles prepared by high pressure homogenization for paclitaxel chemotherapy,” International Journal of Pharmaceutics, vol. 342, no. 1-2, pp. 208–214, 2007.
View at: Publisher Site | Google Scholar
M. Ao, G. Xu, Y. Zhu, and Y. Bai, “Synthesis and properties of ionic liquid-type Gemini imidazolium surfactants,” Journal of Colloid and Interface Science, vol. 326, no. 2, pp. 490–495, 2008.
View at: Publisher Site | Google Scholar
L. Feng, H. L. Wu, P. Ma, R. J. Mumper, and S. R. Benhabbour, “Development and optimization of oil-filled lipid nanoparticles containing docetaxel conjugates designed to control the drug release rate in vitro and in vivo,” International Journal of Nanomedicine, vol. 6, pp. 2545–2556, 2011.
View at: Google Scholar
A. Jain, W. Yan, K. R. Miller, R. O'Carra, J. G. Woodward, and R. J. Mumper, “Tresyl-based conjugation of protein antigen to lipid nanoparticles increases antigen immunogenicity,” International Journal of Pharmaceutics, vol. 401, no. 1-2, pp. 87–92, 2010.
View at: Publisher Site | Google Scholar

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Copyright © 2015 Jiabin Zhang et al. This is an open access article distributed under the Creative Commons Attribution License, which permits unrestricted use, distribution, and reproduction in any medium, provided the original work is properly cited.

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