- Nano Express
- Open Access
In Situ Loading of Basic Fibroblast Growth Factor Within Porous Silica Nanoparticles for a Prolonged Release
© to the authors 2009
- Received: 12 March 2009
- Accepted: 8 July 2009
- Published: 25 July 2009
Basic fibroblast growth factor (bFGF), a protein, plays a key role in wound healing and blood vessel regeneration. However, bFGF is easily degraded in biologic systems. Mesoporous silica nanoparticles (MSNs) with well-tailored porous structure have been used for hosting guest molecules for drug delivery. Here, we report an in situ route to load bFGF in MSNs for a prolonged release. The average diameter (d) of bFGF-loaded MSNs is 57 ± 8 nm produced by a water-in-oil microemulsion method. The in vitro releasing profile of bFGF from MSNs in phosphate buffer saline has been monitored for 20 days through a colorimetric enzyme linked immunosorbent assay. The loading efficiency of bFGF in MSNs is estimated at 72.5 ± 3%. In addition, the cytotoxicity test indicates that the MSNs are not toxic, even at a concentration of 50 μg/mL. It is expected that the in situ loading method makes the MSNs a new delivery system to deliver protein drugs, e.g. growth factors, to help blood vessel regeneration and potentiate greater angiogenesis.
- In situ loading method
- Protein release
Basic fibroblast growth factor (bFGF), an 18 kDa protein involved in angiogenesis, has been shown to stimulate endothelial cell proliferation and to promote the physical organization of endothelial cells into tube-like structures, indicative of new blood vessel growth . Studies have demonstrated that bFGF has a high therapeutic potential for tissue regeneration. For instance, delivery of bFGF to damaged tissues stimulates regeneration of muscle, heart, cartilage, and nerves [2–4]. For skin wound healing, bFGF significantly accelerates soft tissue formation, re-epithelialization, and collagen maturation in human and animals [5–7]. However, direct injection of bFGF into a host leads to rapid diffusion and degradation of the protein . Many attempts have been made to keep bFGF stable in vitro, or in vivo. For instance, Gospodarowicz and Cheng demonstrated that bFGF coupled with heparin was protected from heat and acid deactivation . Furthermore, in order to avoid the over-dosage and degradation of bFGF, various lipid and biocompatible polymers have been used as carriers for the delivery of growth factors including, the encapsulation of heparin–sepharose-bound bFGF in alginate microspheres , the impregnation of collagen sponges with heparin–bFGF–fibrin mixtures , bFGF incorporation into hyaluronate gels , and gelatin hydrogels [2, 12]. However, the release of bFGF from these polymer-based delivery systems was completed within only 3 days. Choi and Park reported that bFGF-loaded poly(d,l-lactide-coglycolide) (PLGA) particles (diameter, d = 200 nm) produced by chemical cross-linking showed a longer release period, around 2 weeks . However, it was difficult to control the release rate and period due to the complicated releasing mechanism for the polymers. Moreover, the major challenge is to eliminate the use of high temperatures during the drug loading process to polymer nanoparticles. For instance, it takes at least 70 °C to entrap the drug in the nanoshell of a lipid polymer, which is not feasible to load temperature sensitive protein, such as bFGF . Furthermore, polymer-based release carriers keep the therapeutic agents entrapped, adsorbed or chemically coupled onto the polymer matrix, which, unfortunately, has side effects on the loaded bFGF because of the crosslinking agents, temperature, and un-desired pH values during the polymer preparation .
Inorganic nanoparticles (diameter, 1 < d < 100 nm) have special properties (e.g. large surface to volume ratio and high atomic fractures), which make them suitable carriers in the blood stream . Quite recently, mesoporous silica nanoparticles (MSNs) have attracted a lot of attention for their unique structure features, including large surface areas (800 m2 g−1), tunable pore sizes (2–10 nm in diameter), and well-defined surface properties . In addition, MSNs have been approved by the Food and Drug Administration (FDA) as a new biocompatible material. Furthermore, MSNs show multifunctional surface modification, controlled releasing capability, and good thermal stability [18, 19], which make MSNs an ideal nonviral carrier for gene, and/or drug delivery. For instance, Lin and Wang utilized the MSNs with honeycomb structure for delivering DNA and chemicals into plants . In the case of the MSNs system, the drugs and imaging agents are encapsulated with covalently bound caps that physically block the drugs from leaching out. Molecules entrapped inside the pores are released by the introduction of uncapping triggers (chemicals that cleave the bonds attaching the caps to the MSNs). However, it takes extra processes to modify the MSNs with capping and uncapping agents. In addition, very few efforts have been made to load protein within silica nanoparticles at room temperature. The possible reason is that the protein is easily denatured during the chemical reactions that are normally required during the synthesis and loading of nanoparticles.
To date, several processes have been developed to produce MSNs. Zhao, et al. reported the generation of MSNs with 4.6–30 nm pores through triblock copolymer synthesis in 1998 . Other methods include the sol–gel process , and the spray drying method . Previous studies indicate that mesoporous silica can be synthesized in either the alkaline route, or the acid route. The acid route leads to a soft network because the hydrolysis is catalyzed easily compared to the condensation , while the alkaline route is favoured to both hydrolysis and condensation, and produces a condensed and compact structure. In this research, a weak acid-modified water-in-oil microemulsion is developed to encapsulate the bFGF within MSNs in situ. The in vitro releasing kinetics of bFGF from MSNs has been investigated through colorimetric enzyme linked immunosorbent assays (ELISAs). It is expected that this new delivery system can help tissue regeneration and wound healing by releasing the growth factors in a controlled and temporal manner.
Encapsulation of bFGF in MSNs
Mesoporous silica nanoparticles (MSNs) used for encapsulating bFGF were further investigated by Hitachi 3400-N scanning electron microscope (SEM) and transmission electron microscope (TEM-EM400) for measuring the particle size and size distribution. To prepare the TEM specimen, bFGF-loaded MSNs were re-dispersed in ethanol–water solution, and then one drop was added on the TEM Cu grid. Furthermore, Zeiss LSM 510 Duo Confocal microscope was carried to study on the uptake of MSNs in human umbilical vein endothelial cells (HUVEC).
Release Kinetic Study
whereR denotes the loading efficiency (%);M′, the total amount (wt) of bFGF loaded in nanoparticles, which is converted fromC′ determined by ELISA kit;M0, the original amount (wt) of bFGF, that is, 10 μg. In Eq. 1,C0refers to the original concentration of bFGF in aqueous phase of microemulsion, i.e. 10 μg in 0.1 mL, andCfis the nonencapsulated free bFGF in the aqueous solution after breaking the microemulsion. In our study,Cfwas measured by the ELISA kit. The result indicated that two strategies gave similar values, i.e., the loading efficiency,R = 72.5 ± 3%.
Biocompatibility of MSNs
The MultiTox-Fluor Multiplex Cytotoxicity Assay (Promega) was used to investigate the biocompatibility or cytotoxicity of the pure MSNs. This assay simultaneously measures cell viability and cytotoxicity, which is independent on total cell number. Furthermore, human umbilical vein endothelial cells (HUVEC) from the American Type Culture Collection (ATCC) were cultured in CS-C medium without serum for endothelial cell lines (Sigma) supplemented with 10% FBS (Invitrogen) and endothelial cell attachment factor (E 9765) (Sigma) at 37 °C, 5% CO2. For the investigation of cytotoxicity of nanoparticles, 1,000 cells per well of 96-well dish were plated and allowed to adhere overnight. The medium was changed and replaced with fresh medium containing MSNs in next day. At specific time points, cytotoxicity and viability were measured as per manufacturer’s instructions using the MultiTox-Fluor Multiplex Cytotoxicity Assay. Six different concentrations of MSNs were used in the test, including 0.01, 0.1, 1, 5, 10, and 50 μg/mL. The control samples measured from day 1 to day 5 were the HUVEC cell culture media without adding MSNs. The cell viability was obtained by using the MultiTox-Fluor Multiplex Cytotoxicity Assay. According to the manufacturer’s instructions (http://www.promega.com/cnotes/cn015/CN015_11.pdf), the assay reagent is composed of two fluorogenic peptide substrates (GF-AFC, live-cell protease substrate and bis-AAF-R110, dead-cell protease substrate) to the assay buffer. This reagent was added to a 96-well plate. After at least 30 min of incubation at 37 °C, the resulting fluorescent signals for the living cell and dead cells were measured at an excitation of 400 nm and an emission of 505 nm, then at an excitation of 485 nm and an emission of 520 nm, respectively.
The structure, shape, and chemicals of MSNs do not change in vitro and/or in vivo because of their chemical and biological stability. The releasing kinetics of encapsulated bFGF is, therefore, mainly controlled by diffusion mechanisms . While, polymers acted as nanocarriers to deliver proteins they suffer from the swelling and/or degradation, which possibly leads to a complicated and nonsatisfied releasing profile.
The result as shown in Fig. 3 indicates that this delivery system based on MSNs can achieve prolonged release of FGF-2 for at least 3 weeks in order to initiate angiogenesis within a cell delivery matrix when the particles is around 40 nm. In addition, avoiding the “initial burst”, in which a large percentage of the drug is released within the first 24–48 h, is a challenge to most delivery vehicles . As seen in our studies, the “initial burst” is also hard to avoid completely for the silica NPs encapsulating bFGF. The reason is possibly related to the high solubility of bFGF in buffer, and the tunable nano-channels in MSNs as showed in Fig. 2b. Our efforts are continuously focusing on how to control the initial burst and increase the loading efficiency.
This study develops a route for in situ loading of bFGF within MSNs at room temperature through a developed water-in-oil microemulstion method. MSN as a new bFGF vehicle system prolongs the release of bFGF for 20 days. The results of cytotoxicity assay show that MSNs are not toxic, even when administered at high concentrations (50 μg/mL). Interestingly, the viability assay shows that MSNs could promote the cell proliferation. This new delivery system may help blood vessel regeneration and potentiate greater angiogenesis. In addition, this research indicates that the porous silica nanoparticles could be potential carriers for immobilizing dyes as a biomarker.
This work was supported by the Discovery Grant (to Dr. Zhang, # 346202) of the Natural Sciences and Engineering Research Council of Canada (NSERC), and the financial support from the University of Western Ontario (UWO).
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