Curcumin Nanocrystallites are an Ideal Nanoplatform for Cancer Chemotherapy

Wang X^1,2, Peng Y², Tan H², Li W²* and Li M¹*

¹Zhongshan School of Medicine, Sun Yat-Sen University, China

²Department of Neurosurgery, The First Affiliated Hospital of Shenzhen University, China

*Corresponding author: Mingtao Li, Zhongshan School of Medicine, Sun Yat-Sen University, Guangzhou 510080, China

Weiping Li, Department of Neurosurgery, Shenzhen Second People’s Hospital, The First Affiliated Hospital of Shenzhen University, Shenzhen 518039, China

Received: September 10, 2019; Accepted: October 24, 2019; Published: October 31, 2019

Abstract

Curcumin, a principal active component extracted from rhi-zomes of turmeric, has a promising clinical activity against a wide variety of tumors. It is extremely low solubility in water is the great limitation in the application of cancer chemotherapy. Nanocrystals have recently emerged as a promising pharmaceutical preparations way for the poorly water soluble drugs. Accordingly, we prepared Curcumin Nanocrystals (CNs) with a mean diameter of 15 nm by quick emulsion freeze-drying method. CNs proved to be effective in drug delivery, such as avoiding uptake by the Reticuloendothelial System (RES), prolonging the circulation times of curcumin as well as Enhancing the well-known Permeation and Retention (EPR) effect, as a result of which CNs accumulate at the tumor site. Furthermore, we design to conjugate a targeting ligand-cyclic iRGD peptide to CNs in order to selectively deliver Curcumin to cancer cells with greater efficiency and enhance the permeability of cells leading more drugs inside cells. Hence, our results suggested that iRGD-CN, which be of both characteristics of passive and active targeting, may be a potential drug delivery system in enhance the effective therapy of curcumin chemotherapy.

Introduction

In the preparation of CNs, Pluronic^®F-127 were used as emulsion stabilizer and eventually a small amount of them wrapped in the surface of the CNs [1,2]. Pluronic^®F-127 are nonionic triblock copolymers composed of a central hydrophobic Chain of poly (Propylene Oxide) (PPO) flanked by two hydrophilic chains of Poly (Ethylene Oxide) (PEO) (PEO-PPO-PEO) [3,4]. These amphiphilic triblock copolymers strengthen stealth properties to CNs, allowing them to reduce potential toxicity and avoid uptake by the RES, which is crucial for achieving long circulation time in blood and enhanced uptake by tumors via EPR effect [5-7]. In addition, the thin coating of Pluronic^®F-127 also provide a binding site for cyclic iRGD peptide, which is active targeting ligand enhancing the therapeutic efficacy. iRGD (CRGDK/RGPD/EC) is a kind of tumor-penetrating peptide which can contribute CNs to increasing cancer vascular and tissue permeability in a αv integrin and neuropilin-1 (expressing at the surface of tumor blood vessel endothelial cells and tumor cells)– dependent manner. iRGD-based targeting mechanism for tumor is that the iRGD motif mediates binding to integrins on tumor endothelium and a proteolytic cleavage then exposes a binding motif for neuropilin-1, which mediates penetration into tumor tissue and cells. Compared with traditional targeting moiety simply paying attention to the ability to identify tumor cells and lacking capacity of leading drugs penetration into tumor tissue and cells, iRGD peptide overcomes this limitation and establishes a capability for tissue/ cells-penetrating drug delivery [1,8]. Current research shows that the microenvironment in solid tumors is very distinct from that in normal tissues. Due to deregulated cancer cell metabolism, highly heterogeneous vasculature and defective blood perfusion, the tumor microenvironment is characterized high interstitial pressure and cell density [9,10]. How to make CNs penetrate tumor blood vessel endothelial cells and tumor tissue is the key to eliminate cancer cells, especially to extirpate interior cancer stem cells [11,12]. Thus, we design an efficient DDS through employing the CNs to be chemically conjugated to the peptide.

Materials and Methods

Materials

Pluronic^®F-127, 4-(Dimethylamino) Pyridine (DMAP), triethylamine, and succinic anhydride were purchased from Sigmae- Aldrich (St. Louis, MO, USA). Uppsala 87 Malignant Glioma (U87) were supplied by American Type Culture Collection (ATCC). Dulbecco’s Modified Eagle’s Medium (DMEM), RMPI 1640 medium, Fetal Bovine Serum (FBS) were provided from Gibco BRL (Grand Island, NY, USA). Curcumin, Cremophor EL, Cell Counting Kit-8 (CCK-8), Rhodamine-phalloidin, and Dimethyl Sulfoxide (DMSO) were purchased from Sigmae-Aldrich (St. Louis, MO, USA). Oregon Green^®488 Taxol, Flutax-2, DAPI (4,6-diamidino-2-phenylindole), Hoechst, LIVE/DEAD Viability/Cytotoxicity Kit, and Cy5 was bought from Molecular Probes (Eugene, OR, USA). Taxol (TA) was supplied by Merck (Germany). DSPE-PEG-iRGD were supplied by GL Biochem Ltd. (Shanghai, China). Anhydrous ethanol and dichloromethane were purchased from Beijing Chemical Reagent Company (Beijing, China).

Pluronic^®F-127 functional group modification

Terminal hydroxyl groups on Pluronic^®F-127 were converted to carboxyl groups in order to efficiently coupling of iRGD peptide to the CNs surface. The modification of Pluronic^®F-127 functional group involves the following procedure. Pluronic^®F-127 (0.2g) was dissolved in THF (10mL), and then DMAP (12mg), triethylamine (100 μL) and succinic anhydride (600mg) were added. The reaction mixture was stirred for 48 h at room temperature. The solution was dried by a rotary evaporator and was then dissolved in of chloroform (75mL). The excess succinic anhydride was removed by filtration with a 0.45 μm PTFE membrane syringe filter. The Pluronic^®F-127-COOH (F127) was purified by precipitation with ice-cold diethylether [13,14]. The product was identified by 1H-NMR spectrometer (Bruker AVANCE III 600MHz) and Fourier Transform Infrared Spectrophotometer (JASCO FT/IR-660).

Preparation and characterization of CNs and iRGD-CNs

CNs were prepared via oil-in-water emulsions freeze-dried method, which generally comprised three steps process. The first step is emulsion preparation. The Oil phase (O) was dichloromethane solution containing 40mg/mL curcumin. Containing 1 wt% Pluronic^®F-127-COOH aqueous solution was the Water phase (W). The volume ratio of oil phase and water phase was fixed at 1:20, and the mixture was mixed through ultrasonic (100w, 10 min) emulsification to obtain emulsion (O/W). Secondly, the above emulsion was further added into 20-fold the volume of the water phase, and the mixture was frozen by liquid nitrogen followed by freeze-drying using a vacuum freeze-dryer. Finally, CNs suspension was obtained when lyophilized products were dispersed into the water and free surfactant were removed by ultracentrifugation (800000rcf, 10min). In this study, CNs were functionalized modifications targeted by DSPE-PEG-iRGD ligand were embedded to the surface of CNs during the process of oil-in-water emulsions freeze-dried. In addition, we used fluorescent dye Cy5 instead of curcumin in the preparation progress to obtain nanocrystals with fluorescence properties so as to study the cellular uptake of CNs and the target of iRGD.

Characterization of CNs

Emulsion droplet size and the desired degree of droplet size uniformity play a key role in the preparation of CNs. Hence, we measured the average particle size and size Polydispersity Index (PDI) of droplets using Zetasizer (Nanoseries, Malvern, UK.). CNs size and morphology were determined by Transmission Electron Microscope (TEM, JEOL, Japan) with an acceleration voltage of 200Kv. The homogeneity of the particles was studied by Atomic Force Microscope (AFM, Bioscope Catalyst). Due to the obvious difference zeta potential of the product during each step of the reaction, the reaction process can be easily detected according to the potential variation.

To assess the encapsulation efficiency of curcumin, free curcumin in the CNs suspension was removed by the method of ultrafiltration, and then curcumin containing in CNs was quantified by HPLC.

In Vitro Cellular uptake

U87 cells were routinely cultured respectively in complete DMEM and RMPI 1640 medium with 10% FBS, 1% penicillin and 1 % streptomycin in a humidified incubator with 5% CO₂ at 37^oC. For the cellular uptake study, U87 cells were seeded at the density of 1×10⁵ cells/well in two 24-well cell plates and incubated at 37^oC for 24h to allow cell attachment. After 24h, the cells were then incubated with CNs and iRGD-CNs (100 μg/mL) at 37^oC for diﬀerent time intervals. The cells were rinsed with PBS (pH 7.2) solution softly, pre detached by 0.25% trypsin. The trypsin was removed by centrifugation at 1000rpm for 5min. The cells were then harvested, re-suspended in 500ml PBS and examined by flow cytometry using a CyAn ADP 9 color flow cytometer (Beckman Coulter). Using the same method, U87 cells were grown in a culture dish at a density of 1×10⁶ cells/dish and incubated at 37^oC for 24h. Following incubation of cells in dishes culture containing 200 μL of CNs and iRGD-CNs. The medium was then removed and cells were washed with PBS (pH 7.2). Finally, the total fluorescence images of nanocrystals internalized into cells were scanned using an In Vivo imaging system (FX Pro, Kodak) with an excitation band pass filter at 480nm and an emission at 633nm. In the Confocal Laser Scanning Microscopy (CLSM) imaging studies, U87 cells were first seeded on Petri dishes for 24h, and the medium was replaced with new medium containing 100 μg/mL of CNs and iRGD-CNs. There are some differences in the following process of the two cell lines. After incubation for 24h at 37^oC, the medium of U87 cells was then removed and cells were washed with PBS (pH 7.2) followed by fixing with 4% paraformaldehyde for 30 min. The cell membrane and nuclei were stained with Rhodamine-phalloidin and DAPI, respectively. CNs and iRGD-CNs were detected fluorescence at 633nm, and the corresponding fluorescent images of the cell membrane and nuclei at 488nm and 405nm by CLSM (TCS SP5, Leica). However, the cell membrane and nuclei of U87 cells were stained as soon as the medium was removed and cells were washed with PBS. The fluorescent dye was Oregon Green^®488 Taxol and Hoechst, whose excitation wavelengths were 488nm and 405nm respectively. And then the fluorescent images of the cells were analyzed using a TCS SP2 confocal microscope.

In Vitro ctotoxicity

The In Vitro cytotoxicity of curcumin, CNs, and iRGD-CNs were evaluated by CCK-8 assay. U87 cells were seeded in 96-well plates at the density of 5×10⁵ cells/well and cultured for 24h at 37^oC. The medium in each well was refreshed with 200 μL medium containing serial dilutions of curcumin, CNs, and iRGD-CNs (corresponding curcumin concentration was 0-25 μg/mL). After incubation for 48 h, 20 μL of Cell Counting Kit-8 was added to all wells, and then the cells were continued to be incubated at 37^oC with 5% CO₂ for 4h. Infinite M200 microplate spectrophotometer (Tecan, Mannedorf, Switzerland) was used to detect the absorbance at 450nm. Percent viability was normalized to cell viability in the absence of the samples.

Results and Discussion

Physicochemical characterization of iRGD-CNs

In an attempt to solve poor drug dissolution problem, we prepared CNs by emulsion technique as an effectual strategy to enhance the saturation solubility and dissolution rate of hydrophobic drugs. During the emulsion preparation, we used the hydrophilic material F127 to stabilize the oil-water interface in virtue of its block copolymer structure with amphiphilic property. The size and morphology of the nanoparticles were characterized by Transmission Electronic Microscopy (TEM). The synthesized CNs dispersed well in cyclohexane and had a diameter of about 15nm. This surface structure characteristic endued CNs with excellent dispersion stability in aqueous solution. To integrate tumor-targeted function, DSPE-PEGiRGD ligand was added during the preparation process of CNs as previously described to obtain iRGD -NDs, which presented uniform structure with an average size of around 15nm by TEM image (Figure 1). Dynamic Light Scattering (DLS) analysis exhibited iRGDCNs with a hydrated particle size of 18nm iRGD was successfully conjugated on the surface of CNs. The slightly increased particle size and zeta potential also indicated the success of the iRGD anchoring on the CNs surface (Table 1).

Table 1: Particle size and zeta potential of the CNs and iRGD-CNs agents.




  
    Groups
    Particle    size (nm)
    Zeta    potential (mV)
  
  
    CNs
    15±1.0
    -6.4±0.57
  
  
    iRGD-CNs
    18±1.2
    1.5±0.48



Table 1: Particle size and zeta potential of the CNs and iRGD-CNs agents.

Figure 1: (A) TEM images clearly exhibit the morphologies of iRGD-CNs. (B) Dynamic Light Scattering (DLS) measurement of the as-prepared iRGD-CNs.

    
    
    Figure 1: (A) TEM images clearly exhibit the morphologies of iRGD-CNs. (B) Dynamic Light Scattering (DLS) measurement of the as-prepared iRGD-CNs.

To achieve efficient accumulation in the tumor site, these nanoparticles should also possess high binding affinity toward cancer cells. We therefore evaluate the iRGD-conjugated effect on cancer cell uptake. As shown in (Figure 2), only a very small amount of CNs could be internalized into U87 cells due to the charge repulsion between the nanoparticles and the cell membrane, both negatively charged. Once iRGD was conjugated, these nanoparticles could be more extensively internalized. This is because the iRGD could bind preferentially to the integrin receptor that is highly expressed on the surface of U87 cells. This iRGD guided delivery efficiency was further verified by CLSM imaging. These results together reflected that the cellular uptake of iRGD modification nanoparticles was significantly promoted for cancer cells.

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Citation: Wang X, Peng Y, Tan H, Li W and Li M. Curcumin Nanocrystallites are an Ideal Nanoplatform for Cancer Chemotherapy. Austin J Cancer Clin Res. 2019; 6(1): 1084.

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