- Nano Express
- Open Access
An injectable hybrid nanoparticle-in-oil-in-water submicron emulsion for improved delivery of poorly soluble drugs
© Wang et al.; licensee Springer. 2012
- Received: 19 February 2012
- Accepted: 25 March 2012
- Published: 13 April 2012
Poor drugability problems are commonly seen in a class of chemical entities with poor solubility in water and oil, and moreover, physicochemical instability of these compounds poses extra challenges in design of dosage forms. Such problems contribute a significant high failure rate in new drug development. A hybrid nanoparicle-in-oil-in-water (N/O/W) submicron emulsion was proposed for improved delivery of poorly soluble and unstable drugs (e.g., dihydroartemisinin (DHA)). DHA is known for its potent antimalarial effect and antitumor activity. However, its insolubility and instability impose big challenges for formulations, and so far, no injectable dosage forms are clinically available yet. Therefore, an injectable DHA N/O/W system was developed. Unlike other widely-explored systems (e.g., liposomes, micelles, and emulsions), in which low drug load and only short-term storage are often found, the hybrid submicron emulsion possesses three-fold higher drug-loading capacity than the conventional O/W emulsion. Of note, it can be manufactured into a freeze-drying form and can render its storage up to 6 months even in room temperature. The in vivo studies demonstrated that the PK profiles were significantly improved, and this injectable system was effective in suppressing tumor growth. The strategy provides a useful solution to effective delivery of such a class of drugs.
- Poor solubility
- Drug delivery
- Nano emulsion
Poor solubility of a chemical entity is a major obstacle affecting its drugability . It is estimated that more than 40% of the new chemical entities generated in drug discovery programs are poorly soluble . With growing interest in the role of modern pharmaceutics in early stage of drug discovery and development, rationale design of drug delivery systems for poorly soluble drugs has been widely explored, such as emulsions [3, 4], solid lipid nanoparticles [5, 6], micelles, and liposomes [7, 8]. Emulsions are one of the most commonly used drug carriers for poorly water-soluble drugs due to the unique advantage in mass manufacturing, easy sterilization, and excellent physicochemical stability. However, there still remain two problems waiting to be solved, i.e., low drug-loading capacity and quick drug release. Moreover, for the drugs that remain insoluble in both water and oil, there is no satisfactory solution yet. As a case in point, dihydroartemisinin (DHA), a potent antimalarial drug [9, 10], is poorly soluble and unstable, and its oral bioavailability is low due to degradation in the gastrointestinal tract and poor intestinal absorption. Moreover, because of its unfavorable solubility property, no injectable dosage form is clinically available yet, thus, severely limiting its use in medical emergency in severe malaria. According to WHO, an estimated 781,000 deaths from malaria in 2009, and most victims are children under five . Furthermore, DHA recently has been demonstrated for its extraordinary antitumor activity and its promising development into anticancer drug [12–14]. Therefore, to develop an injectable drug delivery system for DHA is not only clinically beneficial for these diseases, but also such exploration is meaningful for rationale design of drug delivery for the class of water/oil insoluble drugs.
Dihydroartemisinin (purity > 99%) was kindly provided by Beijing Zhongyan Tongrentang Medicine R&D Co., Ltd. (Beijing, China). Poloxamer 188 was purchased from BASF Corporation (Ludwigshafen, Germany), cholesterol from Pharmacia Biothech (Piscataway, NJ, USA), and soya phosphatidylcholine from Lipoid GmbH (Ludwighafen, Germany). Mannitol, sucrose, and glyceryl monostearate were purchased from Sinopharm Chemical Reagent Co., Ltd. (Shanghai, China). Hepatic H22 cell line was kindly provided by Zhejiang University of Traditional Chinese Medicine. All other chemicals were of analytical grade.
Preparation of DHA N/O/W emulsion
DHA (150 mg) and lecithin (900 mg) were dissolved in 30-ml alcohol and then mixed with soybean oil (5,000 mg) and glyceryl monostearate (150 mg). The mixture was used as oily phase and warmed up to 60°C and then dropwise added to the aqueous phase containing glycerol (1,100 mg) and poloxamer 188 (900 mg) with agitation at high speed and temperature (8,000 to 10,000 rpm and 60°C). After adjusting the pH from 6 to 7, the primary emulsion was homogenized by microfluid technology at a pressure of 200 to 1,000 bar (8 to 10 cycles) to obtain the DHA N/O/W emulsion with DHA concentration about 3.0 mg/ml. In order to maintain DHA stability, the freeze-dried emulsion was prepared with a complex of sucrose and mannitol (4:1) as lyoprotectant.
Meanwhile, the DHA O/W emulsion was prepared as follows. DHA (49 mg) and lecithin (1,000 mg) were dissolved in alcohol and attached to a rotary evaporator to remove the organic solvent. Soybean oil (5,000 mg) was then added to dissolve the dried film as oil phase. Aqueous phase contained glycerol (1,100 mg); poloxamer, 188 (1,000 mg). The DHA O/W emulsion was prepared as described above.
Characterization of the DHA N/O/W emulsion
Size and zeta potential of the DHA N/O/W emulsion were determined by laser scattering technique using Malvern ZS90 (Malvern Instruments Ltd., Malvern, Worcestershire, UK) after appropriate dilution with double distilled water.
The primary N/O/W emulsion with a size of about 10 μm (before microfluid process), through light microscopy (MPS-30, Leica Microsystems, Wetzlar, Hesse, Germany), was employed to observe the encapsulation of particles in O/W emulsion. Furthermore, morphology of the mid-product of DHA N/O/W emulsion (about 1 μm) was studied with transmission electron microscopy (TEM) (JEM-1200EX, JEOL Ltd., Akishima, Tokyo, Japan). The sample for TEM was dropped onto a 400-mesh copper grid coated with carbon film. The sample was dried in air before TEM observation. The sample for freeze-fracture transmission electron microscopy (FF-TEM) was prepared as follows. A droplet of microemulsion was sandwiched between two copper electron microscopy grids, snapfrozen by immersion in liquid ethane, and then loaded into a double-replica device and immersed in liquid nitrogen (−196°C). The double replica device was mounted on the rotary sample stage of a Balzers BAF-400D freeze etch device (Balzers AG, Balzers, Liechtenstein) cooled to −110°C. Fracturing was carried out at a vacuum of 3 × 10−3 mbar. The fractured surfaces were shadowed with platinum (45°) and carbon (90°). The replicas were then washed in chloroform, methanol, and finally, distilled water. Dried replicas were examined with TEM operating at an accelerating voltage of 80 kV.
Drug loading capacity
The DHA N/O/W emulsion was dissolved in methanol and then injected to the high-performance liquid chromatography (HPLC) system. Chromatographic separation was achieved using a C18 column (150 × 4.6 mm, 5 μm, Agilent Technologies, Palo Alto, CA, USA) with column temperature at 40°C. The mobile phase consisted of 40:60 double-distilled water containing 0.1% acetic acid (Millipore Corporation, Milford, MA, USA)/acetonitrile (HPLC grade, Merck & Co., Inc., Whitehouse Station, NJ, USA). The flow rate was set to 1.0 ml/min, and UV detection wavelength was 210 nm.
The experimental protocols were approved by the Animal Ethics Review Committee of Zhejiang University. The male rabbits (2.0 ± 0.2 kg) were divided into three groups (6 per group). DHA solution, DHA O/W emulsion or DHA N/O/W emulsion was injected via ear vein at a dose of 6.2 mg/kg. Blood samples were collected from the marginal vein on another ear before administration and at predetermined time points after intravenous administration. Plasma sample (100 μl) was spiked with 10 μl of the IS solution (artemisinin, 1 μg/ml), and the mixture was vortexed for 10 s. The sample was extracted with 2-ml ethyl acetate, vortexed for 3 min, and centrifuged for 15 min at 3,500 rpm. The upper layer was transferred into another test tube and evaporated to dryness under a gentle stream of N2 gas at 37°C. The residue was reconstituted in 100 μl of methanol/water (60:40). The concentration of DHA in plasma samples was determined by LC-MS method (ESI, positive mode, Agilent 1100 LC-MSD, Agilent Technologies, Palo Alto, CA, USA). Pharmacokinetic analysis was conducted using Kinetica Software (Version 4.4, Thermo Electron Corporation, Waltham, MA, USA).
In vivo antitumor efficacy of DHA N/O/W emulsion
where d and D are the shortest and the longest diameter of the tumor in mm, repectively.
When the tumor grew to a mean size of approximately 300 mm3, mice were treated intravenously (i.v.) with DHA solution, DHA O/W emulsion, or N/O/W emulsion.
Hemolysis test and vascular irritation test
where Asample is the absorbance of the tested sample; Anegative, the absorbance of the negative control (i.e., mixture of equal volumes of 2% erythrocytes and saline); and Apositive, the absorbance of the positive control (i.e., mixture of equal volumes of 2% erythrocytes and distilled water).
For vascular irritation test, DHA N/O/W emulsion with a DHA dose of 6.2 mg/kg was injected to the marginal ear vein once per day for 7 days. At the eighth day, the rabbits were killed by aortic bleeding under pentobarbital anesthesia. The vascular irritation was investigated by histological examination of the injection site.
Each experiment was performed in triplicate, and the values were expressed as mean ± S.D. Statistical analysis was performed using Student's t test. Significant differences are demonstrated by symbols (*, **).
Preparation and characterization of DHA N/O/W emulsion
DHA N/O/W emulsion was prepared by a modified solvent evaporation and membrane emulsification method. The drug-loading capacity was improved by the DHA N/O/W emulsion, in which DHA concentration was 3.0 mg/ml, over three times higher than that of the DHA O/W emulsion (0.98 mg/ml).
Pharmacokinetic parameters of DHA
DHA N/O/W emulsion
DHA O/W emulsion
9.40 ± 0.28*,**
3.97 ± 0.34
3.10 ± 0.09
160.91 ± 47.21*,**
73.31 ± 1.61*
20.20 ± 6.56
0.0023 ± 0.0002*,**
0.0038 ± 0.0002*
0.0069 ± 0.0013
219,759.00 ± 14,782.77*,**
131,564.5 ± 8,396.89*
73,025.35 ± 14,149.00
97.65 ± 20.27*,**
32.22 ± 4.03*
9.40 ± 2.44
In vivo antitumor efficacy of DHA N/O/W emulsion
In vivo anti-tumor effects of DHA and DHA N/O/W emulsion on growth of H 22 tumor in ICR mice (n = 10)
Body weight (g) (initial/endpoint)
Tumor weight (g)
21.9 ± 1.3/27.8 ± 2.2
1.4 ± 0.4
21.2 ± 1.2/25.3 ± 1.7
1.1 ± 0.3
DHA N/O/W (low dose)
22.3 ± 0.9/28.6 ± 2.3
1.1 ± 0.2
DHA N/O/W (high dose)
21.7 ± 1.1/26.3 ± 3.8
0.7 ± 0.2
Elementary safety assay
Hemolysis test of DHA N/O/W dry emulsion by spectrophotometry
Emulsion volume/total volume (%)
Hemolytic degree (%)
A novel N/O/W submicron emulsion with high drug-loading capacity was prepared for intravenous administration of poorly soluble and unstable drugs. Our strategy is able to not only enhance the drug solubility in the emulsion but also improve its storage stability by freeze-drying. The pharmacokinetics of N/O/W emulsion are characterized by the significantly prolonged half-life and slow plasma clearance compared with conventional O/W emulsion and DHA solution. Presumably due to the improved PK profiles, the toxic effect of DHA was greatly reduced. Furthermore, the antitumor efficacy was demonstrated in vivo studies using a hepatic H22 tumor transplanted mouse model. More importantly, with the advantages of the high drug-loading capacity, easy manufacturing process, and excellent biocompatibility, the N/O/W emulsion provides a promising solution for developing injectable drug delivery systems for a class of drugs of poor water solubility and stability.
This study was funded by the National Natural Science Foundation of China (NSFC nos. 30873176 and 81172996) as well as partially supported by Shanghai Pujiang Scholarship and School of Pharmacy, Fudan University & The Open Project Program of Key Lab of Smart Drug Delivery (Fudan University), MOE & PLA, China.
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