To prepare a biodegradable polymeric carrier for oral delivery of a water-insoluble drug capsaicin (CAP) and evaluate its quality.
CAP-loaded methoxy poly (ethylene glycol)-poly(ε-caprolactone) nanoparticles (CAP/NPs) were prepared using a modified emulsification solvent diffusion technique. The quality of CAP/NPs were evaluated using transmission electron microscopy, powder X-ray diffraction, differential scanning calorimetry and Fourier transform infrared techniques. A dialysis method was used to analyze the in vitro release profile of CAP from the CAP/NPs. Adult male rats were orally administered CAP/NPs (35 mg/kg), and the plasma concentrations of CAP were measured with a validated HPLC method. The morphology of rat gastric mucosa was studied with HE staining.
CAP/NPs had an average diameter of 82.54±0.51 nm, high drug-loading capacity of 14.0%±0.13% and high stability. CAP/NPs showed a biphasic release profile in vitro: the burst release was less than 25% of the loaded drug within 12 h followed by a more sustained release for 60 h. The pharmacokinetics study showed that the mean maximum plasma concentration was observed 4 h after oral administered of CAP/NPs, and approximately 90 ng/mL of CAP was detected in serum after 36 h. The area under the curve for the CAP/NPs group was approximately 6-fold higher than that for raw CAP suspension. Histological studies showed that CAP/NPs markedly reduced CAP-caused gastric mucosa irritation.
CAP/NPs significantly enhance the bioavailability of CAP and markedly reduce gastric mucosa irritation in rats.
Capsaicin (CAP), an active ingredient in hot peppers of the genus Capsicum, has a variety of pharmacological activities in the cardiovascular and nervous systems1,2. Clinically, CAP is indicated in lumbago and sciatica and exhibits various degrees of inhibition against some food-borne pathogenic bacteria such as Listeria monocytogenes, Staphylococcus aureus, Salmonella typhimurium, and Bacillus cereus1. Importantly, several studies have demonstrated that CAP could effectively inhibit the growth of colorectal cancer and tumor formation through a variety of mechanisms including p53, TRPV6, and E2F3,4. The clinical utilization of CAP is handicapped by rapid first-pass metabolism and a short half-life (less than 8 min) after intravenous administration1. Furthermore, its poor aqueous solubility has led to poor oral absorption and low bioavailability whether administered orally or intravenously. Currently, the usage of CAP is limited to transdermal delivery or as a skin permeation enhancer.
Poly(ε-caprolactone) (PCL), approved by the United States Food and Drug Administration (FDA) as a biomedical material, has been extensively used in biodegradable pharmaceutical applications. Compared with other biodegradable polyesters, PCL exhibits lower cost, better biocompatibility and higher safety attributes. PCL can be readily loaded with a variety of hydrophobic drugs within the polymer bulk and avoids particle uptake by phagocytic cells in the liver or spleen5,6. The application of PCL, however, is limited by its slow degradation rate in vivo. Grafting PCL to other water-soluble polymers has been widely reported to enhance its biodegradation rate. Methoxy poly(ethylene glycol) (MPEG)-based modification has attracted increasing attention in the field of drug delivery due to its relatively low melting point that enables it to be fabricated by existing melt processing techniques and the ability to stabilize the delivery vehicle against undesirable aggregation and non-specific electrostatic interactions with its surroundings7. Furthermore, PEG segments also counteract protein absorption, which increase the circulatory half-life in the body8,9,10 due to its chain flexibility, high surface density and the absence of functional groups. Thus, in the present work, the amphiphilic matrix of methoxy poly(ethylene glycol)-poly(ε-caprolactone) (MPEG-PCL) containing a high percentage of PEG segments was synthesized via ring opening polymerization11 and used for the delivery of CAP for the first time.
Additionally, a simple, rapid, sensitive and reliable high-performance liquid chromatography (HPLC) method was established for determining pharmacokinetic parameters after oral administration in rats. Calibration curves with R2=0.994 were constructed over a concentration range of 80–2000 ng/mL. Therefore, in the present study, we focused on the development of CAP-loaded MPEG-PCL nanoparticles as an oral formulation aimed at improving solubility and bioavailability and reducing the side effects of CAP.
Materials and methods
Methoxy poly(ethylene glycol) (Mn=2000) and ε-caprolactone and were obtained from Jenkem Technology Co, Ltd (Beijing, China) and Adamas Corporation (Shanghai Local Agent, China), respectively. CAP (99.5% purity) was purchased from Yuanmu Biotechnology Co, Ltd (Shanghai, China). Double distilled water was produced using a Millipore water purification system (Millipore Corporation, USA) and stannous octoate [Sn(Oct)2, Jenkem] was distilled prior usage. Acetonitrile and methanol used as mobile phase in HPLC were obtained from Sinopharm Chemical Reagent Co, Ltd (Shanghai, China). All other chemicals are reagent grade or higher and were used without further purification.
Synthesis and characterization of MPEG-PCL block copolymers
MPEG-PCL copolymer with a designed molecular weight of 14 000 g/mol was synthesized via ring-opening polymerization with some modification of a previously reported method11. Predetermined amounts of MPEG and ε-caprolactone were put in a dried three-necked flask containing stannous octoate [Sn(Oct)2] dissolved in anhydrous toluene solution. The reaction system was refluxed under dry nitrogen atmosphere at 130 °C for 24 h. The crude copolymer was dissolved in dichloromethane (DCM) followed by evaporation of the toluene solution. The solution was then added to cold diethyl ether (DEE) to eliminate the unreacted MPEG. Subsequently, the resultant block copolymer was dried to a constant weight in a vacuum oven at room temperature and stored in air-tight bags pending characterization.
The formation of MPEG-PCL was determined by proton nuclear magnetic resonance (1H NMR) and gel permeation chromatography (GPC). 1H NMR spectrum was obtained using a Bruker AVANCE 600 spectrometer (Bruker, Germany) with deuterated chloroform as the solvent. In addition, the number average molecular weights (Mn), the weight average molecular weight (Mw) and the polydispersity index (PDI) were confirmed via a gel permeation chromatography (Waters E2695) system equipped with a refractive index detector and a Styragel HR column. HPLC-grade tetrahydrofuran (THF) was introduced as the eluent at a flow rate 1.0 mL/min. The calibration curve was generated using polystyrene standards with a molecular weight range from 900 to 30 000 g/mol.
Preparation of CAP-loaded MPEG-PCL nanoparticles
CAP-loaded MPEG-PCL nanoparticles were prepared via emulsion solvent evaporation with minor modification according to the procedure reported by Zhang et al12. MPEG-PCL (25 mg) and different amounts of CAP were dissolved in 1 mL of dichloromethane. Next, dichloromethane was carefully added to 8 mL of sodium cholate solution (0.8%, w/v) and then sonicated at 600 W in an ice bath using a probe sonicator (XinZhi Biotechnology Co Ltd, China). The oil-in-water (o/w) emulsion formed was vigorously stirred with a magnetic stirrer (100 rounds per minute at room temperature) for 12 h to evaporate the solvent thoroughly. During the process of evaporation, the rationally designed copolymer self-assembled to form polymer nanoparticles with an inner hydrophobic core, which facilitated the loading of CAP in the aqueous solution. Subsequently, nanoparticles were gently washed twice with distilled water to remove free CAP on the surface followed by centrifugation (14 000 rounds per minute, 4 °C for 40 min). After discarding the supernatant, CAP/NPs were resuspended in 1 mL of phosphate-buffered saline (PBS; pH 7.4, 0.1 mol/L) and then stored at 4 °C for further use. Blank NPs were also prepared with the same method at room temperature.
Drug loading and entrapment efficiency
A Shimadzu HPLC Instrument system (Shimadzu, SCL-10A, Japan) equipped with a UV-detector (Shimadzu SPD-10A, Japan) was used for CAP quantification. An external method was used to determine the drug-loading rate of the CAP/NPs. Chromatographic analysis was performed in isocratic mode using a reversed phase C18 column (4.6 mm×150 mm, particles size 5 μm, Waters, USA) and the detection wavelength was 280 nm. A methanol-water mixture (70:30, v/v) was used as mobile phase at flow rate of 1 mL/min at 30 °C and sample solution was injected at a volume of 20 μL. The HPLC was calibrated with standard solutions of 5–100 μg/mL of CAP dissolved in methanol (correlation coefficient of R2=0.994) and the low limit of detection was 30 ng/mL. The relative standard deviations (%RSD) were all less than 5.6%. The drug loading (1) and encapsulation efficiencies (2) were calculated based on the following equations:
Particle size and surface morphology
The average particle size and zeta potential of CAP/NPs and blank NPs were investigated by dynamic light scattering (DLS) with a Malvern Zetasizer (Malvern Instruments, UK) operating at a scattering angle of 90o at 25 °C. In brief, each fresh sample was diluted to the appropriate concentration to ensure free diffusion and unhindered Brownian motion of the particles5 and was transferred into a quartz cuvette. All results were calculated from the measurement performed in triplicate and were expressed as the mean size±standard deviation. The morphology of prepared NPs was observed with a transmission electron microscope (TEM) (JEM-2100, JEOL, Japan). Two drops of CAP/NPs placed on a copper grid with a nitrocellulose covering were stained with phosphotungstic acid (2%, w/v) and left to dry at room temperature. Particles were then evaluated after scanning under the microscope.
FT-IR spectroscopy analysis
The FT-IR spectra of pure drug, the physical mixture, polymers, blank NPs and drug-loaded NPs were obtained using a Nicolet AVATAR-370 FT-IR spectrophotometer (Thermo Electron Corporation, USA) at room temperature. In brief, each sample was thoroughly mixed with powdered KBr and compressed to a disc with pressure of 7 MPa before the FT-IR analysis. The IR spectra were obtained in the wavelength range of 4000–600 cm−1 using a resolution of 4 cm−1 and 32 scans were performed for each spectrum.
Crystallographic assays of pure drug, the physical mixture, polymers, blank NPs and drug-loaded NPs were conducted using a powder X-ray diffractometer (XRD; D8-ADVANCE, Bruker, Germany) with a Cu Kα radiation source at 40 kV and 20 mA. Before the analysis, each sample was pressed into a thin film with a Compression Molding Machine and then placed in a steel holder. The scanning range of 2θ was from 5° to 60° at a rate of 7°/min.
Differential scanning calorimetry
The thermal properties of pure drug, the physical mixture, polymers, blank NPs and drug-loaded NPs were characterized by differential scanning calorimetry (DSC; PerkinElmer, USA). Each sample was placed into standard Al-crucible pans prior to accurately weighing and were then heated at rate of 10 °C/min over 30 °C to 100 °C. Ultra-high pure nitrogen was used at a flow of 20 mL/min.
Stability of nanoparticles
Stability of nanoparticles was evaluated by measuring size variation and zeta potential measurement. Namely, the nanoparticles dissolved in PBS were stored at different temperatures and ambient humidity conditions (4 °C/65% RH, 25 °C/65% RH and 40 °C/75% RH) and evaluated for particle size, zeta potential and drug content. The samples were withdrawn at specified time intervals of 0, 1, 2, and 3 months13,14,15. The changes in mean size and zeta potential were monitored by the Malvern Zetasizer operating at a scattering angle of 90o at 25 °C. Drug content analysis was conducted using the validated HPLC method previously mentioned.
In vitro release studies
The in vitro release behavior of CAP/NPs into two release media was investigated by a dialysis method over 72 h16. In brief, CAP/NPs solution placed and sealed in dialysis bags (MWCO=3500 Da, Greenbird Inc, Shanghai, China) was incubated in 100 mL of the release media at 37 °C under vigorous shaking (100 rounds per minute) for 72 h. The release media, simulated gastric fluid (SGF; pH 1.2; 0.1 mol/L) or PBS (pH 7.4; 0.1 mol/L), contained Tween-80 (0.3%, w/v) to assure sink conditions. At discrete time intervals (0.25, 0.5, 1, 2, 4, 6, 8, 12, 24, 36, 48, 60, and 72 h), 0.5 mL of release media was drawn and replenished with an equal volume of fresh media. Then, samples were centrifuged (10 000 rounds per minute for 10 min) to separate the released drug from the nanoparticulate CAP17,18. The concentration of CAP in the removed supernatant was determined using the HPLC system. CAP released from the stock solution was set as control. The results were the mean of three test runs and all values were expressed as the mean±standard deviation. To evaluate the possible release mechanism, zero-order, first-order, Higuchi, and Weibull models were used to fit the in vitro drug release pattern. The fitting to different release models was conducted using Microsoft office Excel® and the final curves were accomplished using Originlab® 8.0. The Weibull model is represented by the following equation (3):
where M is the accumulated release rate and t is time; a and b are constant. The goodness of fitting for the release kinetic models was evaluated with correlation coefficient values (R2).
Preparation of test animals
The study protocol was approved by the Ethics Committee of Jiangsu University. Ten male Sprague-Dawley (SD) rats weighing 250–300 g were purchased from the Animal Centre of Jiangsu University and randomly divided into two groups (n=5) for pharmacokinetic investigation. Animals were starved overnight (12 h) with free access to water before dosing to avoid drug-food interactions. CAP/NPs were orally administered to one group and the other group received crude drug dispersed in 0.5% CMC-Na solution at the CAP dose of 35 mg/kg body weight. Blood samples of approximately 500 μL were collected via the orbital veins into heparinized polyethylene tubes at scheduled time points (0.25, 0.5, 1, 2, 4, 6, 8, 12, 24, and 36 h) and centrifuged at 3000 rounds per minute for 10 min to separate plasma. Then, the supernatant plasma fraction was transferred into a clear glass tube. Harvested plasma samples were stored at −70 °C in an ultra-low temperature freezer until further analysis.
Plasma sample preparation
The CAP in serum was extracted by the Liquid-Liquid extraction method (LLE). After 200 μL of plasma was mixed with 400 μL doubled distilled water in a 10-mL glass tube, an aliquot of 50 μL internal standard (IS; 1-Naphthol) working solution and 500 μL acetonitrile were successively added to the mixture. The resulting sample was vortex-mixed vigorously for 1 min to precipitate plasma proteins followed by adding 3 mL of a cyclohexane-ethyl acetate mixture (1:1, v/v). The resultant mixture was subjected to centrifugation at 3000 rounds per minute for 10 min. Then, the upper layer was transferred into a tube and evaporated to dryness under a gentle stream of nitrogen gas at 40 °C. The residue was reconstituted with 100 μL of methanol and centrifuged at 3000 rounds per minute for 5 min. A 20 μL aliquot of the supernatant was injected into the HPLC system for quantitative analysis.
Validation of HPLC Method
An internal method was applied to determine the amount of CAP in plasma. Therefore, two different HPLC methods were employed for the drug loading and in vivo experiments. The HPLC separation was performed on an Inertsil ODS-SP analytical column (4.6 mm×150 mm, 5 μm, Shimadzu, Japan). The system operated under an isocratic flow rate of 1 mL/min using a mobile phase of acetonitrile-water (43:57, v/v), which was filtered through a membrane (0.22 μm) and degassed in a sonicator bath for 30 min prior to usage. The injection volume for HPLC analysis was set at 20 μL and the temperature of column was maintained at 50 °C during analysis. A calibration curve (y=0.002x−0.0154) was constructed using six calibration standards that showed excellent linearity over the concentration range of 80–2000 ng/mL (correlation coefficient, R2=0.994). The accuracy and precision of the assay were determined by three replicates of spiked plasma samples at low, medium and high concentrations (125, 1000, and 2000 ng/mL). The extraction recoveries were in the range of 80.5%–86.4%. The limit of detection (LOD)19 of this assay was 30 ng/mL at a signal-to-noise ratio (S/N) of >3 and the lowest limit of quantification (LOQ) determined was 75 ng/mL (S/N ratio >10) with a %RSD of <15%. Accuracy was calculated using equation (4):
The intra- and inter-day precision was expressed as the relative standard deviation and the results were obtained via analysis of samples on three separate days.
Analysis of Pharmacokinetic parameters
Pharmacokinetic parameters of the drug, namely, peak plasma concentration (Cmax), time to Cmax (Tmax), mean residence time (MRT) and area under the concentration-time curve (AUCt) were calculated using the BAPP 2.3 pharmacokinetic software (purchased from the Center of Drug Metabolism of China Pharmaceutical University, China)20. All parameter values are reported as the mean value±standard deviation unless otherwise noted. The relative bioavailability (F) after administration was determined by calculating the ratio of AUC for the test formulation (AUCT) and AUC for the reference formulation (AUCR) according to the following equation (5):
In vitro-in vivo correlation
In vitro-in vivo correlation (IVIVC) refers to the predictive mathematical model describing the relationship between in vitro dissolution and in vivo input rate21. Although four categories of IVIVCs have been described in the FDA guidance, a level A correlation model is used to describe the relationship because that is considered most informative and very useful from a regulatory viewpoint. In addition, CAP, a poorly water-soluble drug, exhibits low solubility and low permeability22. The results of the fraction absorbed (FRA) and fraction of drug dissolved (FRD) were obtained using the method of Wagner-Nelson using the BAPP software. The relationship between FRA and FRD was fitted using the nonlinear regression model as the following equation (6):
where a, b, c represent regression parameters of the equation, Y is the FRA in vivo and X is the FRD in vitro. The IVIVC was evaluated by the correlation coefficient (R2).
Gastric mucosa irritation test
Nine male SD rats weighting 300±20 g were randomly divided into three groups. After 12 h of fasting, one group was treated with physiological saline as control and the other two groups were orally gavaged with free CAP (suspended in 0.5% CMC-Na solution) or NPs at the CAP dose of 35 mg/kg. Two hours later, stomachs were removed, cut open along the greater curvature and rinsed thoroughly with physiological saline. Subsequently, the samples were persevered in 10% formalin. Sections (3–4 μm) of tissue were cut using a microtome and stained with hematoxylin and eosin (H&E) before microscopic examination.
Characterization of the amphiphilic copolymer
Figure 1 shows the 1H NMR spectrum of the MPEG-PCL block copolymer. The signal at δ 3.649 ppm was assigned to the −CH2 protons of the PEG chain. In addition, the peaks at δ 2.294–2.319, 1.619–1.678, 1.384–1.410, and 4.050–4.072 ppm were attributed to the various methylene protons of the PCL units corresponding to the results reported in the literature23,24. The Mn obtained from 1H NMR was calculated to be approximately 16 000 g/mol by comparing the peak intensity at approximately 2.31 with 3.65 ppm. The Mn and Mw detected from the GPC were summarized in Table 1. Notably, GPC chromatographs from the block copolymer showed a unimodal shape and narrow molecular weight distributions.
Characterization of nanoparticles
A drug loading content of 14.0%±0.13% and encapsulation efficiency of 81.5%±0.9% were obtained using a CAP feeding ratio of 20%. As observed in Figure 2A, the prepared CAP/NPs exhibited a narrow size distribution with an average diameter of 82.54±0.51 nm and a low polydispersity index (PDI) in the range of 0.09±0.02. In addition, the zeta potential of CAP/NPs was found to be −24.67±4.3 mV, indicating the high stability of NPs.
The morphology of NPs prepared using the modified emulsification solvent diffusion method is shown in Figure 2B. According to the TEM images, the prepared CAP/NPs had a spherical appearance with an approximate average diameter of 80 nm, which was consistent with the results determined by dynamic light scattering technique.
As shown in Figure 3A, typical absorption peaks of the carbonyl groups (C=O) of PCL appeared at approximately 1725 cm−1 and the peaks at 2875 cm−1 and 2937 cm−1 were assigned to the stretching vibration of C-H bond of MPEG and PCL. The spectrum of the blank NPs was similar to that of the copolymer because they are characterized by the bands described above. Three characteristic absorbance bands of raw CAP were clearly observed at approximately 1600, 2922, and 3278 cm−1. These bands were also found in the physical mixture. The remaining peaks in the mixture were attributed to the induction of MPEG-PCL, which was confirmed by comparing of the spectra of the mixture with that of the copolymer. Moreover, in the case of fingerprint regions, there were obvious differences between the mixture and NPs. The fingerprint regions of the NPs were similar to the copolymer, whereas the mixture exhibited a CAP-like fingerprint.
To elucidate potential changes of drug crystals in the nanoparticles formulation, X-ray powder diffraction (XRD) was performed and the spectra of CAP, CAP/NPs, MPEG-PCL, blank NPs and the physical mixture were shown in Figure 3B. Raw CAP material is crystalline in nature, as demonstrated by crystallographic analysis, with characteristic peaks at approximately 5.6°, 11.5°, 21.5°, and 24.6°. The MPEG-PCL was amorphous, which was confirmed by the absence of diffraction peaks. In addition, most crystalline peaks of CAP were apparent in the spectrum of the mixtu re indicating that the physical state of drug in the mixture was not changed.
Thermal behaviors of CAP, MPEG-PCL, NPs, blank NPs and the physical mixture of CAP and the synthesized copolymer were analyzed by DSC and the results of thermal analysis are shown in Figure 4. CAP exhibits a melting peak between 63 °C and 70 °C, centered at approximately 67 °C as observed in the figure, which was consistent with a previous report25. MPEG-PCL showed a melting point at approximately 61 °C as well. It is important to mention that a marked shift in peak position was observed for the physical mixture, which is indicative of a crystalline state for CAP in the mixture. The behavior can be attributed to the interactions between CAP and the polymer in the solid state. For lyophilized CAP/NPs, no inflexion point at 67 °C was measured.
As shown in Table 2, no significant change in the mean diameter of NPs was observed after 3 months of storage at 4 °C/65% RH, 25 °C/65% RH and 40 °C/75% RH and the particle size did not exceed 90 nm. Additionally, the drug content of CAP/NPs showed only minor changes at the various temperatures during 3 months. In addition, the surface charge of NPs was measured to be approximately −24 mV. These results further confirmed that the NPs were highly stable in PBS.
In vitro release of CAP/NPs
The in vitro release behaviors of CAP/NPs in two release media are shown in Figure 5. It was clearly observed that the release profiles of CAP/NPs in SGF and PBS were statistically similar because there was no significant difference (P>0.05) between the release profiles of CAP from either media. This phenomenon demonstrates that the release media, SGF or PBS, has little influence on the in vitro release behavior of the NPs. In addition, the CAP-loaded MPEG-PCL nanoparticles showed a biphasic release profile. The burst of CAP from the formulation within 12 h was less than 25% in either media followed by a more sustained release rate for 60 h. Compared to the nanoparticle formulation, the release profiles of the CAP stock solution had marked differences, showing its release behavior was dependent on pH. The CAP stock solution release rate was faster in SGF than PBS. Approximately 68% of CAP was released from the stock solution in PBS within 4 h compared with nearly 100% in SGF. Furthermore, based on the correlation coefficient criterion, the release profiles of the NPs in SGF and PBS were best fitted with the Weibull mathematical model (R2=0.972 and 0.969, respectively).
In vivo pharmacokinetics
The data from the validation of the assay method in rat plasma are presented in Table 3. The precision of intra- and inter-day were 1.16%–4.47% and 1.08%–7.91%, respectively, and all values of accuracy were found to be satisfactory and in line with international criteria26. This suggested that the method is suitable for quantitative analysis of CAP in plasma samples. Figure 6 shows the mean CAP plasma concentration versus time profiles after oral administration at the 35 mg/kg CAP dose in two formulations (raw CAP suspension and CAP loaded in MPEG-PCL nanoparticles). The relevant pharmacokinetic parameters have also been summarized in Table 4. With regard to the single compartmental analysis, the NPs exhibited pharmacokinetic parameters that were significantly altered compared to those of the free CAP. After oral administration of the free CAP suspension, a maximum plasma concentration (Cmax) of 491.94±17.89 ng/mL was reached in 0.5 h, indicating that the drug was absorbed rapidly. Subsequently, plasma concentrations decreased sharply resulting in a high Ke (0.187±0.006) and short half-life (3.70±0.11 h). These results suggest that the drug was rapidly distributed and metabolized leaving a minimum drug concentration after 24 h. By contrast, CAP/NPs showed a markedly delayed blood clearance. Its pharmacokinetic parameters suggested that the NPs could extend the half-life of CAP from 3.70±0.11 h to 13.88±13.73 h (P<0.01) and delay the MRT from 5.91±0.38 h to 18.02±19.91 h (P<0.01). It is also worth noting that the Cmax of the NPs (743.44±10.67 ng/mL) was reached within 4 h, demonstrating that there are different absorption rates for free CAP and CAP/NPs. Clearly, the nanoparticles are effective at increasing drug absorption because the delayed Tmax (4 h) demonstrates sustained release of CAP. In addition, the AUC0–t for the formulation was approximately 6-fold higher than that of free CAP (P<0.01). The relative bioavailability of CAP/NPs showed approximately 6-fold increase compared to free drug.
In vitro-in vivo correlation
Exploring the correlation between in vitro permeation and in vivo absorption is an important part in the dosage form development process because it can shorten the drug development period and economize resources27. The point-to-point relationship between in vitro and in vivo release profiles was a level A correlation as defined by the US Food and Drug Administration28. Level A correlation between in vitro dissolutions (in SGF and PBS) and in vivo absorption was constructed. Good point-to-point relationship of in vitro permeation and in vivo absorption were observed for the NPs with a correlation coefficient of 0.998 and 0.996 in SGF and PBS, respectively. It is important to note that reliable IVIVCs allow prediction of the in vivo bioavailability or bioequivalence of CAP based on the in vitro drug dissolution.
Gastric mucosa irritation test
In this investigation, it was anticipated that the CAP-loaded copolymer nanoparticles could reduce the irritation effect on the gastrointestinal tract compared with that caused by CAP administered as an aqueous suspension. As shown in Figure 7C, marked mucosal bleeding and inflammatory cell infiltrations were observed in rat stomachs after administration of pure CAP suspension. However, few or no lesions were observed in the mucosal surface of the rats that received the NPs formulation (Figure 7B).
PCL is one of the most promising polymers for controlled and site-specific drug delivery because of its biocompatibility and good biodegradable nature29. It can also readily blend efficiently with many other polymers, especially grafted MPEG block to satisfy the required biophysical properties for most formulations. The amphiphilic copolymer of MPEG-PCL containing a high percentage of PEG segments was synthesized by ring opening polymerization with Sn(Oct)2 as the catalyst. In this study, molecular weight of the copolymer was controlled by adjusting the molar ratio of ε-CL and MPEG. In addition, the critical micelle concentration of the copolymer decreased with increasing PCL length which was consistent with published literature23.
CAP has been extensively investigated in pharmacy and neuroscience30 due to its varied pharmacological activities. However, owing to its high hydrophobic structure, CAP exhibits very poor aqueous solubility, which results in formulation difficulties. Several reports have been published on the delivery of CAP using liposomes31 and microemulsions1. These nanosized delivery systems have already proven their effectiveness in solubilizing CAP. However, there are a few drawbacks of these systems, such as high quantities of surfactants and co-surfactants, low drug loading and being unstable systems. Thus, in our study, synthesized MPEG-PCL was used as the carrier of CAP for its ability to overcome the deficiencies mentioned above. We found that the solubility of CAP in water was notably improved by the MPEG-PCL vehicle compared to the unformulated drug. This can be attributed to the hydrophobic core formed by the amphiphilic copolymer in the aqueous medium. The cargo space in turn loads CAP, thus allowing it to exist in the molecular or amorphous form.
Although several methods are used to prepare MPEG-PCL nanoparticles, the emulsion solvent evaporation method was adopted in this study because it is simple, reproducible, economic and widely employed32. EE% and DE% are important indexes for a drug delivery system. This is true for expensive drugs, especially those used in the treatment of cancer33. We observed that increased drug-to-polymer ratios resulted in marginal elevation of drug loading but a gradual decline in EE%. However, no obvious difference was found in particle size and PDI, which was consistent with a previous report34. In our work, the mean droplet size of the prepared nanoparticles was approximately 80 nm with a narrow distribution. Many related studies have shown that the particle size and distribution (PDI) of the NPs are very important factors for systemic drug uptake. Smaller particle sizes (<200 nm) and narrow distribution range decrease the rate of mononuclear phagocyte system uptake and tend to accumulate in tumor sites35,36. As such, the relatively small particle size and narrow PDI of CAP/NPs could allow for the accumulation of more CAP at the site of action thereby eliciting a sustained effect. According to TEM images, the prepared CAP/NPs had a spherical appearance with an approximate average diameter of 80 nm, which was consistent with the result obtained by DLS. In addition, it was clearly observed that no drug crystals surrounded the NPs, suggesting that the preparation process was free from drug crystallization. The MPEG-PCL spectrum was also in line with previous reports7,24, further implying that MPEG-PCL was successfully synthesized. There was little or no interaction between the drug and carrier demonstrated by the lack of a new absorption peak from the FT-IR spectra. Additionally, due the absence of crystalline peaks in the pattern of CAP/NPs, CAP can be said to be molecularly dispersed in the copolymer. These results were further supported by data obtained from DSC measurements.
Formulation stability plays important roles in drug development procedures, long-term storage and transportation. The stability of CAP/NPs was studied by storing NPs in PBS at different temperature for three months. There was no significant change in the mean diameter or the surface charge of NPs over the period or the drug content. This fact may be attributed to the PEG chains on the surface of the nanoparticles, which prevent the aggregation of CAP/NPs. Compared to the CAP stock solution, the in vitro release of CAP/NPs in both media showed a relatively slower release rate, possibly due to the effect of both drug diffusion and polymer swelling.
Following oral administration, the bioavailability of CAP-loaded MPEG-PCL was significantly improved compared to CAP in aqueous suspension. Cmax and AUC are important features of the blood level profile. AUC depicts the extent of drug absorption. We observed that both AUC and Cmax of CAP/NPs were significantly greater than the control group. These results could be due to the behavior of the copolymer nanoparticles, which reduce drug uptake by plasma proteins and the mononuclear phagocyte system while protecting CAP from degradation. CAP has been used for the treatment of chronic musculoskeletal or neuropathic pain for many years37. Its range of clinical usage is often limited due to the incidence of gastrointestinal irritation and hemorrhage. CAP/NPs, in this study, visibly reduced the irritation effect on the gastrointestinal tract compared with the aqueous suspension. The reduced direct contact of CAP with the surface of gastrointestinal tract mucosa offered by the protective effect of the carrier could account for this phenomenon. These results, therefore, establish that the amphiphilic copolymer can significantly decrease the gastric mucosa irritation side-effect of CAP.
In the present study, the CAP nanoparticles based on the MPEG-PCL copolymer were fabricated by the solvent emulsification/evaporation technique where particles with small size, uniform distribution and higher encapsulation efficiency were successfully produced. The nanoparticle formulation was characterized by TEM, XRD, DSC, and FT-IR techniques. The in vitro release behavior of the NPs exhibited a sustained release of CAP, suggesting that the release behavior of the NPs was governed by MPEG-PCL. The results of histological studies showed that CAP entrapped by the copolymer can markedly reduce irritation in the gastric mucosa in rats. Furthermore, after oral administration of 35 mg/kg CAP as a NPs formulation and free CAP, plasma concentrations of CAP were detected by a validated HPLC method. The NPs have the potential for significantly lowering the clearance of CAP and increasing its bioavailability compared with the control formulation. Based on these results, it can be concluded that the MPEG-PCL nanoparticles investigated in this study may be a good drug delivery vehicle for CAP.
Tavano L, Alfano P, Muzzalupo R, de Cindio B . Niosomes vs microemulsions: New carriers for topical delivery of Capsaicin. Colloids Surf B Biointerfaces 2011; 87: 333–9.
Huang YB, Lin YH, Lu TM, Wang RJ, Tsai YH, Wu PC . Transdermal delivery of capsaicin derivative-sodium nonivamide acetate using microemulsions as vehicles. Int J Pharm 2008; 349: 206–11.
Lee SH, Richardson RL, Dashwood RH, Baek SJ . Capsaicin represses transcriptional activity of β-catenin in human colorectal cancer cells. J Nutr Biochem 2012; 23: 646–55.
Mori A, Lehmann S, O'Kelly J, Kumagai T, Desmond JC, Pervan M, et al. Capsaicin, a component of red peppers, inhibits the growth of androgen-independent, p53 mutant prostate cancer cells. Cancer Res 2006; 66: 3222–9.
Zamani S, Khoee S . Preparation of core-shell chitosan/PCL-PEG triblock copolymer nanoparticles with ABA and BAB morphologies: Effect of intraparticle interactions on physicochemical properties. Polymer 2012; 53: 5723–36.
Lu F, Lei L, Shen YY, Hou JW, Chen WL, Li YG, et al. Effects of amphiphilic PCL-PEG-PCL copolymer addition on 5-fluorouracil release from biodegradable PCL films for stent application. Int J Pharm 2011; 419: 77–84.
Tanaka K, Kanazawa T, Shibata Y, Suda Y, Fukuda T, Takashima Y, et al. Development of cell-penetrating peptide-modified MPEG-PCL diblock copolymeric nanoparticles for systemic gene delivery. Int J Pharm 2010; 396: 229–38.
Endres TK, Beck-Broichsitter M, Samsonova O, Renette T, Kissel TH . Self-assembled biodegradable amphiphilic PEG-PCL-lPEI triblock copolymers at the borderline between micelles and nanoparticles designed for drug and gene delivery. Biomaterials 2011; 32: 7721–31.
Wilson DR, Zhang N, Silvers AL, Forstner MB, Bader RA . Synthesis and evaluation of cyclosporine A-loaded polysialic acid-polycaprolactone micelles for rheumatoid arthritis. Eur J Pharm Sci 2014; 51: 146–56.
Zhang H, Wilson J, Zhang J, Luo Y . Characterization of potential degradation products in a PEGylating reagent 20 kDa monomethoxy polyethylene glycol propionaldehyde by RP-HPLC, APCI-MS and NMR. J Pharm Biomed Anal 2014; 89: 221–6.
Jiang X, Xin H, Sha X, Gu J, Jiang Y, Law K, et al. PEGylated poly(trimethylene carbonate) nanoparticles loaded with paclitaxel for the treatment of advanced glioma: In vitro and in vivo evaluation. Int J Pharm 2011; 420: 385–94.
Zhang Y, Zhang Q, Zha L, Yang W, Wang C, Jiang X, et al. Preparation, characterization and application of pyrene-loaded methoxy poly(ethylene glycol)-poly(lactic acid) copolymer nanoparticles. Colloid Polym Sci 2004; 282: 1323–8.
Han HS, Lee J, Kim HR, Chae SY, Kim M, Saravanakumar G, et al. Robust PEGylated hyaluronic acid nanoparticles as the carrier of doxorubicin: Mineralization and its effect on tumor targetability in vivo. J Control Release 2013; 168: 105–14.
Wei K, Peng X, Zou F . Folate-decorated PEG-PLGA nanoparticles with silica shells for capecitabine controlled and targeted delivery. Int J Pharm 2014; 464: 225–33.
Parmar N, Singla N, Amin S, Kohli K . Study of cosurfactant effect on nanoemulsifying area and development of lercanidipine loaded (SNEDDS) self nanoemulsifying drug delivery system. Colloids Surf B Biointerfaces 2011; 86: 327–38.
Li TSC, Yawata T, Honke K . Efficient siRNA delivery and tumor accumulation mediated by ionically cross-linked folic acid-poly(ethylene glycol)-chitosan oligosaccharide lactate nanoparticles: For the potential targeted ovarian cancer gene therapy. Eur J Pharm Sci 2014; 52: 48–61.
Mohanty C, Sahoo SK . The in vitro stability and in vivo pharmacokinetics of curcumin prepared as an aqueous nanoparticulate formulation. Biomaterials 2010; 31: 6597–611.
Das RK, Kasoju N, Bora U . Encapsulation of curcumin in alginate-chitosan-pluronic composite nanoparticles for delivery to cancer cells. Nanomedicine 2010; 6: 153–60.
De Baere S, Eeckhaut V, Steppe M, De Maesschalck C, De Backer P, Van Immerseel F, et al. Development of a HPLC-UV method for the quantitative determination of four short-chain fatty acids and lactic acid produced by intestinal bacteria during in vitro fermentation. J Pharm Biomed Anal 2013; 80: 107–15.
Yu JN, Zhu Y, Wang L, Peng M, Tong SS, Cao X, et al. Enhancement of oral bioavailability of the poorly water-soluble drug silybin by sodium cholate/phospholipid-mixed micelles. Acta Pharmacol Sin 2010; 31: 759–64.
Chu C, Tong SS, Xu Y, Wang L, Fu M, Ge YR, et al. Proliposomes for oral delivery of dehydrosilymarin: preparation and evaluation in vitro and in vivo. Acta Pharmacol Sin 2011; 32: 973–80.
Uppoor VRS . Regulatory perspectives on in vitro (dissolution)/in vivo (bioavailability) correlations. J Control Release 2001; 72: 127–32.
Xie W, Zhu W, Shen Z . Synthesis, isothermal crystallization and micellization of mPEG-PCL diblock copolymers catalyzed by yttrium complex. Polymer 2007; 48: 6791–8.
Cai R, Li R, Qian J, Xie A, Nie K . The morphology and fabrication of nanostructured micelle by a novel block copolymer with linear-dendritic structure. Mater Sci Eng C Mater Biol Appl 2013; 33: 2070–7.
Zi P, Yang X, Kuang H, Yang Y, Yu L . Effect of HPβCD on solubility and transdermal delivery of capsaicin through rat skin. Int J Pharm 2008; 358: 151–8.
Shah V, Midha K, Findlay JA, Hill H, Hulse J, McGilveray I, et al. Bioanalytical method validation — a revisit with a decade of progress. Pharm Res 2000; 17: 1551–7.
Chakraborty S, Shukla D, Mishra B, Singh S . Lipid — An emerging platform for oral delivery of drugs with poor bioavailability. Eur J Pharm Biopharm 2009; 73: 1–15.
Lu Y, Kim S, Park K . In vitro–in vivo correlation: Perspectives on model development. Int J Pharm 2011; 418: 142–8.
Dash TK, Konkimalla VB . Poly-є-caprolactone based formulations for drug delivery and tissue engineering: A review. J Control Release 2012; 158: 15–33.
Xing F, Cheng G, Yi K, Ma L . Nanoencapsulation of capsaicin by complex coacervation of gelatin, acacia, and tannins. J Appl Polymer Sci 2005; 96: 2225–9.
Tyagi P, Chancellor MB, Li Z, de Groat WC, Yoshimura N, Fraser MO, et al. Urodynamic and immunohistochemical evaluation of intravesical capsaicin delivery using thermosensitive hydrogel and liposomes. J Urol 2004; 171: 483–9.
Rao JP, Geckeler KE . Polymer nanoparticles: Preparation techniques and size-control parameters. Prog Polymer Sci 2011; 36: 887–913.
Zhang Z, Feng SS . The drug encapsulation efficiency, in vitro drug release, cellular uptake and cytotoxicity of paclitaxel-loaded poly(lactide)-tocopheryl polyethylene glycol succinate nanoparticles. Biomaterials 2006; 27: 4025–33.
Gu C, Le V, Lang M, Liu J . Preparation of polysaccharide derivates chitosan-graft-poly(ε-caprolactone) amphiphilic copolymer micelles for 5-fluorouracil drug delivery. Colloids Surf B Biointerfaces 2014; 116: 745–50.
Danhier F, Feron O, Préat V . To exploit the tumor microenvironment: Passive and active tumor targeting of nanocarriers for anti-cancer drug delivery. J Control Release 2010; 148: 135–46.
Bernabeu E, Helguera G, Legaspi MJ, Gonzalez L, Hocht C, Taira C, et al. Paclitaxel-loaded PCL-TPGS nanoparticles: In vitro and in vivo performance compared with Abraxane®. Colloids Surf B Biointerfaces 2014; 113: 43–50.
Knolle E, Zadrazil M, Kovacs GG, Medwed S, Scharbert G, Schemper M . Comparison of cooling and EMLA to reduce the burning pain during capsaicin 8% patch application: A randomized, double-blind, placebo-controlled study. Pain 2013; 154: 2729–36.
This work was supported by the National Natural Science Foundation of China (30973677), National “Twelfth Five-Year” Plan for Science & Technology Support (2012BAD36B01), the Doctoral Fund of Ministry of Education of China (20113227110012), Special Funds for 333 (BRA2013198) and 331 Projects and Industry-University-Research Institution Cooperation (JHB2012-37, GY2012049, and GY2011028) in Jiangsu Province and Zhenjiang City. The authors also thank the Jiangsu University Ethics Committee for their guidance in the animal experiments.
About this article
Cite this article
Peng, W., Jiang, X., Zhu, Y. et al. Oral delivery of capsaicin using MPEG-PCL nanoparticles. Acta Pharmacol Sin 36, 139–148 (2015). https://doi.org/10.1038/aps.2014.113
- gastric mucosa irritation
Preparation, Optimization, and Evaluation of Methoxy Poly(ethylene glycol)-co-Poly(ε-caprolactone) Nanoparticles Loaded by Rivastigmine for Brain Delivery
ACS Chemical Neuroscience (2020)
Preparation and Optimization of Capsaicin-Loaded Chitosan Nanoparticles as Delivery Systems Using Box-Behnken Design
Materials Science Forum (2020)
The Effect of Natural Antioxidants in the Development of Metabolic Syndrome: Focus on Bergamot Polyphenolic Fraction
Pharmaceutical Development and Technology (2020)
In vitro endothelial differentiation evaluation on polycaprolactone-methoxy polyethylene glycol electrospun membrane and fabrication of multilayered small-diameter hybrid vascular graft
Journal of Biomaterials Applications (2020)