Pharmacokinetic studies of nanoparticles as a delivery system for conventional drugs and herb-derived compounds for cancer therapy: a systematic review

Abstract

The poor pharmacokinetic characteristics of most anticancer drugs have limited their clinical effectiveness. The application of nanoparticles as a novel drug delivery system has provided opportunities to tackle the current challenges facing conventional drug delivery systems such as poor pharmacokinetics, lack of specificity to tumor cells, multidrug resistance, and toxicity. This systematic review aims to examine the application of pharmacokinetic studies of nanoparticles loaded in conventional drugs and herb-derived compounds for cancer therapy. The pharmacokinetic parameters of several herbal medicines and chemotherapeutic drugs loaded into nanoparticles were reported. This included area under the curve (AUC) of plasma concentration–time profile, maximum plasma concentration (C_max), time to maximum plasma concentration (T_max), volume of distribution (V_d or V_ss), elimination half-life (t_½), and clearance (CL). The systematic review was conducted using information available in the PubMed and Science Direct databases up to February 2019. The search terms employed were: pharmacokinetics, pharmacokinetic study, nanoparticles, anticancer, traditional medicine, herbal medicine, herb-derived compounds, natural products, and chemotherapy. Overall, nanoparticle carriers not only significantly improved pharmacokinetics but also further enhanced permeability, solubility, stability, specificity, and selectivity of the carried anticancer drugs/herb-derived compounds to target tumor cells. Additionally, they also limited hepatic first-pass metabolism and P-glycoprotein (P-gp) efflux of the carried anticancer drugs/herb-derived compounds. Based on this systematic review, polymeric nanoparticles were the most commonly used nanocarrier to improve the pharmacokinetic parameters. The use of nanoparticles as a novel drug delivery system has the potential to improve both pharmacokinetics and cytotoxicity activity of the loaded drugs/herb-derived compounds for cancer therapy.

Introduction

Cancer is the leading cause of death globally.¹ Chemotherapy, radiation therapy, and surgery are the main therapeutic approaches for cancer.^1,2 The success of chemotherapy has been limited due to the lack of drug specificity to tumor cells, insufficient drug concentration in tumor cells, serious adverse effects, and the emergence of multidrug-resistant tumor cells.^1–3 Several strategies have been proposed to tackle these challenges facing conventional chemotherapeutic drugs, which includes the use of traditional or herbal medicines for cancer therapy. The use of herbal medicines for cancer therapy has been rising all over the world due to their biological activity as well as fewer adverse effects as compared to conventional chemotherapeutic drugs. Pharmacokinetics is the study of the relationship between the dose of a drug and its concentrations in the body fluids over time. This relationship is controlled mainly by the rate and extent of drug absorption, distribution, metabolism, and excretion processes, known as ADME. The critical pharmacokinetic parameters used to define these processes include bioavailability (F), elimination half-life (t_1/2), volume of distribution (V_d or V_ss), and clearance (CL) (Figure 1). Despite the impressive benefits of several herbal medicines, they exhibit some challenges such as poor pharmacokinetic profiles and the requirement of high doses which are commonly associated with toxicity.¹ The goal of improving the pharmacokinetic profile of a drug is to obtain the desired therapeutic outcome with minimum toxicity.

Figure 1.

Schematic diagram showing the four pharmacokinetic processes: absorption, distribution, metabolism and excretion (ADME) including their pharmacokinetic parameters.

Recently, the use of novel drug delivery systems such as nanoparticles has paved the way to the development of enhancing the pharmacokinetics of anticancer drugs.^5–9 Herb-derived active compounds or conventional chemical synthetic drugs incorporated with nanoparticles offer a solution to overcome their unsuitable pharmacokinetic properties, specificity, efficacy, and toxicity. Encapsulation of these compounds/drugs with nanoparticles would likely impact the pharmacokinetics and stability of the carried compounds. To our knowledge, the impact of nanoparticles on pharmacokinetic properties of the herb-derived active compounds or conventional chemical synthetic drugs has not yet been reviewed thoroughly. This systematic review aims to examine pharmacokinetic studies of nanoparticles loaded with herb-derived compounds and conventional chemotherapeutic drugs for cancer therapy.

Materials and methods

Study selection and inclusion and exclusion criteria

The systematic review was performed until February 2019 using PubMed and Science Direct databases. The search terms used were: “Pharmacokinetics”, AND/OR “Pharmacokinetic study”, AND “Nanoparticles”, AND “Anticancer”, AND/OR “Traditional medicine”, AND/OR “Herbal medicine” AND/OR “Herb-derived compounds”, AND/OR “Natural products”, AND “Chemotherapy”. The articles published from various journals were retrieved and saved in EndNote X8 for further analysis. The inclusion criteria were 1) full-text articles published in English, 2) In vitro or in vivo or clinical studies with application of nanoparticles of herb-derived compounds or conventional drugs for cancer chemotherapy, and 3) articles with in vivo/clinical pharmacokinetic studies reporting at least area under plasma concentration–time curve (AUC). All duplicates, review articles, articles with unclear methodology, or articles related to the application of nanoparticles in diagnostic/imaging, immunotherapy, radiotherapy, photothermal therapy, lipoprotein nanoparticles, gene therapy, hydrogel nanoparticles, conjugated ligands, and targeted therapy, as well as combined anticancer drugs were excluded from the analysis.

Data extraction and collection

The following study characteristics were extracted from each article that fulfilled the inclusion criteria and had none of the exclusion criteria: nanoparticles, drug-loaded, the analytical method applied, type of study, animal or human used, dose and route of loaded drugs given, and pharmacokinetic parameters (at least AUC). Final eligibility check of the full-text articles was performed; only articles that were relevant to the review question and keywords were obtained and processed for final analysis.

Results and discussion

A total of 403 relevant research articles published up to February 2019 were retrieved from PubMed and Science Direct databases. All articles were imported and merged in EndNote reference management software. One hundred sixty-nine duplicate articles and 39 review articles were excluded. Of the remaining 195 articles, 167 articles were available as full-texts for eligibility screening. Finally, 50 articles fulfilling the inclusion criteria were included in the study (Figure 2). The pharmacokinetic studies of the nanoparticles of herb-derived compounds and conventional chemotherapeutic drugs for cancer are summarized in Tables 1 and 2.

Figure 2.

Flowchart summarizing inclusion and exclusion of the articles for the study.

Table 1.

Summary of the in vivo/clinical pharmacokinetic studies of conventional chemotherapeutic drugs for cancer included in the analysis. Data are presented as mean values for nanoformulation vs free drug

Drug-loaded	Nanoparticle	Animals used (n)/cell line	Route, dose	Analytical technique	Pharmacokinetic parameters (mean)	Outcomes	Reference
Daunorubicin	CS–PLGA and PLGA	Wister rats (n=6) MCF-7 cell line	Oral, 10 mg/kg bw	UHPLC-MS/MS	AUC0–48: 15,729, 8674.65 vs 1393 ng.hr/mL; Cmax: 591, 318.55 vs 44.65 ng/mL: Tmax: 4.00, 4.00 vs 2.00 hrs; t1⁄2: 152.7, 119.39 vs 54.55 hrs.	Improved pharmacokinetics with CS-PLGA loaded drug than PLGA loaded drug with increased AUC (11.29-fold), Cmax (1.86-fold), Tmax (2-fold), and prolonged t1/2 (2.8-fold). Potential to avoid first pass metabolism with CYP450 and P-gp mediated efflux.	22
Lecithmer	Wistar rats (n=6) K562and Hop62celllines	IV, 4 mg/kg bw	HPLC	AUC: 31.2 vs 39.7 ng hr/mL; t1⁄2: 1.96 vs 1.63 hrs; Vd: 81.68 vs 57.46 L; CL: 28.87 vs 23.24 L/hrs	The only significantly improved pharmacokinetic was Vd (1.42-fold) with the rapid uptake of the reticuloendothelial system. Slightly Prolonged t1/2 (1.2-fold) decreased AUC (1.3-fold); Increased CL (1.24-fold)	23
Docetaxel	PHBV	Charles Foster Rats (n=6). MCF-7 cell line	IV, 25 mg/kg bw	HPLC	AUC0-t: 914.9 vs 565 μg/mL*hr; Cmax: 15.53 vs 41.06 μg/mL; Tmax: 72 vs 6 hrs; t1⁄2: 41.8 vs 5.09 hrs; CL: 0.019 vs 0.044 L/hr; Vss: 2.49 vs 0.171 L/hrs	Improved pharmacokinetics: Increased AUC (1.6-fold); prolonged t1/2(8.2-fold); increased Vd (2.3-fold); decreased CL (2.3-fold)	3
	LCG-SNELS vs MCG-SNELS	Rats (n=3) Caco-2 cell line	Oral, 20 mg/kg bw	UPLC	AUC: 9197.7, 7425.8 vs 847.2 ng·hr/mL; Cmax: 1597.2, 612.5 vs 346.9 ng/mL; Tmax: 1.42, 2.74 vs 3.27 hrs	Improved pharmacokinetics: Increased AUC and Cmax of LCG-SNELS loaded drug compared with MCH-SNELS loaded drug and free drug; LCG-SNELS: a preferred drug carrier than MCG-SNELS for better drug delivery to tumor cells.	11
PS-PDLLA	Male Sprague–Dawley (SD) rats (n=3). PC-3 cell line	IV, 1 mg/kg bw	(LC-MS/MS)	AUC: 23.56 vs 10.18 μg·min/mL; t1⁄2: 134.7 vs 57.8 mins; CL: 42.60 vs 99.03 mL/min/kg; Vss: 3260.9 vs 864.3 mL/kg	Improved pharmacokinetics: Increased AUC (2.31-fold); prolonged t1/2 (2.33-fold); decreased CL (due to sustained release and stability of the drug in the serum).	7
Docetaxel	Poly (TMCC-co-LA)-g-PEG	Tumor (MDA-MB-231-H2N) bearing female mice (n=15).	IV, 1.5 mg/kg bw	UPLC-MS	AUC0-8hr: 3.52×103 vs 1.49 x 103 hr.ng/mL; t1⁄2: 5.33 vs 3.32 h; Vd: 2.17×103 vs 4.59×103 mL/kg; CL: 282 vs 958 mL/hr/kg	Improved pharmacokinetics: Decreased Vd (2-fold); prolonged t1/2 (1.6-fold); increased AUC0-8h (2-fold); decreased CL (3-fold)	10
	PLA-TPGS Vs PLGA	Male Sprague–Dawley (SD) rats (n=4)	IV, 10 mg/kg bw	HPLC	AUC0-72hr: 49.9, 28.0 vs 23.4 mg/L*hr; Cmax: 11.0, 10.2 vs 15.9 mg/L; Tmax: 0.5, 0.5 vs 0.5 hr; t1⁄2: 27.9, 4.4 vs 2.1 hrs; Vd: 7.8, 1.6 vs 1.4 L/kg; CL:0.2, 0.3 vs 0.4 L/hr/kg	Improved pharmacokinetics of PLA-TPGS: Increased AUC0-72h (2.13-fold); prolonged t1/2 (13.2-fold); decreased CL; increased Vd	12
	PLGA–PEG Vs PLGA	female BALB/c mice (n=4)	IV, 5 mg/kg bw	Mass spectrometer	AUC: 9221, 6601 vs 1688±373 ng.h/mL; t1⁄2: 15.87, 6.05 vs 4.30 hrs; Vd: 290.41, 150.81 vs 383.57 mL; CL: 12.54, 17.23 vs 61.79 mL/hrs	Improved pharmacokinetics of PLGA-PEG-loaded drug compared with free drug solution and PLGA-loaded drug: Prolonged t1/2 (3.7-fold); increased AUC (5.4-fold); decreased CL (5-fold); decreased Vd (1.3-fold) PEG contributed extended circulation and sustained drug delivery.	2
	Thiolated chitosan	Wistar rats (n=5) Caco-2 cells	Oral, 10 mg/kg bw	HPLC analysis	AUC: 44,998 vs 4243 ng.hr/mL; Cmax: 341 vs 456 ng/mL; Tmax: 5 vs 2 hrs; t1⁄2:102.5 vs 11.7 hrs	Improved pharmacokinetics: Increased oral F, sustained release; Prolonged t1/2 . The improvement of pharmacokinetics could be related to muco-adhesion properties, P-gp efflux inhibition, and permeability-enhancing effects of thiolated chitosan.	6
PLGA–mPEG	Tumor (C26 colon carcinoma) bearing mice (n=6). MCF-7 breast and C26 colon cancer cells	IV, 15 mg/kg bw	HPLC	AUC: (101.0 vs 36.8) μg.hr/mL; Cmax: 16.3 vs 17.5 μg/mL); t1⁄2:7.26 vs 1.93 hrs; CL: 148.4 vs 407.1 mL/hr/kg	Improved pharmacokinetics: increased AUC (2.7-fold), prolonged t1/2 (3.76-fold), and lowered CL (2.7-fold). Sustained release with increased accumulation in tumor cells and enhanced cytotoxicity against colon cancer.	13
Docetaxel	CMS-PEG	Tumor bearing BALB/c mice (n=3) LL/2 lung and EMT-6 mammary carcinoma cell lines.	IV, 40 mg/kg bw	LC/MS	AUC: 881 vs 22.8 µg.hr/mL; Cmax: 27.4 vs 1.6 µg/mL; t1⁄2: 53.8 vs 10.3 hrs; CL: 43.9 vs 1752 mL/hr/kg; Vd: 3418 vs 25,957 mL/kg	Improved pharmacokinetics: Increased AUC (38.6-fold); prolonged t1/2 (5.2-fold); decreased CL (2.5%); decreased Vd (13.2%). Improved cytotoxic efficacy and cellular uptake of the loaded drug in tumor cells.	9
PALA micelles	Male Sprague–Dawley (SD) rats (n=6) human MCF-7 breast cell line.	IV, 2.5 mg/kg bw	HPLC	AUC0–12: 2.67 vs 1.763 μg.hr/mL; t1⁄2: 1.16 vs 0.76 hrs; CL: 0.849 vs 1.151 L/hr/kg	Improved pharmacokinetics: Prolonged t1/2 (1.53-fold); increased AUC (1.51-fold). Increased cytotoxicity against human MCF-7 breast cancer.	5
Doxorubicin	CHGC	Male Sprague–Dawley rats (n=6)	IV, 2 mg/kg bw	HPLC	AUC: 4.403 vs 0.666 mg.hr/L; CL: 0.454 vs 3.005 L/hr/kg	Improved pharmacokinetics: Increased AUC (6.61-fold); decreased CL. Improved pharmacokinetics is due to slow release of the drug from nanoparticle.	20
	PAD–PPI	Tumor-inducing albino rats (n=4) Lung cancer cell (A549)	IV, 5 mg/kg bw	HPLC	AUC: 35.53 vs 11.23 mg. hr/mL; Tmax: 7.27 vs 1.49 hrs; CL: 140.726 vs 444.278 mg hr/mL	Improved pharmacokinetics: Increased AUC (3.2-fold); decreased CL (3.12-fold). Improved cytotoxic effect of drug against cancer cell.	21
	PLGA	Sprague–Dawley rats (n=3)	Oral, 10 mg/kg bw	HPLC	AUC: 5282 vs 1452 ng.hr/mL; Cmax: 154.08 vs 64.68 ng/mL; Tmax: 36 vs 6 hrs	Improved pharmacokinetics: Increased F and Cmax; prolonged t1/2	16
mPEG-b-PCL	Male Sprague–Dawley rats (n=4) MCF-7 and MCF-7/ADR cells	IV, 5 mg/kg bw	Mass spectrometry	AUC0–24: 2268.426 vs 379.92 μg.hr/L; Cmax: 3617.1 vs 1704.6 mg/L; t1⁄2:1.95 vs 0.4 hrs; Vd: 0.006 vs 0.009±0.006 L/kg; CL: 0.002 vs 0.013 L/hr/kg	Improved pharmacokinetics: Increased AUC (5.97-fold); prolonged t1/2 (4.54-fold). Significantly increased cytotoxicity and reduced resistance in MCF-7/ADR cells	14
Doxorubicin	CS-g-TPGS	Female Sprague−Dawley rats (n=4) HepG2, BEL-7402, MCF-7, BEL-7402/5-Fu, and MCF-7/DOX cells	Oral, 10 mg/kg bw	HPLC	AUC: 3.439 vs 1.459 mg.hr/L; Cmax: 0.451 vs 0.390 μg.hr/mL; Tmax: 2 vs 2 hrs; t1⁄2: 10.93 vs 4.33 hrs; CL: 2.899 vs 6.856 L/hr/kg	Improved pharmacokinetics: Increased AUC (2.36-fold); prolonged t1/2 (2.53-fold); decreased CL. Chitosan (CT) nanoparticles shown as suitable carrier in drug-resistant cancer cells and increased cytotoxicity.	15
	Mannosylated- SLNs	Tumor bearing Male Balb/c mice (n=3) A549 and MCF-7 cell lines	IV, 5 mgkg bw	HPLC	AUC: 55.99 vs 11.31 µg.hr/mL; Cmax: 4.0 vs 5.01 µg/mL; t1⁄2:14.53 vs 1.56 hrs; CL: 8.01 vs 43.03 mL/hr	Improved pharmacokinetics: Increased AUC (5-fold); prolonged t1/2 (9.3-fold); decreased CL	17
	CSD-PEG	Male Sprague–Dawley (SD) rats (n=3). SKOV-3 cells	IV, 4 mg/kg bw	HPLC	AUC: 234.42 vs 96.05 μg·min/mL; t1⁄2: 327.86 vs 60.09 mins; CL: 17.35 vs 41.95±4.22 mL/min/kg; Vss: 3153.22 vs 1105.95 mL/kg.	Improved pharmacokinetics: Prolonged t1/2; increased AUC; decreased CL. Promising anticancer activity.	19
Nanodisk	Wistar rats (n=6) MCF-7 and P-gp overexpressing MCF-7/Adr cells	IV, 5 mg/kg bw	UPLC−MS−MS	AUC: 17,452.5 vs 550.8 μg·hr/L; t1⁄2: 41.9 vs 3.5 hrs	Improved pharmacokinetics: Prolonged t1/2 (11.7-fold); increased AUC (31.7-fold). Increased cytotoxicity activity against tumor resistant cells (MCF-7/Adr cells).	18
Estrone (ESC8)	SLN NLC Liposome	Sprague–Dawley rats (n=3) MDA-MB-231 (HTB-26), MDA-MB-468 (HTB-132), BT-474 (HTB-20), and SK-BR-3 (HTB-30)	Oral, 20 mg/kg bw	HPLC	AUC: 17,728.97, 16,047.25, 8991.76 vs 12,357.10 μg.hr/mL; Cmax: 890.62, 792.53, 486.53 vs 534.70 μg/mL; Tmax: 7.32, 7.45, 6.80 vs 8.50 hrs; t1⁄2: 5.08, 5.16, 4.71 vs 5.89 hrs; Vd: 2.07, 2.32, 3.78 vs 8.60 mL; CL: 0.28, 0.31, 0.56 vs 1.01 L/hr	Improved pharmacokinetics: SLN and NLC increased AUC, decreased both CL and Vd. Improved cytotoxicity activity of solid lipid-loaded estrone against triple negative and nontriple negative breast cancer cell lines compared to NLC, liposome nanoparticles and free drug.	30
5-Fluorouracil (5-FU)	PEG-PBLG	Rabbit. Human colon (LoVo) and oral squamous (Tca8113) carcinoma cells	IV, 30 mg/kg bw	HPLC	AUC: 5794.7 vs 6263.8 μg.hr/L; Cmax: 4563.5 vs 17,047.3 μg/L; Tmax: 1.25 vs 0 hr; t1⁄2: 33.3 vs 0.088 hr; Vd: 0.114 vs 0.069 L	Prolonged t1/2; increased distribution time; decreased (slightly) AUC. Significantly improved antitumor activity against colon and oral cancer cells.	24
Gemcitabine	mPEG-PLGA co-polymer	Balb-c mice (n=4) MiaPaCa-2 and MCF-7 carcinoma cell lines	IV, 2 mg/kg bw	LC-MS	AUC: 312.5, 209.5 vs 96.6 ng·hr/mL; t1⁄2: 3.8, 0.4 vs 0.2 hr; CL: 6400.3, 9545.8 vs 20,709.3 mL/hr/kg	Improved pharmacokinetics of PEGylated PLGA loaded drug compared to non-PEGylated PLGA NPs loaded drug and free drug: Increased AUC; prolonged t1/2 (slightly); decreased CL. Increased cytotoxicity against MiaPaCa-2 and MCF-7 cancer cell lines.	28
Methotrexate (MTX)	Glycine-PLGA	Wistar rats (n=3) MDA-MB-231 cells	IV, 5 mg/kg bw	RP-HPLC	AUC: 130.1 (30.9) μg.hr/mL; Vd: 0.52 (0.65) L; t1⁄2: 4.30 (2.47) hrs	Improved pharmacokinetics: Increased AUC (4-fold); Prolonged t1/2 (2-fold); decreased Vd (1-fold) Substantial increase of cytotoxicity against cancer cells.	26
Mifepristone (MIF)	CS	Male rats (n=4) A549, Hela, RL95-2 and HepG2 cancer cells	Oral, 30 mg/kg bw	LC-MS/MS	AUC0-24: 6.3 vs 2.0 mg.hr/L; Cmax: 0.79 vs 0.36 mg/L; Tmax: 5.0 vs 3.4 hrs; t1⁄2: 4.0 vs 3.0 hrs	Improved pharmacokinetics: Improved AUC and Cmax, prolonged t1/2. Chitosan improved cytotoxicity of MIF against cancer cells.	27
Noscapine (NOS)	PCL-PEG	Wistar rats (n=3). MCF-7 cell line	IV, 50 mg/kg bw	HPLC	AUC: 9351.74 vs 7308.96 ng.hr/mL; Cmax: 2055.97 vs 3642.28 ng/mL; t1⁄2: 22.92 vs 5.12 hrs	Improved pharmacokinetics: Increased AUC; prolonged t1/2 (4.47-fold); increased F. Improve cytotoxicity against breast cancer cells	31
Oxaliplatin	FESNS	Male Sprague-Dawley (SD) rats (n=6)	Oral, 10 mg/kg bw	HPLC	AUC: 22,280.4, 17, 585.2 vs 3733.9 ng.hr/mL; Cmax: 8621.8, 4653.0 vs 304.6 ng/mL; Tmax: 1.3, 1.7 vs 1.9 hrs	Improved pharmacokinetics: Increased AUC (4–6 fold); increased F	25
Paclitaxel	PEG2000, PEG6000, PEG10000	Male Wistar rats (n=6)	Oral, 10 mg/kg bw	HPLC	AUC: 56, 32, 13 vs 81 µg.hr/mL; Cmax: 2.1, 1.9, 1.4 vs 204 µg/mL; Tmax: 5.8, 3.0, 3.3 vs 0.01 hr; t1⁄2: 9.3, 6.2, 29 vs 2.6 hrs	PEGylation of nanoparticles with either PEG6000 or PEG2000 as carriers were more adhesive in the GI mucosal than nanoparticles PEGylated with 1000 as they were located at the surface of the absorptive membrane for a long period, and slowly release the loaded drug.	4
	TPGS-PLGA	Sprague–Dawley rats (n=3) C6 glioma cells	IV, 10 mg/kg bw	LC/MS/MS	AUC: 27,200 vs 35,470 ng.hr/mL; t1⁄2: 16.8 vs 0.830 hrs	Decreased AUC (slightly); prolonged t1/2 (20-fold) Greater cytotoxicity activity against C6 glioma cells.	1
PCL–TPGS	Wistar rats (n=5) MCF-7 and MDA-MB 231 human breast cancer cell lines	IV, 6 mg/kg bw	HPLC	AUC: 7.07 vs 2.62 μg.hr/mL; t1⁄2: 10.13 vs 0.87 hrs; CL: 15.86 vs 49.15 mL/min; Vss: 8.89 vs 2.13 L	Improved pharmacokinetics: Increased AUC (2.7-fold); prolonged t1/2 (11.6-fold); Decreased CL (3-fold) Improved anticancer activity against breast cancer cells.	8
Sirolimus	mPEG–PLA	Male Sprague-Dawley (SD) rats (n=3) A549, MCF7, NCI-H460 and MDA-MB-231 cells	IV, 10 mg/kg bw	LC-MS/MS	AUC: 16,901.7 vs 5366.7 µg.hr/mL; Cmax: 11,303.3 vs 2890 µg/mL; Tmax: 0.25 vs 0.25 hrs	Improved pharmacokinetics: Increased AUC (3.15-fold) and Cmax (3.91- fold). High cytotoxic activity against human cancer cells.	32
Temozolomide (TMZ)	PAMAM-CT	Wistar rats (n=6) U-251 and T-98G cells	IP, 3 mg/kg bw	UV-Visible Spectrophotometer	AUC: 4643.94 vs 3820.77 μg.hr/mL; Vd: 0.041 vs 0.0373 L/kg; t1⁄2:22.74 vs 15.348 hrs; CL: 0.00125 vs 0.00168 L/hr/kg	Improved pharmacokinetics: Increased AUC (1.2-fold); prolonged t1/2 (1.5-fold). Improved cytotoxic potential against cancer cells.	33
Anastrozole	PLGA, PLA and PCL	Wistar rats (n=6) breast cancer cell lines (BT-549 and MCF-7)	IV, 1 mg/kg bw	HPLC	AUC: 100.2, 405.7, 416.2 vs 21.0 μg.hr/mL; Cmax: 1.2, 2.0, 4.6 vs 8.3 μg/mL; t1⁄2: 196.12, 322.32, 293.19 vs 9.08 hrs; Vd: 2.8, 1.146, 1.01 vs 0.623 L/kg; CL: 0.009, 0.0024, 0.0023 vs 0.0475 L/hr/kg	Improved pharmacokinetics: Increased AUC (4.77, 19.31, and 19.81-fold, respectively); prolonged t1/2. Dose dependent cytotoxicity activity against breast cancer cells.	29

Abbreviations: Nano carriers: CHGC, cholesterol-modified glycol chitosan; CMS-PEG, PEGylated carboxymethyl cellulose; CS, chitosan; CSD-PEG, chondroitin sulfate A-deoxycholic acid-polyethylene glycol; CS-g-TPGS, chitosan-D-α-tocopheryl polyethylene glycol succinate; CS-PLGA, chitosan-poly(lactic-co-glycolic acid); FESNS, fat employing supercritical nano system; LCG-SNELS, long-chain glyceride-self-nanoemulsifying lipidic nanomicelles systems; MCG-SNELS, medium-chain glyceride-self-nanoemulsifying lipidic nanomicelles systems; mPEG-b-PCL, methoxy poly(ethylene glycol)-b-poly(ε-caprolactone); mPEG-PLA, methoxy poly(ethylene glycol)-b- poly(lactic acid); mPEG-PLGA, methoxy poly(ethylene glycol)-b- poly (lactic-co-glycolic acid); NLC, nanostructured lipid carriers; PAD-PPI, polyaldehydodextran-polypropylene imine; PALA, poly(d,L-lactic acid); PAMAM-CT, polyamidoamine-chitosan; PCL, poly(ε-caprolactone); PCL-PEG, polyethylene glycol-co-poly(ε-caprolactone); PCL-TPGS, Polyethylene glycol-co-D-α-tocopheryl polyethylene glycol succinate; PEG, polyethylene glycol; PEG10000, polyethylene glycol molecular weight 10,000; PEG2000, polyethylene glycol molecular weight 2000; PEG6000, polyethylene glycol molecular weight 6000; PEG-PBLG, poly(ethylene glycol) and poly(γ-benzyl-L-glutamate); PHBV, polyhydroxybutyrate-co-hydroxyvalerate; PLA,poly(lactic acid); PLA-TPGS, poly(lactic acid)-D-alpha-tocopheryl polyethylene glycol 1000 succinate; PLGA, poly (lactic-co-glycolic acid); PLGA-mPEG, poly(lactic-co-glycolic acid)-b-methoxy poly(ethylene glycol); PLGA-PEG, poly(lactic-co-glycolic acid)-poly(ethylene glycol); Poly(TMCC-co-LA)-g-PEG, poly(2-methyl-2-carboxytrimethylene carbonate-co-D,L-lactide)-graft-poly(ethylene glycol); PS-PDLLA, poly (styrene)-b-poly(DL-lactide); SLN, solid lipid nanoparticles; TPGS-PLGA, D-α-tocopheryl polyethylene glycol succinate-poly(lactic-co-glycolic acid). Pharmacokinetic parameters: AUC, area under plasma concentration–time profile; C_max, maximum plasma concentration; CL, total clearance; F, bioavailability; t_max, time to maximum plasma concentration; t_1/2, elimination half-life; V_d, apparent volume of distribution; V_ss, volume of distribution at steady-state.

Table 2.

Summary of the in vivo/clinical pharmacokinetic studies of the nanoparticles of herb-derived compounds for cancer included in the analysis. Data are presented as mean values for nanoformulation vs free compound

Drug-loaded	Nanoparticle	Animal used (number)/cell line	Route, dose	Analytical technique	Pharmacokinetic parameters (mean)	Outcomes	Reference
α -Tocopherol succinate (α -TOS)	Nanoemulsion	Wistar male rats (n=6) MCF-7 cells	IP, 100 mg/kg bw	HPLC.	AUC: 1141.56 vs 637.98 mg.hr/mL; Cmax: 33.84 vs 19.40 mg/mL; Tmax: 5.00 vs 9.00 hrs; t1⁄2: 16.99 vs 7.82 hrs; CL: 0.10 vs 0.18 L/hr	Improved pharmacokinetics: Increased Cmax(1.74-fold); increased AUC (1.79-fold); prolonged t1/2 (2.17-fold); decreased CL (slightly). Improved the anti-cancer activity against cancer cells.	50
Topotecan (Topo)	PLGA	Swiss albino mice (n=6) SKOV3 cells	IV, 10 mg/kg bw	LC-MS	AUC: 35,667.5 vs 7479.75 ng hr/mL; Cmax: 1326 vs 2100 ng/mL; Tmax: 3 vs 0.5 hr	Improved pharmacokinetics: Increased F (13.05-fold). Enhanced cytotoxicity effect against cancer cells.	42
Protopana-xadiol (PPD) Contain ginsenosides, derived from Araliaceae	Cubosomes	Male rats (n=6)	Oral, 2 mg/kg bw	Mass spectrometry	AUC: 43.37 vs 25.76 mg.min/L; Cmax: 1004 vs 73.45 ng/mL; Tmax: 125 vs 85 mins; t1⁄2:372.59 vs 324.01 mins; CL: 0.068 vs 0.071 L/min/kg	Improved oral bioavailability and prolonged t1/2 (slightly).	45
Hydroxy-camptothecin (HCPT)	PEG-PBLG	New Zealand rabbits (n=3)	IV, 12 mg/kg bw	HPLC	AUC: 2175.9 vs 2459.0 µg.hr/L; Cmax: 1513.5 vs 2627.8 µg/L; Tmax: 1 vs 0 hr; t1⁄2:10.1 vs 4.5 hrs; Vd: 20 vs 7.3 L	Improved pharmacokinetics: Decreased Cmax and AUC; increased Vd; increased t1/2.	41
10-Hydroxy-camptothecin (10-HCPT)	Nanocrystals	Sprague–Dawley rats (n=10)	IV, 5 mg/kg bw	HPLC	AUC: 4867.7 vs 1735.9 ng.hr/mL; CL: 10.65 vs 484.99 mL/hr; t1⁄2: 1.85 vs 0.62 hrs	Improved pharmacokinetics: Increased AUC (2.98-fold); prolonged t1/2 (2.81-fold); decreased CL (45.5-fold). Effective drug delivery for HCPT.	40
Genistein (Gen)	mPEG-PCL/MCTs	Male Sprague–Dawley rats (n=5)	IV, 10 mg/kg bw	UPLC-QTOF/MS	AUC0-t: 8.48 vs 2.97 µM*hr; t1⁄2: 9.96 vs 2.15 hrs; CL: 0.73 vs 2.94 L/hrs	Improved pharmacokinetics of Gen containing micellar emulsions as nanocarriers: Increased AUC (4.6-fold); prolonged t1/2 (2.86-fold); decreased CL	49
Curcumin	PC-SNEDDS	Male Sprague–Dawley rats (n=3). MDA-MB-231 breast cancer cell line	Oral, 100 mg/kg bw	LC-MS/MS	AUC: 2196.9 vs 41.8 ng.hr/L; Cmax: 487.7 vs 21.6 ng/mL; Tmax: 1.0 vs 1.0 hr; t1⁄2: 21.0 vs 4.1 hrs; CL: 46.0 vs 2421.7 L/hr/kg; Vd: 144.5 vs 5607.3 L/kg	Improved pharmacokinetics: Increased AUC (52-fold); prolongedt1/2 (5-fold); decreased CL (50-fold); decreased Vd (38.8-fold).	34
	Lipid nanocapsules	Rats (n=3). Rat 9L glioma cells	IV, 10 mg/kg bw	LC-MS/MS	AUC: 72.98 vs 18.77 μg.hr/mL; Cmax: 70.05 vs 13.05 μg/mL; t1⁄2: 3.25 vs 1.15 hrs; CL: 0.04 vs 0.13 μg/mL/hr	Improved pharmacokinetics: Increased AUC (3.9-fold) and Cmax (5.3-fold); decreased CL.	36
	Cationic Copolymer (EE100)	Albino Wistar rats (n=6) Colorectal cancer cells (Colon-26)	Oral, 50 mg/kg bw	HPLC	AUC: 2199.116 vs 23.225 ng.hr/mL; Cmax: 870.3104 vs 9.582 ng/mL; Tmax: 0.5 vs 0.5 hr; t1⁄2: 4.811 vs 1.25 hrs	Improved pharmacokinetics: Increased oral bioavailability. Improved cytotoxicity against colorectal cancer cells.	35
	mPEG-PCL	Wistar rats (n=6). Hela and HT-29 cells	IV, 15 mg/kg bw	HPLC	AUC: 4464.601 vs 967.221 μg.hr/L; Vd: 6.271 vs 4.432 L/kg; CL: 3.36 vs 15.508 L/hr/kg; t1⁄2:1.294 vs 0.198 hrs	Improved pharmacokinetics: Increased AUC; prolonged t1/2; increased Vd; decreased CL.	38
PDLLA-G	Male Sprague–Dawley (SD) rats (n=3). MDA-MB-231 cells	IV, 12 mg/kg bw	LC–MS/MS	AUC: 1810.09 vs 1.79 μg.min/mL; t1⁄2: 85.7 vs 6.62 h; CL: 6.87 vs 6817.94 mL/min/kg; Vss: 123.56 vs 62,061.86 mL/kg	Improved pharmacokinetics: Increased AUC; prolonged t1/2.	39
Curcumin and Rutin	Chitosan	Rabbits (n=3)	Oral, 35 mg each	RP-UFLC	AUC: 4322.37, 1219.80, 7621.79 vs 1146.73 ng.h/mL; Cmax: 971.72, 317.97, 1113.55 vs 262.85 ng/mL; Tmax: 1 hr for all; t1⁄2: 2.62, 1.78, 3.357 vs 1.74 hrs	Improved pharmacokinetics: Increased AUC of curcumin (3.5-fold) and rutin (6.65-fold); increased Cmax of curcumin (3.06-fold) and rutin(4.24-fold).	37
Brucea javanicaoil (BJO) is from Brucea javanica of the family Simaroubaceae	Cationic nanoemulsion	Male Sprague–Dawley (SD) rats (n=6). Human lung adenocarcinoma line A549 cells xenografts in nude mice.	Oral, 505 mg/kg bw	UPLC-MS/MS	AUC: 1203.4 vs 982.5 mg·hrs/L; Cmax: 210.2 vs 164.2 mg/L; Tmax: 3.5 vs 3.0 hrs; t1⁄2: 4.5 vs 3.3 hrs	Improved pharmacokinetics: Increased AUC and t1/2 (1.6- and 1.3-fold, respectively). Reduced growth of lung cancer and decreased the frequency of dosing.	48
Camptothecin (CPT)	SLN	BALB/c mice (n=4). Caco-2, HT-29, HepG2 and MCF-7 cell lines.	Oral, 30 mg/kg bw	HPLC	AUC: 17.19 vs 7.22 μg.hr/L; Cmax: 3.28 vs 0.69 μg/mL	Improved pharmacokinetics: Increased AUC and Cmax (2.38- and 4.75-fold, respectively). Higher cytotoxicity against all four cell lines.	43
Celastrol (CST) Isolated from Trypterygium wilfordii hook	Phytosomes	Rabbits (n=6)	Oral, 40 mg/kg bw	HPLC	AUC: 767.51 vs 186.84 ng.hr/mL; Cmax: 460 vs 92 ng/mL; Tmax: 0.5 vs 1 hr; t1⁄2: 10.1 vs 0.96 hrs	Improved pharmacokinetics: Increased Cmax and AUC; prolonged t1/2. The phospholipid component of phytosomes enhanced the fluidity of cell membrane, solubility, and intestinal absorption.	47
Amoitone B Cytosporone B (Csn-B) analog, derived from Dothiorella sp. HTF3.	Nanocrystals	New Zealand white rabbits (n=4)	IV, 8.0 mg/kg bw	HPLC	AUC: 4.902 vs 3.439 mg.hr/L; t1⁄2: 8.446 vs 2.999 hrs; CL: 1.632 vs 2.327 L/hr/kg; Vd: 0.626 vs 0.283 L/kg	Improved pharmacokinetics: Increased AUC (1.4-fold); prolonged t1/2 (2.8-fold); decreased CL; increased Vd (slightly).	44
Biochanin A (BCA) From red clover	PEG–NLC	Female Sprague–Dawley (SD) rats (n=6) Human breast cancer cell line (MCF-7)	Oral, 4 mg/kg bw	HPLC	AUC: 590.01 vs 203.71 ng.hr/mL; Cmax: 165.82 vs 10.53 ng/mL; Tmax: 0.50 vs 0.33 hr	Improved pharmacokinetics: Increased AUC (2.9-fold) and Cmax Increased cytotoxicity in MCF-7 cells.	46

Abbreviations: Nanocarriers: mPEG-PCL/MCTs, methoxy poly(ethylene glycol)-b-poly(ε-caprolactone) and medium-chain triglycerides; mPEG-PCL, methoxy poly(ethylene glycol)-b-poly(ε -caprolactone); PCL, poly(ε-caprolactone); PC-SNEDDS, phospholipid complexes and self-nano-emulsifying drug delivery system; PDLLA-G, poly(D,L-lactic acid)-glycerol; PDLLA-G, poly(D,L-lactic acid)-glycerol; PEG-NLC, poly(ethylene glycol)-nanostructured lipid carriers; PEG-PBLG, poly(ethylene-glycol)-poly(gamma-benzyl-L-glutamate); PLA, poly(lactic acid); PLGA, poly(lactic-co-glycolic acid); SLN, solid lipid nanoparticles. Pharmacokinetic parameters: AUC, area under plasma concentration–time profile; C_max, maximum plasma concentration; CL, total clearance; F, bioavailability; t_max, time to maximum plasma concentration; t_1/2, elimination half-life; V_d, apparent volume of distribution; V_ss, volume of distribution at steady-state.

Pharmacokinetic studies for nanoparticle-loaded chemotherapeutic drugs

Taxanes

Paclitaxel (PTX)^1,4 and docetaxel (DTX)^2,3,5,6 are semisynthetic anticancer drugs derived from the plants of the genus Taxus (yews). The anticancer activity of taxanes involves disruption of the mitotic spindle by binding to microtubules and thereby inhibiting the depolymerization of the microtubules, leading to mitotic arrest at the G2/M phase of the cell cycle.^1–4,6,7 PTX and DTX display anticancer activity and have been used in the treatment of various cancers especially breast,^2–4,6–11 ovarian,^{1–4,6–8,11} lung,^{1–4,6,7,9,11} head and neck,^1,2,6,11 colon,^1,4 bladder,^1,2 prostate,^2,7,11 and gastric^2,3 cancers, esophageal, endometrium carcinoma,² hepatocarcinoma,¹² acute leukemia,¹ and Kaposi’s sarcoma.⁴ The clinical application of currently available taxanes meets some challenges including poor water solubility, high protein binding, first-pass metabolism, high affinity to P-glycoprotein (P-gp), and some serious side effects. The toxicity such as hypersensitivity, neuropathy, neurotoxicity, and cardiotoxicity is caused by the formulation excipients, ie, Tween 80, cremophor EL, and ethanol to increase its solubility. These excipients not only contribute to toxicity but also alter the pharmacokinetics of both drugs. One of the strategies proposed to address the problem of toxicity and poor pharmacokinetic properties with these drugs is the use of a novel drug delivery system such as nanoparticles. A wide range of biocompatible, biodegradable, and nontoxic polymeric nanoparticles were employed to improve the pharmacokinetic profiles of DTX and PTX to increase the plasma drug concentrations and solubility, and intracellular accumulation to tumors cells via enhanced permeability and retention (EPR) effect.^{1–4,6–9,11,12}

DTX encapsulated with pegylated carboxymethylcellulose (PEG-CMS) was evaluated against tumor-bearing Bagg Albino (BALB/c) mice at 40 mg/kg body weight injected via the tail vein. This nanoparticle provided improved pharmacokinetics of DTX (38-fold increase in AUC, 5.2-fold prolongation of t_1/2, 2.5% decrease in CL, and 13.2% decrease in V_d) compared with the free drug.⁹ This resulted in the increase of drug uptake to tumor cells in EMT-6 tumor-bearing mice with reduced toxicity. Similar findings were observed with poly (2-methyl, 2-carboxytrimethylene carbonate-co-D, L-lactide)-g-poly(ethylene glycol) (TMCCco-LA)-g-PEG nanoparticle delivering DTX, and free DTX. Improved drug plasma concentration in tumor-bearing mice was found with the increase of AUC (2-fold), prolongation of t_1/2 (1.6-fold), and decrease of both Vd (2-fold) and CL (3-fold). These changes likely contributed to the favorable pharmacokinetic profile and tumor accumulation of DTX.¹⁰ Likewise, poly(lactide-co-glycolide)-monomethoxy-poly-(polyethylene glycol) (PLGA-mPEG)-loaded DTX was shown to provide sustained release of DTX and increase the accumulation of the drug in tumor cells of mice and thus, enhancement of cytotoxic activity.¹³ The change in the pharmacokinetics of DTX with increase of AUC (2.7-fold), prolongation of t_1/2 (3.76-fold), and decrease of CL (2.7-fold) was brought by the addition of PEG to the PLGA nanoparticle which contributed to increased blood circulation, decreased drug-protein binding, and reduced elimination of loaded drug by reticuloendothelial system (RES) organs such as liver and spleen.

Formulations of DTX using PLA-TPGS, PS-PDLLA, and PALA polymeric nanoparticles were found to improve the pharmacokinetics of DTX in Sprague–Dawley (SD) rats.^5,7,12 The AUC was increased (1.5-2.31-fold), and the t_1/2 was prolonged (1.53-13.2-fold) with a significant reduction of drug CL. The improved bioavailability of PLA-TPGS nanoparticle-loaded DTX due to an inhibitory effect on P-gp resulted in enhancing cellular uptake of the drug to cancer cells and overcoming multidrug resistance. The decrease in clearance of the loaded drug was due to sustained release and stability of the drug in the serum. Another study evaluated the pharmacokinetics of PEGylated PLGA nanoparticle-loaded DTX in tumor-bearing mice. The pharmacokinetics of DTX was found to be improved with an increase in AUC (5.4-fold), prolongation of t_1/2 (3.7-fold), and decrease of CL (5-fold) and V_d (1.3-fold).²

Lipid-based nanocarriers such as self-nano emulsifying lipidic nanomicellar systems (SNELS) were also used to deliver DTX. Both long-chain and medium-chain glycerides were applied to enhance oral drug bioavailability.¹¹ The nanocarriers of long-chain glycerides enriched with SNELS delivering DTX were shown to markedly increase the AUC and C_max of DTX compared with the medium-chain glyceride SNELS. The superiority of the long-chain carrier was mainly due to inhibition of P-gp efflux, together with the increase of intestinal lymphatic transport of drug with reduction of the first-pass metabolism. Finally, poly(hydroxybutyrate-co-hydroxyvalerate) (PHBV) delivering DTX was shown to improve the pharmacokinetics of DTX resulting in the increase of AUC (1.6-fold), the prolongation of t_1/2 (8.2-fold), the expansion of V_d (2.3-fold), and the reduction of CL (2.3-fold).³ Similarly, DTX incorporated into thiolated chitosan provided higher oral drug bioavailability, sustained release, and longer t_1/2 compared to the unloaded drug.⁶ The 10.6-fold increase of mean AUC of DTX when loaded with thiolated chitosan could be related to its muco-adhesion properties on the gastrointestinal tract.

In contrast to DTX, improvement of drug bioavailability was not demonstrated with PTX when encapsulated with PEG with different molecular weights (2000, 6000, and 10,000)⁴ and PLGA-TPGS,¹ but t_1/2 was mostly prolonged. PEGylation of nanoparticles with either PEG6000 or PEG2000 as carriers was more adhesive in the gastrointestinal mucosa than PEGy1000. Both were located at the surface of the absorptive membrane for an extended period, and the loaded drug was slowly released. When PTX was loaded with PCL-TPGS on the other hand, the AUC was increased by 2.7-fold, the t_1/2 was significantly increased, while the CL was significantly decreased (3-fold).⁸

Anthracycline antibiotics

The anthracycline antibiotics doxorubicin (DOX) and daunorubicin (DNR) are broadly used for the treatment of a variety of cancers. They exert their action on cancer cells by intercalation into DNA base pairs resulting in blockage of DNA and RNA synthesis and DNA scission, which suppresses the replication of DNA and induces cell apoptosis.¹⁴ The pharmacokinetic study in male SD rats showed that entrapment of DOX in polymersomes resulted in the prolongation of drug t_1/2 by 4.54-fold, and the increase in AUC by 5.97-fold compared with free drug. These pharmacokinetic changes significantly enhanced cytotoxicity and reduced resistance of MCF-7/ADR cells to DOX.¹⁴ An improved pharmacokinetic profile of DOX and its cytotoxicity were also reported when loaded in chitosan-g-TPGS (CT). This makes CT a suitable carrier in drug-resistant cancer cells.¹⁵ In another in vivo study using DOX loaded in PLGA administered to SD, the formulation provided relatively well-sustained plasma concentration, enhanced AUC, and significantly delayed T_max (36 hrs) when compared to free DTX.¹⁶ Furthermore, improved pharmacokinetics and antitumor activity of the mannosylated solid lipid nanoparticles delivering DOX were demonstrated in Balb/c mice compared with free drug. The approximately 9.31-fold increase of t_1/2 and the 5-fold increase of AUC suggested that mannosylated solid lipid nanoparticles could selectively deliver DOX to tumor cells.¹⁷

A nanodisk formulation of DOX was reported to provide larger AUC, longer t_1/2, and higher cytotoxicity in MCF-7/ADR cells compared with free drug.¹⁸ Additionally, DOX encapsulated into the chondroitin sulfate A-deoxycholic acid-polyethylene glycol (CSD-PEG) also showed similar improvement in pharmacokinetics and stability of DOX in blood.¹⁹ Cholesterol-modified glycol chitosan (CHGC) delivering DOX improved F of about 6.61 times higher than the free drug. The improved pharmacokinetics could be due to the slow release of the drug from the nanoparticle, which contributed to higher uptake by the cancer cells.²⁰ Dextran-conjugated with polypropylene imine (PAD-PPI) delivering DOX was reported to increase AUC and decrease CL by 3.2-fold and 3.12-fold, respectively, compared with free drug. This nanoparticle resulted in the improved cytotoxic effect of DOX to the tumor cells.²¹

For DNR, the increase in C_max (1.86-fold), AUC (11.29-fold), T_max (2-fold), and prolongation of t½ (2.8-fold) compared with free MTX was reported in Wistar rats after oral administration of the drug incorporated with chitosan-poly(lactic-co-glycolic acid) (CS-PLGA) nanoparticle.²² This was due to the potential of the nanoparticle to avoid P-gp-mediated-drug efflux and hepatic first-pass metabolism by cytochrome P450 (CYP450) enzymes. On the other hand, improvement of the pharmacokinetics of DNR conjugated into lecithmer was not well demonstrated in Wistar rats.²³ Drug-loaded nanoparticle exhibited an increase in V_d (1.42-fold) and a decrease in AUC (1.3-fold) compared with free drug. The larger V_d of DNR-loaded lecithmer was associated with rapid tissue distribution and uptake of the drug by the RES organs.

Other anticancer drugs

5-Fluorouracil (5-FU), a pyrimidine analog for various types of solid tumors, is a prodrug which covalently binds to thymidylate synthase and interferes with thymidylate synthesis, resulting in inhibition of synthesis of both DNA and RNA. In rabbits, a dose of 30 mg/kg of 5-FU (30 mg/kg body weight) loaded into poly-ethylene glycol and poly (γ-benzyl-L-glutamate) (PEG-PBLG) was reported to result in lower F with slightly favorable t_1/2 compared with the non-conjugated drug. The PEG-PBLG nanoparticle significantly improved antitumor activity against human colon and oral cancer cells.²⁴

The bioavailability of the platinum-based oxaliplatin (OLP) containing Fat Employing Supercritical Nano System (FESNS) as nanoparticle was shown to be improved compared with free OLP formulation.²⁵ Furthermore, improvement in the pharmacokinetic profile of methotrexate (MTX) was reported when loaded in glycine-PLGA nanoparticle with an increase in AUC (4-fold), the prolongation of t_1/2 (1.74-fold), and the reduction of V_d (1-fold).²⁶ The nanoparticle substantially increased the cytotoxicity of MTX against MDA-MB-231 cancer cells. Different nanoparticles were shown to improve pharmacokinetics, particularly oral bioavailability of mifepristone, gemcitabine, anastrozole, and estrone. Improved bioavailability and cytotoxicity against cancer cells of mifepristone were shown when encapsulated with chitosan.²⁷ Improved bioavailability, reduced CL, and prolonged t_1/2 were reported with PLGA nanoparticle-loaded gemcitabine, resulting in enhanced cytotoxicity against MiaPaCa-2 and MCF-7 cells.²⁸ The pharmacokinetic profiles and cytotoxic activity of anastrozole, the aromatase inhibitor used in postmenopausal breast cancer, were shown to be significantly improved when encapsulated in PLGA, PLA, and PCL polymers.²⁹ Estrone was formulated with solid lipid nanoparticles (SLN), nanostructured lipid carriers (NLC), and liposomes. Mean AUC values of the drug were greatly increased with SLN (17,728 μg/mL*h²) and NLC (16,047 μg/mL*h²), but slightly decreased with liposomes (8991 μg/mL*h²) compared with free estrone (12,357 μg/mL*h²). Both CL and V_d were decreased. SLN emerges as a promising carrier of estrone to cancer cells.³⁰ Noscapine, a derivative of alkaloid opium with anti-tubulin action, is currently under investigation for cancer. Poly(ethylene glycol)-co-poly(ε-caprolactone) (PCL-PEG) nanoparticle delivering noscapine was evaluated in Wistar rats, and drug bioavailability and t_1/2 were shown to be increased along with the improvement of cytotoxicity against breast cancer cells.³¹ The pharmacokinetic profile of polymeric nanoparticle containing polyethylene glycol-poly-l-lactic acid (mPEG–PLA) delivering sirolimus, an mTOR inhibitor, was significantly improved with the increase of AUC (3-fold) and C_max (3.91-fold) compared with free sirolimus.³² The nanoparticle improved the cytotoxic activity of sirolimus against human cancer cell lines. In another study of polyamidoamine-chitosan (PCT) carrying temozolomide, promising pharmacokinetic profiles were reported with improved AUC (1.2-fold) and prolonged t_1/2 (1.5-fold) compared with free drug.³³

Pharmacokinetic studies for nanoparticles loaded herb-derived compounds in traditional or herbal medicines

Various nanoparticles were developed for the selective delivery of active compounds from traditional or herbal medicines to cancer cells. Curcumin, a molecule found in various spices, notably turmeric, has been used for the treatment of various types of cancer particularly breast, stomach, intestine, colorectal, prostate, ovarian, and melanoma.^34,35 Curcumin exerts its anticancer activity by regulating signaling pathways such as Akt/mTOR, NF-κB, and HIF-1α which are important for cell proliferation and apoptosis.^34,36 Compared with free drug, the AUC and t_1/2 of curcumin-loaded in phospholipid complex in self-nano-emulsifying drug delivery system (SNEDDS) were increased by 52-fold and 5-fold, respectively. The V_d and CL were decreased by 38.8-fold and 50-fold, respectively. The improved oral bioavailability of curcumin resulted in improved luminal solubility. The higher release rate in the intestinal fluids improved absorption by enhancing compound permeability and avoiding hepatic first-pass metabolism.³⁴ The significant improvement in the oral bioavailability of curcumin was reported when encapsulated into cationic polymer EE100 with increased cytotoxic activity against colorectal cancer.³⁵

The mean AUC values of chitosan-loaded curcumin, chitosan-loaded rutin, free curcumin, and free rutin were 4322, 7621, 1219, and 1146 ng/mL, respectively. Chitosan nanoparticle loading resulted in the improvement of bioavailability of curcumin and rutin by 3.5-fold and 6.65-fold, respectively, compared with free compounds.³⁷ Similarly, another study in rats showed that lipid nanocapsules (LNC) efficiently delivered curcumin into tumor cells and improved its pharmacokinetics.³⁶ The AUC and C_max were increased by 3.9-fold and 5.3-fold, respectively, while the CL was decreased by 3-fold. These results suggested that LNC could be used for the delivery of traditional medicines to cancer cells. The methoxy poly(ethylene glycol)-b-poly(ε-caprolactone) (mPEG-PCL) micelles could extend the plasma concentration and delay the clearance of curcumin.³⁸ The bioavailability and t_1/2 of curcumin were greatly improved when loaded with Poly (D, L-lactic acid)-glycerol (PDLLA-G) when compared with free curcumin.³⁹

Camptothecins constitute a class of anticancer alkaloid traditionally from Chinese medicine that possesses potential anticancer activity against colon, breast, colorectal, stomach, liver, leukemia, and ovarian cancers. Their mechanism of action involves inhibition of tumor-specific topoisomerase I, a critical enzyme responsible for cutting and re-ligating single DNA strands, which results in DNA damage.^40–43 The pharmacokinetic profile and anticancer activity of nanocrystals and PEG-PBLG loaded into hydroxycamptothecin (HCPT) were evaluated in rats and rabbits.^40,41 Nanocrystals improved the pharmacokinetics of HCPT with an increase of AUC (2.98-fold), the prolongation of t_1/2 (2.81-fold), and the decrease of V_d (45.5-fold) compared with free HCPT. The nanocrystals emerged as an effective drug delivery system for HCPT.⁴⁰ On the other hand, another study in rabbits reported a decrease in C_max and bioavailability of HCPT when loaded in PEG-PBLG compared with free drug. The nanoparticle provided sustained release and prolongation of t_1/2.⁴¹ Topotecan, a topoisomerase inhibitor which is a synthetic analog of camptothecin, was shown to enhance intracellular uptake and result in a 13-fold increase in bioavailability of topotecan-loaded PLGA compared with free topotecan.⁴² The increased bioavailability was associated with enhanced cytotoxic activity against SKOV3 cancer cells. Similarly, the bioavailability of the solid lipid nanoparticles (SLN) delivering camptothecin (CPT) was shown to be improved by 2.38-fold.⁴³

Amoitone B is a cytosporone B (Csn-B) analog obtained from Dothiorella sp. HTF3. It exhibits anticancer activity by tightly binding to a nuclear orphan receptor (Nur77) and induces mitochondrial apoptosis. When Amoitone B was loaded into nanocrystals (NC-Am), the bioavailability was increased by 1.4-fold and the t_1/2 was prolonged by 2.8-fold. The nanocrystals improved solubility and reduced toxicity of Amoitone B.⁴⁴ Further, cubic nanoparticles improved oral bioavailability and anticancer activity of protopanaxadiol (PPD).⁴⁵ PPD which contains ginsenosides derived from the Araliaceae family was proved to exhibit potential anticancer activity. In another study, biochanin A (BCA), the compound from a phytoestrogenic plant of red clover, was found to exhibit estrogenic activity and cytotoxic activity against human breast cancer cells. The bioavailability of PEG-NLC-loaded BCA was increased by about 2.9-fold after oral administration to rats compared with BCA suspension. This subsequently improved the cytotoxic activity of BCA against MCF-7 cells.⁴⁶ The bioavailability of celastrol was increased by 4.11-fold, and the t_1/2 was prolonged by 10-fold when loaded with phytosomes compared with celastrol suspension.⁴⁷ This suggested that the phospholipid component of phytosomes enhanced the fluidity of cell membrane, solubility, and intestinal absorption.

Cationic nanoemulsions (CN) containing chitosan delivering Brucea javanicaoil (BJO) resulted in higher cytotoxicity and antitumor activity in a xenografted mouse model (A549 cells). The AUC of BJO-CN was increased by 1.6-fold, and the t_1/2 was prolonged by 1.3-fold compared with BJO emulsion. CN has been demonstrated as a promising drug delivery system and has the potential to reduce the required frequency of BJO dosing.⁴⁸ Genistein (Gen), an active compound found in soybeans, exerted its anticancer activity by inducing apoptosis through inhibiting tyrosine kinases and NF-κB. Micellar emulsions containing methoxy poly (ethylene glycol)-block-(ε-caprolactone) and medium-chain triglycerides (mPEG -PCL/MCTs) as nanocarriers delivering Gen prolonged t_1/2 (2.86-fold) reduced CL (10.13-fold) and improved AUC (4.6-fold).⁴⁹ Similarly, α-tocopherol succinate-loaded in nano-emulsion increased AUC (2.17-fold) and prolonged t_1/2 (2.17-fold) compared with free α –TOS.⁵⁰ The nano-emulsion proved to be a promising drug delivery system for cancer cells.

Conclusion

It is evident that the pharmacokinetic profiles of conventional chemotherapeutic drugs as well as traditional/herbal medicines used for cancer treatment are significantly improved when loaded with nanoparticles. The main benefits of using nanoparticles for drug delivery are enhancement of vascular and gastrointestinal permeability and selectivity of drugs/compound to tumor cells. The improved permeability and selectivity resulted in the improvement of cellular drug uptake, the inhibition of drug hepatic first-pass metabolism and P-gp efflux, the increase in drug solubility and stability, and the decrease in the rate of drug elimination by the RES organs. Subsequent reduction of dose frequency further contributes to the improvement of patient compliance and minimizes toxicity. It is noted however that the physicochemical properties of the chemotherapeutic drugs or herb-derived compounds play a crucial rule in designing effective and appropriate nanocarriers. The use of nanoparticles as a novel drug delivery system for cancer therapy has the potential to dramatically improve both pharmacokinetics and cytotoxicity activity of the loaded drugs/herb-derived compounds for cancer therapy.

Abbreviations list

MCF-7/ADR, Michigan Cancer Foundation-7-Adriamycin resistant; MDA-MB-231, M.D. Anderson-Metastasis Breast cancer; Akt/mTOR, protein kinase B/mammalian target of rapamycin; NF-κB, nuclear factor kappa-light-chain-enhancer of activated B cells; HIF-1α, Hypoxia-inducible factor 1-alpha.

Disclosure

The authors report no conflicts of interest in this work.