In vitro and in vivo evaluation of docetaxel-loaded stearic acid-modified Bletilla striata polysaccharide copolymer micelles
In vitro and in vivo evaluation of docetaxel- loaded stearic acid-modified Bletilla striata polysaccharide copolymer micelles
Qingxiang Guan 0 1 2
Guangyuan Zhang 0 1 2
Dandan Sun 0 1 2
Yue Wang 0 2
Kun Liu 0 1 2
Miao Wang 0 1 2
Cheng Sun 0 1 2
Zhuo Zhang 0 2
Bingjin Li 0 2 4
Jiayin Lv 0 2
0 Funding: The research was supported by Graduate Innovation Fund of Jilin University (2016225); Jilin Science and Technology Agency funding , 20140307018YY; 20140414040GH
1 School of Pharmacy, Jilin University , Changchun , China , 2 Faculty of Chemistry, Northeast Normal University , Changchun, China, 3 China- Japan Union Hospital of Jilin University , Changchun , China
2 Editor: Lei Li , Xi
3 an Jiaotong University , CHINA
4 The Second Hospital of Jilin University , Changchun , China
Bletilla striata polysaccharides (BSPs) have been used in pharmaceutical and biomedical industry, the aim of the present study was to explore a BSPs amphiphilic derivative to overcome its application limit as poorly water-soluble drug carriers due to water-soluble polymers. Stearic acid (SA) was selected as a hydrophobic block to modify B. striata polysaccharides (SA-BSPs). Docetaxel (DTX)-loaded SA-BSPs (DTX-SA-BSPs) copolymer micelles were prepared and characterized. The DTX release percentage in vitro and DTX concentration in vivo was carried out by using high performance liquid chromatography. HepG2 and HeLa cells were subjected to MTT (3-(4, 5-dimethylthiazol-2-yl)-2, 5-diphenyl tetrazonium bromide) assay to evaluate the cell viability. In vitro evaluation of copolymer micelles showed higher drug encapsulation and loading capacity. The release percentage of DTX from DTX-SA-BSPs copolymer micelles and docetaxel injection was 66.93 ± 1.79% and 97.06 ± 1.56% in 2 days, respectively. The DTX-SA-BSPs copolymer micelles exhibited a sustained release of DTX. A 50% increase in growth inhibition was observed for HepG2 cells treated with DTX-SA-BSPs copolymer micelles as compared to those treated with docetaxel injection for 72 h. DTX-SA-BSPs copolymer micelles presented a similar growth inhibition effect on Hela cells. Furthermore, absolute bioavailability of DTX-SA-BSPs copolymer micelles was shown to be 1.39-fold higher than that of docetaxel injection. Therefore, SABSPs copolymer micelles may be used as potential biocompatible polymers for cancer chemotherapy.
Data Availability Statement: All relevant data are
within the paper.
Competing interests: The authors have declared
that no competing interests exist.
Self-assembled copolymer micelles consisting of amphiphilic block copolymer in aqueous
medium are receiving considerable attention as gene and drug nanocarriers because of their
particular characteristics [1±3]. Micelles always have a unique coreÐshell backbone
composed of a hydrophilic shell and a hydrophobic core [
]. Hydrophobic drugs can be
incorporated into the hydrophobic core of copolymer micelles, whereas the hydrophilic shell
can stabilize and protect the drug in the aqueous medium. Furthermore, the hydrophilic
shell can prolong the blood circulation time of micelles as a result of steric stabilization,
which helps micelles escape mononuclear phagocyte system uptake after intravenous
]. These self-assemblies have potential uses in medicine and biotechnology
because of their unique coreÐshell backbone, various amphiphilic block copolymers have
been synthesized and their characteristics have been investigated widely[
many efforts have been performed to prepare non-toxic and biocompatibility amphiphilic
block copolymers on the basis of natural polysaccharides.
The water soluble polysaccharides(dextran, pullulan and heparin) have been modified to
obtain the amphiphilic polymers by including the hydrophobic groups, such as alkyl, aralkyl,
and deoxycholic [
]. The amphiphilic polymers were liable to self-aggregated copolymer
micelles because of inter and/or intra molecular hydrophobic interactions in water medium
]. The amphiphilic polymers have been used with various targeting ligands, such as
antibodies, peptides and anti-cancer drugs, greatly improving the precision of drug targeting to
the tumor cells via endocytosis mechanisms [
Bletilla striata (Thunb.) Reichb.f. polysaccharides (BSPs), the major active ingredients of B.
striata, were extracted from the tubers, and are composed of (1!2)-α-D-mannopyranose and
(1!4)-β-D-glucose, as characterized by nuclear magnetic resonance spectroscopy . BSPs
have been used in pharmaceutical and biomedical industry because of their negligible
cytotoxic effects and properties, such as biocompatibility and biodegradability [17±19]. Therefore,
BSPs may be potential candidates for various pharmaceutical applications, such as drug
delivery system [
]. The BSPs have shown to inhibit the hepatocellular carcinoma growth after
transarterial chemoembolization [
]. The 5-fluorouracil B. striata microspheres were
characterized with long-term high efficacy and low toxicity compared to 5-fluorouracil injection
]. However, BSPs are water-soluble polymers which limit its use as a poorly water-soluble
drug carrier. To solve this problem, alkyl, aralkyl, and deoxycholic acid were used to modify
water-soluble copolymer to improve its hydrophobic property .
In the present study, stearic acid-modified B. striata polysaccharide (SA-BSPs) copolymers
were synthesized by covalent attachment of stearic acid to polysaccharides and amphiphilic
polymers with possible application in pharmaceutical industry were obtained. The chemical
structure of the SA-BSPs is presented in Fig 1A. The SA-BSPs were characterized by using
Fourier transform infrared (FTIR) spectroscopy, 1H nuclear magnetic resonance (1H-NMR)
spectroscopy, and critical aggregation concentrations (CAC) techniques. Docetaxel was
selected for the preparation of DTX-SA-BSPs copolymer micelles. Polydispersity index,
particle diameter, zeta potential, drug loading capacity (LC), encapsulation efficiency (EE), drug
release in vitro and absolute bioavailability in vivo were also presented. Further, the antitumor
activity of DTX-SA-BSPs and SA-BSPs copolymer micelles was measured in vitro using Hela
human cervical cancer cells and HepG2 human liver cancer cells.
Materials and methods
Docetaxel injection (Duopafei1) was purchased from Qi Lu Pharmaceutical Co., Ltd. (Jinan,
China). Acetonitrile and methanol were supplied by Fisher (USA, chromatographic grade).
Docetaxel was provided by Shanghai Boyle chemical Co., Ltd (Shanghai, China). Bletilla striata
polysaccharides were purchased from Shanxi Pioneer Biotech Co., Ltd (Shanxi, China).
4-Dimethylaminopyridine (DMAP) and 1-ethyl-3-[3-(dimethyl amino) propyl] carbodiimide
(EDC) were supplied by Energy Chemical Co., Ltd. (Shanghai, China). Stearic acid (SA) was
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Fig 1. Synthetic route of SA-BSPs copolymer and Fourier Transform Infrared (FTIR) spectra. (A)
Stearic acid (SA) conjugated B. striata polysaccharides (BSPs) was synthetized by grafting SA onto the
hydroxyl group of BSPs. (B) Figure showing FTIR spectra of BSPs (a) and SA-BSPs (b). FTIR experiments
were recorded at 25ÊC on Shimadzu 8300 FTIR spectrometer with a KBr tablet with the range of 400±4000
purchased from Sino pharm Chemical Regent Co., Ltd (Beijing, China). All the other reagents
used were of analytical purity grade and obtained commercially.
Synthesis of SA-BSPs copolymer
The SA-BSPs copolymers were synthesized using SA, EDC, and DMAP, as shown in Fig 1A.
SA (1.812 g), EDC (1.380 g), and DMAP (0.7636 g) were added in 15 mL dimethyl sulfoxide
(DMSO) solution and then the mixture was stirred for 2 h at 25ÊC. The BSPs (5.774 g) were
dissolved in 20 mL of DMSO under stirring condition. The BSPs solution was then added
dropwise to the mixed solution (15 mL) at 25ÊC and kept for 48 h at 38ÊC, as described [
The reaction solution was diluted 10-fold with cold ethanol. The precipitate was recovered by
filtration, washed three times, first with ethanol (100 mL) and then with diethyl ether
(100 mL), and dried in vacuum at 50ÊC.
Characterization of SA-BSPs copolymers
The BSPs and SA-BSPs copolymers were analyzed using FTIR spectroscopy on a Shimadzu
8300 FTIR spectrometer with a KBr tablet with the range of 400±4000 cm-1 (Shimadzu, Tokyo,
The 1H NMR spectra of the samples (5 mg) were determined in DMSO-d6 solution
(500 μL) using a 500 MHz NMR spectrometer (AVIII, Bruker, 500 MHz) at 25ÊC, as described
]. All the spectra were analyzed and processed with Bruker Topspin version 3.0
software. The substituted degree (DS) of the SA-BSPs group was measured by lH NMR.
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DS was calculated according to the following equation described in :
Ad5:53 Ad4:55 100 %
Aδ1.24 was the peak area of methylene protons and Aδ0.85 was the peak area of methyl protons.
Aδ5.43 was the peak area of hydrogen [H (1, 6)] protons and Aδ4.55 was the peak area of
hydrogen [H (1, 4)] protons.
The self-aggregation property of SA-BSPs was measured by RF-5301 fluorescence
spectrophotometer with pyrene as a hydrophobic fluorescence probe [
]. The initial concentration
of pyrene solution was 1.2×10−6 mol/L (M). The pyrene solution was mixed with SA-BSPs
copolymer micelles solution to obtain a SA-BSPs with concentration range of 1.0×10−5~1
mg/mL, and the final pyrene concentration was 6.0×10−7 M. Fluorescence emission spectra
was investigated by excitation at the wavelength of λ ex = 334 nm. Slit width was set at 5 nm
and 2.5 nm for the excitation and emission respectively. Based on the pyrene excitation spectra
and red shift of the spectra with SA-BSPs concentration increase, the critical aggregation
concentrations of the SA-BSPs self-aggregates were calculated by the Benesi-Hildebrand
Preparation of DTX-SA-BSPs copolymer micelles
The SA-BSPs (50 mg) dissolved in 4 mL DMSO solution was transferred into a cellophane
membrane dialysis bag and dialyzed with 500 mL of deionized water each time for 7 times
]. Deionized water (500 mL) was changed every 2 h for 4 times and then every 8 h for 3
times under stirring condition at 100 rpm/min at 25ÊC. The copolymer micelles solution
filtered through a 0.45 μm membrane filter was adjusted to 100 mL by adding deionized water.
Docetaxel (20 mg) was completely dissolved in 10 mL absolute ethanol and then slowly added
into copolymer micelles solution dropwise under magnetic stirring condition at a speed of 100
rpm/min for 2 h. The DTX-SA-BSPs copolymer micelles were harvested by evaporating the
ethanol with vacuum rotary evaporation instrument and the volume was adjusted to 100 mL
by adding deionized water. The DTX-SA-BSPs copolymer micelles with 2% mannitol (W/V)
as lyoprotectant were placed into glass dishes, frozen for 2 h under -20ÊC and then placed in a
freeze-dryer (Free Zone 12 Liter, Labconco Corporation manufactures laboratory equipment
Co., USA) at -40ÊC for 48 h with a pressure of 50 Pascal to get the lyophilized DTX-SA-BSPs
Characterization of DTX-SA-BSPs copolymer micelles
The zeta potential and particle diameter of DTX-SA-BSPs copolymer micelles were measured
using a dynamic light scattering (DLS) particle size analyzer with a scattering angle of 90Ê
(Zetasizer Nano ZS, Malvern Instruments, UK) at 25ÊC, as described [
]. All the experiments
were carried out in triplicate and data were expressed as mean values with their standard
The surface morphology of the DTX-SA-BSPs copolymer micelles was determined using
the transmission electron microscope (TEM, JEM-2010, Japan). Each sample was prepared by
the same procedure as described for zeta potential measurements [
]. A droplet from each
sample was stained with 1% phosphotungstic acid solution for 10 min and was placed on a
copper grid. Subsequently, the excess solution was removed with filter paper. The sample was
dried at 25ÊC, and then was subjected to TEM observation. All the experiments were carried
out in triplicate.
For measuring the drug content and loading efficiency, the DTX in DTX-SA-BSPs
copolymer micelles was separated from the copolymer micelles by centrifugation at a speed of 12,000
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rpm for 10 min. The clear supernatant was analyzed for the contents of DTX by high
performance liquid chromatography (HPLC) (LC-20AT, Shimadzu) at 230 nm. The drug LC and EE
of DTX-SA-BSPs copolymer micelles were calculated as follows:
LC% Weight of DTX in the SA BSPs=Weight of SA BSPs 100 %
EE% Weight of DTX in the SA
BSPs=Weight of the feeding DTX
In vitro study
In vitro drug release. The in vitro release profile of DTX from DTX-SA-BSPs copolymer
micelles was investigated by using the dialysis method. The DTX-SA-BSPs copolymer micelles
and docetaxel injection were suspended in 3 mL of distilled water, bringing the final
concentration of DTX to 100 μg/mL, and the solution was transferred into a cellophane membrane
dialysis bag (8±12 kDa). The dialysis bag was then suspended in 15 mL phosphate buffer saline
(PBS, pH 7.4) with 0.2% of Tween 80, and subjected to horizontal stirring at a speed of 100
rpm/min at 37±0.5ÊC [
]. An aliquot of 5 mL sample was withdrawn at different time points
(0, 1, 2, 3, 5, 7, 8, 9, 24 and 48 h) and the solution was compensated with an equal volume of
the fresh medium maintained at same temperature. The content of DTX was measured by
using HPLC. Sink condition was maintained throughout the release periods. All the
experiments were performed in triplicate.
In vitro cytotoxicity study. The in vitro cytotoxicity was carried out on Hela and HepG2
cells using the MTT (3-(4, 5-dimethylthiazol-2-yl)-2, 5-diphenyl tetrazonium bromide) assay,
as described [
]. Briefly, Hela and HepG2 cells with 5×104 viable cells per well of initial
density were plated in a 96-well plate and incubated for 24 h. The cells were exposed to different
doses of docetaxel injection, blank SA-BSPs copolymer micelles and DTX-SA-BSPs copolymer
micelles at 37ÊC. The DTX concentrations of 0.0005, 0.005, 0.05, and 0.5 μg/mL were used.
After 72-h incubation, 20 μL of MTT solution (5 mg/mL) was added to each well of the plate.
Following 4 h of MTT treatment, 150 μL of DMSO was added to each well to dissolve the
formazan crystals, and the absorbance was measured at 492 nm using a microplate reader
(FL600, Bio-Tek Inc., Winooski, VT). The cell viability (represented in %) was calculated
according to the following equation [
Cell viability %
OD492; blank 100 %
OD492, sample represents the values obtained from the samples treated with docetaxel injection,
blank SA-BSPs copolymer micelles or DTX-SA-BSPs copolymer micelles; OD492, control
represents the values obtained from the cells treated with incubated solution and OD492, blank
represents the values obtained from only incubated solution.
In vivo study
The in vivo bioavailability assay of DTX-SA-BSPs copolymer micelles was conducted
according to the Guidelines for Care and Use of Laboratory Animals. Male Wistar rats were obtained
from the Laboratory Animal Center of Jilin University (Changchun, China). The rats were
maintained at 20 ± 2ÊC and 50±60% relative humidity. A 12-h dark/light cycle was maintained
throughout the study. All the animals were maintained in fasting condition for 12 h with free
access to water before the experiment. The animals were randomly divided into two groups,
and each group received either DTX-SA-BSPs copolymer micelles or docetaxel injection at an
equivalent dose of 20 mg/kg (DTX/rat body weight) through the tail vein injection. Blood
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sample (0.5 mL) was collected in heparinized tubes from the retro-orbital plexus while the rats
were anesthetized under diethyl ether inhalation after 0, 10, 30, 60, 120, 180, 240, 300, and 360
min of vein injection. The blood sample was then separated from the heparinized blood by
centrifugation using a centrifuge 5415C (Eppendorf, Germany), and stored at -20ÊC until
]. All the data were analyzed using the DAS 2.1 pharmacokinetic software (a program
by Chinese Pharmacological Society, China), and the results were represented as mean values
with standard deviations. The study was conducted in accordance with the Guide for the Care
and Use of Laboratory Animals published by the National Institutes of Health and with the
recommendations and approval of the Ethics Committee on Animal Experiments of Jilin
University. All efforts were made to minimize suffering. All rats were killed by barbiturate
overdose after experiments.
Characterization of SA-BSPs copolymers and DTX-SA-BSPs copolymer micelles
Synthetic route of SA conjugated BSPs is presented in Fig 1A. SA, EDC, and DMAP were used
to synthesize the SA-BSPs amphiphilic copolymer. The FTIR spectra of BSPs and SA-BSPs are
shown in Fig 1B. Compared to the standard spectrum of BSPs, a new peak showing the
characteristic absorption at 1730 cm-1 was observed for SA-BSPs. The characteristic absorption peaks
at 892.98 and 825.48 cm-1 showed the existence of û-glucosyl and mannose residues,
respectively. The absorption peaks at 1035.7 and 1159.1 cm-1 indicated pyran-glycosylation of BSPs.
The presence of methyl (-CH3) group is indicated by a strong absorption at 2926.5 cm-1.
Characteristic peak at 3388.55 cm-1 can be attributed to the hydroxyl group (-OH) stretching. Fig 2
show the 1H NMR spectra of BSPs and SA-BSPs in DMSO-d6, and the peak areas of 1H NMR
signals are listed in Table 1. The δ1.24 and δ0.85 ppm correspond to the peak of methylene and
Fig 2. 1H nuclear magnetic resonance (1H-NMR) spectra of BSPs (A) and SA-BSPs (B) in DMSOd6.
1H-NMR spectra indicated the generation of methylene (δ1.24) and methyl (δ0.85) protons after the addition of
SA to the reaction mixture containing BSPs.
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methyl protons, respectively. Hydroxyl proton signals were observed at δ4.5±5.6 ppm. The
δ5.43 ppm peak corresponds to (1!6)-linked hydrogen protons, while δ4.55 ppm peak
indicated the presence of (1!4)-linked hydrogen protons in BSPs. Furthermore, the DS of
SA-BSPs was 12.94%, which was calculated from the peak areas (Table 1) of 1H NMR signals.
Critical aggregation concentration (CAC) spectra are shown in Fig 3. The fluorescence
intensity of SA-BSPs copolymer micelles was shown to increase significantly with an increase
in the concentration (Fig 3A). A clear cross point (Fig 3B) was obtained for changes in
I372/I382, and the CAC was approximately 3.09 μg/mL.
The average diameter, zeta potential, EE % and LC % of the copolymer micelles are shown
in Table 2. The average particle diameter of SA-BSPs copolymer micelle was 60.52 ± 3.34 nm,
whereas the zeta potential was -20.12 ± 0.57 mV. The study showed that the LC and EE
percentages were improved with the increase of drug verse carrier mass ratio from 1:20 to 1:9
(W/W). The EE and LC observed were 81.11 ± 0.18% and 9.13 ± 0.17%, respectively, when the
drug versus carrier mass ratio was 1:9. The values of LC and EE decreased when the mass ratio
of the drug versus carrier was beyond 1:8. The spherical morphology of DTX-SA-BSPs
copolymer micelles is shown in Fig 4.
In vitro drug release. The release profiles of DTX from DTX-SA-BSPs copolymer micelles
and docetaxel injection are shown in Fig 5. The release percentage of DTX from docetaxel
injection was faster and higher 64.87 ± 1.44% than that from DTX-SA-BSPs copolymer
micelles 49.21 ± 2.15% in the phosphate buffer saline (pH 7.4) solution containing 0.2% of
Tween 80 at 9 h. The DTX-SA-BSPs copolymer micelles tended to be stable even after 10 h.
The release percentage of DTX from DTX-SA-BSPs copolymer micelles was 60.04 ± 3.06% in
the first 24 h and 66.93 ± 1.79% in 2 days. The release percentage of DTX from docetaxel
injection was approximately 100% after 48 h.
Fig 3. Fluorescence emission spectra of SA-BSPs copolymer micelles in distilled water at 25ÊC. (A)
Emission spectra of pyrene (6×10−7 M) at the presence of SA conjugated BSPs. (B) Plot of the intensity ratio
of I372/I382 from emission spectra vs log C of the SA-BSPs copolymer micelles.
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In vitro cytotoxicity study. The viability of Hela and HepG2 cells treated with blank
SA-BSPs copolymer micelles, docetaxel injection and DTX-SA-BSPs copolymer micelles (with
equal doses of DTX) for 72 h is shown in Fig 6. When drug concentration was 0.05 μg/mL, the
cell viability of docetaxel injection and DTX-SA-BSPs copolymer micelles on HeLa cells were
60.3 ± 4.6% and 50.3 ± 3.9%, respectively, whereas at 0.5 μg/mL DTX concentration the cell
viability was 55.5 ± 2.6% and 45.5 ± 1.9%, respectively (Fig 6A). The HepG2 cells viability was
approximately 79.5 ± 3.4% and 46.5 ± 3.5% when treated with docetaxel injection, and
48.6 ± 0.4% and 16.5 ± 0.6% when treated with DTX-SA-BSPs copolymer micelles respectively,
at a DTX concentration of 0.05 and 0.5 μg/mL (Fig 6B). A 50% increase in the growth
inhibition was observed for HepG2 cells treated with DTX-SA-BSPs copolymer micelles compared
to the cells treated with docetaxel injection after 72 h.
Fig 4. Transmission electron microscopy image of DTX-SA-BSPs copolymer micelles. The TEM image
was offered with a magnitude 20000× and scale 500 nm.
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Fig 5. In vitro release profiles of DTX from docetaxel injection (-■-) and DTX-SA-BSPs copolymer micelles (-▲-) in pH 7.4
phosphate-buffered saline containing 0.2% of Tween 80 at 37 ± 0.5ÊC.
In vivo study. The mean plasma concentration-time profile of docetaxel injection and
DTX-SA-BSPs copolymer micelles, injected intravenously, is shown in Fig 7, and the
corresponding pharmacokinetic parameters are listed in Table 3. Several pharmacokinetic
parameters, including clearance (CL), area of concentration-time curve (AUC0-1), AUC0-t, and mean
residence time (MRT) were shown to be different for DTX between docetaxel injection and
DTX-SA-BSPs copolymer micelles. In case of DTX-SA-BSPs copolymer micelles, the AUC0-1
and AUC0-t values were significantly higher, with a little decrease in clearance (p<0.05)
compared to the docetaxel injection. Further, the MRT was also extended (p<0.05) in
DTX-SA-BSPs copolymer micelles. The AUC0-1 of DTX-SA-BSPs copolymer micelles was
approximately 1.37-fold higher than that of docetaxel injection (65.39±5.21 μg/mL h vs 47.73
±0.49 μg/mL h, p<0.05).
A new peak showing the characteristic absorption band at 1730 cm-1 in SA-BSPs was assigned
to (-OCO-) group, further demonstrating successful conjugation of SA with BSPs. The
characteristic absorption peak at 825.48 cm-1 showed the existence of mannose in BSPs . Thus,
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Fig 6. Cytotoxic effects of SA-BSPs copolymer micelles, docetaxel injection and DTX-SA-BSPs copolymer micelles on Hela (A)
and HepG2 (B) cells after 72 h incubation. Results were expressed as mean ± S.D. (n = 6) (**, p<0.05 vs docetaxel injection. *, p<0.05 vs
DTX-SA-BSPs copolymer micelles)
the FTIR and 1H NMR techniques demonstrated that SA was successfully conjugated with
The structural changes upon dilution of the SA-BSPs copolymer micelles solution in water
was determined by fluorescence spectrophotometer with pyrene as a hydrophobic fluorescence
probe. Pyrene is strongly emitted in hydrophobic condition or in a nonpolar environment,
whereas, it is fairly quenched in polar solvent. Therefore, we investigated the self-aggregated
behaviors of SA-BSPs copolymer micelles in water by using fluorescence excitation spectra.
The CAC of SA-BSPs copolymer micelles was about 3.09 μg/mL, which is similar to the system
of amphiphilic block copolymers [
]. At low concentration (concentration<CAC), there was
negligible change in the fluorescence intensity, whereas, a remarkable increase was observe red
in the intensity with increasing concentration, as shown by a previous report [
Amphiphilic copolymers, such as hydrophilic polysaccharides and block copolymers, have
been reported to easily form nanosized carrier with a core-shell structure in an aqueous
]. These properties of amphiphilic block copolymers make them superior
vehicles for entrapping and loading hydrophobic antitumor drugs . SA-BSPs amphiphilic
copolymers were synthesized through covalent attachment of SA to BSPs. The copolymer can
easily self-assemble into micelles due to SA block in aqueous solution while BSPs can't. The
particle size of DTX-SA-BSP copolymer micelles 97.01 ± 3.17 nm was larger than that of blank
SA-BSP copolymer micelles 60.52 ± 3.34 nm, indicating that particle diameter enlarged with
DTX addition because DTX was carried to enter the hydrophobic cores of SA-BSPs copolymer
micelles and resulted in the increase in volume of DTX-SA-BSPs copolymer micelles. The
small size of the particles (less than 100 nm in diameter) has been shown to facilitate easy
lymphatic transport and enhanced blood transmission of an antitumor drug, avoiding the
reticuloendothelial system (RES) and passively delivering the antitumor drug [
The mean particle diameter and LC % showed an increasing trend, whereas, no distinct
zeta potential change was observed, after loading the DTX below a 1:8 mass ratio of drug verse
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Fig 7. Mean plasma concentration-time curves of DTX in rats after a single i.v. dose (20 mg/kg) of DTX-SA-BSPs copolymer
micelles and docetaxel injection in vivo pharmacokinetics study. Data were represented as mean ± S.D. of 3±5 experiments.
SA-BSPs copolymer. Therefore, we selected the mass ratio of 1:9 (drug/carrier) as the optimal
formulation for further study, which was decided based on triplicate experiments. After
lyophilization, the average EE and LC of freeze-dried DTX-SA-BSPs copolymer micelles were
8.97 ± 0.23% and 80.83 ± 0.49%, respectively. The results demonstrated that average LC and
EE percentage decreased after freeze-dried process.
*Signi®cantly different from docetaxel injection (p<0.05) by Student t-test.
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The release percentage of DTX from docetaxel injection was faster and higher than that
from DTX-SA-BSPs copolymer micelles in the same aqueous media. The difference in DTX
release rate was mainly because of the core-shell structure of SA-BSPs copolymer micelles.
Lipophilic DTX was surrounded by the hydrophobic core-shell structure of the SA-BSPs, and
the drug release was attributed to diffusion and dissolution [
]. These results revealed that
DTX was gradually released from the DTX-SA-BSPs copolymer micelles, and a constant
release rate was maintained for a relatively longer time. These properties of the micelles may
reduce the injection frequency of the drug, which might be an encouraging strategy for their
The viability of Hela and HepG2 cells treated with docetaxel injection was higher than that
of cells treated with DTX-SA-BSPs copolymer micelles, at a drug concentration of 0.05 and
0.5 μg/mL. The results revealed that DTX-SA-BSPs copolymer micelles significantly decreased
the cancer cell viability compared to docetaxel injection, perhaps because of better
biocompatibility of SA-BSPs and DTX-SA-BSPs copolymer micelles. The DTX-SA-BSPs copolymer
micelles were able to easily attach onto the cell surface, and accelerate the drug release near the
cell membrane, thus developing a concentration gradient, further promoting the DTX
penetration into the cell [
]. Carcinogenic cells possessing special endocytic activity internalized
the BSPs graft copolymer micelles, which may have increased the drug concentration inside
the cells. In addition, DTX-SA-BSPs copolymer micelles may have protected the DTX from
the effect of P-glycoprotein (P-gp) pumps, which further resulted in increased drug
concentration inside the cancerous cells. Moreover, intracellular delivery of DTX-SA-BSPs could have
improved the drug concentration near the site of action [
The analysis of pharmacokinetic parameters between docetaxel injection and
DTX-SA-BSPs revealed that DTX-SA-BSPs copolymer micelles were able to delay the
elimination of DTX, and maintained a constant blood circulating concentration in rats. The increased
AUC and elongated MRT of DTX-SA-BSPs copolymer micelles further indicated that the
micelles might possess a longer blood circulating effect. The longer circulating effect may also
be attributed to the location of DTX at the core of SA-BSPs copolymer micelles, whereas the
hydrophilic shell can stabilize and protect the drug in the aqueous medium. The special
coreshell structure delayed the degradation and slowed down the release of DTX compared to the
docetaxel injection. The smaller size of DTX-SA-BSPs copolymer micelles (<200 nm) might
help it in escaping from RES recognition [
], and could be another reason for being slowly
removed from the circulation compared to the docetaxel injection.
The present study was an effort to deliver DTX using nanoparticulate drug delivery system
in order to minimize the toxicity associated with its use and improve its therapeutic efficacy.
The SA-BSPs copolymer micelles were successfully applied as a macromolecular material to
encapsulate the DTX using an emulsion method. The copolymer micelles displayed a high
drug-loading capability and encapsulation efficiency with an average particle size of 97.01
±3.17 nm. Compared to the docetaxel injection, the DTX-SA-BSPs copolymer micelles were
more effective in inhibiting the growth of HepG2 and Hela cancer cells. The DTX-SA-BSPs
copolymer micelles also maintained a constant release rate for a relatively longer time and
stayed in plasma for longer than docetaxel injection. Absolute bioavailability of
DTX-SA-BSPs copolymer micelles was 1.39-fold higher than that of docetaxel injection.
Overall, DTX-SA-BSPs copolymer micelles might be an efficient way to increase the absolute
bioavailability of poorly water-soluble drugs and an encouraging strategy for use in clinical
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The authors are grateful to Lichun Zhao professor who provides us with Hela and HepG2
cells. The research was supported by Graduate Innovation Fund of Jilin University (2016225);
Jilin Science and Technology Agency funding (20140307018YY; 20140414040GH,).
Conceptualization: QXG BJL.
Data curation: QXG.
Formal analysis: QXG BJL.
Funding acquisition: QXG.
Investigation: YW KL MW CS.
Methodology: QXG GYZ BJL.
Project administration: QXG.
Supervision: QXG ZZ JYL.
Writing ± original draft: QXG GYZ BJL.
Writing ± review & editing: QXG.
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