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Article

Polysialic Acid Modified Liposomes for Improving Pharmacokinetics and Overcoming Accelerated Blood Clearance Phenomenon

by
Xi Han
1,2,
Ting Zhang
1,2,
Mengyang Liu
1,
Yanzhi Song
1,
Xinrong Liu
1 and
Yihui Deng
1,*
1
College of Pharmacy, Shenyang Pharmaceutical University, Shenyang 110016, China
2
College of Pharmaceutical Science, Zhejiang Chinese Medical University, Hangzhou 310053, China
*
Author to whom correspondence should be addressed.
Coatings 2020, 10(9), 834; https://doi.org/10.3390/coatings10090834
Submission received: 4 August 2020 / Revised: 24 August 2020 / Accepted: 26 August 2020 / Published: 28 August 2020
Browse Figures
Versions Notes

Abstract

:
Poly (ethylene glycol) (PEG) modified nanocarriers are being used widely in the drug delivery system (DDS). However, the “accelerated blood clearance (ABC) phenomenon” was induced upon repeated administration of PEG-modified liposomes, resulting in reduced blood circulation time, and increased accumulation in liver and spleen. To avoid the unexpected phenomenon, polysialic acid (PSA) was selected to modify liposomes. PSA is a natural, highly hydrophilic polysaccharide polymer for which no receptors exists in the body. It is non-immunogenic, biodegradable and endows the conjugated bioactive macromolecule and drugs with increased circulation time in vivo. In the present study, the in vivo evaluation showed that PSA modified liposomes (PSA-Lip) afford extended blood circulation in wistar rats and beagle dogs. Moreover, the ABC phenomenon did not occur and the IgM antibody was not induced after repeated injections of PSA-Lip. These results strongly suggest that PSA modification represents a promising strategy to afford good stealth of the liposomes without evoking the ABC phenomenon.

1. Introduction

It is well known that common nanocarriers are easily recognized by the mononuclear phagocyte system (MPS), and are therefore rapidly cleared from the blood circulation, distributed in the liver and spleen, which affect the effectiveness. In the development history of the drug delivery system (DDS), the PEGylation technology of drug molecules and carriers has a landmark significance [1,2]. PEGylation technology can reduce the recognition of drugs/carriers by MPS and prolong blood circulation time, thereby using the enhanced permeability and retention (EPR) effect to achieve disease sites targeting [3,4]. PEGylation technology has many advantages such as prolonging circulation time, improving water solubility and increasing stability. The application of PEGylation technology in many aspects has been approved by the FDA for clinical use [5].
Liposomes are phospholipid bilayer vesicles with an aqueous phase inside. Because of this special constitution, liposomes could encapsulate both hydrophilic and hydrophobic drugs. Liposomes are widely used in medicine and other fields, owing to their unique characteristic, such as biodegradability and biocompatibility, improving the therapeutic index and reducing systemic toxicity [6,7]. However, conventional liposomes have the problems of poor colloidal stability, and rapid clearance from the blood by MPS [8,9]. Polyethylene glycol (PEG), the hydrophilic, neutral polymers, could increase the hydrophilicity and provide a hydration layer on the liposome surface, which help the modified liposomes decrease recognition by the MPS, and prolong circulation time in vivo after intravenous injection [10]. It has been thought that PEG could serve as the gold standard material in the drug carrier construction [11,12]. Nevertheless, it has been pointed out that the PEGylated liposomes would be cleared from blood quickly and gathered in the liver and spleen after an interval of several days when the second dose was administered intravenously. This is called “accelerated blood clearance (ABC) phenomenon” [13,14].
It was reported that ABC phenomenon contained sequential events, the first injected dose of PEGylated liposomes induced anti-PEG IgM antibody production in the spleen; the second dose of PEGylated liposomes were quickly recognized and bound by the IgM antibody, and the complement was activated by C3 fragments opsonization and enhanced uptake by MPS [15]. The long circulation advantages of PEGylated liposomes would be greatly decreased by the ABC phenomenon. If the PEGylated liposomes encapsulated cytotoxicity drug, the ABC phenomenon would causes serious toxic effects due to the accumulation in MPS in liver and spleen [16]. In addition, it has been reported that acute hypersensitivity reactions was caused by PEGylated liposomes after injections in some individuals. In the hypersensitive individuals the plasma SC5b-9 was significantly increased after injections of PEG modified liposomes [17]. Therefore, the hypersensitivity reactions was corrected with complement activation. In order to solve the ABC phenomenon of PEGylation technology, researchers have changed the dosing interval, the modification density of PEG derivatives, and the physicochemical properties of PEG preparations [13,18,19]. However, most of these approaches did not eliminate the ABC phenomenon completely and therapeutic efficacy of PEGylated liposomes was weakened. Taken together, as long as PEG exists in the drug carrier construction, the ABC phenomenon is inevitable. Therefore, seeking an alternative approach remains extremely urgent by extending the circularly stability of modified liposomes and avoiding the ABC phenomenon.
Polysialic acid (PSA), composed of a-2,8-linked 5-N-acetylneuraminic acid (Neu5Ac), is a highly hydrophilic polysaccharide in mammalian tissue. PSA is an endogenous substance, which is non-toxic, non-immunogenic and bio-degradable [20,21]. PSA is a post-translational modification of neural cell adhesion molecule (NCAM) [22]. Studies have shown that [23] PSA would increase the hydrodynamic radius of modified NCAM, improve the repulsive ability between NCAM molecules, and PSA also weakened the adhesion force between modified NCAM and other molecules. In addition, PSA in microorganisms is consistent with the structure and immunogenicity of PSA in mammals [24]. Neisseria will use PSA to wrap themselves and recruit H factor to prevent complement C fragments from depositing on cell surfaces, inhibit the formation of attack complexes, mask potential epitopes and reduces recognition by the immune system [25,26]. Therefore, PSA can escape immune system surveillance through immune camouflage. Meanwhile, the repellent layer of PSA will weaken the recognition of opsonins and reduce MPS uptake. Based on the above properties, PSA can be suitably applied to long-circulation drug delivery system [27,28]. Some studies on PSA modified liposome-based drug delivery system have been reported by our group. In our previous work [29], PSA-polyethylene glycol (PSA-PEG) conjugate was synthesized for the decoration of liposomal epirubicin. The liposomal formulations had good storage and dilution stability. In vivo antitumor studies revealed that PSA-PEG modified liposomal epirubicin, serving as a binding molecule to the tumor site, exhibited increased accumulation in tumor area, enhanced the antitumor activity with reduced systemic toxicity. Luo et al. [30] synthesized a PSA-p-octadecylamine conjugate (PSA-p-ODA) and decorate it on the surface of liposomal pixantrone, Experimental results showed that the modification of PSA-p-ODA could prolong the circulation time of the liposomal pixantrone, and targeted to peripheral blood neutrophils, which provide a neutrophil-mediated drug delivery system for the eradication of tumors.
In previous study, the PSA derivative was synthesized with octadeyl dimethyl betaine (BS18) and the synthetic product PSA-BS18 was modified on the liposomes (PSA-Lip) [31]. The PSA-Lip presented extended residence in the blood circulation. In the present study, the systemic study was conducted to investigate whether PSA-Lip would overcome the ABC phenomenon and complement activation after intravenous administrations.

2. Materials and Methods

2.1. Materials

Hydrogenated soy phosphatidylcholine (HSPC) and 1,2-dioctadecanoyl-sn-glycero-3-phospho-(1′-rac-glycerol) (sodium salt) (DSPG) was got from Lucas Meyer (Düsseldorf, Germany). 1,2-Distearoyl-sn-glycero-3-phosphoethanolamine-N-[methoxy (polyethylene glycol)-2000] (mPEG2000-DSPE) and cholesterol (CH) were obtained from Shanghai Advanced Vehicle Technology Pharmaceutical L.T.D. (Shanghai, China). 1,1′-dioctadecyl-3,3,3′,3′-tetramethyl indotricarbocyanine Iodide (DiR) was purchased from American ATT Bioquest, Inc (Sunnyvale, CA, USA). Sephadex®G-50 was purchased from Pharmacia Biotech Inc. (Piscataway, NJ, USA). Polysialic acid-octadecyl dimethyl betaine (PSA-BS18) was synthesized in our laboratory [31].

2.2. Animals

Male wistar rats, weighting 180–220 g and male beagle dogs, weighting 10–12 kg were provided by the Laboratory Animal Center of Shenyang Pharmaceutical University (Shenyang, China). All animal experiments are in compliance with animal ethics committee standards [32]. Laboratory Animal Center of Shenyang Pharmaceutical University, the approval number is: IACUC-C2018-6-11-202.

2.3. Synthesis of PSA-BS18

PSA-BS18 was synthesized by combining the hydroxyl groups of PSA with the carboxyl group of BS18. EDC/NHS was used as a catalyst; the synthetic study was reported previously [31].

2.4. Preparation of Liposomes

Liposomes were prepared by the lyophilized hydration method [33]. For the common liposomes (CLip), HSPC, DSPG, CH were dissolved in the organic solvent tert-butanol, 3:1:2 (mol/mol), and PEGylated liposomes (PEG-Lip), HSPC, DSPG, CH and mPEG2000-DSPE were dissolved in the organic solvent tert-butanol, 3:1:2:0.32 (mol/mol). For PSA modified liposomes (PSA-Lip), HSPC, DSPG and CH were dissolved in the organic solvent tert-butanol, 3:1:2 (mol/mol). PSA-BS18 was added in water phase. The water phase was then injected into the lipid solution phase at 60 °C. The obtained lipid solution was freeze-dried. Then 5% glucose was added to the lyophilized cake for hydration under continuous agitation at 60 °C for 20 min. The hydration solution was sonicated by an ultrasonic cell pulverizer for 200 W, 2 min and 400 W, 6 min. At last, the liposome suspension passed through 0.45-, and 0.22-µm microporous filters in sequence.
In the preparation of DiR labeled CLip, PSA-Lip and PEG-Lip, DiR was added in the mixture solution before the lyophilization, and the other process was as same as mentioned above.

2.5. Characterization of Liposomes

2.5.1. Particle Size, PDI and Zeta Potential

The particle size, polydispersity index (PDI) and zeta potential of liposomes formulations were detected by dynamic and electrophoretic light scattering using a NICOMPTM 380 submicron particle analyzer (PSS Nicomp, Santa Babara, CA, USA). The instruments were equipped with a He–Ne laser at a wavelength of 632.8 nm at 25 °C. Measurements were taken at a fixed scattering angle of 90°.

2.5.2. Morphology of Liposomes

The morphology of liposome formulations was observed by transmission electron microscopy (TEM, JEOL, Tokyo, Japan). The liposomes were placed on carbon-coated grids, and the surplus was removed with filter paper and allowed to air dry at room temperature. Then the liposomes were negatively stained by adding phosphotungstic acid 2% (w/v) solution onto the grids. The samples were air dried overnight at room temperature before measurement by TEM.

2.5.3. Determination of the Encapsulation Efficiency

Sephadex G-50 column was used to separate the DiR labeled liposomes and unentrapped DiR. The DiR entrapped in liposomes (Wenc) was dissolved with methanol and detected by a microplate reader fluorescence spectrophotometer (Bio-Rad Laboratories, Inc., Hercules, CA, USA) at 750/790 nm. The total amount of DiR (Wtol) of the liposomes was dissolved with methanol and detected. The encapsulation efficiency (EE) of the liposome formulations was calculated using the formula: EE = (Wenc)/(Wtol) × 100%.

2.6. Determination of the Fixed Aqueous Layer Thickness (FALT)

A classic method based on the Gouy–Chapman theory was used to measure the FALTs of CLip, PEG-Lip and PSA-Lip [34,35]. 10, 50, 100, 150, and 200 mM NaCl solutions were prepared. To avoid the influence of trace divalent ions on the determination, 0.1 mM EDTA-2Na was added.
κ =   C / 0.3
Lnψ(L) = LnA − kL
where κ is the Debye–Hückel parameter and A is regarded as a constant and C is the molar concentration of NaCl. The zeta potentials of the varying NaCl concentrations are measured and plotted against κ, the slope L gives the FALT in nm units.

2.7. Pharmacokinetics of Liposomes in Wistar Rats

2.7.1. Pharmacokinetics of Liposomes after Single Injection

Male wistar rats were randomly divided into three groups (n = 3). For the pharmacokinetics study involving a single injection, DiR labeled CLip, PEG-Lip and PSA-Lip were intravenously with a phospholipid concentration of 5 μmol/kg via the tail vein under ether anesthesia. Blood samples were obtained from orbital venous plexus and placed into heparinized centrifuge tubes at 1, 5, 15, and 30 min, 1, 4, 8, 12, and 24 h after the injection. Plasma was isolated from blood samples by centrifugation (2264× g, 10 min). The plasma was precipitated with methanol and centrifuged at 11,180× g for 10 min. Then the obtained supernatant was added into 96-well plate and detected with microplate reader fluorescence spectrophotometer with excitation/emission wavelengths at 750/790 nm, respectively. DAS.2 software was used to calculate the pharmacokinetics parameters.

2.7.2. Pharmacokinetics and Biodistribution of Liposomes after Repeated Injections

To investigate the biodistribution and pharmacokinetics involving the repeated injection, the detailed protocols descript in Table 1. The PSA-Lip and PEG-Lip were intravenously injected via the tail vein under ether anesthesia as the first injection. Control group received an injection of 5% Glu. 7 days later, the blood samples were obtained 0.5 h before the repeated administrations. DiR labeled PSA-Lip and PEG-Lip were injected intravenously at a dose of 5 μmol phospholipid/kg, the blood samples were got from the orbital venous plexus at 1, 5, 15, and 30 min, 1, 2, and 4 h after the second administration. After the last time point, the rats were sacrificed and livers and spleens were excised. The collected blood samples were processed using the same procedure described in Section 2.7.1. The tissue were homogenized using a Tissue Tearor and precipitated with methanol and centrifuged at 11,180× g for 10 min. Then the obtained supernatant was added into 96-well plate and detected with microplate reader fluorescence spectrophotometer with excitation/emission wavelengths at 750/790 nm.

2.8. Pharmacokinetics of Liposomes in Beagle Dogs

Male beagle dogs were randomly divided into 4 groups (n = 3). The test protocols were show in Table 2. The beagle dogs were intravenously injected in right forelimb with PSA-Lip and PEG-Lip at a dose of 5 μmol phospholipid/kg. Control group received an injection of 5% Glu. 7 days later, the blood samples were obtained 0.5 h before the repeated administrations. DiR labeled PEG-Lip and PSA-Lip were injected intravenously at a dose of 5 μmol phospholipid/kg for the second injection. At various time points of 1, 5, 15, and 30 min, 1, 2, and 4 h after injection, 2 mL of blood from the left forelimb vein was placed in a heparinized tube, and processed using the same procedure described in Section 2.7.1.

2.9. Quantification of IgM

PSA-BS18 and mPEG2000-DSPE (0.2 mM) were added into a 96-well plate, and the coated plate was dried at room temperature. Tris-buffer containing 1% BSA solution was added to block the wells. Then the wells were washed three times with a Tris buffered saline solution containing 0.05% CHAPS. 100-µL of diluted serum samples of rats and beagle dogs were then added to the wells respectively and incubated for 90 min, and then washed 5 times as described above. Horseradish peroxidase -conjugated rabbit anti-rat/dog antibody was added into each well (100 μL/well) at a concentration of 1 μg/mL. After 60 min incubation at room temperature, the wells were washed 5 times. 1 mg/mL of o-phenylene diamine (100 μL/well) was added into the wells and incubated for 15 min. 2 M H2SO4 (100 μL/well) was added to terminate the reaction. The absorbance was detected at 490 nm by microplate reader fluorescence spectrophotometer.

2.10. Statistical Analysis

All data were expressed as the mean ± S.D. Statistical comparisons were calculated by Students t-test or Tukey’s test with SPSS 17.0 software. p < 0.05 is considered as statistically significant. p < 0.01 is considered as statistically extremely significant.

3. Results and Discussion

3.1. The Characteristics of the Prepared Liposomes

The physicochemical property of the prepared liposome were presented in Table 3. The mean particle size of the liposome formulations was 90–110 nm. The zeta potentials varied from −10 to −20 mV. The morphology of liposomes was observed using TEM. As shown in Figure 1, the prepared liposomes were in near spherical shape. The encapsulation efficiency of the DiR in the labeled liposomes were all above 95%, which was in agreement with the previous study [30,31] from our group.

3.2. The Comparison of FALT around Liposomes

FALT is considered to influence the biochemical property of the polymer-modified liposomes. Shimada et al. [36] established a method to measure the FALT around liposomes. The results showed that as FALT on the liposomes increased, macrophage uptake decreased, which led to a prolonged circulation time in blood. Thus, FALT was used as a quantitative measure of liposomes for avoiding opsonization and uptake by the MPS.
From Equations (1) and (2) in Section 2.6: the FALTs of the Clip, PSA-Lip and PEG-Lip were determined to be 0.28, 0.83 and 2.61 nm, respectively. The FALT of PSA-Lip (0.83 nm) was thicker than CLip (0.28 nm) (p < 0.05). The increasing FALT of PSA-Lip would led a reduction in uptake by macrophages, resulting in a prolonged blood circulation.

3.3. Pharmacokinetics of Liposomes after Single Injection in Wistar Rats

To investigate whether PSA modification could afford the stealthiness in the blood circulation, PSA-Lip were intravenously administered in wistar rats. As shown in Figure 2, the blood clearance rate of PSA-Lip was significantly slower compared to that of CLip. Table 4 presented the pharmacokinetic parameters. The area under the blood concentration-time curve (AUC) of PSA-Lip was significantly higher than Clip (p < 0.01). The clearance (CLz) value of PSA-Lip (0.085 ± 0.008 L∙kg−1·h−1) was significantly lower (p < 0.01) than Clip (0.512 ± 0.141 L∙kg−1·h−1). In addition, the mean residence time (MRT) of PSA-Lip (9.23 ± 0.46 h) also increased significantly (p < 0.01) in comparison to that of Clip (5.12 ± 1.01 h). The results showed that PSA-Lip could afford extended blood circulation time in vivo. The immunological properties of α-2,8-linked PSA were reported to be consistent with those in mammals [24]. Therefore, PSA can be used as an endogenous immune camouflage material to protect the modified liposomes from recognizing by the immune system. Meanwhile, numerous studies [30,31,37,38] have shown that PSA can prolong the circulation time of modified drugs/carriers in vivo. Among them, the determination of PSA’s fixed hydration layer thickness (FALT) corroborates the hydration cloud theory proposed by Bader [34], and the presence of FALT can help PSA modified drugs/carriers escape the recognition of opsonins in the blood, decrease MPS uptake and prolong residence time in the body.

3.4. Pharmacokinetics and Bio-Distribution of Various Liposomes after the Repeated Injections in Wistar Rats

Ishida et al. [19] pointed out that when PEGylated liposomes were intravenously injected at a dose of 0.001–0.1 μmol phospholipid/kg as the first injection, the ABC phenomenon clearly occurred upon repeated injections. Furthermore, five to seven day intervals between PEGylated liposome injections induced much more pronounced ABC phenomenon [39,40,41,42,43].
To explore whether the ABC phenomenon would be induced by the PSA modification in wistar rats, blank liposomes were intravenously administered as the first injection, and the corresponding DiR labeled liposomes (5 μmol phospholipid/kg) were administered intravenously seven days later. As illustrated in Figure 3A, after repeated injections, PEGylated liposomes were rapidly cleared (p < 0.01). The blood clearance of pre-injection with PEG-Lip at the dose of 0.1 μmol phospholipid/kg was higher than that of 5 μmol phospholipid/kg. The accumulation in liver and spleen increased significantly (p < 0.01) after the repeated injections (Figure 3B). The results indicated that PEGylated liposomes caused an obvious ABC phenomenon. As for PSA-Lip, the blood clearance curves were very similar between the single dose and second injection both at the dose of 0.1 and 5 μmol phospholipid/kg (Figure 4A). Hepatic and splenic aggregation also did not increase significantly (p > 0.05) in comparison with the control group (Figure 4B). The results suggested that PSA-Lip did not induce the ABC phenomenon after repeated injections.
According to reports, the ABC index can be used as an effective parameter to evaluate the degree of ABC phenomenon. The ABC index = AUC of the second dose/AUC of the first dose. A higher ABC index means a weaker induction of the ABC phenomenon [44]. Interestingly, a study from Zhao et al. [45] has implied that ABC phenomenon is suitable for evaluation by the ABC index (0–30 min). In the present study, the ABC index (0–30 min) of Group C and Group D were 1.01 ± 0.06 and 0.98 ± 0.08 respectively, while Group E and Group F was 0.71 ± 0.13 and 0.23 ± 0.04, respectively. These results also demonstrated that PSA-Lip did not induce the ABC phenomenon.

3.5. Pharmacokinetics of Various Liposomes after the Injections in Beagle Dogs

Different animal models have been used to study the ABC phenomenon, such as mice, rats, rabbits, beagle dogs and so on [13]. Recently, Suzuki and coworkers [46] revealed that beagle dogs were more sensitive to the immune response than other animals models. Under the same degree of stimulation, ABC phenomenon is more likely to be induced in beagle dogs. The dogs could produce the severe ABC phenomenon when administrated with blank PEGylated liposomes at a higher phospholipid dose of 16.7 µmol phospholipids/kg, while in the rats were pretreated with a high dose (≥5 µmol phospholipids/kg), the ABC phenomenon was weakened [19,47]. Hence, difference between species should be considered in the study of long-circulation formulations. In the present study, the beagle dog was also selected as animal model to study the ABC phenomenon of the repeated injections of PSA-Lip, which could investigate the immunogenicity of PSA-Lip comprehensively.
As shown in Figure 5, the DiR of the plasma decreased significantly after repeated injections of PEG-Lip in beagle dogs, and the ABC index (0–30 min) was 0.09 ± 0.02. No obvious change between the single and repeated injections of PSA-Lip was observed, the ABC index (0–30 min) was 1.04 ± 0.05. The results revealed that the ABC phenomenon was not triggered by PSA-Lip after repeated injections in the beagle dogs.

3.6. Determination of the Production of Anti-PEG (PSA) IgM

The IgM antibody was produced in the first injection as an immune response, which would stimulate the complement system and resulted in uptake by Kupffer cell endocytosis following the second injection of liposomes [48]. As illustrated in Figure 6, the first injection of PEG-Lip significantly produced IgM antibody (compared to control, p < 0.01). In contrast, the first injection of PSA-Lip did not induce the IgM in the serum, and would not bound on the second injection of PSA-Lip.
A previous study [13] reported that PEG on the PEGylated liposomes acted as a TI-2 antigen and the repeating subunit of PEG may be an immunogenic epitope. This epitope may be a binding site for the derived anti-PEG IgM, which induced fast blood clearance in vivo following the second injection. The results in our study showed that the first injection of PSA-Lip did not induce IgM production, resulting in no combination with the second injection of PSA-Lip. PSA is a linear polymer connected by Neu5Ac with α-2,8 ketone glycoside bonds. It is an endogenous substance, which is biocompatible and non-immunogenic [20,49,50]. Fernandes et al. [21] also proposed that the immunogenicity of PSA-conjugated asparaginase did not increase against naive asparaginase. These findings were consistent with the above results.
In this study, two animal models of wistar rat and beagle dog are used to investigate the ABC phenomenon of PSA modified liposomes for the repeated injections. The results showed that the first injection of PSA-modified liposomes in wistar rats or beagle dogs did not cause changes in the pharmacokinetic behavior of the second injection and did not produce ABC phenomenon. On the one hand, PSA is no-immunogenic and does not cause an immune response in vivo [51]; on the other hand, PSA can inhibit the body’s immune response, and the modified liposome does not induce the production of anti-PSA-IgM, which plays an immune camouflage role. Therefore, no ABC phenomenon was induced.
Our research group has devoted the effect to overcoming the ABC phenomenon caused by PEGylated formulations in recent years. Studied pointed out that not only PEGylated liposomes [14] could induce the ABC phenomenon, but also repeated injections of PEGylated solid lipid nanoparticles [45], PEGylated emulsions [52] and PEGylated micelles [53] could trigger ABC phenomenon. A variety of strategies have been proposed to address this dilemma, such as, amelioration of dosing regimen [52], alteration of linkages of PEG derivatives and molecular weights of PEG [54], but they were still unsatisfactory in eliminating the ABC phenomenon. As an endogenous substance, PSA is non-immunogenicity and can escape immune system surveillance through immune camouflage. In the previous work, we modified PSA derivatives on the surface of liposomal chemotherapy drugs for anti-tumor therapy, and the results showed that PSA modification exhibited an extended circulation time and excellent anti-tumor efficacy [30,31]. To further verify its application prospects in drug delivery systems, the ABC phenomenon of PSA modified liposomes in beagle dogs and wistar rats was conducted. The results of this study showed that repeated injections of PSA would not induce the ABC phenomenon in both beagle dogs and wistar rats, which presents a promising approach for constructing drug delivery system.

4. Conclusions

In the present study, PSA was selected to modified liposomes and a systematic study was conducted. Because of the hydrophilic and non-immunogenic properties, PSA can be used as a modification material to extend the circulation time in drug delivery system. And the ABC phenomenon and IgM antibody production was not induced after repeated injections. Because of its inherent biodegradability and immunogenicity, PSA represents a good option for drug delivery in clinical treatments that require prolonged intravenous therapy.

Author Contributions

Methodology, X.H. and M.L.; data curation, X.H. and T.Z.; writing—original draft preparation, X.H. and T.Z.; writing—review and editing, Y.S.; project administration, X.L.; funding acquisition, Y.D. All authors have read and agreed to the published version of the manuscript.

Funding

This research was funded by the National Natural Science Foundation of China. (NO.81973271 and 81903808).

Conflicts of Interest

The authors declare no conflict of interest.

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Coatings 10 00834 g001 550
Figure 1. The TEM images of (A) Clip, (B) PSA-Lip, and (C) PEG-lip. Scale bars represented 200 nm.
Figure 1. The TEM images of (A) Clip, (B) PSA-Lip, and (C) PEG-lip. Scale bars represented 200 nm.
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Figure 2. The blood clearance of various DiR labeled liposomes after intravenous administration in wistar rats at a dose of 5 µmol phospholipids/kg. Data were shown as mean ± S.D., n = 3.
Figure 2. The blood clearance of various DiR labeled liposomes after intravenous administration in wistar rats at a dose of 5 µmol phospholipids/kg. Data were shown as mean ± S.D., n = 3.
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Figure 3. (A) Pharmacokinetic profile in wistar rats after the repeated injection of PEG-Lip (0–4 h). (B) Hepatic and splenic accumulation (4 h) in rats after second injection of PEG-Lip. Data were shown as mean ± S.D., n = 3. * p < 0.05, ** p < 0.01.
Figure 3. (A) Pharmacokinetic profile in wistar rats after the repeated injection of PEG-Lip (0–4 h). (B) Hepatic and splenic accumulation (4 h) in rats after second injection of PEG-Lip. Data were shown as mean ± S.D., n = 3. * p < 0.05, ** p < 0.01.
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Figure 4. (A) Pharmacokinetic profile in wistar rats after the repeated injection of PSA-Lip (0–4 h). (B) Hepatic and splenic accumulation (4 h) in rats after second injection of PSA-Lip. Data were shown as mean ± S.D., n = 3.
Figure 4. (A) Pharmacokinetic profile in wistar rats after the repeated injection of PSA-Lip (0–4 h). (B) Hepatic and splenic accumulation (4 h) in rats after second injection of PSA-Lip. Data were shown as mean ± S.D., n = 3.
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Figure 5. Pharmacokinetic profile (0–4 h) in beagle dogs after intravenous single and repeated injections of DiR labeled liposomes. Data were shown as mean ± S.D., n = 3.
Figure 5. Pharmacokinetic profile (0–4 h) in beagle dogs after intravenous single and repeated injections of DiR labeled liposomes. Data were shown as mean ± S.D., n = 3.
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Figure 6. Anti-PEG (PSA) IgM production induced by the initial injection (A) in wistar rats and (B) in beagle dogs. Data were shown as mean ± S.D., n = 3. ** p < 0.01.
Figure 6. Anti-PEG (PSA) IgM production induced by the initial injection (A) in wistar rats and (B) in beagle dogs. Data were shown as mean ± S.D., n = 3. ** p < 0.01.
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Table
Table 1. The injection scheme of PSA-Lip and PEG-Lip in wistar rats.
Table 1. The injection scheme of PSA-Lip and PEG-Lip in wistar rats.
GroupFirst Injection
(Blank Liposomes)		Second Injection
(DiR Labeled Liposomes)
A5%GluPSA-Lip (5 μmol phospholipid/kg)
B5%GluPEG-Lip (5 μmol phospholipid/kg)
CPSA-Lip (0.1 μmol phospholipid/kg)PSA-Lip (5 μmol phospholipid/kg)
DPSA-Lip (5 μmol phospholipid/kg)PSA-Lip (5 μmol phospholipid/kg)
EPEG-Lip (0.1 μmol phospholipid/kg)PEG-Lip (5 μmol phospholipid/kg)
FPEG-Lip (5 μmol phospholipid/kg)PEG-Lip (5 μmol phospholipid/kg)
Table
Table 2. The injection scheme of PSA-Lip and PEG-Lip in beagle dogs.
Table 2. The injection scheme of PSA-Lip and PEG-Lip in beagle dogs.
GroupFirst Injection
(Blank Liposomes)		Second Injection
(DiR Labeled Liposomes)
Ⅰ5%GluPSA-Lip (5 μmol phospholipid/kg)
Ⅱ5%GluPEG-Lip (5 μmol phospholipid/kg)
ⅢPSA-Lip (5 μmol phospholipid/kg)PSA-Lip (5 μmol phospholipid/kg)
ⅣPEG-Lip (5 μmol phospholipid/kg)PEG-Lip (5 μmol phospholipid/kg)
Table
Table 3. The characteristics of the prepared liposomes.
Table 3. The characteristics of the prepared liposomes.
FormulationParticle Size (nm)PolydispersityZeta Potential (mV) EE (%)FALT (nm)
Clip128.4 ± 3.40.154 ± 0.012−12.1 ± 3.095.2 ± 1.60.28 ± 0.04
PSA-Lip125.6 ± 8.30.164 ± 0.021−18.6 ± 5.196.3 ± 1.40.83 ± 0.05
PEG-Lip111.3 ± 5.60.132 ± 0.011−16.7 ± 2.696.1 ± 2.32.61 ± 0.08
Table
Table 4. Pharmacokinetic parameters of various DiR labeled liposomes after single intravenous administration in wistar rats (n = 3).
Table 4. Pharmacokinetic parameters of various DiR labeled liposomes after single intravenous administration in wistar rats (n = 3).
ParameterCLipPSA-LipPEG-Lip
Cmax (μg·L−1)1146.3 ± 233.21992.3 ±125.61996.3 ± 114.3
AUC (0-t) (μg·L−1·h)2223.3 ±125.67213.8 ± 100.2715781.4 ± 336.28
MRT (0-t)(h)5.12 ± 1.019.23 ± 0.4612.32 ± 0.65
CLz (L·kg−1·h−1)0.512 ± 0.1410.085 ± 0.0080.017 ± 0.004

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Han, X.; Zhang, T.; Liu, M.; Song, Y.; Liu, X.; Deng, Y. Polysialic Acid Modified Liposomes for Improving Pharmacokinetics and Overcoming Accelerated Blood Clearance Phenomenon. Coatings 2020, 10, 834. https://doi.org/10.3390/coatings10090834

AMA Style

Han X, Zhang T, Liu M, Song Y, Liu X, Deng Y. Polysialic Acid Modified Liposomes for Improving Pharmacokinetics and Overcoming Accelerated Blood Clearance Phenomenon. Coatings. 2020; 10(9):834. https://doi.org/10.3390/coatings10090834

Chicago/Turabian Style

Han, Xi, Ting Zhang, Mengyang Liu, Yanzhi Song, Xinrong Liu, and Yihui Deng. 2020. "Polysialic Acid Modified Liposomes for Improving Pharmacokinetics and Overcoming Accelerated Blood Clearance Phenomenon" Coatings 10, no. 9: 834. https://doi.org/10.3390/coatings10090834

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