Enhanced immunization via dissolving microneedle array-based delivery system incorporating subunit vaccine and saponin adjuvant
Received 15 January 2017
Accepted for publication 18 April 2017
Published 4 July 2017 Volume 2017:12 Pages 4763—4772
Checked for plagiarism Yes
Review by Single anonymous peer review
Peer reviewer comments 4
Editor who approved publication: Dr Linlin Sun
Ji-Hui Zhao,1,* Qi-Bo Zhang,1,* Bao Liu,2 Xiang-Hua Piao,1 Yu-Lu Yan,1 Xiao-Ge Hu,1 Kuan Zhou,1 Yong-Tai Zhang,1 Nian-Ping Feng1
1School of Pharmacy, Shanghai University of Traditional Chinese Medicine, Shanghai, People’s Republic of China; 2Anethesiology Department, Augusta University, Augusta, GA, USA
*These authors contributed equally to this work
Purpose: To enhance the immunogenicity of the model subunit vaccine, ovalbumin (OVA) was combined with platycodin (PD), a saponin adjuvant. To reduce the toxicity of PD, OVA, and adjuvant were loaded together into liposomes before being incorporated into a dissolving microneedle array.
Methods: OVA- and PD-loaded liposomes (OVA-PD-Lipos) were prepared using the film dispersion method. Their uptake behavior, toxicity to mouse bone marrow dendritic cells (BMDCs), and hemolytic activity to rabbit red blood cells (RBCs) were evaluated. The OVA-PD-Lipos were incorporated into a dissolving microneedle array. The chemical stability of OVA and the physical stability of OVA-PD-Lipos in microneedle arrays were investigated. The immune response of Institute of Cancer Research mice and potential skin irritation reaction of rabbits to OVA-PD-Lipos-MNs were evaluated.
Results: The uptake of OVA by mouse BMDCs was greatly enhanced when OVA was prepared as OVA-PD-Lipos, and in this form, the toxicity of PD was dramatically reduced. OVA was chemically stable as OVA-PD-Lipos, when OVA-PD-Lipos was incorporated into a dissolving microneedle array. Institute of Cancer Research mice treated with OVA-PD-Lipos-MNs showed a significantly enhanced immune response. PD combined with OVA elicited a balanced Th1 and Th2 humoral immune response in mice, with minimal irritation in rabbit skin.
Conclusion: The dissolving microneedle array-based system is a promising delivery vehicle for subunit vaccine and its adjuvant.
Keywords: subunit vaccine, saponin adjuvant, liposomes, dissolving microneedle array, intradermal vaccination
Subunit vaccines provide excellent safety but poor immunogenicity. The primary strategies for enhancing immunogenicity are to combine antigens with adjuvants and to incorporate the mixture into nanoscale delivery systems to facilitate uptake and presentation by dendritic cells (DCs). However, adjuvants can introduce health risks. For example, saponins are a chemically heterogeneous group of steroid and triterpenoid glycosides present in a wide range of plant species, characterized as potent adjuvants enhancing both Th1 (humoral) and Th2 (cellular) responses. Quillaia saponin and its derivative Iscomatrix™ are widely used in animal vaccines, but are not considered suitable for human use because of their toxicity.1 Recently, adjuvants based on saponins from traditional Chinese medicinal herbs have been described.2 One promising example is platycodin (PD), it exhibits potent adjuvant activity with less toxicity than Quillaia saponin.3 It is a potential adjuvant for human use, but its toxicity still exceeds acceptable levels.
DCs play a vital role in the process of immune response elicitation mediated by vaccines.4,5 Although subcutaneous and intramuscular routes are typically used for vaccination, skin harbors a widespread network of DCs, which contains a well-developed immune system with good connection to regional lymphatic tissues, making it an attractive site for efficient immunization.6 Because intradermal vaccination can elicit more potent immune responses than subcutaneous or intramuscular vaccination, its use has spread rapidly.6,7 Although conventional intradermal vaccination involves injection with a syringe needle, it is possible to incorporate vaccines into dissolving microneedles. This approach to intradermal vaccination offers better patient compliance, reliability, and simplicity.8–11
In this study, the model antigen ovalbumin (OVA) and the adjuvant PD were loaded into liposomes to facilitate uptake of the vaccine by DCs and to reduce the toxicity of the adjuvant. The uptake behavior and toxicity of the OVA- and PD-loaded liposomes (OVA-PD-Lipos) were evaluated using cultured mouse bone marrow dendritic cells (BMDCs), and their hemolytic activity was evaluated in rabbit red blood cells (RBCs). To enhance vaccination efficiency, OVA-PD-Lipos were incorporated into dissolving microneedles. The immunization efficiency of the OVA-PD-Lipos-incorporated microneedles (OVA-PD-Lipos-MNs) was investigated in mice, and their ability to provoke skin irritation was evaluated using rabbits.
Materials and methods
OVA (grade VII), granulocyte macrophage-colony stimulating factor (GM-CSF) from mouse, 2-mercaptoethanol, cholesterol, Sephadex® G-50, and octadecylamine were purchased from Sigma-Aldrich (St Louis, MO, USA). PD (98%) was obtained from Meilunbio (Dalian, China). Hydrogenated egg phosphatidylcholine (HEPC) was obtained from AVT (Shanghai, China). Polyvinylpyrrolidone-K17 (PVP-K17) and PVP-K30 were provided by BOAI NKY Pharmaceuticals Ltd. (Tianjin, China).
Preparation and characterization of OVA-PD-Lipos
OVA- and PD-loaded liposomes were prepared using the film dispersion method, and their particle size was reduced by filtration through polycarbonate membranes.12 Briefly, HEPC (13.0 mg), cholesterol (7.0 mg), and octadecylamine (1.1 mg) were dissolved in chloroform. After the chloroform was removed by rotary evaporation, a thin lipid film remained in the flask. The film was hydrated with 1 mL of drug solution (0.5 mg/mL for OVA and 0.4 mg/mL for PD) for 0.5 h, and the particle size of OVA-PD-Lipos was reduced and made uniform by filtration through a series of polycarbonate membranes using a mini-extruder (Avestin Inc. Ottawa, Canada). Membrane pore sizes (in sequence) were 400, 200, and 100 nm.
The mean particle size and zeta potential of OVA-PD-Lipos were measured by photo-correlation spectroscopy using a Nano ZS90 Zetasizer (Malvern Instruments Ltd, Worcestershire, UK). The entrapment efficiency of OVA in OVA-PD-Lipos was evaluated by filtering the OVA-PD-Lipos suspension through an ultracentrifugation tube (NMWL, 100 kDa, Merck KGaA, Darmstadt, Germany) at 4,500 rpm for 20 min, and measuring the OVA level in the filtrate. OVA entrapment efficiency was calculated as follows:
where Wt is the total amount of OVA added and Wf is the amount of free OVA.
The entrapment efficiency of PD in OVA-PD-Lipos was measured using the mini-column centrifugation method as described previously.13 OVA-PD-Lipos were separated from free PD by filtration through a Sephadex G-50-filling mini-column under centrifugation. The PD level in OVA-PD-Lipos was determined using high-performance liquid chromatography, and entrapment efficiency was calculated accordingly.
Hemolytic activity of OVA-PD-Lipos
Rabbit RBCs were used to test whether incorporation of PD into liposomes reduces the hemolytic activity of OVA-PD-Lipos. Rabbit blood was collected in a heparinized tube and fibers were removed by stirring the blood gently with a medical cotton stick. The RBCs were separated by centrifugation at 1,000 rcf for 10 min, then washed and centrifuged in normal saline four to five times. PD solution or OVA-PD-Lipos suspension (40 μg/mL) was incubated in three replicates with an equal volume of 1% RBC suspension for 30 min at 37°C. Following incubation, supernatant from each sample was collected after centrifugation at 1,000 rcf for 10 min, and absorbance was measured at 415 nm. A suspension of empty liposomes served as measurement reference (blank), and normal saline and distilled water served as negative and positive controls, respectively.
Toxicity of OVA-PD-Lipos
Cultured mouse BMDCs were used to evaluate whether incorporation of PD into liposomes reduces the toxicity of OVA-PD-Lipos. Bone marrow cells were withdrawn from the femurs and tibias of male C57BL/6 mice provided by the Experimental Animal Center, Shanghai University of Traditional Chinese Medicine, as reported previously.14 Then, the cells were depleted of RBCs with RBC lysis buffer solution. BMDCs were prepared and maintained in RPMI 1640 medium containing 10% fetal bovine serum and 1% penicillin/streptomycin supplemented with recombinant murine GM-CSF (20 ng/mL) and β-mercaptoethanol (50 nM). On days 3 and 5, half of the medium was replaced with fresh RPMI 1640 containing 10% fetal bovine serum and 1% penicillin/streptomycin supplemented with recombinant murine GM-CSF (40 ng/mL) and 50 nM or 50 μM β-ME. On day 7, BMDCs were harvested and seeded into 96-well plates at 1×105 cells per well, cultured for 24 h, then incubated with OVA-PD-Lipos (1–50 μg/mL, 6 wells per level) for another 24 h, with PD solution serving as a control. After the incubation, BMDC viability was measured using the MTT assay.15
Uptake of OVA-PD-Lipos by BMDCs
To evaluate whether the uptake of OVA is facilitated when loaded into liposomes, OVA was labeled with fluorescein isothiocyanate (FITC), and the uptake behavior of FITC-OVA-PD-Lipos was investigated using mouse BMDCs.
FITC-OVA was prepared as described previously.16 Briefly, 10 mg FITC and 50 mg OVA were dissolved in 5 mL carbonate buffer solution (220 mM, pH 9.6), and kept under darkness with magnetic stirring at 4°C for 18 h. Free FITC was removed by filtering the FITC-OVA solution through an ultracentrifugation tube (NMWL, 10 kDa, Merck KGaA) at 2,200 rcf for 20 min.
Mouse BMDCs were seeded into a 6-well plate at 2×106 cells per well, and maintained in RPMI 1640 medium containing 10% fetal bovine serum and 1% penicillin/streptomycin supplemented with recombinant murine GM-CSF (20 ng/mL) and β-mercaptoethanol (50 μM) for 24 h. FITC-OVA or FITC-OVA-PD-Lipos (100 μg/mL) were added and incubated with the BMDCs for 4 h. After incubation, BMDCs were separated, washed, and resuspended. The fluorescence of the suspensions was measured using a BD FACSCalibur flow cytometer (Becton, Dickinson and Company, Franklin Lakes, NJ, USA).
Fabrication of OVA-PD-Lipos-MNs
Hyaluronic acid microneedle arrays containing 200 (10×20) microneedles were used as master molds for fabricating OVA-PD-Lipos-MNs. Microneedle base diameter was 300 μm and height was 356 μm. Polydimethylsiloxane (PDMS) was poured over the master mold and heated at 80°C for 3 h. After the PDMS had cured thoroughly, the master mold was peeled off carefully, and the inverse microneedle mold (PDMS mold) was obtained.
OVA-PD-Lipos-MNs were fabricated as described previously with minor modifications.17 OVA-PD-Lipos were lyophilized and reconstituted in distilled water. The concentration of both OVA and PD was 2.5 mg/mL. PVP-K17 was dissolved in OVA-PD-Lipos suspension (1:2, w/w), and PVP-K30 was dissolved in distilled water (1:1, w/w). These solutions served as the microneedle matrix solution and the base substrate solution, respectively. The microneedle matrix solution was added onto the surface of the PDMS mold, forced into the cavities using centrifugation, and then dried in a sealed desiccator after pipetting residual solution from the surface of the PDMS mold. The base substrate solution was added on the surface of the PDMS mold, air bubbles were removed under vacuum, and the preparation was dried thoroughly. Then, the OVA-PD-Lipos-MNs were peeled off from the PDMS mold.
Physical stability of OVA-PD-Lipos in OVA-PD-Lipos-MNs
The physical stability of OVA-PD-Lipos in OVA-PD-Lipos-MNs was evaluated as described previously.17 OVA-PD-Lipos-MNs were dissolved in distilled water to release OVA-PD-Lipos. The morphology of the OVA-PD-Lipos after release was observed using a JEM-1400 transmission electron microscope (JEOL Ltd., Tokyo, Japan), and compared with empty liposomes or a suspension of OVA-PD-Lipos that had not been associated with MNs.
Chemical stability of OVA in OVA-PD-Lipos-MNs
The chemical stability of OVA in OVA-PD-Lipos-MNs was investigated using sodium dodecyl sulfate polyacrylamide gel electrophoresis (SDS-PAGE), with free OVA and OVA-PD-Lipos as controls. OVA was freed from OVA-PD-Lipos or OVA-PD-Lipos-MNs (after dissolving in distilled water) by the addition of 10% triton (w/w). SDS-PAGE was conducted using a 5% stacking gel and 10% separation gel. Samples were heated to 100°C, maintained at this temperature for 10 min, loaded onto the vertical slab gel, and subjected to electrophoresis at 60 mV for 30 min and then at 80 mV. After electrophoresis, gels were fixed and stained with Coomassie brilliant blue.
Insertion of OVA-PD-Lipos-MNs into skin
In vitro and in vivo experiments were conducted to evaluate whether OVA-PD-Lipos-MNs have sufficient mechanical strength to penetrate skin, dissolve rapidly, and release the subunit vaccine. To test skin penetration, OVA-PD-Lipos-MNs were inserted into mouse skin in vitro and held for 2 min. The treated mouse skin was stained with 0.4% trypan blue to observe the penetration site directly, or embedded into paraffin, cut into vertical slices, stained with hematoxylin–eosin, and observed using microscope. To test dissolving properties, OVA-PD-Lipos-MNs were inserted into mouse skin in vivo, held for 10, 30, or 60 s, and then the insertion site was imaged using a scanning electron microscope (JEM-1230, JEOL Ltd.). Finally, to test delivery efficiency, FITC-OVA-PD-Lipos was prepared as described and loaded into dissolving microneedle arrays. The arrays were inserted into nude mouse skin in vivo. The nude mice were provided by the Experimental Animal Center, Shanghai University of Traditional Chinese Medicine. As a control, medical gauze soaked with FITC-OVA-PD-Lipos suspension was applied to the skin. After 30 min, fluorescence intensity of the skin sample was measured using a fluorescence imaging system (IVIS Lumina XR, Caliper Life Sciences, Inc., Waltham, MA, USA).
Immunization of mice with OVA-PD-Lipos-MNs
The immunization efficiency of OVA-PD-Lipos-MNs was evaluated in Institute of Cancer Research (ICR) mice. Female mice (18±2 g, 5 weeks old) were obtained from the Experimental Animal Center, Shanghai University of Traditional Chinese Medicine, and divided randomly into 6 groups: OVA, OVA + PD, OVA-PD-Lipos, OVA-MNs, OVA-PD-MNs, and OVA-PD-Lipos-MNs (n=6 per group). Animals in each group were immunized first with 25 μg OVA and/or PD, and boosted with 25 μg OVA and/or PD 2 weeks later. Animals in the OVA, OVA + PD, and OVA-PD-Lipos groups were injected subcutaneously with OVA solution, OVA and PD solution, or OVA-PD-Lipos, respectively. Animals in the OVA-MNs, OVA-PD-MNs, and OVA-PD-Lipos-MNs groups were administered with OVA-MNs (free OVA-loaded dissolving microneedles), OVA-PD-MNs (free OVA- and PD-loaded dissolving microneedles), or OVA-PD-Lipos-MNs, respectively. Two weeks after the second immunization, blood samples were drawn from mice in each group, and centrifuged at 3,000 rpm for 20 min to obtain serum. OVA-specific IgG, IgG1, and IgG2b levels in the serum samples were measured using ELISA kits (Shanghai Xin Yu Biotech Co., Ltd., Shanghai, China), following the manufacturer’s instructions.
Evaluation of skin irritation caused by OVA-PD-Lipos-MNs
The potential for OVA-PD-Lipos-MNs to irritate normal skin after multiple-dose administration was investigated in accordance with OECD Guideline 404, “Acute Dermal Irritation/Corrosion”.18 New Zealand rabbits (2.0–2.5 kg) were divided randomly into four groups (blank control, blank MNs, OVA-PD-MNs, and OVA-PD-Lipos-MNs; n=4 animals per group). A small region on the left flank of each rabbit (~3×3 cm) was shaved with an electric clipper. After the rabbits had recovered for 24 h, they were inspected visually for skin damage. Rabbits without skin damage were enrolled in the experiments. Rabbits in the blank MNs, OVA-PD-MNs, and OVA-PD-Lipos-MNs groups were treated with blank MNs, OVA-PD-MNs (free OVA- and PD-loaded microneedles), or OVA-PD-Lipos-MNs, respectively, once daily for 3 consecutive days. The microneedles were inserted into shaved rabbit skin, held for 3 min, fixed with medical tape for 4 h and then removed. After removal, the treated skin was cleaned with warm distilled water. The treated area was inspected visually for skin irritation and images were recorded before each treatment, 1 h after microneedle removal following the first and second treatments, and 1, 24, 48 and 72 h after removal of the microneedles following the final treatment. Rabbits in the blank control group were observed in parallel with the other groups.
The Institutional Animal Ethical Committee of the Shanghai University of Traditional Chinese Medicine approved the experimental procedures and all procedures followed the guidelines of the Institutional Animal Ethical Committee of the Shanghai University of Traditional Chinese Medicine.
Data are expressed as the mean ± SD. One-way analysis of variance was used to determine significance among the treatment groups, after which least significant difference–t-test were used for comparison between individual groups. A value of P<0.05 was considered to be significant.
Results and discussion
Characterization of OVA-PD-Lipos
The mean particle size of OVA-PD-Lipos was 135.8 nm. The liposomes were relatively uniform in size, as indicated by their small polydispersity index (0.137). The Zeta potential of OVA-PD-Lipos was 45.7 mV, which might be attributed to the addition of octadecylamine in the formulation of OVA-PD-Lipos. The entrapment efficiencies of OVA and PD in OVA-PD-Lipos were 58.98%±4.01% and 46.19%±2.65%, respectively.
Hemolytic activity of OVA-PD-Lipos
Hemolysis is the primary toxic effect of PD and other saponin adjuvants.13 Using rabbit RBCs, the hemolytic activities of OVA-PD-Lipos, PD solution, blank liposomes, and normal saline were compared. As shown in Figure 1, PD solution caused severe hemolytic activity, as indicated by its high hemolysis percentage (nearly 70%), whereas OVA-PD-Lipos exhibited far lower hemolytic activity (<7%), similar to blank liposomes and normal saline. This result demonstrates that the hemolytic effects of PD can be reduced dramatically when PD is incorporated into liposomes, consistent with previous reports.13
Figure 1 Hemolytic activity of OVA-PD-Lipos in rabbit RBCs (n=3).
Toxicity of OVA-PD-Lipos to BMDCs
Because DCs play a vital role in the elicitation of the immune response by vaccines, it is important to demonstrate that their function is not compromised by OVA-PD-Lipos. OVA-PD-Lipos toxicity was tested using cultured mouse BMDCs, and compared to the toxicity exhibited by PD solution. As shown in Figure 2, free PD exhibited obvious toxicity to BMDCs at concentrations over 5 μg/mL, and BMDC viability was <10% when the concentration of free PD reached 20 μg/mL. In contrast, OVA-PD-Lipos exhibited minimal toxicity to BMDCs, and BMDC viability was never below 70% across the range of PD concentrations tested (1–50 μg/mL). These data demonstrate that PD is dramatically reduced in toxicity when incorporated into liposomes. Interactions between saponin and cholesterol in the cell membrane, and the resulting membrane damage, may underlie saponin-induced hemolysis and other toxicities.19 The incorporation of PD into OVA-PD-Lipos may reduce interactions with cholesterol and account for the reduction in toxicity to mouse BMDCs as well as the reduction in hemolytic activity.
Figure 2 Toxicity of OVA-PD-Lipos to cultured mouse BMDCs (n=6).
Uptake of OVA-PD-Lipos by BMDCs
The uptake and presentation of subunit vaccine by DCs are crucial steps in subunit vaccine mediated immunization. The uptake behavior of OVA-PD-Lipos was investigated in comparison with OVA solution, using cultured mouse BMDCs as a model. OVA uptake increased more than one order of magnitude when OVA was incorporated into liposomes (Figure 3). A possible explanation is that uptake through endocytosis is facilitated by nanoscale carriers loaded with subunit vaccines, as reported previously.20 Recently, it has been reported that the targeting efficiency of nanoparticles to DCs might be improved by surface modification of ligands to receptors overexpressed on DC’s surface.21 To further improve the DC targeting efficiency of subunit vaccine delivery system, surfacially modified nanoparticles might be incorporated into the dissolving microneedle array.
Physical stability of OVA-PD-Lipos in OVA-PD-Lipos-MNs
The physical stability of OVA-PD-Lipos in OVA-PD-Lipos-MNs was investigated using transmission electron microscopy. Loaded microneedles were dissolved in distilled water, and their morphology was compared with suspensions of OVA-PD-Lipos and blank liposomes. OVA-PD-Lipos released from dissolving microneedles were smooth, spherical particles, relatively uniform in size, and nearly identical in appearance to OVA-PD-Lipos and blank liposomes (Figure 4). OVA-PD-Lipos in suspension and after release from dissolving microneedle arrays were slightly larger than empty liposomes, possibly due to the incorporation of OVA and PD. These results suggest that OVA-PD-Lipos in dissolving microneedle arrays exhibit good physical stability.
Chemical stability of OVA in OVA-PD-Lipos-MNs
The chemical stability of OVA in OVA-PD-Lipos-MNs was investigated using SDS-PAGE. As shown in Figure 5, only one band was observed in lanes containing OVA-PD-Lipos or OVA-PD-Lipos-MNs. The bands comigrate with the 44-kDa protein marker, which has a similar molecular weight as free OVA (lane B). This result indicates that OVA has good chemical stability when OVA-PD-Lipos are incorporated into dissolving microneedles.
Insertion of OVA-PD-Lipos-MNs into skin
The behavior of OVA-PD-Lipos-MNs inserted into skin was investigated in vitro and in vivo. As shown in Figure 6, an array of needle holes is observed after insertion of OVA-PD-Lipos-MNs into mouse skin in vitro. Obvious needle holes are also visible in a vertical slice through the treated skin. These results demonstrate that OVA-PD-Lipos-MNs insert reliably into skin. OVA delivery by the microneedles was tested in vivo using FITC-OVA. Nude mice treated with FITC-OVA-PD-Lipos-MNs exhibited intense fluorescence, showing that the dissolving microneedle arrays effectively deliver OVA into skin (Figure 7). In contrast, no fluorescence is observed if the skin is treated using FITC-OVA-PD-Lipos, demonstrating that OVA penetrates minimally into intact skin through passive diffusion, even if incorporated into liposomes. The exclusion is probably due to the high molecular weight of FITC-OVA-PD-Lipos. As shown in Figure 8, OVA-PD-Lipos-MNs dissolve within 1 min after insertion into mouse skin in vivo. Together, these results demonstrate that the dissolving microneedle array system can effectively deliver, and rapidly release, subunit vaccines into skin.
Figure 8 Dissolution of OVA-PD-Lipos-MNs after insertion into mouse skin in vivo.
Immunization of mice using OVA-PD-Lipos-MNs
The immunization efficiency of OVA-PD-Lipos-MNs was compared in ICR mice with five preparations: free OVA, free OVA loaded into dissolving microneedles, OVA- and PD-loaded into dissolving microneedles, free OVA plus PD, and OVA-PD-Lipos (OVA, OVA-MNs, OVA-PD-MNs, OVA + PD, and OVA-PD-Lipos, respectively). After immunization, OVA specific IgG, IgG1, and IgG2b levels in mouse serum were measured (Figure 9).
The lowest mean OVA-specific IgG levels were seen in mice immunized with OVA solution alone or with OVA-MNs. These were statistically indistinguishable, but were significantly different (P<0.05) from the higher OVA-specific IgG levels observed in mice immunized with PD + OVA, OVA-PD-MNs, or OVA-PD-Lipos. The difference demonstrates that immunization efficiency is improved when OVA is combined with adjuvant. The highest OVA-specific IgG level, exhibited by mice immunized with OVA-PD-Lipos-MNs, was significantly different from all the others (P<0.05). Immunization efficiency is clearly enhanced when OVA is combined with adjuvant and an effective delivery system. This is consistent with results presented earlier showing that loading OVA-PD-Lipos into dissolving microneedle arrays enhances physical targeting efficiency (Figure 7), and with our results showing that incorporating OVA and PD into liposomes enhances uptake of OVA-PD-Lipos by BMDCs (Figure 3), possibly via endocytosis. It is, therefore, likely that the high OVA-specific IgG level exhibited by mice immunized with OVA-PD-Lipos-MNs is the result of increased uptake of OVA by DCs, due to the microneedle delivery system as well as the positive immunogenic effect of PD adjuvant.
The results obtained for IgG1 or IgG2b levels were similar to those obtained for IgG, except that IgG1 or IgG2b levels in mice immunized with OVA versus OVA + PD were statistically indistinguishable. OVA’s immunization efficiency is only slightly enhanced when it is simply combined with adjuvant. Alternatively, the IgG1 and IgG2b subclasses of IgG may be less responsive to adjuvant than IgG. Compared with mice immunized with OVA alone (OVA solution or OVA-MNs), higher levels of IgG1 and IgG2b were observed in all mice when OVA was combined with PD, except for mice immunized with OVA + PD. This suggests that PD not only increases OVA’s immunization efficiency, but also elicits a balanced Th1 and Th2 type humoral immunity response, consistent with suggestions that PD can be used as an adjuvant in both prophylactic and therapeutic vaccines.3
Evaluation of skin irritation caused by OVA-PD-Lipos-MNs
Because a goal of this study is to evaluate PD-Lipos-MNs as a vehicle for the intradermal delivery of vaccines, the ability of OVA-PD-Lipos-MNs to provoke skin irritation was investigated using rabbits. Animals were treated with OVA-PD-Lipos-MNs and controls once daily for three consecutive days and then visually monitored (Figure 10). Microneedles loaded with PD + OVA produced the most serious irritation response, which disappeared 72 h after the last treatment. In contrast, no skin irritation occurred in untreated rabbits (blank control group), in rabbits treated with blank dissolving microneedle arrays, or in those treated with OVA-PD-Lipos-MNs. These results demonstrate that PD toxicity is reduced dramatically when incorporated into liposomes and loaded into dissolving microneedle arrays, and are consistent with the hemolytic activity and cell toxicity experiments described earlier.
The immune response of ICR mice to the model subunit vaccine OVA was significantly enhanced when OVA and its adjuvant were incorporated together into a dissolving microneedle delivery system. PD, a novel saponin adjuvant, elicited a balanced Th1 and Th2 type humoral immune response when combined with OVA, and may serve as potent adjuvant for both prophylactic and therapeutic vaccines. The dissolving microneedle array based system is a promising delivery vehicle for a subunit vaccine and its adjuvant.
This work was supported by the Program from Shanghai University of Traditional Chinese Medicine (No 2015YSN09).
The authors report no conflicts of interest in this work.
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