The PLGA nanoparticles for sustainable release of CGRP to ameliorate the inflammatory and vascular disorders in the lung of CGRP-deficient rats.

The calcitonin gene-related peptide (CGRP) has been demonstrated relating to vascular and inflammatory regulations not only the nerve systems. As the anti-inflammation factor and the most potent vasodilator, the CGRP holds therapeutic potentials for the treatment of cardiovascular diseases which was, however, limited by its peptide nature and short half-life. With advantages in improving the stability, circulation time and protection from degradation, the nanoparticles were promising as delivery carriers for the peptide. Nevertheless, few nanoparticulate systems were developed to deliver the CGRP peptide for the modulation of vascular or inflammatory functions instead of neural regulation. In this study, the CGRP was encapsulated into the poly (lactic-co-glycolic acid) (PLGA) nanoparticle for sustained release of CGRP in vivo. The nanoparticles recovered the systemic level of CGRP and the vascular inflammatory factors in the CGRP+/- rats comparing to the administration of (Dulbecco's Phosphate Buffered Saline) DPBS or peptide only. With the decrease of vascular wall thickness and the attenuation of the T cell infiltration in the lung, the polymer based CGRP delivery system showed potentials to facilitate the therapeutic effects of the CGRP which may help for the development of CGRP-based therapy in vascular and inflammatory disorder related diseases.

Introduction

As a 37 amino acid neuropeptide, the CGRP was mainly secreted by central and peripheral nervous systems and was known playing important roles in neurotransmission [1]. The CGRP has two known isoforms (α-CGRP and β-CGRP) whereas the α-CGRP is the most abundant form (>80%) in the nervous systems [2]. Besides its neural functions, the α-CGRP was also known functioning in vascular and inflammatory regulations since the wide distribution of its receptor including in the endothelial cells [3], smooth muscle cells [4], dendritic cells [5], bone marrow cells [6], macrophages [7] and lymphocyte cells [8]. The CGRP is the most potent endogenous vasodilator identified to date [9]. After stimulated by the CGRP, the endothelial cells activated the eNOS enzyme to release NO via the Gαs-adenylate cyclase-cAMP-PKA pathway and the free diffusion of NO activated the NO/cGMP/PKG signaling pathway in the smooth muscle cells, which led to the relaxation of blood vessels [10]. The CGRP could promote the proliferation of endothelial cells and apoptosis of smooth muscle cells, which lead to the beneficial effects in ischemia and hyperplasia [11-13]. Encapsulated in the chitosan-strontium-calcium phosphate cement, the CGRP could promote the proliferation of endothelial cells in vitro, suggesting the therapeutic potentials to regulate the vascular systems [3].

The CGRP was also considered to be the synthetic product of the immune system, playing a corresponding immunomodulatory role in macrophages [14], neutrophils [15], dendritic cells [16], B lymphocyte [17], T lymphocyte [18], and other immune cells [19]. Having the effects to inhibit the pro-inflammatory factors such as TNF-α, IFN-γ, IL-2, IL-1β or IL-8 and up regulate the IL-10 and IL-4, the CGRP acts as an anti-inflammatory factor [20-22]. After the administration of exogenous CGRP, the inflammatory cytokines such as the TNF-α, IL-1β, IL-8 and IL-6 were decreased and the therapeutic effects were found in the rats with the severe necrotizing pancreatitis [23,24]. Besides, the CGRP can also prevent inflammatory liver injury in mice [25]. All that indicated the CGRP as therapeutics for the treatment of inflammation-related diseases.

Despite the potentials in modulating vascular and inflammatory functions, the short half-life of the CGRP (<10 min) with peptide nature hampered its translational applications [26]. To prolong the half-life, an α-CGRP analogue acylated with an albumin-binding fatty acid moiety allowing reversible albumin binding was developed which showed protective effects against end-organ damage in hypertension, cardiac hypertrophy and heart failure [27]. Nevertheless, the functional mechanism of the albumin-binding α-analogue, e.g. the binding ability to the vascular CGRP receptor, comparing to its native form still needed to be elucidated [28]. Nanoparticulate systems avoid the chemical modification of peptides and keep their natural properties, having been known to improve the stability, half-life and the distribution of drugs in vivo. The polyethylenimine (PEI) linked chitosan was utilized to deliver the plasmid CGRP for fracture healing [23]. A Tat peptide-decorated gelatin-siloxane (Tat-GS) nanoparticle was demonstrated to encapsulate the plasmid DNA of CGRP to attenuate cerebral vasospasm and improve neurological outcomes in a rat model of subarachnoid hemorrhage [29]. However, the nanoparticle-based delivery systems to exert the function of CGRP peptide itself have less been developed.

Therefore, the study aimed to investigate the potential of nanoparticulate system to deliver the CGRP peptide with sustainable release property to prolong the interaction of the peptide with biological surroundings in vivo. Having been approved by the FDA, the poly(lactic-co-glycolic acid) (PLGA) was widely used for the delivery of drugs [30-33]. The polyethylene glycol (PEG) was demonstrated to prevent the nanoparticles from ingestion and clearance by macrophages, prolong circulation time, increase the distribution of diseased tissue and block protein adsorption and cellular influence [34-36]. In this study, using the nanoprecipitation method, a facial fabrication strategy was developed to encapsulate the CGRP in the PLGA modified with PEG for sustained release of the peptide in vivo. To preliminarily demonstrate the efficiency of the delivery system, the nanoparticles were intravenously administered to the CGRP+/− deficient rats and the functions to regulate the immune response and vascular structure were investigated. Using a conventional nanoparticulate system, the study demonstrated the translational potentials of the CGRP peptide as drug for the treatment of cardiovascular or inflammatory related diseases.

Materials and methods

Materials

DPBS was obtained from Hyclone (Logan, Utah, America). PLGA (50:50) (RG502H) and PLGA-b-PEG were from Sigma. 4% polyformaldehyde (PFA) was purchased from the Servicebio (Wuhan, China). α-CGRP was purchased from GL Biochem (Shanghai, China) Ltd. DMSO was obtained from Beyotime Biotechnology (Shanghai, China). Dialysis bags (MWCO: 10000 Da) were purchased from Shanghai Yuanye Bio-Technology Co., Ltd (Shanghai, China). Other chemicals and instruments used were specified in each experiment.

Fabrication of nanoparticles

After dissolving the CGRP with PLGA in the DMSO, the oil phase was dropwise added into the water to form nanoparticles. To optimize the fabrication process, the volume ratio of oil phase to water phase, the weight ratio of CGRP to PLGA and the time of evaporation were adjusted. The final conditions to avoid the formation of aggregates were utilized for following experiments. The PLGA-PEG nanoparticles with or without the CGRP loading were fabricated as the PLGA nanoparticles.

Characterization of nanoparticles

The particle size and polymer dispersity index (PDI) were measured using the dynamic light scattering (DLS) method of the LiteSizer (Anton Paar, Shanghai, China). The zeta potential was measured by diluting NPs appropriately with distilled water, which was then analyzed using the electrophoretic mobility method on the same instrument. To investigate the stability of nanoparticles, the sizes and zeta-potentials of 1 mg/mL nanoparticle solutions were analyzed at indicated time points after the fabrication. Statistical analysis was calculated from 3 duplicate samples.

The morphology of NPs was examined with a FEI 200 kV transmission electron microscopy (TEM, Tecnai G2, America) after negative staining with 1 wt% uranyl acetate Briefly, 5 μL of nanoparticle suspension (10 mg/mL) was deposited onto a 400-mesh carbon-coated copper grid (Beijing Zhongjingkeyi Technology Co., Ltd). Ten minutes after the sample was deposited, the grid was rinsed with 5 drops of distilled water, followed by staining with a drop of 1 wt% uranyl acetate. The grid was subsequently dried and visualized using the FEI 200 kV Sphera microscope.

Loading efficiency and cumulative release

The CGRP loaded nanoparticles were first frozen at −80 °C and then freeze-dried with a lyophilizer. Then, the nanoparticles lyophilized powder was dissolved in DMSO, and the absorbance was measured with Nanodrop 2000 spectrophotometer (Thermo Fisher Scientific, US) at 260 nm. According to the preestablished standard curve of CGRP in DMSO, the drug loading efficiency (LE) and drug encapsulation efficiency (EE) were calculated as follows: where MCGRP is the mass of CGRP loaded in the NPs, MPLGA is the mass of polymer in the formulation and Madded is the mass of CGRP added. Three independent replicates were used for each group.

The drug (CGRP) released from PLGA-CGRP (PC) and PLGA-PEG-CGRP (PPC) nanoparticles was studied separately using a dialysis method. Briefly, 1 mL PC and PPC solutions (containing 100 μg CGRP) were added to dialysis bags (MWCO: 10000 Da). The dialysis bags were then immersed in 5 mL of phosphate-buffered saline (PBS) solution (release medium, pH 7.4) at 37 °C on a constant temperature oscillator (SHA-C, Changzhou Guohua electrics co., ltd, China) with shaking speed of 120 rpm. 500 μL of release medium was collected for analysis at different time intervals and replaced with an equivalent volume of fresh PBS at 37 °C. The cumulative amount of the released CGRP was quantified by Nanodrop 2000 spectrophotometer (Thermo Fisher Scientific, US) at 260 nm and statistical results were analyzed from three measurements for each sample.

Treatment of nanoparticles in the CGRP+/− rats

All the animal care and experimental protocols were performed in accordance with protocols reviewed and approved by the Animal Ethical and Experimental Committee of the Fujian Medical University. Animals were housed in rat cages under a temperature-controlled environment (20–22 °C) with 12:12-h light/dark cycles, with ad libitum access to drinking water and standard rat chow. Male Sprague-Dawley wild-type (WT) rats (200–250 g, 8–10 w) were obtained from GemPharmatech Co., Ltd. The α-CGRP knockout (α-CGRP+/−) rat model was generated as described [37]. After the fertilization, the heterozygous α-CGRP ± rats were utilized for animal studies. All animals were weighed and then randomly assigned to receive: DPBS, free CGRP, PLGA-CGRP and PEG-PLGA-CGRP nanoparticles with the dose of 50 nmol/kg of CGRP and injection volume of 500 μL/200 g. After the intravenous administration once a week for four times, the rats were euthanized and the blood and organs were extracted at 1 week post the final injection of nanoparticles.

Hematoxylin-eosin and immunohistochemistry staining

The main organs (heart, lung, liver, kidney, spleen and pancreas) were excised and immersion-fixed in 4% PFA for at least 12 h. Then, the cross-sections were prepared and stained with hematoxylin and eosin (H&E) (G1003, Servicebio, Wuhan, China). To investigate the distribution of T cells in the lung, the CD3 immunohistochemical staining was analyzed. After deparaffinzing, rehydrating, antigen retrieval, blocking endogenous peroxidase activity and serum sealing, the sections were incubated with CD3 primary antibody (1:200 dilution, Abcam, Cambridge, England) and secondary antibody (HRP labeled) (Servicebio, Wuhan, China). All the sections were imaged under an Upright optical microscope (Nikon Eclipse E100, Japan) and Imaging system (Nikon, Nikon DS-U3), following the DAB chromogenic reaction, nucleus counterstaining dehydration and mounting.

Elisa

The concentrations of CGRP, IL-6, IL-8, TNF-α, IL-1β, IL-4, IL-10 and VEGF from the serum and the lung samples were analyzed using the ELISA kits according to the manufacturer’s instructions (Jiangsu Meimian industrial Co., Ltd). Briefly, after the adding of standard, sample and enzyme solutions successively, the plates were incubated for 60 min at 37 °C. After the chromogen solution was added to the well and reacted at 37 °C for 15 minutes, the absorbance of the plate was read at 450 nm within 15 minutes after the termination solution was added.

qPCR

The total RNA of lungs was extracted using the Eastep® Super Total RNA Extraction Kit (Shanghai Promega Biotech Co., Ltd, Beijing China), followed by reverse transcription into cDNA using 5× FastKing-RT SuperMix (TIANGEN Biotech (Beijing) Co., Ltd). Then the gene expression levels were analyzed using the SYBR Green real-time PCR kit (TIANGEN Biotech (Beijing) Co., Ltd) and quantified with the Bio-Rad CFX96 Real time PCR System (Bio-Rad, Hercules, CA). The gene expression levels were normalized to GAPDH values respectively and the relative expression was measured by the comparative CT method. The mean gene expression level was calculated from 3 duplicate samples. The Table 1 showed the primers used.

Table 1.

The sequences of primers used in this study.

	Forward	Reverse
GAPDH	AGGTTGTCTCCTGTGACTTCA	TGTTGCTGTAGCCATATTCATTGT
IL-1β	GCTACCTATGTCTTGCCCGT	TCACACACTAGCAGGTCGTC
IL-6	GACTTCCAGCCAGTTGCCTT	CTGGTCTGTTGTGGGTGGTAT
VEGF	TTACTGCTGTACCTCCACCAT	CAGGACGGCTTGAAGATATACTC
PKA	GCTATATTCAGGTGACAGACTTCG	TAACCAGCAGCCATCTCGTA
PKG	TCCTAGATCACCGAGGTTATGC	GCCAGTCAGAAGCTCATACATC
IL-10	GTGGAGCAGGTGAAGAATGATT	CACGTAGGCTTCTATGCAGTTG
IL-4	CAAGTCTGGGGTTCTCGGTG	AGTGTTGTGAGCGTGGACTC
eNOS	GCTGCCACCTGATCCTAACT	GCTGCCACCTGATCCTAACT

Statistical analysis

Statistical comparisons among above three groups were analyzed by one-way ANOVA analysis followed by Tukey’s multiple comparison test. All statistical tests were conducted using GraphPad Prism software. p < .05 was considered to be statistically significant.

Results and discussion

Fabrication and characterization of nanoparticles

The PLGA nanoparticles (P NPs) were obtained via a nanoprecipitation method. After dissolving the CGRP with PLGA in the DMSO, the oil phase was added into the water to form nanoparticles. To optimize the fabrication process, the volume ratio of oil phase to water phase, the weight ratio of CGRP to PLGA and the time of evaporation were adjusted and the increase of these parameters led to the formation of aggregates. At 1:10 volume ratio of oil to water phase and 1:100 weight ratio of CGRP to PLGA, almost no aggregates were found in the solution (Supplemental Table 1) which could be observed and demonstrated by the photo of the final nanoparticle solutions and the distribution width of the diameters (Supplemental Figure 1). The optimized conditions were utilized to fabricate the following P NPs with (P-C NPs) or without the loading of CGRP and the PLGA-PEG nanoparticles (PP NPs) with (PP-C NPs) or without the CGRP loading. After the loading of the CGRP, the UV-VIS spectrum of P-C NPs showed a peak at 260 nm, like the CGRP, while the spectrum of P NPs didn’t show the same peak (Supplemental Figure 2), demonstrating the successful loading of the CGRP in the P-C NPs. The encapsulation efficiency and the loading efficiency of CGRP in the P-C NPs were 41.16 ± 3.90% and 0.41 ± 0.04% respectively. With the PEGylation of PLGA, the encapsulation efficiency and the loading efficiency increased to 60.24 ± 11.76% and 0.60 ± 0.12% respectively. Through the interfacial turbulences occurring at the interfaces of solvent and the non-solvent which resulted from the complex and cumulated process such as flow, diffusion and surface tension variations, the nanoprecipitation offered a rapid and facile strategy to fabricate small nanoparticles [38,39]. Due to the resistance forces between hydrophilic peptide and hydrophobic PLGA molecules, the diffusion of CGRP was very fast when contacted with the water phase which may result in the relatively lower loading efficiency of the peptide comparing to the double emulsion method [40-42]. However, the final loading efficiency, in this study, was comparable to other studies using the nanoprecipitation strategy with loading efficiencies ranging from 0.2% to 0.5% [43-46]. The PEG with hydrophilicity may retard the diffusion of the peptide which may lead to the higher loading efficiency comparing to the PLGA without modification.

Under the TEM imaging, the nanoparticles showed the round shapes which were not changed by the loading of CGRP (Figure 1(A)). The encapsulation of CGRP increased the hydrodynamic diameter of P NPs from 101 ± 1.6 nm to 150 ± 2.7 nm and the diameter of PP NPs from 122 ± 0.2 nm to 131 ± 1.5 nm (Figure 1(B)). The PDI below 20% demonstrated the uniform sizes of the nanoparticles (Figure 1(B)). Having a positive charge (2.7 ± 0.2), the CGRP raised the zeta-potentials of P-C NPs and PP-C NPs comparing to P NPs and PP NPs respectively (Figure 1(C)). When the nanoparticles were stored in the water, little alterations of diameters (Figure 1(D)) or zeta-potentials (Figure 1(E)) occurred, suggesting the stability of the nanoparticles.

Figure 1.

(A) TEM images, (B) diameter and (C) zeta-potentials of nanoparticles. Long term stability of the (D) diameter and (E) zeta-potential of nanoparticles in the water. (F) The sustained-release profile of CGRP from P-C NPs and PP-C NPs in the PBS under 37 °C for 120 h. (Mean ± SD, n = 3). (scale bar in magnified image, 100 nm).

As shown in Figure 1(F), there was an initial burst release of CGRP during the first 24 h for both P-C NPs and PP-C NPs in the PBS buffer which may result from the CGRP molecules embedding at the outermost layers and absorbing to the surfaces of the nanoparticles. After the first initial burst, the nanoparticles showed the sustained-release pattern and had an overall about 20% and 40% of CGRP release from P-C NPs and PP-C NPs respectively within 120 h. The diffusion of drugs, erosion and swelling of the polymer matrix and degradation of the polymer could all contribute to the release of the drugs from nanoparticles [47]. In this study, the slow degradation rate of PLGA and diffusion of the CGRP may lead to the sustained-release profile of CGRP [48]. It was worthy to mention that the release of CGRP from PP-C NPs was higher and faster than P-C NPs. The PEGylation increased the hydrophilicity of the nanoparticles to allow more water molecules to incorporate into the nanoparticles which may accelerate the degradation of the polymer [49]. Besides, the particle size, porosity and hardness of the PEGylated nanoparticles may also contribute to the release characteristics of CGRP [50].

The regulation of factors in serum by the nanoparticles

To investigate the efficiency of the PLGA loaded CGRP, the nanoparticles were administered to the CGRP+/− rats in which the expression of CGRP was deficient (Figure 2(A)). After the treatment for one month, the administration of PP-C NPs recovered CGRP in serum of CGRP+/− rats to the level of wild type (WT) rats, comparing to the treatment of DPBS, CGRP peptide only and P-C NPs (Figure 2(B)). It demonstrated the ability of PEGylated nanoparticles to protect the CGRP from fast elimination and the sustainable release maintained the CGRP concentration in serum at a comparable level to the wild type. To elucidate the effects of the recovery of CGRP level, the pro- and anti-inflammatory factors in serum were analyzed. Interestingly, as shown in Figure 2(B), the deficiency of CGRP increased the levels of pro-inflammatory factors (IL-1β and IL-8), anti-inflammatory factors (IL-10 and IL-4) and the vascularization related factor (VEGF) in circulation. The administration of P-C NPs and PP-C NPs showed the tendency to down regulate all of the factors in serum while the treatment of CGRP had lower or no down-regulation effects. For the regulation of IL-8 and VEGF, the P-C NPs and PP-C NPs decreased the levels to the similar extents. However, the reduction of the IL-1β, IL-10 and IL-4 levels in the PP-C NPs group were higher than the P-C NPs. All that suggested the ability of PP-C NPs to recover the CGRP in long-term and regulate the systemic inflammatory factors to the normal level.

Figure 2.

(A) Scheme of experiment design to investigate the function of CGRP loaded nanoparticles to modulate inflammatory and vascular factors in CGRP+/− rats. (B) Concentration of the CGRP and other factors in serum post the administration in the CGRP+/− rats comparing to the wild type. (Mean ± SEM, n = 3; *, p < .05; **, p < .01; ***, p < .001).

The inflammatory and vascular modulation in the lung by the nanoparticles

The CGRP was previously found to reduce the thickness of the vascular wall and ameliorate the function of vasculature in the artery injury model or cardiovascular diseases such as hypertension or ischemia [11,13,27,29]. In the CGRP+/− rats, the thickness of the vascular wall in the lung was increased comparing to the wild type (Figure 3(A)) whereas no changes occurred in other organs including the liver, spleen, kidney, heart and pancreas (Supplemental Figure 3). Previous studies have demonstrated the ability of CGRP to induce the pulmonary vasodilation and increase the diameter of pulmonary blood vessels [4,51-53]. In this study, the administration of P-C NPs or PP-C NPs reduced the wall thickness but the CGRP peptide only did not recover the vascular structures, suggesting the superiority of CGRP encapsulated nanoparticles to modulate pulmonary vasculatures comparing to free CGRP peptide (Figure 3(A)). In addition to the pulmonary vessels, the CGRP has also been demonstrated relating to the immunomodulation in lung tissue [2]. Corresponding to previous study, the study here found the accumulation of T cells around the pulmonary blood vessels in the CGRP+/− rats. Comparing to the treatments of DPBS, CGRP and P-C NPs, the PP-C NPs decreased the T cell number around the vessels to the WT level (Figure 3(B)) which proved the efficiency of PP-C NPs to modulate the pulmonary inflammation.

Figure 3.

(A) Hematoxylin-eosin (HE) staining and (B) CD3+ T cell immunohistochemistry staining of the lung sections after different treatments. The outer and inner surfaces of the blood vessels in (A) were outlined by the black dashed lines and the thicknesses of the vascular walls were indicated by the distances from the outer surfaces to the inner surfaces which were marked out by the black full lines.

To further demonstrate the inflammatory and vascular modulation of nanoparticles, the lung tissues were homogenized and the expression of these factors at protein and mRNA level was investigated. The P-C NPs and PP-C NPs increased the CGRP to the WT level while the administration of peptide only did not (Figure 4(A)). Previous in vitro analysis has shown the diphasic controlled release ability of CGRP loaded nanoparticles despite only 20% and 40% of CGRP released in the P-C NPs and PP-C NPs respectively within 120 h. Actually, the release rate of the peptide in vivo would be accelerated due to the complex environment such as the enzymes, interstitial fluid and local pH [54,55]. The study demonstrated the superiority of nanoparticles to control the release and maintain the high levels of CGRP in vivo which may result in the therapeutic effects of the drug-loaded nanoparticles. Corresponding to the analysis in serum, the administration of PP-C NPs showed the greatest ability to restore the IL-1β, IL-10 and IL-4 proteins to the normal WT level in the lung of the CGRP+/− rats (Figure 4(A)). The expression of VEGF, which was related to the proliferation of endothelial cells and angiogenesis [56,57], was also up-regulated to the WT level after the administration of P-C NPs and PP-C NPs comparing to the injection of DPBS or peptide only (Figure 4(A)). It was interesting that the VEGF showed an opposite change in the serum and the lung after the deficiency of CGRP in the DPBS control group comparing to the WT rats which may be related to the complicated roles of VEGF. Previous studies have also reported that, in the lung injury, the serum VEGF was increased to enhance the vascular permeability and infiltration of inflammatory cells but the VEGF in the lung was decreased to induce pulmonary endothelial cells death both of which aggravated the preexisting lung injury [58,59]. The treatment of P-C NPs or PP-C NPs recovered the VEGF to the normal balance in the serum and lung tissue due to the recovery of CGRP level. All that suggested the superiority of nanoparticles comparing to CGRP treatment at the protein level. However, at the mRNA level, the CGRP group showed similar effects with the P-C NPs and PP-C NPs groups (Figure 4(B)). With the deficiency of CGRP, the mRNA expression of IL-1β, IL-6 and IL-4 were increased while the IL-10 was decreased. After the treatment of CGRP, P-C NPs and PP-C NPs, the mRNA of IL-1β, IL-6 and IL-4 was down-regulated to the WT level. The CGRP was reported to activate the PKA pathway, promote the expression of eNOS and release of NO in endothelial cells, which activated the PKG pathways in the smooth muscle cells and led to the relaxation of blood vessels [12,60,61]. In this study, the administration of CGRP, P-C NPs or PP-C NPs all similarly decreased the mRNA expression of PKA and PKG to the WT level comparing to the DPBS group. The expression of eNOS and VEGF at the mRNA level after the treatment of PP-C NPs were increased comparing to the administration of CGRP and P-C NPs, which may indicate the ability of PP-C NPs to increase the pulmonary vasodilation.

Figure 4.

(A) Contents of CGRP and other factors in the lungs after the treatment of nanoparticles in the CGRP+/− rats comparing to wild type rats. (B) mRNA expression of factors in the CGRP+/− rats comparing to wild type rats post the treatments. (Mean ± SEM, n = 3; *, p < .05; **, p < .01, ****, p < .0001).

Conclusion

To sustainably release the CGRP for prolonging the interaction of CGRP with surrounding cells, the PLGA/PLGA-PEG nanoparticles were fabricated via a facial nanoprecipitation method. The nanoparticles containing CGRP showed the reduction of the thickness of vascular wall, decrease of T cell infiltration and adjustment of anti- or pro-inflammatory factors to the WT level in the lung of CGRP+/− rats, demonstrating the potentials of CGRP loaded nanoparticles to modulate the vascular and inflammatory functions in diseases. The study showed the ability of nanoparticles to facilitate the function of CGRP in vivo which may have translational significance for CGRP in vascular and inflammatory disorders related diseases.

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