Enhanced Anti-Brain Metastasis from Non-Small Cell Lung Cancer of Osimertinib and Doxorubicin Co-Delivery Targeted Nanocarrier.

PURPOSE: Currently, the treatment of brain metastases from non-small cell lung cancer (NSCLC) is rather difficult in the clinic. A combination of small molecule-targeted drug and chemo-drug is a promising therapeutic strategy for the treatment of NSCLC brain metastases. But the efficacy of this combination therapy is not satisfactory due to the blood-brain barrier (BBB). Therefore, it is urgent to develop a drug delivery system to enhance the synergistic therapeutic effects of small molecule-targeted drug and chemo-drug for the treatment of NSCLC brain metastases.
METHODS: T7 peptide installed and osimertinib (AZD9291) loaded intracellular glutathione (GSH) responsive doxorubicin prodrug self-assembly nanocarriers (T7-DSNPs/9291) have been developed as a targeted co-delivery system to enhance the combined therapeutic effect on brain metastases from NSCLC. In vitro cell experiments, including intracellular uptake assay, in vitro BBB transportation, and MTT assay were used to demonstrate the efficacy of T7-DSNPs/9291 in NSCLC brain metastasis in vitro. Real-time fluorescence imaging analysis, magnetic resonance imaging analysis, and Kaplan-Meier survival curves were used to study the effect of T7-DSNPs/9291 on an animal model in vivo.
RESULTS: T7-DSNPs/9291 could significantly enhance BBB penetration of AZD9291 and doxorubicin via transferrin receptor-mediated transcytosis. Moreover, T7-DSNPs/9291 showed significant anti-NSCLC brain metastasis effect and prolonged median survival of an intracranial NSCLC brain metastasis animal model.
CONCLUSION: T7-DSNPs/9291 is a potential drug delivery system for the combined therapy of brain metastasis from NSCLC.

Introduction

Lung cancer is the most serious cause of cancer death in humans.1 About 1/3 of non-small cell lung cancer (NSCLC) patients have brain metastasis during the follow-up standard-of-care treatment.2 Although symptomatic treatments such as the application of dehydration drugs and anti-tumor treatments such as whole-brain radiotherapy have brought some benefits to patients, the therapy of brain metastases from NSCLC is rather difficult, and the prognosis is still poor.3–6

Epidermal growth factor receptor-tyrosine kinase inhibitor (EGFR-TKI) has been adopted in the clinical treatment of NSCLC. Osimertinib (AZD9291), the third-generation EGFR-TKI, is a mutant selective irreversible EGFR inhibitor that is effective against both EGFR-TKI-sensitive mutations and T790M-resistant mutations.7 It is reported that AZD9291 showed better potential for the treatment of the brain metastasis from NSCLC and a lessened risk of brain progression compared with other EGFR-TKIs.8–10 However, the permeability of EGFR-TKIs into the brain is very limited because of the blood–brain barrier (BBB) and drug efflux proteins such as P-glycoprotein and breast cancer resistance protein which are overexpressed along with the BBB.11–13 Therefore, it is urgent to enhance the brain permeability of AZD9291 to improve its therapeutic effect against brain metastasis from NSCLC.

A combination of different classes of drugs has been widely used in cancer therapy, which has overcome the common issues of drug resistance and toxicity caused by monotherapy, and achieved a better curative effect.14 It is reported that AZD9291 combined with chemotherapeutic drugs is a potential therapeutic schedule of brain metastasis from NSCLC.15 Doxorubicin (DOX) is one of the original anthracyclines leading to DNA damage and cell death,16 which has been used in combination therapy for NSCLC.17 However, due to the different rates of metabolism within the body, the different properties of the pharmacokinetics and biodistribution of multiple drugs can lead to constant changes in the ratio of drugs, preventing drugs from being effective.18 Therefore, a co-delivery system has been developed to avoid this limitation by carrying multiple therapeutic agents in a nanocarrier which can bring the drug to the tumor site.19–21 In addition, it is necessary to construct a delivery system for stimulatory response in tumor cells, which enables the triggered release of AZD9291 and DOX in the NSCLC brain metastasis tumor cells. Studies have shown that the intracellular glutathione (GSH) concentration is 1000 times higher than extracellular levels, and this has become an important “switching molecule” that controls the intracellular intelligent release of drugs.22–24 The disulfide bond (-S-S-) is the most commonly used functionalized linker for the development of an intracellular GSH-responsive drug delivery system,25,26 which has been demonstrated to be stable in the blood circulation system but can split rapidly in tumor cells triggered by the reductive microenvironment.27–29 Thus, in this study, the GSH-responsive DOX prodrug (DOX-S-S-C18) conjugate was used as the nanocarrier backbone, as it can form nanoparticles without any surfactant with an ultra-high AZD9291 loading content. Furthermore, in order to improve the BBB penetration, the nanocarrier was installed with a BBB targeting moiety (T7 peptide), which was mediated transcytosis by transferrin receptor (TfR).

Herein, T7-installed AZD9291-loaded PEGylated DOX-SS-C18 conjugate self-assembled nanocarrier (T7-DSNPs/9291) was constructed (Figure 1). After intravenous (i.v.) injection, T7- DSNPs/9291 was expected to be stable in the physiological condition to avoid drug premature release and reduce the toxicity of the off-target effect. Then, T7 peptide could enhance the penetration of T7-DSNPs/9291 across BBB through transferrin-mediated transcytosis. When the T7-DSNPs/9291 was internalized into the NSCLC brain metastasis tumor cells, the nanocarrier could be disassembled under high intracellular GSH level and stimuli-responsively released AZD9291 and DOX which acted on the respective target to enhance the anti-brain metastasis from NSCLC (Figure 1).

Figure 1

Schematic design of AZD9291-loaded T7 modified PEGylated DOX-SS-C18 conjugated self-assembled nanocarrier (T7-DSNPs/9291) for the treatment of brain metastases from NSCLC.

Experimental

Materials

Doxorubicin and AZD9291 were purchased from Hubei Dixin Chemical Manufacturing Co., Ltd. (Wuhan, China). T7 (CHAIYPRH) peptide was obtained by GL Biochem Co., Ltd. (Shanghai, China). T7-PEG-DSPE was synthesized in line with our previous report.30,31 MeO-PEG2000-DSPE and Maleimide-PEG2000-DSPE were obtained from CordenPharma Co., Switzerland. All the other reagents were used as received.

Animals and Cell Lines

Male Balb/c nude mice weighing 20 ± 2 g were obtained from BK animal Ltd. (Shanghai, China). PC-9 cells (human lung cancer cells) and BCEC cells (rat’s brain capillary endothelial cell line) were purchased from the Institute of Biochemistry and Cell Biology, Shanghai Institutes for Biological Sciences, Chinese Academy of Sciences (Shanghai, China).

Preparation of Nanocarrier

The DOX-SS-C18 conjugate was synthesized as provided in the Synthesis of GSH-responsive DOX prodrug (DOX-SS-C18) section of the . The organic solvent evaporation was employed to prepare DOX-SS-C18 conjugate self-assembled nanoparticles (DSNPs). Briefly, DOX-SS-C18 conjugates (10 mg) were dissolved in tetrahydrofuran (200 μL) first. The resulting solution was then injected dropwise into distilled water (20 mL). After stirring for 5 minutes, the organic solvent in the solution was further eliminated by rotary evaporator, and the 0.22 μm mixed cellulose (MCE) syringe filter was used to filter the nanoparticles. AZD9291-loaded DSNPs (DSNPs/9291) were prepared by the above method with AZD9291 (5 mg) dissolved in an organic solvent. AZD9291-loaded PEGylated DOX-SS-C18 conjugate nanoparticles (PEG-DSNPs/9291) and T7-DSNPs/9291 were prepared by adding MeO-PEG2000-DSPE or T7-PEG-DSPE (T7-PEG-DSPE/DSNPs = 15/100, w/w; MeO-PEG-DSPE or T7-PEG-DSPE/DSNPs/9291 = 10/100, w/w) in an organic solvent. Coumarin-6 or Dir fluorescence-labeled nanoparticles were prepared via coumarin-6 or Dir co-dissolved with AZD9291 in the organic solvent during nanoparticle preparation.

Physicochemical Characterization of Nanocarrier

Morphology of the nanocarrier was observed by transmission electronic microscopy (TEM) (Tecnai G2 Spirit Bio TWIN, FEI, USA). The ζ potential, particle size, and size distribution of the nanocarrier were measured by DLS (Zs90, Malvern, UK). The experimental method for disassembled nanoparticles was shown in the Reduction-triggered disassembly of T7-DSNPs/9291 section.

In vitro Release

The in vitro release behavior of T7-DSNPs/9291 was investigated by ultrafiltration centrifugation. The release media was buffer solution containing 1 μM GSH and 10 mM GSH, respectively. Briefly, T7-DSNPs/9291 was scattered into 5 mL of release medium and shaken at 37°C at the speed of 150 rpm/min. Then, the solution was transferred to an ultrafiltration device (MWCO = 30 K Da) at the predetermined time. After centrifuged at 4500 rpm, the DOX and AZD9291 concentration of filtrate were measured by high performance liquid chromatography.

In vitro Uptake Evaluation

For the qualitative experiment, BCEC cells (2×104 cells/well) were seeded into 24-well plates. After 24 h, the cells were administrated by various coumarin-6 fluorescence-labeled nanocarriers at 1, 2, and 5 μg/mL, respectively. After washing by pre-cooled PBS buffer 3 times, the cells were fixed in 4% (w/v) paraformaldehyde solution at room temperature. Finally, the cells were stained by Hoechst 33,342 and then viewed by fluorescent microscopy (Imager A1, Zeiss, Germany). The qualitative analysis on PC-9 cells was shown in the Qualitative analysis of PC-9 cells uptake of T7-DSNPs/9291 section of the .

For quantitative evaluation, BCEC cells (1 × 105 cells/well) were seeded into 24-well plates. The cell culture and administration methods were the same as those referred to in the qualitative experiment. Then, the cells were lysed by 1% TritonX-100. The cell protein content was measured by the BCA protein assay. The coumarin-6 concentration of the lysate was detected by a fluorescence spectrophotometer.

In vitro BBB Transportation

The BBB model was constructed as previously.32 BCEC (1 x 104 cells/pore) was seeded on a transwell filter. When 90% confluence was reached, the cells were serum-starved with 1 μmol/L hydrocortisone for another 3 days. After monitoring transepithelial electrical resistance (TEER), the cells were used for BBB transportation evaluation. Free AZD9291 + DOX, PEG-DSNPs/9291, and T7-DSNPs/9291 (equivalent to 10 μg/mL AZD9291) were dropped into the top chamber. After incubation for 2 h, 800 μL samples were taken out from the base chamber. For the ligand competition inhibition evaluation, T7 (50 μg/mL) was administrated into the top chamber beforehand. After 1 h incubation, the T7 solution was substituted by the T7-DSNPs/9291 solution, and the next steps were consistent with the above-mentioned steps. The DOX and AZD9291 concentration in the base chamber was detected by high performance liquid chromatography.

In vitro Cytotoxicity Assay

The in vitro cytotoxicity of T7-DSNPs/9291 was evaluated by MTT assay. Briefly, BCEC or PC-9 cells (4 × 103 cells/well) were seeded into 96-well plates. Twenty-four hours later, the medium was substituted by various formulations at the different concentrations of AZD9291. After 48 h incubation, the MTT solution was added into the well. Four hours later, 200 μL DMSO was added into each well to dissolve the crystal. The absorbance was measured by a microplate reader at 490 nm (Thermo Multiskan MK3, USA).

In vivo Real-Time Fluorescence Imaging

An intracranial PC-9 tumor mice model was constructed as reported.33 Briefly, 4 μL PC-9 cell suspension (2×105 cells) was implanted into the right striatum of anesthetized BAlB/c nude mice by chloral hydrate at a rate of 0.8 μL/min. After 21 days, these mice were then randomized for subsequent studies. Intracranial PC-9 tumor mice were administrated with 250 μL Dir labeled T7-DSNPs/9291 and PEG-DSNPs/9291 via tail vein and imaged using the in vivo imaging system (IVIS Spectrum, PerkinElmer, USA) at 4, 12, and 24 h post-administration, respectively. To investigate the distribution of various nanoparticles in the tumor site and primary organs, these mice were executed and the primary organs were harvested and imaged by IVIS Spectrum after 24 h. After fixing in 4% paraformaldehyde and dehydrating in 15% and 30% sucrose solution, respectively, the brain tissues were cut by the frozen microtome. Afterward, the brain sections were stained with DAPI for 10 min. The distribution of nanoparticles in the brain section was viewed by a laser confocal microscope.

In vivo Anti-Tumor Efficacy

The in vivo anti-brain metastasis from NSCL of T7-DSNPs/9291 was studied by established intracranial PC-9 tumor mice. Each group contained 8 mice were injected with saline, DOX+AZD9291, T7-DSNPs, PEG-DSNPs/9291, and T7-DSNPs/9291 at a dose of 5 mg/kg AZD9291 and 6 mg/kg DOX, respectively, on 2, 4, 6, and 8 days after PC-9 transplantation. On day 21, the intracranial tumor growth of the mice was monitored by magnetic resonance imaging (MRI). Kaplan–Meier survival curves of each group mice were also plotted.

Statistical Analysis

These data were statistically analyzed by one-way ANOVA and two-way ANOVA using SPSS 22.0. Asterisks are used to indicate statistical significance (*P < 0.05, **P < 0.01, ***P < 0.001).

Results and Discussion

Characterization of T7-DSNPs/9291

The structure of DOX-SS-C18 conjugate was characterized by MS, 1H NMR, and 13C NMR (). The MS (m/z) of DOX-SS-C18: calculated for [C49H69NO14S2] [M]+ = 959, found: 958.93. The 1H NMR spectra of DOX-SS-C18 (DMSO, δ): 13.98(s, 1H, 11-OH), 13.21(s, 1H, 6-OH), 7.88–7.55(m, 4H, 2-H, 3-H, 4-H, 4ʹ-NH), 5.44(s, 1H, 2ʹ-H), 5.23(d, 1H, 5ʹ-H), 4.88–4.85(m, 3H, 14–2H, OH), 4.60–4.58(d, 2H, 4ʹ-H, 10-H), 4.18–4.16(m, 1H, OH), 4.02–3.94(m, 6H, 15–3H, 5”-2H, OH), 3.67(s, 2H, 2״-2H), 3.48–3.46(m, 3H, 3״-2H, 6ʹ-H), 2.93–2.82(dd, 2H, 7–2H), 2.19–2.10(m, 2H, 3ʹ-2H), 1.86–1.13(m, 37H, 9–2H, 7ʹ-3H, 6״~21״-32H), 0.86–0.82(t, 3H, 22״-3H). The 13C NMR spectra of DOX-SS-C18 (DMSO, δ): 214.38(C13), 186.77–186.65(C12, C5), 169.58(C1״), 167.37(C4״), 161.16(C1), 156.58(C6), 154.97(C11), 136.58–134.48(C3, C10a, C4a, C6a), 120.24–119.34(C12a, C2, C4), 111.06–110.94(C11a, C5a), 100.83(C2ʹ), 75.38(C8), 70.40–67.10(C6ʹ, C5ʹ, C10), 65.24(C5״), 64.21(C14), 56.96(C15), 45.88(C4ʹ), 42.22(C2״), 37.02–36.98(C3ʹ, C3״), 31.79–25.71(C6״-20״, C9, C7), 22.59(C21״), 17.46(C7ʹ), 14.22(C22״). These results showed that the DOX-SS-C18 conjugate was synthesized successfully.

In this study, T7-DSNPS/9291 was prepared via organic solvent evaporation. The driving forces for the self-assembly of the nanocarrier may be non-bonded hydrophobic interactions, and the balance of the intermolecular force and the establishment of a favorable conformation may indicate that S-S bonds show a distinct preference for dihedral angles approaching 90°.25 Furthermore, the T7 peptide was modified on the surface of the nanoparticles due to electrostatic adsorption, or it was engaged in NH-π stacking with doxorubicin, in which the amide NH of T7 interacts with π cloud of doxorubicin.34 The properties of various nanoparticles including ζ potential, particle size, and drug loading content are shown in . The drug loading content of AZD9291 and DOX reached 28.62% and 34.34%, respectively. The ultra-high drug loading of AZD9291 may result from the stable π-π stacking between the phenyl group of the AZD9291 structure with the anthracene ring of the DOX structure or NH of T7 interaction with π cloud of DOX. The particle size of DSNPS/9291, PEG-DSNPS/9291, and T7-DSNPS/9291 was 85.19 ± 0.85 nm, 88.53 ± 1.87 nm, and 90.56 ± 1.63 nm, respectively. The PDI of all the nanoparticles performed decently. Meanwhile, TEM images showed uniformly spherical morphology of T7-DSNPs/9291 (Figure 2A) and the size of the nanoparticles was around 100 nm, which was consistent with the result of DLS (Figure 2B).

Figure 2

Characterization of T7-DSNPs/9291. TEM images of T7-DSNPs/9291(A) and DLS analysis of T7-DSNPs/9291 (B).

The TEM image of T7-DSNPs/9291 incubated with GSH (Figure 3A) and the size distribution of T7-DSNPs/9291 incubated with GSH during 8 h (Figure 3B) displayed the deformation and expansion of nanocarrier, which revealed T7-DSNPs/9291 had the GSH responsiveness. In the investigation of the triggered-release profile of T7-DSNPs/9291 (Figure 3C), almost no AZD9291 and DOX were released under the presence of 1 μM GSH. This phenomenon can be explained that the concentration of GSH is not high enough to disrupt the disulfide bond of T7-DSNPs/9291 in this condition, and the π-π stacking between the phenyl group of the AZD9291 structure with the anthracene ring of the DOX structure is stable enough. In contrast, with the 10 mM GSH incubation, sudden explosive release of AZD9291 and DOX was performed in the first hour, and the cumulative release of AZD9291 and DOX from T7-DSNPs/9291 reached 63.95% and 62.64% after 8 hours, respectively. These results indicated that T7-DSNPs/9291 might be stable in the circulation system to minimize the premature release of AZD9291 and DOX. Meanwhile, AZD9291 and DOX could be rapidly released from the nanocarrier to inhibit tumor cells under the trigger of GSH when they were internalized into the cytoplasm. Therefore, the co-delivery system developed in this study may minimize the premature release of therapeutic drugs and enhance the anti-tumor efficacy of AZD9291 and DOX.

Figure 3

Response of nanoparticles to reductive stimulation. TEM images of T7-DSNPs/9291 incubated with 10 mM GSH (A). Size distribution of T7-DSNPs/9291 in response to GSH (B). Reduction-triggered release of payload from T7-DSNPs/9291 in different release condition (n = 3) (C).

Cellular Uptake

Coumarin-6 was used as a fluorescent probe to study the cellular uptake characteristics of T7-DSNPs/9291 qualitatively. The fluorescence of the T7-DSNPs/9291 group was significantly stronger than that of the PEG-DSNPs/9291 group with 1 h incubation at various concentrations of fluorescent probe (Figure 4A). In addition, the fluorescence of T7-DSNPs/9291 incubated for 2 h was significantly higher than that of the nanoparticles incubated for 1 h. These results showed that uptake of nanoparticles by BCEC cells exhibited concentration- and time-dependently under various conditions, and the same conclusion was obtained in PC-9 cells (). Quantitative cellular uptake of T7-DSNPs/9291 and PEG-DSNPs/9291 in BCEC cells also showed a concentration-dependent effect (Figure 4B). According to these results, when the concentration of coumarin-6 was 1, 2, 5, and 10 μg/mL, the cellular uptake of the T7-DSNPs/9291 was 1.86, 1.76, 1.54, and 1.62 times higher than the PEG-DSNPs/9291, respectively. Qualitative and quantitative analysis showed that T7 peptide modification can significantly increase the endocytosis of nanoparticles. Therefore, T7-DSNPs/9291 may be a potential nanocarrier for overcoming BBB.

Figure 4

In vitro cellular uptake and penetration capacity of T7-DSNPs/9291. BCEC uptake of T7-DSNPs/9291 and PEG-DSNPs/9291 at 37°C incubated with 100, 200, and 500 ng/mL coumarin-6 for 1 h and 2 h, respectively. Bar: 200 μm (A). BCEC uptake of PEG-DSNPs/9291 and T7-DSNPs/9291 incubated with coumarin-6 concentrations ranged from 1 to 10 μg/mL (n = 3) (B). Trans-BBB transport of AZD9291 and DOX, T7-DSNPs, PEG-DSNPs/9291, and T7-DSNPs/9291 through in vitro BBB model (n=3) (C). ***P < 0.001, **P < 0.01.

To study the in vitro permeability across BBB of various formulations, free AZD9291 and DOX, PEG-DSNPs/9291, T7-DSNPs/9291 were put in the top chamber and the concentration of AZD9291 and DOX in the base chamber was monitored, respectively. From Figure 4C, it is indicated that AZD9291 proportion of the free AZD9291+DOX, PEG-DSNPs/9291, T7-DSNPs/9291, and T7 competitive inhibition of T7-DSNPs/9291 group across the BCEC monolayer was about 0.71%, 1.53%, 2.55%, and 1.45%, respectively, and the DOX proportion of the four groups was about 1.53%, 2.09%, 2.63%, and 1.89%, respectively, which indicated no significant difference in the transmittance of AZD9291 and DOX of the same formulation. These results suggested the nanoparticle formulation could enhance AZD9291 and DOX transport across BCEC monolayer in vitro compared with that of free drug. Furthermore, the T7-modified group significantly increased BCEC monolayer penetration compared with the plain group. The transportation across BCEC monolayer of T7-DSNPs/9291 was higher than that of the one pre-incubated with T7 peptide, indicating that the transcytosis of T7-DSNPs/9291 across the BCEC monolayer is mediated by TfR, and T7-modified nanoparticles could increase the penetration of AZD9291 and DOX into the brain. Taken together, T7-DSNPs/9291 may improve the BBB permeability of AZD9291 and DOX, which is a benefit to the treatment of brain metastases from NSCLC.

In vitro Cytotoxicity

To evaluate the effect of T7-DSNPs/9291 on the BBB, the in vitro cytotoxicity of each formulation to BCEC cells was examined by MTT assay. As exhibited in Figure 5A, T7-DSNPs, PEG-DSNPs/9291, and T7-DSNPs/9291 had negligible toxicity to BCEC cells, ranging from 0.01 to 5 μg/mL of AZD9291 and 0.012 to 6 μg/mL of DOX, probably owing to the insufficient GSH inside of BCEC, resulting in disulfide bonds not being disrupted to release AZD9291 and DOX. Meanwhile, free AZD9291 and DOX significantly inhibited the growth of BCEC cells at the same concentration. These results indicated that the co-delivery nanocarrier could relieve the toxicity of AZD9291 and DOX to the blood–brain barrier.

Figure 5

Cytotoxicity of AZD9291 + DOX, T7-DSNPs, PEG-DSNPs/9291, and T7-DSNPs/9291 in BCEC cells (n = 6) (A) or PC-9 cells for 48 h (n = 6) (B).

However, at the same dose of AZD9291 and DOX, it was shown that the cytotoxicity of various AZD9291 formulations to PC-9 cells was concentration-dependent, and the cytotoxicity of T7-DSNPs/9291 (IC50 value of AZD9291 and DOX: 2.041±0.31 μg/mL and 2.449±0.389 μg/mL) was evidently higher compared with the T7-DSNPs group (IC50 value of DOX: 11.567±1.063 μg/mL) (Figure 5B; ), indicating that nanoparticles could co-deliver AZD9291 and DOX into tumor cells and release both of them under high GSH conditions to achieve better anti-tumor effect than monotherapy. Cytotoxicity was produced and the nanoparticle system retained the cytotoxic effect of AZD9291 on NSCLC cells.

Taken together, these above results indicated that T7-DSNPs/9291 could not only combine cytotoxicity of AZD9291 with DOX to cancer cells, but could also reduce the toxicity of therapeutic drugs to cerebral capillary endothelial cells.

In order to evaluate the in vivo distribution and BBB penetration ability of nanocarrier, Dir labeled PEG-DSNPs/9291 and T7-DSNPs/9291 were intravenously injected to intracranial PC-9 tumor nude mice to investigate the fluorescence distribution, respectively. From Figure 6A, we can see that the fluorescence intensity of the T7-DSNPs/9291 group is obviously higher at any time point than the PEG-DSNPs/9291 group in the intracranial PC-9 tumor-bearing brain. At 12 and 24 h post-administration, PEG-DSNPs/9291 was rarely detected in the brain, while T7-DSNPs/9291 showed strong intensity in the brain. Twenty-four hours after injection, the distribution of nanoparticles in the mouse brain tissue section was qualitatively observed using a laser confocal microscope (Figure 6B). The red fluorescence intensity in the brain of the T7-DSNPs/9291 group was significantly stronger than that of the PEG-DSNPs/9291 group. The ex vivo fluorescence of the brain also confirmed the accumulation of the T7-DSNPs/9291 group was much more than the PEG-DSNPs/9291 group in the brain (Figure 6C). Similarly, the corresponding semi-quantitative results for the brain showed that the tumor fluorescence of the T7-DSNPs/9291 group was 2.05 times higher than the PEG-DSNPs/9291 group (Figure 6D). These results indicated that T7 peptide modification could significantly increase the BBB transport of nanocarriers by TfR-mediated transcytosis. Therefore, the AZD9291 and DOX co-delivery nanoparticles could be utilized as a brain-targeted drug carrier for the treatment of brain metastases from NSCLC.

Figure 6

In vivo distribution of T7-DSNPs/9291. In vivo real-time fluorescence distribution of intracranial PC-9 tumor mice administrated with Dir labeled PEG-DSNPs/9291 (left, untargeted) and T7-DSNPs/9291 (right, targeted) at 4, 12, 24 h post-injection (A). The brain section distribution of PEG-DSNPs/9291 and T7-DSNPs/9291 of intracranial PC-9 tumor nude mice after 24 hours of administration. Scale is 200×. Blue, DAPI; red, Dir; Bar: 400 μm (B). Ex vivo fluorescence distribution in main organs 24 h post-administration with Dir labeled T7-DSNPs/9291(right) and PEG-DSNPs/9291 (left) (C). The semiquantitative radiant analysis of brains, *P < 0.05 (D) and organs (E).

However, the in vivo real-time fluorescence distribution also indicated that the T7-DSNPs/9291 and the PEG-DSNPs/9291 were mainly accumulated into the liver, which might be due to the nonspecific uptake of nanoparticles by the reticuloendothelial system (Figure 6E).

In vivo Anti-Brain Metastasis From NSCLC Efficacy

Brain MRI showed that the size of NSCLC brain metastasis tumor of mice treated with T7-DSNPs/9291 nanoparticles was significantly smaller than the other four groups at 21 days, and T7-DSNPs/9291 significantly inhibited the metastasis of NSCLC to the left side of the brain (Figure 7A). As displayed in Figure 7B, the median survival time of intracranial PC-9 tumor-bearing mice treated with T7-DSNPs/9291 was 35 days, which was the longest compared with those groups administrated with saline (21 days), free drug (24 days), T7-DSNPs (26 days) and PEG-DSNPs/9291 (28 days) (). At the same time, the result showed that the antitumor efficiency of the nanocarrier was better than that of combined free drugs. What is more, T7-DSNPs/9291 showed a better therapeutic effect than that of PEG-DSNPs/9291 since the modification of the T7 peptide improved the BBB penetrability of the nanocarrier. And the antitumor efficiency of T7-DSNPs/9291 was also better than T7-DSNPs due to the combination of DOX and AZD9291. These results indicated that the AZD9291 and DOX co-delivery nanoparticles showed a great enhancement in the efficacy against brain metastases from NSCLC compared with a single administration, which could provide a potential drug co-delivery strategy for the treatment of brain metastases from NSCLC.

Figure 7

In vivo antitumor efficiency of T7-DSNPs/9291. Representative brain MRI images of the normal mice (1) and intracranial PC-9 orthotopic transplanted mice administrated with saline (2), AZD9291+ DOX (3), T7-DSNPs (4), PEG-DSNPs/9291 (5), and T7-DSNPs/9291 (6) (A). Kaplan–Meier survival curve of intracranial PC-9 tumor mice administrated with various formulations every three days 4 times after PC-9 implantation at a dose of 5 mg/kg AZD9291and 6 mg/kg DOX (n = 8) (B).

Conclusions

In this study, we have constructed a GSH-responsive doxorubicin prodrug self-assembled brain-targeted nanocarrier with satisfactory AZD9291 loading capacity to deliver AZD9291 and DOX for the combined therapy of brain metastases from NSCLC. In vitro release assays explained that T7-DSNPs/9291 GSH-triggered release of AZD9291 and DOX. The cellular study indicated that T7-DSNPs/9291 could significantly enhance the uptake and penetration across BBB, and improve the anti-tumor effect on PC-9 cells while minimizing the toxicity of drug to normal cells. What is more, in vivo experiments demonstrated that T7-DSNPs/9291 significantly prolong the survival of mice. These results indicated that the T7-DSNPs/9291 was a potential brain targeted drug carrier allowing both drugs to work concurrently at the corresponding location for the combination therapy of brain metastases from NSCLC.