Original Article | Open Access | Published:

Programmable co-delivery of the immune checkpoint inhibitor NLG919 and chemotherapeutic doxorubicin via a redox-responsive immunostimulatory polymeric prodrug carrier

Acta Pharmacologica Sinica volume 38, pages 823834 (2017) | Download Citation

Abstract

To achieve synergistic therapeutic efficacy and prevent cancer relapse, chemotherapy and immunotherapy have been combined as a new modality for tumor treatment. In this work, we designed a redox-responsive immunostimulatory polymeric prodrug carrier, PSSN10, for programmable co-delivery of an immune checkpoint inhibitor NLG919 (NLG) and a chemotherapeutic doxorubicin (DOX). NLG-containing PSSN10 prodrug polymers were self-assembled into nano-sized micelles that served as a carrier to load DOX (DOX/PSSN10 micelles). DOX/PSSN10 micelles displayed spherical morphology with a size of 170 nm. DOX was effectively loaded into PSSN10 micelles with a loading efficiency of 84.0%. In vitro DOX release studies showed that rapid drug release could be achieved in the highly redox environment after intracellular uptake by tumor cells. In 4T1.2 tumor-bearing mice, DOX/PSSN10 micelles exhibited greater accumulation of DOX and NLG in the tumor tissues compared with other organs. The PSSN10 carrier dose-dependently enhanced T-cell immune responses in the lymphocyte-Panc02 co-culture experiments, and significantly inhibited tumor growth in vivo. DOX/PSSN10 micelles showed potent cytotoxicity in vitro against 4T1.2 mouse breast cancer cells and PC-3 human prostate cancer cells comparable to that of DOX. In 4T1.2 tumor-bearing mice, DOX/PSSN10 mixed micelles (5 mg DOX/kg, iv) was more effective than DOXIL (a clinical formulation of liposomal DOX) or free DOX in inhibiting the tumor growth and prolonging the survival of the treated mice. In addition, a more immunoactive tumor microenvironment was observed in the mice treated with PSSN10 or DOX/PSSN10 micelles compared with the other treatment groups. In conclusion, systemic delivery of DOX via PSSN10 nanocarrier results in synergistic anti-tumor activity.

Introduction

Chemotherapy is one of the most widely used treatments for cancers. Although chemotherapeutic agents kill tumor cells mainly through cytostatic and/or cytotoxic effects, a large body of evidence suggests that chemotherapy-elicited immune responses also contribute to overall antitumor activity1. However, the overall effect of chemotherapy is limited by the various negative regulatory mechanisms, such as inhibitory immune checkpoints, deployed by tumors to evade immune surveillance and suppress immune responses2,3. For example, cytotoxic T-lymphocyte-associated protein 4 (CTLA-4) is an immune checkpoint receptor expressed by activated T cells and transmits an inhibitory signal to T cells4. Tumors exploit CTLA-4 signaling to inhibit the initiation of an immune response, resulting in decreased T-cell activation and proliferation5. Like CTLA-4, programmed cell death protein 1 (PD-1) receptor is expressed on the surface of activated T cells. Its ligand PD-L1, which is overexpressed by tumor cells, interacts with PD-1, leading to inhibition of cytotoxic T cells. Tumor cells utilize the PD-L1/PD-1 pathway to evade detection and inhibit the immune response6,7,8. To enhance anti-tumor immunity and prevent cancer relapse, checkpoint blockade immunotherapy and chemotherapy have been combined as an attractive modality for cancer treatment9,10,11.

Indoleamine 2,3-dioxygenase-1 (IDO1) is an immunosuppressive protein that helps tumors evade the immune system and facilitates tumor growth and metastasis12,13,14. IDO1 is overexpressed by most tumors and mediates the degradation of the essential amino acid tryptophan (Trp) to kynurenine (Kyn) and other metabolites, resulting in suppression of effector T cells and promotion of regulatory T cell proliferation15. Thus, blocking the function of IDO1 is a promising strategy to reactivate the immune response against cancer16.

NLG919 is a nontoxic IDO1-selective inhibitor that blocks IDO-mediated immune suppressive pathways and leads to tumor regression in preclinical models17. Inhibition of the IDO pathway can act synergistically with chemotherapy18,19. However, the success of an immunochemotherapy that combines NLG919 with a chemotherapeutic drug is limited by the lack of a strategy to effectively co-deliver the two therapeutics to the tumors. Co-loading of the two agents into a nanocarrier may meet with limited success due to the differences in their physiochemical properties. In addition, tempo-spatial control of the release of the different drugs is difficult; all of the loaded drug is often released simultaneously.

To solve these problems, our group previously developed a PEG-NLG conjugate (PEG2k-Fmoc-NLG) as a prodrug carrier for co-delivery of NLG919 and the chemotherapeutic drug paclitaxel (PTX)20. The immune-enhancing function of NLG and the tumor killing effect of PTX synergistically contributed to increased anti-tumor efficacy. In this work, we further improved the NLG-based prodrug system by increasing the units of NLG per prodrug molecule via reversible addition-fragmentation chain transfer (RAFT) polymerization technology (Supplementary Figure S1). The new PSSN10 system consists of a POEG hydrophilic block and a PNLG hydrophobic block with a number of NLG919 motifs attached via redox-sensitive linkages (Figure 1). The PNLG hydrophobic block in the polymeric carrier not only provides immunostimulatory properties but also facilitates the encapsulation of doxorubicin (DOX), a potent chemotherapeutic agent that induces immunogenic tumor cell death21. NLG919 and DOX are incorporated into this system through chemical conjugation and physical “loading”, respectively, which allows the programmed release of DOX and NLG919 in the tumors. In addition, a disulfide linkage was introduced between NLG919 and the polymer backbone to facilitate the cleavage of NLG919 from the polymeric carrier at tumor sites. The effect of the PSSN10 polymer on IDO activity and T cell proliferation was tested. The efficiency of the nanocarrier in selective delivery of DOX to tumors was examined. The synergistic antitumor activity of DOX formulated in the immunostimulatory nanocarrier and the underlying mechanism were also investigated.

Figure 1
Figure 1

(A) Schematic illustration of the redox-responsive immunostimulatory PSSN10 polymeric prodrug carrier for co-delivery of NLG919 and DOX. (B) The particle size distribution of PSSN10 micelles measured by DLS (Inset: TEM image of PSSN10 micelle using negative staining; scale bar is 100 nm). (C) The particle size distribution of DOX/PSSN10 mixed micelles measured by DLS (Inset: TEM image of DOX/PSSN10 mixed micelles using negative staining; scale bar is 100 nm). (D) The in vitro release profiles of DOX from the DOX/PSSN10 mixed micelles in PBS with different GSH concentrations (0, 10 μmol/L, 10 mmol/L) at 37 °C.

Materials and methods

Materials

DOX·HCl was purchased from LC Laboratories. 4-Nitrophenyl chloroformate was purchased from Acros. Dulbecco's modified Eagle's medium (DMEM), trypsin-EDTA solution, 3-(4,5-dimethylthiazol-2-yl)-2,5-diphenyl tetrazolium bromide (MTT), Triton X-100 and Hoechst 33342 were purchased from Sigma-Aldrich. Penicillin-streptomycin solution and fetal bovine serum (FBS) were purchased from Invitrogen. 2-Azobis(isobutyronitrile) (AIBN, Sigma-Aldrich) was purified by recrystallization in anhydrous ethanol22. N,N′-(t-butyoxycarbonyl)cystamine (MBC)23 and POEG macroCTA24 were prepared according to the literature. All other reagents were of analytical or chromatographic grade.

Synthesis of 4-nitrophenyl-actived NLG919 (NLG-NO2)

NLG919 (225 mg, 0.80 mmol), 4-nitrophenyl chloroformate (327 mg, 1.6 mmol) and 400 μL of N,N-diisopropylethylamine (DIPEA) were dissolved in 8 mL of anhydrous dichloromethane (DCM) and stirred overnight at room temperature. The product (NLG-NO2) was obtained by column chromatography purification.

Synthesis of POEG-b-PMBC polymers

MBC monomer (144 mg, 0.45 mmol), POEG macroCTA (175 mg, 0.0194 mmol), AIBN (1 mg, 0.0062 mmol) and 1 mL of 1,4-dioxane were added to a Schlenk tube and deoxygenated by free-pump-thawing three times. The Schlenk tube was then immersed in an oil bath at 90 °C. After 24 h, the mixture was precipitated in diethyl ether 3 times to yield the POEG-b-PMBC polymers.

Synthesis of PSSN10 polymers

POEG-b-PMBC polymers were deprotected in a mixture of TFA/DCM (1/1, v/v) at room temperature for 2 h, precipitated in cold diethyl ether 3 times, and dried under vacuum to give the Boc-deprotected polymer products. Then, the as-synthesized Boc-deprotected polymers (118 mg, 0.01 mmol) and NLG-NO2 (179 mg, 0.4 mmol) were dissolved in 2 mL of DMF with 200 μL of DIPEA. After stirring at room temperature for 24 h, the reaction mixture was precipitated in diethyl ether 3 times. The final product, PSSN10, was obtained after vacuum drying.

Preparation of blank and DOX-loaded micelles

The blank and DOX-loaded PSSN10 micelles were prepared by a dialysis method. DOX·HCl was first dissolved in methanol at a concentration of 5 mg/mL with triethylamine (3 equiv) to remove HCl. PSSN10 polymer was dissolved in THF at a concentration of 50 mg/mL. Then, the DOX solution was mixed with the PSSN10 polymer solution at a DOX/polymer mass ratio of 1:20, followed by dropwise addition of 0.5 mL of PBS. After removing solvent under reduced pressure, the solution was dialyzed against PBS overnight (MWCO 3.5 kDa). Blank micelles were similarly prepared except that no DOX was added. For determination of the DOX concentration, DOX-loaded micelles were dissolved in DMSO and detected by fluorescence spectroscopy with excitation at 490 nm. Drug loading capacity (DLC) and drug loading efficiency (DLE) were calculated according to the following formula:

DLC (wt%)=(weight of loaded drug/weight of input polymer+drug)×100%

DLE (%)=(weight of loaded drug/weight of drug in feed)×100%

Critical micelle concentration (CMC) measurement

The CMC value of PSSN10 micelles was measured using Nile red as a fluorescence probe25. Briefly, 10 μL of a 0.05 mg/mL stock solution of Nile red in DCM was added to each tube. After the solvent was completely evaporated, PSSN10 solution in PBS ranging from 1.0×10−4 to 5×10−1 mg/mL was added. The mixtures were incubated overnight and then evaluated by fluorescence spectrometry.

Polymer and micelle characterization

1H NMR spectroscopy was performed on a Varian-400 FT-NMR spectrometer (400.0 MHz) with CDCl3 and DMSO-d6 as the solvent. The molecular weight (Mn and Mw) and distribution (Mw/Mn) of the synthesized polymers were measured by gel permeation chromatography (GPC) with a Waters 2414 refractive index detector. A series of polystyrene standards with a narrow molecular weight distribution were applied to calibrate the GPC elution traces. Tetrahydrofuran (THF) was used as the eluent at a flow rate of 1.0 mL/min at 35 °C, and a series of commercial polystyrene standards were used for the calibration. The size distribution and morphology of blank and drug-loaded micelles were examined by dynamic light scattering (DLS, Malvern Zeta Nanosizer) and transmission electron microscopy (TEM, negative staining method), respectively.

In vitro DOX release

The in vitro DOX release profiles of DOX-loaded PSSN10 micelles were examined under different GSH concentrations (0, 10 μmol/L, 10 mmol/L). DOX-loaded micelles with a DOX concentration of 0.25 mg/mL were transferred into a dialysis bag (MWCO=3.5 kDa, Spectrum Laboratories) and immersed in a tank containing 50 mL of DPBS (pH=7.4) with different GSH concentrations (0, 10 μmol/L, 10 mmol/L) with gentle shaking at 37 °C. At specific time intervals, 4 mL of PBS solution outside the dialysis bag was withdrawn and replaced with 4 mL fresh solution. The amount of DOX released was determined by fluorescence spectrometry as described above.

Cell culture

Mouse metastatic breast cancer cells (4T1.2), human prostatic carcinoma cells (PC3) and human cervical cancer cells (HeLa) were cultured in DMEM culture medium containing 10% (v/v) fetal bovine serum, 100 IU/mL penicillin and 100 μg/mL streptomycin at 37 °C in a humidified 5% CO2 atmosphere.

In vitro IDO inhibition

The IDO inhibitory activity of PSSN10 was tested by an IDO assay26. Briefly, HeLa cells were plated in a 96-well plate (5×103 cells/well) and allowed to grow overnight. Recombinant human IFN-γ (50 ng/mL) was then added to each well, followed by various concentrations of PSSN10 or free NLG919 (NLG919 concentrations: 50 nmol/L–20 μmol/L). After incubation for 48 h, 150 μL of the supernatant was transferred to a new 96-well plate. Then, 75 μL of 30% trichloroacetic acid was added, and the mixture was incubated at 50 °C for 30 min to hydrolyze N-formylkynurenine to kynurenine. For the colorimetric assay, the supernatants were transferred to a new 96-well plate and incubated with an equal volume of Ehrlich reagent (2% p-dimethylamino-benzaldehyde in glacial acetic acid, w/v) for 10 min at room temperature. The reaction product was measured at 490 nm by a plate reader. For HPLC-MS detection (Wastes Alliance 2695 Separation Module combined with Waters Micromass Quattro MicroTM API MS detector), the plate was centrifuged for 10 min at 2500 rounds per minute, and 100 μL of the supernatant from each well was collected for tryptophan and kynurenine assays.

T-cell proliferation study

A lymphocyte-Panc02 cell co-culture experiment was performed to determine whether PSSN10 can reverse IDO1-mediated inhibition of T-cell proliferation27. Murine Panc02 cells were stimulated by IFN-γ (50 ng/mL) to induce IDO expression and then irradiated (6000 rad) before coculture. Splenocyte suspensions were generated from BALB/c mice by passage through nylon wool columns after lysis of red blood cells. IFN-γ-stimulated Panc02 cells (1×105 cells/well) were mixed with splenocytes (5×105 cells/well, pre-stained with 5-(and 6)-carboxyfluorescein diacetate (CFSE)) in a 96-well plate. Various concentrations of PSSN10 and NLG919 were added to the cells. Then, 100 ng/mL anti-CD3 (clone 2C11) and 10 ng/mL mouse recombinant IL-2 were added to the cocultures. The proliferation of CD8+ and CD4+T cells was measured by flow cytometric analysis after 3 d of coculture.

In vitro cytotoxicity assay

4T1.2 and PC3 cancer cell lines were used for in vitro cytotoxicity study. Cells were seeded in 96-well plates at densities of 1.5×103 (4T1.2) and 3×103 (PC3) cells/well. After incubation for 24 h, the cells were treated with free DOX, PSSN10 and DOX/PSSN10 micelles in a gradient concentration. After incubation for 72 h, the cell viability was measured via MTT assay as reported before28. Untreated cells were included as a control.

Cell uptake and intracellular trafficking

4T1.2 cells were cultured in glass-bottom dishes (1×105 cells/dish) for 24 h and then treated with DOX/PSSN10 micelles and free DOX (DOX concentration: 20 μg/mL) in FBS-free culture medium. After 4 h, the cells were stained with Hoechst 33342 for 20 min and washed with PBS 3 times. The fluorescence images were obtained using a confocal laser scanning microscope (CLSM, FluoView 1000, Olympus, Japan).

Animals

Female BALB/c mice (6–8 weeks) and C57BL/6 mice (4–6 weeks) were purchased from Charles River (Davis, CA, USA). All animals were housed under pathogen-free conditions according to AAALAC guidelines. All animal-related experiments were performed in full compliance with institutional guidelines and approved by the Animal Use and Care Administrative Advisory Committee at the University of Pittsburgh.

Quantification of the Trp/Kyn ratio in plasma and tumor tissues

The kynurenine to tryptophan ratios in plasma or tumors in 4T1.2 tumor-bearing mice were examined by HPLC-MS/MS as an indication of IDO enzyme activity29. BALB/c mice bearing 4T1.2 tumors of 50 mm3 were treated with DPBS, DOX, DOXIL, PSSN10, DOX/PSSN10 at a DOX dosage of 5 mg/kg via the tail vein once every 3 d 3 times. One day after the last treatment, plasma and tumor samples were harvested. Plasma samples were mixed with methanol (plasma:methanol, 1:2.5, v/v) and centrifuged at 14 500 rounds per minute for 15 min. Supernatants were collected for HPLC-MS quantification of kynurenine and tryptophan.

Tumor samples were homogenized in water, and the homogenates were mixed with acetonitrile (1:1, v/v) and centrifuged. The supernatants were transferred to clean tubes. Equal volumes of methanol were added to precipitate proteins, and supernatants were collected for HPLC-MS measurement.

Plasma pharmacokinetics and tissue distribution

Female BALB/c mice (5 mice/group) were iv administered DOX·HCl and DOX-loaded PSSN10 micelles at a DOX dose of 5 mg/kg. Blood samples were collected at different time points (3 min, 10 min, 30 min, 1 h, 2 h, 4 h, 8 h and 12 h) and centrifuged at 2500 rounds per minute for 15 min. A 350-μL volume of acetonitrile was added to the plasma and centrifuged at 12 000 rounds per minute for 5 min. Then, the supernatants were collected and dried under airflow. The DOX concentrations in the samples were analyzed by HPLC. The pharmacokinetic parameters were calculated based on a noncompartment model by Phoenix WinNonlin.

For the tissue distribution study, DOX·HCl and DOX/PSSN10 micelles were iv injected into female BALB/c mice bearing 4T1.2 tumors at a DOX dose of 5 mg/kg. At 24-h post injection, the mice were sacrificed, and the major organs were excised. The tissues were weighed and homogenized in 2 mL of solvent (acetonitrile:H2O=1:1, v/v). The samples were centrifuged at 3500 rounds per minute for 10 min, and the supernatants were collected and dried under airflow. The residues were then dissolved in 200 μL of solvent (methanol:H2O=1:1, v/v) and centrifuged at 14 500 rounds per minute for 10 min. The DOX concentrations in the clear supernatants were detected by HPLC.

In vivo therapeutic efficacy

Female BALB/c mice bearing 4T1.2 tumors were iv administered saline, free DOX, blank PSSN10 micelles or DOX/PSSN10 mixed micelles (5 mg DOX/kg) once every two days 3 times. Tumor volumes were calculated according to the formula (L×W2)/2, in which L is the longest and W is the shortest tumor diameter (mm), and presented as the relative tumor volume (the tumor volume at a given time point divided by the tumor volume prior to the first treatment). In addition, changes in the body weights of all mice were monitored. At the completion of the experiment, tumor tissues were excised, fixed with 10% formaldehyde and embedded in paraffin. Tissues sliced at 5 μm were stained by hematoxylin and eosin (H&E) and observed by a Zeiss Axiostar plus Microscope (PA, USA). The Kaplan-Meier survival of the tumor-bearing mice (n=8) was followed within 45 d. Mice were considered dead either when the mice died during treatment or when the tumor volume reached 1000 mm3.

Quantification of tumor-infiltrating lymphocytes

The immune cell populations in the tumors following various treatments were measured by flow cytometry30. One day after the last treatment, cell suspensions from the spleens or tumors were filtered, and red blood cells were lysed. For extracellular staining, cells were co-incubated with combinations of antibodies (CD8, CD4, CD11b, Gr-1, CD45, F4/80 and CD206). For intracellular staining, cells were fixed immediately after cell surface staining following the manufacturer's description (eBioscience). Then, combinations of antibodies (IFN-γ, FoxP3 and granzyme B) were added to cells in permeabilization buffer. For IFN-γ staining, cells were stimulated with PMA (5 ng/mL) and ionomycin (500 ng/mL) in the presence of 10 mg/mL BFA for 4 h followed by extracellular and intracellular staining. The data were analyzed using FlowJo software (Tree Star Inc).

Results

Synthesis and characterization of the PSSN10 polymer

Supplementary Figure 1 shows the synthesis scheme for the PSSN10 polymer. (i) The hydroxyl group of NLG919 was activated with 4-nitrophenyl chloroformate to give NLG-NO2. (ii) The MBC monomer was synthesized according to the literature23. (iii) POEG (Mn=9 kDa) was synthesized by RAFT polymerization as reported previously24 and further served as a Macro-RAFT agent to initiate polymerization of the MBC monomer. The POEG-b-PMBC polymer was obtained after precipitation, which was followed by deprotection of the Boc-groups in TFA/DCM solution to yield the POEG-b-PSS polymer. The POEG-b-PSSNLG polymer was finally synthesized by the chemical coupling of NLG-NO2 to the Boc-deprotected POEG-b-PSS polymer. The 1H NMR spectrum of the POEG-b-PSSNLG polymer is shown in Supplementary Figure S2. Typical peaks at 7.72–7.17, 5.59, 2.04–0.75 ppm were observed in the 1H NMR spectrum of POEG-b-PSSNLG and corresponded to the protons of the NLG group. Comparing the intensities of Ic (at 5.59 ppm) and Ia (at 3.39 ppm) revealed that 10 NLG units were conjugated on each copolymer, which translated into a DLC of NLG as high as 28% (wt). The POEG-b-PSSNLG prodrug polymer was denoted as PSSN10 in the following study.

Preparation and characterization of blank and DOX-loaded micelles

PSSN10 prodrug micelles were prepared using a dialysis method. Supplementary Figure S3 shows that the critical micelle concentration (CMC) of PSSN10 was 15.5 mg/L. The relatively low CMC provides good stability of PSSN10 micelles upon dilution in blood. DLS measurements showed that the PSSN10 prodrug micelles had a unimodal size distribution with an average diameter of 134.7 nm (Figure 1B). After loading of DOX, the particle size increased to 175.1 nm (Figure 1C). TEM images confirmed the spherical morphology of both PSSN10 micelles and DOX/PSSN10 mixed micelles. DOX was effectively loaded into PSSN10 micelles at a DLC of 4.0% with a loading efficiency of 84.0%.

In vitro DOX release studies were performed in PBS solution with different GSH concentrations (0, 10 μmol/L, 10 mmol/L). As shown in Figure 1D, DOX cumulative release from DOX/PSSN10 mixed micelles was approximately 36% after 24 h in the absence of GSH. No acceleration of DOX release was observed in the presence of 10 μmol/L GSH, which mimics the slightly redox environment of the extracellular compartment. However, in the presence of 10 mmol/L GSH, approximately 70% of DOX was released within 24 h, indicating that rapid drug release could be achieved in the highly redox environment after intracellular uptake by tumor cells.

In vitro biological activities of PSSN10

To evaluate the IDO inhibitory effect of the PSSN10 prodrug carrier in vitro, HeLa cells were pretreated with IFN-γ to induce IDO expression, and the amount of kynurenine (Kyn) was measured following treatment with PSSN10 and NLG919. As shown in Figure 2A, free NLG919 and PSSN10 blocked IDO function in an NLG concentration-dependent manner, although PSSN10 exhibited a smaller IDO inhibitory effect than free NLG919. We also synthesized PCCN10 polymers without a disulfide linkage (Supplementary Figure S4) as a control. Compared with PCCN10, PSSN10 was more active in inhibiting IDO activity, which might be due to the efficient cleavage of the disulfide linkage in PSSN10 in response to intracellular GSH and suggests the importance of introducing a disulfide linkage into the NLG-based prodrug polymer. Thus, subsequent studies focused on the PSSN10 polymers.

Figure 2
Figure 2

In vitro biological activities of PSSN10. (A) In vitro inhibitory effect of IDO activity. HeLa cells were treated with IFN-γ together with PCCN10, PSSN10 and free NLG919. Kynurenine in supernatants was measured 2 d later. (B) The effect of PSSN10 on reversing T-cell suppression mediated by IDO-expressing mouse pancreatic cancer cells (Panc02). Panc02 cells and splenocytes were mixed and treated with IL-2, anti-CD3 antibody, IFN-γ together with PSSN10 and free NLG919 for 3 d. T-cell proliferation was measured by FACS analysis. *P<0.05 (vs control).

An in vitro lymphocyte-Panc02 (a murine pancreatic cancer cell line) co-culture experiment was then conducted to examine whether T-cell proliferation was enhanced by the IDO inhibitory effect of PSSN10. Figure 2B shows that co-culture of splenocytes isolated from BALB/c mice with IDO+ tumor cells led to significant inhibition of the proliferation of both CD4+ T cell and CD8+ T cells. This inhibition was almost completely reversed by free NLG919 at 20 μmol/L. Figure 2B also showed that PSSN10 blocked the inhibition by the tumor cells in a concentration-dependent manner. At the same NLG concentration of 20 μmol/L, the effect of PSSN10 was comparable to that of free NLG919.

Cytotoxicity and intracellular trafficking of DOX/PSSN10 mixed micelles

MTT assays were performed in 4T1.2 and PC3 cells to evaluate the cytotoxicity of DOX/PSSN10 mixed micelles. As shown in Figure 3A, PSSN10 alone was not effective in inhibiting tumor cell growth. Free DOX exhibited a cytotoxic effect on tumor cells in a concentration-dependent manner. The cytotoxicity of DOX-loaded micelles against 4T1.2 tumor cells was comparable to that of free DOX. Similar results were obtained with the PC3 cell line (Figure 3B).

Figure 3
Figure 3

MTT assay of cytotoxicity of PSSN10, DOX and DOX/PSSN10 mixed micelles in (A) 4T1.2 mouse breast cancer cells and (B) PC-3 human prostate cancer cells. Cells were treated for 72 h, and the results are reported as the mean±SD for triplicate samples. (C) Confocal laser scanning microscopy images of 4T1.2 cells at 4 h after treatment with free DOX or DOX/PSSN10 mixed micelles. The nuclei were stained with Hoechst 33342.

Intracellular trafficking of DOX-loaded PSSN10 micelles was evaluated in 4T1.2 cells by confocal laser scanning microscopy with free DOX as a control (Figure 3C). At 4 h after treatment with free DOX or DOX-loaded PSSN10 micelles, large amounts of fluorescence signals were observed in the perinuclear region of cells. Some of the DOX fluorescence signals were observed in nuclei for cells treated with DOX/PSSN10 mixed micelles, indicating the efficient intracellular delivery of DOX/PSSN10.

Plasma pharmacokinetics and tissue distribution

Free DOX·HCl and DOX/PSSN10 mixed micelles (5 mg DOX/kg) were injected into BALB/c mice, and the DOX concentrations in plasma were measured at different time points. As shown in Figure 4A, DOX/PSSN10 remained in the blood circulation for a significantly longer time than free DOX. The pharmacokinetic parameters were calculated based on a noncompartment model and are outlined in Table 1. The DOX/PSSN10 formulation showed a significantly higher T1/2, area under curve (AUC0–inf) and Cmax than free DOX. By contrast, the volume distribution (Vd) and clearance (CL) of DOX/PSSN10 were significantly lower than those of free DOX, which suggests a prolonged circulation time of the DOX/PSSN10 formulation in the blood.

Figure 4
Figure 4

Pharmacokinetics and biodistribution of DOX-loaded PSSN10 micelles. (A) Blood kinetics of DOX in BALB/c mice following iv administration of DOX-loaded PSSN10 micelles at a dose of 5 mg of DOX/kg with free DOX as a control. (B) Tissue distribution of NLG in 4T1.2 tumor-bearing BALB/c mice 24 h following iv administration of DOX-loaded PSSN10 micelles. (C) Tissue distribution of DOX in 4T1.2 tumor-bearing BALB/c mice 24 h following iv administration of DOX-loaded PSSN10 or free DOX (5 mg DOX/kg). *P<0.05, **P<0.01 (DOX/PSSN10 vs DOX).

Table 1: Pharmacokinetic parameters of DOX in different formulations.

The tissue distributions of both NLG and DOX from DOX/PSSN10 mixed micelles were also investigated in BALB/c mice bearing 4T1.2 tumors. Figure 4B shows the biodistribution of NLG at 24 h following iv administration of DOX/PSSN10 micelles. Significantly higher concentrations of NLG were detected in the tumors than in other organs/tissues, including the heart, liver, spleen, lung and kidney. In addition, very little NLG was found in the blood, suggesting the good stability of PSSN10 in the blood circulation. Figure 4B shows the biodistribution of DOX at 24 h following iv administration of DOX/PSSN10 micelles with free DOX as a control. Significantly greater amounts of DOX in tumors were detected for DOX/PSSN10 mixed micelles compared with free DOX. DOX/PSSN10 mixed micelles also showed higher accumulation in tumors than in other organs/tissues. These data suggest that DOX and NLG can be selectively delivered to tumor sites via the PSSN10 prodrug carrier.

In vivo therapeutic study

Figure 5A shows the in vivo therapeutic effects of PSSN10 and DOX/PSSN10 with free DOX and DOXIL (a clinical formulation of liposomal DOX) as controls (5 mg DOX/kg). The PSSN10 carrier alone showed a modest effect in inhibiting tumor growth, comparable to those of DOX and DOXIL. This is in contrast to the in vitro cytotoxicity, in which PSSN10 showed little effect (Figure 3A, 3B), suggesting that the IDO inhibitory effect rather than a direct cytotoxic effect contributed to the in vivo antitumor activity of PSSN10. DOX formulated in PSSN10 micelles showed enhanced antitumor activity that was significantly higher than that of DOXIL.

Figure 5
Figure 5

(A) In vivo antitumor activity of PSSN10 and various DOX formulations in a syngeneic murine breast cancer model (4T1.2). Three injections were administered on d 0, 3 and 6. **P<0.01. (B) Kaplan-Meier survival of 4T1.2 tumor-bearing mice after various treatments. (C) Histological analyses of H&E stained sections of tumor tissues collected on d 19.

Figure 5B shows the Kaplan-Meier survival curves of 4T1.2 tumor-bearing mice following different treatments. All formulations improved the survival rate compared to the saline control group. Among them, the DOX/PSSN10 formulation resulted in the longest overall survival, with a median survival of 40 d.

Figure 5C shows the histology of tumors following different treatments. Tumors from the mice treated with DOX/PSSN10 had more necrotic/apoptotic cells compared to the tumors from the other treatment groups.

Effect of DOX/PSSN10 treatment on the tumor immune microenvironment

The concentrations of Kyn, an indicator of IDO enzyme activity, in tumor tissue and blood following the various treatments were measured by HPLC-MS. As shown in Figure 6, the Kyn concentrations in both blood and tumors were significantly decreased following treatment with PSSN10 and DOX/PSSN10, respectively. Interestingly, the levels of Kyn in the blood were also significantly decreased in mice treated with DOXIL.

Figure 6
Figure 6

Kynurenine concentrations in (A) tumor and (B) blood of BALB/c mice bearing s.c. 4T1.2 tumors following various treatments. *P<0.05 (vs control).

We then further examined changes in the immune cell subpopulation in the tumor tissues of the mice that received different treatments. As shown in Figure 7A, PSSN10 treatment led to a significant increase in the relative numbers of CD4+ T cells and CD8+ T cells in the tumors compared with the control, DOX or DOXIL groups. There was no significant difference in the relative numbers of CD4+ T cells between PSSN10 and DOX/PSSN10 (Figure 7A).

Figure 7
Figure 7

Flow cytometry analysis of immune cell subsets in tumor tissues. Tumor bearing mice received various treatments at a DOX dosage of 5 mg/kg for three times at an interval of 3 d and tumoral T-cell infiltration, including (A) CD4+ and CD8+, (B) granzyme B-positive CD8+ T cells, were measured by flow cytometry. (C) FoxP3+ T regulatory cells, (D) MDSC subsets (Gr-1highCD11b+ granulocytic (G-MDSC) and Gr-1intCD11b+ monocytic (M-MDSC)) and (E) tumor-associated macrophage (TAM) populations (M1-type (CD11b+/F4/80+/CD206) and M2-type (CD11b+/F4/80+/CD206+)) were also detected by flow cytometry. The bars represent means±SEM. *P<0.05 (vs control); &P<0.05 (vs DOX); #P<0.05 (vs DOXIL).

Figure 7B shows that the relative number of granzyme B-positive CD8+ T cells in tumors was increased in all treatment groups compared with the control group. The relative number of granzyme B-positive CD8+ T cells in tumor tissues was higher in the groups treated with PSSN10 or DOX/PSSN10 than in the DOX-treated group. No significant difference was found in the relative number of granzyme B-positive CD8+ T cells between the PSSN10 and DOX/PSSN10 groups.

Figure 7C shows that the relative cell number of regulatory T cells (Treg) was reduced in all treatment groups compared with the control group. Similarly, the relative cell number of granulocytic myeloid-derived suppressor cells (G-MDSCs) in the tumors was reduced in all treatment groups (Figure 7D). No significant difference was found in the relative cell number of Treg cells (Figure 7C) or G-MDSCs (Figure 7D) between the PSSN10 and DOX/PSSN10 groups. There was also a slight decrease in the relative cell number of monocytic MDSCs (M-MDSCs) in the tumors after various treatments (Figure 7D).

Figure 7E shows that the relative cell number of M1 (CD11b+F4/80+CD206) tumor-associated macrophages in the tumors was slightly increased in all treatment groups. By contrast, the relative cell number of M2 (CD11b+F4/80+CD206+) tumor-associated macrophages was significantly reduced following treatment with DOXIL, PSSN10 or DOX/PSSN10.

Overall, these data suggest a more immunoactive tumor microenvironment in mice treated with PSSN10 or DOX/PSSN10 compared with the control or other treatment groups. This conclusion is consistent with the greater in vivo IDO inhibitory effect of DOX/PSSN10 compared with DOXIL or the other groups (Figure 6).

Discussion

Checkpoint blockade immunotherapy has been developed as a promising treatment modality for various malignancies31,32. Currently, immune checkpoint blockade is achieved with monoclonal antibodies specific for different immune checkpoint proteins33. Recently, there has been growing interest in developing small-molecule immune checkpoint inhibitors34,35. Compared to antibody-based immunotherapeutics, small-molecule checkpoint inhibitors have the advantages of excellent safety, ease of production and more efficient delivery into the tumor site35.

IDO1 is an important immune checkpoint protein that suppresses T cell proliferation through Trp catabolism and Kyn production. 1-Methyl-d-tryptophan (1-MT) and NLG919 are two important small-molecule inhibitors with distinct mechanisms for blocking IDO1-mediated tumor immune escape36. Compared to 1-MT, NLG919 is a more potent IDO1-selective inhibitor, with an EC50 of 75 nmol/L37. Some studies have shown that IDO inhibitors can improve the therapeutic efficacy of chemotherapy or work synergistically with chemotherapy18,19. However, there is limited information about combination therapy of NLG919 with a chemotherapeutic drug38.

Our group previously developed a PEG-NLG conjugate (PEG2k-Fmoc-NLG) as a prodrug nanocarrier for co-delivery of NLG919 and paclitaxel (PTX), a commonly used chemotherapeutic drug20. The immune-enhancing function of NLG and the tumor-killing effect of PTX synergistically contributed to the increased anti-tumor efficacy. In this work, we further improved the NLG-based prodrug carrier system by increasing the number of NLG units per carrier molecule via RAFT polymerization. Compared to the previous system, the NLG loading content in the new PSSN10 system increased from 9.4% to 19.7%, which could help decrease the amounts of carrier materials for in vivo application. In addition, a disulfide linkage was introduced in the PSSN10 system to promote the release of NLG from the prodrug carrier (data not shown).

PSSN10 readily formed small-sized micelles capable of loading various types of anticancer agents, including DOX, PTX, docetaxel and curcumin (data not shown). We focused on DOX in this work because DOX can elicit caspase-dependent immunogenicity and enhance the proliferation of tumor antigen-specific CD8+ T cells in tumor-draining lymph nodes39,40,41,42. A recent study demonstrated that the effectiveness of immune checkpoint blockade is dependent on preexisting antitumor immunity3. In addition, it has been reported that post-chemotherapy delivery of immunotherapy is a more effective treatment mode in inhibiting tumor progression43. Therefore, combining PSSN10 with DOX, which is capable of inducing immunogenic tumor cell death, represents a rational approach for cancer immunochemotherapy.

One unique feature of our approach is the programmable release of NLG and DOX to maximize the efficacy of the combination therapy. DOX was physically loaded into PSSN10 micelles and rapidly released from the micelles upon reaching the tumor site. DOX-mediated killing of tumor cells and/or the direct effect of DOX on immune cells could lead to enhanced tumor antigen presentation and improved antitumor immunity. By contrast, NLG was covalently linked to the polymer and was released at a relatively slower pace, which would help maintain or enhance the anti-tumor immune response over a prolonged period of time by reversing IDO-mediated immune suppression. Indeed, DOX/PSSN10 mixed micelles were significantly more effective than DOXIL or free DOX in inhibiting the tumor growth and prolonging the survival of treated mice. The superior antitumor activity of DOX/PSSN10 mixed micelles is likely due to the effective delivery of both NLG and DOX to the tumor tissue as demonstrated in the biodistribution study (Figure 4). The synergistic action between DOX and released NLG may also play an important role.

The immunological analysis indicated that tumor tissues from mice treated with PSSN10 were more immunoactive, with a higher percentage of functional T cells (CD4+ and CD8+) and lower percentages of Treg cells and MDSCs compared with untreated tumors or tumors treated with DOX or DOXIL (Figure 7). Incorporation of DOX into the PSSN10 system did not affect the function of PSSN10 in enhancing T cell proliferation and suppressing Treg cells and G-MDSCs. By contrast, our previous study of the PTX-loaded PEG2k-Fmoc-NLG system showed that incorporation of PTX led to a reduction in the percentage of total intratumoral T cells and an increase in the percentage of MDSC cells compared to PEG2k-Fmoc-NLG alone43. It is not clear if this divergence is due to the differences in drugs or the dosages of the drugs in the two different studies. More studies are needed to better understand the underlying mechanisms.

In conclusion, we have developed a new redox-sensitive system, PSSN10, for programmable co-delivery of DOX and NLG. Our data suggest that DOX/PSSN10 has potential as an effective combination regime for cancer immunochemotherapy.

Author contribution

Jing-jing SUN and Yi-chao CHEN contributed equally. Study concept and design: Song LI, Jing-jing SUN and Yi-xian HUANG; chemical synthesis and micelle characterization: Jing-jing SUN; biological study: Yi-chao CHEN, Jing-jing SUN and Yan-hua LIU; analysis of data: Yi-chao CHEN, Jing-jing SUN and Wen-chen ZHAO; drafting of the manuscript: Jing-jing SUN and Song LI.

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Acknowledgements

This work was supported by NIH grants RO1CA173887, RO1GM102989, and R21CA173887.

Author information

Author notes

    • Jing-jing Sun
    •  & Yi-chao Chen

    These authors contributed equally to this work.

Affiliations

  1. Center for Pharmacogenetics

    • Jing-jing Sun
    • , Yi-chao Chen
    • , Yi-xian Huang
    •  & Song Li
  2. Department of Pharmaceutical Sciences, School of Pharmacy;

    • Jing-jing Sun
    • , Yi-chao Chen
    • , Yi-xian Huang
    • , Wen-chen Zhao
    • , Raman Venkataramanan
    •  & Song Li
  3. University of Pittsburgh Cancer Institute, University of Pittsburgh, Pittsburgh, PA 15261, USA

    • Jing-jing Sun
    • , Yi-chao Chen
    • , Yi-xian Huang
    • , Bin-feng Lu
    •  & Song Li
  4. Department of Pharmaceutics, School of Pharmacy, Ningxia Medical University, Yinchuan 750004, China

    • Yan-hua Liu
  5. Department of Immunology, School of Medicine, University of Pittsburgh, Pittsburgh, PA 15261, USA

    • Bin-feng Lu

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Correspondence to Song Li.

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    Figure S1

    Synthesis scheme of PSSN10 polymers via RAFT polymerization and post-modification.

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https://doi.org/10.1038/aps.2017.44

Supplementary information is available on the website of Acta Pharmacologica Sinica.

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