Polymer nanoparticles that respond to two triggers for combined treatment of muscle-invasive bladder cancer

Doxorubicin and ε-Caprolactone were purchased from Aladdin co. (Shanghai, China). IR780 was purchased from Sigma-Aldrich co. (St. Louis, USA), PEG was obtained from Peng Sheng Biological Co., Ltd (Shanghai, China). Poly(lactic-co-glycolic acid) (PLGA) and human serum albumin was obtained from Aladdin co. (Shanghai, China). MTT Cell Proliferation and Cytotoxicity Assay Kit was obtained from Beyotime (Shanghai, China). TUNEL Apoptosis Assay Kit was provided by Beyotime Institute of Biotechnology (Haimen, China). Ki67 antibody was provided by Cell Signaling Technology (MA, USA). 1 × Phosphate buffer solution (PBS) and deionized water were used in the experiments. All C57BL/6 female mice (18–20 g) were obtained from Yangzhou University Medical Center. All other reagents were purchased from Nanjing Wanqing Chemical Glassware Instrument Company and used as received.

We firstly synthesized HO-PCL-b-PEG¹¹⁴ with the terminal group of hydroxyl group. The specific synthesis steps are shown in Fig. 1. The synthesis of HO-PCL-b-PEG¹¹⁴ is carried out by using PEG¹¹⁴-OH as an initiator and stannous octoate (Sn(Oct)₂) as a catalyst to initiate ring-opening polymerization of monomer ε-caprolactone (ε-CL). Specifically, 2 g of dry treated CH₃O-PEG¹¹⁴-OH (0.4 mmol) and 4 g of de-vaporized ε-CL (35.1 mmol) were weighed and dissolved in 10 mL of vacuum-distilled anhydrous toluene, followed by one drop of Sn(Oct)₂. The liquid nitrogen was frozen, evacuated, purged with nitrogen, thawed, and cycled three times. After reacting for 24 h in a 110 °C oil bath, it was added dropwise to 500 mL of ice diethyl ether under stirring to precipitate. It was suction filtered, washed with diethyl ether three times, and dried in vacuo to get white solid HO-PCL-b-PEG114. The degree of polymerization of the PCL segment was calculated by nuclear magnetic resonance to be Dp = 87. The block copolymer was HO-PCL87-b-PEG114. To synthesis PCL-PEG-SS, 0.5 g HO-PCL87-b-PEG114 were dissolved in 20 mL DMSO and thenadded 4-(dimethylamino) pyridine (DMPA, 0.2 g) solution in DMSO (3 mL) and lipoic acid anhydride (0.6 g) in DMSO (3 mL), respectively. The reaction was stirred for 48 h under nitrogen at 30 °C. The product was isolated by precipitation in cold ethanol, washed several times with ethanol, and dried in vacuo.

After hydrophobization of doxorubicin, certain amount of DOX (1.0 mg), IR780 (1.0 mg) and polymer PEG-PCL-SS (20 mg) were dissolved in DMSO, and then added to PBS (pH 7.4) under ultrasonic conditions. The solution was concentrated by ultrafiltration to remove free DOX and IR780. The drug loading was calculated by the drug amount in NPs, according to the standard curve of DOX and IR780 measured by UV absorption spectroscopy. Nanoparticles loaded with near-infrared photosensitizers were prepared by hydrophobic interaction of PCL and hydrophobic small molecules. The DTT was accurately weighed and the nanoparticles were reacted using DTT (10 μL, 10 mg/mL). Because DTT can partially hydrolyze the disulfide bond of the nanoparticles within a controllable range, the spatial structure of the nanoparticles after reflection is more compact. The nanoparticles loaded with photosensitizer and chemotherapeutic drugs were obtained by dialysis and concentration. As a control, non-crosslinked PEG-PCL NPs were prepared the same as PEG-PCL-SS NPs. To evaluate the delivery advantages of PEG-PCL-SS NPs, two other NPs (PLGA and Albumin) were prepared as described before [19–21]. Briefly, The PLGA NPs were prepared in a solvent displacement process. DOX (1 mg), IR780 (1 mg) and 20 mg PLGA first dissolved in DMSO (1 mL). 1 mL of the solution was added dropwise to 10 mL of water. The mixture was then stirred in open air for 2 h. Then the solution was concentrated by ultrafiltration to remove free DOX and IR780. DOX and IR780-loaded Albumin nanoparticles were prepared via a molecular switch method as described previously [21, 22]. The drug loading was calculated by the drug amount in NPs, according to the UV standard curve of DOX and IR780.

Particle size and surface potential were measured by a Brookhaven BI-90Plus laser particle size analyzer. Transmission electron microscopy was used to observe the morphology of the nanoparticles. Samples were prepared by dropping a suitable concentration of the nanoparticle solution on a 200 mesh copper mesh and dried overnight.

Murine bladder carcinoma MB49 cells were obtained from Shanghai Institute of Biochemistry and Cell Biology, Chinese Academy of Sciences. The cell line was maintained in RPMI 1640 cell culture media supplemented with 10% fetal calf serum (Hyclone, Logan, UT) and antimicrobial-antimycotic (Gibco/Invitrogen, Carlsbad, CA) in a humidified incubator at 37 °C in an atmosphere composed of 5% CO₂. The cell line was transduced with the firefly luciferase gene by a lentivirus vector.

We prepared internal cross-linked polymeric nanoparticles containing IR780, internal cross-linked polymeric nanoparticles containing doxorubicin and IR780, and a PBS solution (pH7.4). The 808 nm near-infrared laser irradiation system was applied on the samples for 1–3 min, and the temperature probe measurement system was conducted. The photothermal effect of the IR780-containing nanoparticles was evaluated (50 μg/mL IR780).

DOX and IR780 were encapsulated into the inner crosslinked polymeric nanoparticles. After dialysis, a small amount of organic solvent was removed. The dialysis bag filled with nanoparticles was placed in a PBS solution (pH7.4) with or without GSH (5 mM or 10 mM). The internal chemical structure of the internally crosslinked polymeric nanoparticles is changed when interacted with GSH, and the drugs are continuously released from the drug-loaded nanoparticles. We then used near-infrared laser irradiation to irradiate the cross-linked polymeric nanoparticles. The near-infrared laser can promote the photothermal reaction of IR780 in the drug-loaded nanoparticles, and further promote the release of the drug from the nanoparticles. The drug content of nanoparticles in PBS (pH 7.4) was measured at different time points (0 to 72 h) under different experimental conditions, and the drug release curve was obtained.

MB49 cells were cultured for 24 h and then treated free doxorubicin solution (1.0 μg/mL), free IR780 solution (1.0 μg/mL), and drug-loaded nanoparticles containing doxorubicin and IR780for 6 h. The cells were washed with PBS twice and imaged by a fluorescence microscopy to determine the cellular uptake of the nanoparticles.

Different concentrations of doxorubicin-containing nanoparticles (DOX, from 0.11 to 1.775 μg/mL), IR780-containing nanoparticles (IR780, from 0.078 to 1.25 μg/mL), drug-loaded nanoparticles containing doxorubicin and IR780, and nanoparticles without any drugs were added to the cells. After 24 h, the cell viability and optimum concentration of the formulations was evaluated by MTT assays by measuring the absorbance of the solution at 570 nm.

Different concentrations of free doxorubicin solution, free IR780 solution, doxorubicin-containing nanoparticles, IR780-containing nanoparticles, doxorubicin and IR780 nanoparticles were prepared and added to the cells. The tumor cells were fully ingested with drugs or drug-loaded nanoparticles for 12 h, IR780 containing groups were irradiated with 808 nm near-infrared laser for 3 min, and then cultured for 24 h. MTT assays were conducted with the same procedure described previously.

All mice received care following the guidelines of the Care and Use of Laboratory Animals and their use followed the terms of the Institutional Animal Care regulations and Use Committee of Nanjing University. All animal experiments were approved by the Administration Committee of Experimental Animals in Jiangsu Province and the Ethic Committee of Nanjing University.

After anesthetizing C57BL/6 mice with 2% pentobarbital, the midline incision was taken to expose the bladder position of the mouse. After using the syringe to absorb the urine in the bladder, the MB49 bladder cancer cell suspension was injected into the bladder muscle layer. Small animal CT examination was performed at day 7 after successful surgery to observe whether there was a tumor in the bladder area.

Pharmacokinetics study following single-dose intravenous injection was conducted in tumor-free male mice. The mice were randomly divided into PEG-PCL-SS NPs group, PEG-PCL NPs group, PLGA NPs group and Albumin NPs group (three mice per group). The formulations were administered via intravenous injection with the IR780 dose of 10 mg/kg. Blood samples were collected by retro-orbital bleeding at different time points (1 to 72 h) after administration. The content of IR780 in the serum samples was measured using a Varioskan Flash Spectral Scanning multimode plate reader (Thermo Fisher Scientific, Waltham, MA, USA). PK Solver Version 2.0, was used to calculate pharmacokinetic parameters from the plasma concentration versus time data [23].

The free IR780 solution and the nanoparticles loaded with doxorubicin and IR780 (0.3 mg IR780/kg body weight) were injected into the tumor-bearing mice by tail vein administration. Images were taken at 6, 12, 24 and 48 h after injection using the in vivo imaging system (IVIS Lumina XR III, USA). As a control, normal mice (without tumor) were injected with DOX&IR780@PEG-PCL-SS NPs and imaged at 6, 12, 24 and 48 h after injection using the in vivo imaging system. The mice were sacrificed at 48 h after injection, and the major organs including the heart, liver, spleen, lung, kidney and bladder tumor were collected for ex vivo imaging. The excitation wavelength of IR-780 is 745 nm and its emission spectrum is 780–900 nm.

The luciferase-expressing MB49 cell line was constructed and used for in vivo imaging of the tumor. Saline, doxorubicin-containing nanoparticles (4 mg/kg IR780), IR780-containing nanoparticles (2.5 mg/kg DOX), "drug-loaded nanoparticles containing doxorubicin and IR780" (2.5 mg/kg DOX, 4 mg/kg IR780) were injected into randomized mouse groups by tail vein administration. The experimental groups were irradiated with 808 nm near-infrared laser after 24 h, and repeated administration after one week. The mice were sacrificed after 3 weeks, and the heart, liver, spleen, lung, kidney and bladder of the mice were harvested for further study.

Polymeric nanoparticles loaded with different concentrations of doxorubicin (0 mg/kg, 1.25 mg/kg, 2.5 mg/kg and 5.0 mg/kg) and IR780 (0 mg/kg, 1.25 mg/kg, 2.5 mg/kg and 5.0 mg/kg) were synthesized and injected into the mice by tail vein administration. After 24 h, the mice were sacrificed and blood samples were harvested by retro-orbital bleeding. ALT, AST, BUN, and Cr in the blood samples were immediately detected.

After the mice were sacrificed, the heart, liver, spleen, lung, kidney and bladder of the mice were harvested for hematoxylin and eosin (H&E) staining, the TUNEL assay and Ki67 immunofluorescence. After dehydration and fixation, the sections were stained with H&E, and the bladder and tumor tissues were stained with TUNEL to observe the apoptosis in the bladder cancer tissues. Briefly for the TUNEL assay, the sections were fully deparaffinized and hydrated. 20 μg/mL DNase-free proteinase K was added to the samples and kept them at room temperature for 30 min. After washing twice in PBS, samples were incubated with 50 μL of TUNEL inspection fluid for 60 min before rinsed three times with PBS. Results were imaged under a fluorescent microscopy by using 488 nm excitation and 530 nm emission. For Ki67 immunofluorescence study, the sections were fully deparaffinized and hydrated, and the tissue was permeabilized with 0.3% triton X-100 (prepared in PBS) for 10 min at room temperature, and blocked with 5% BSA for 1 h. Use the corresponding antibody diluent to dilute the primary antibody and incubate at room temperature for 3 h. Wash the sections with PBS, use the corresponding antibody diluent to dilute the secondary antibody, incubate at room temperature for 60 min, and observe after mounting. Results were imaged under a fluorescent microscopy by using 585 nm excitation and 624 nm emission.

The chemical synthesis process of PEG-PCL-SS conjugates was illustrated in Fig. 1. Firstly, The synthesis of HO-PCL-b-PEG114 is carried out by using PEG114-OH as an initiator and stannous octoate (Sn(Oct)₂) as a catalyst to initiate ring-opening polymerization of monomer ε-caprolactone (ε-CL). Then, to synthesis PCL-PEG-SS, HO-PCL-b-PEG114 reacted with DMPA and lipoic acid anhydride for 48 h (Fig. 1a). Drug loaded nanoparticles were prepared through a co-precipitation method. Briefly, hydrophobizated doxorubicin, IR780 and polymer PCL-PEG-SS dissolved in DMSO, were added to PBS (pH7.4) under ultrasonic conditions. Nanoparticles loading with near-infrared photosensitizers and chemotherapeutics were formed by hydrophobic interaction of PCL part of PCL-PEG-SS and hydrophobic small molecules. Under DTT catalysis condition, the intramolecular disulfide bonds of PCL-PEG-SS will be broken, while intermolecular disulfide bonds may form inside the nanoparticles through the disulphide–sulfhydryl interchange reaction and stabilize the nanoparticles, which makes the spatial structure of nanoparticles more compact (Fig. 1b). The resulting cross-linked PCL-PEG-SS nanoparticles are stable under high salt concentration.

The characteristics of the DOX&IR780@PEG-PCL-SS NPs are shown in Fig. 2. The results of ¹H NMR result prove that we synthesized the carrier PEG-PCL-SS (Fig. 2a). The drug loading of IR780 and DOX in NPs were 4.3% and 3.8% respectively. The average size (tested by DLS) of DOX&IR780@PEG-PCL-SS NPs was 59.24 ± 18.47 nm and DOX&IR780@PEG-PCL-SS NPs were generally spherical in shape as shown in the TEM image (Fig. 2b, c). To compare the size change of PEG-PCL-SS NPs, cross-linked PEG-PCL-SS NPs and drug-loaded PEG-PCL-SS NPs were prepared. The particle size change of all these NPs was shown in Additional file 1: Figure S1. When DTT was added to PEG-PCL-SS NPs or DOX&IR780@PEG-PCL-SS NPs, the particle sizes were reduced because of internal cross-linking ability of disulfide bond. Full wavelength absorption of DOX&IR780@PEG-PCL-SS NPs shows that the nanoparticles have two absorption peaks at 497 nm and 780 nm, which are the characteristics of doxorubicin and IR780, respectively. While DOX and IR780 are hydrophobic, the UV spectrum proves that both drugs successfully assembled into nanoparticles. XPS experiment was carried out here to evaluate the superficial elements of DOX&IR780@PEG-PCL-SS NPs. From the results shown in Additional file 1: Figure S2, a significant Cl peak was observed in free DOX, while “I” element peak was observed in IR780. When IR780 and DOX were encapsulated into PEG-PCL-SS NPs, the intensity of O and N peak did not change greatly. However, the intensity of Cl and “I” peaks were significantly lower than that of free DOX, free IR780, or physical mixture. These results indicated that the superficial elements of DOX&IR780@PEG-PCL-SS NPs were mainly composed of PEG-PCL-SS while the DOX and IR780 were mostly located inside nanoparticles.

IR780 can be used as an effective photothermal agent. Under 808 nm laser irradiation, the IR780 NPs and DOX&IR780 NPs (50 μg/mL IR780) can increase the temperature over time, while the temperature of PBS group was only slightly increased. It demonstrated that IR780 has a significant photothermal effect (up to 53.6 °C) and the addition of DOX does not affect the photothermal effect (Fig. 3a). The prepared nanoparticles were then placed into the environment at 37 °C and 4 °C and particle sizes were measured every 24 h (Fig. 3b). The results show that the nanoparticles have excellent stability for at least 144 h at 4 °C or body temperature. To prove the advantage of PEG-PCL-SS NPs, two other common carriers-based (PLGA and Albumin) nanoparticles were prepared [24]. After PEGylation, the size of PEG-PCL-SS NPs was about 60 nm, smaller than PLGA and Albumin NPs (Additional file 1: Figure S3). For the stability study, both PEG-PCL, PLGA and albumin NPs will precipitate in one week, while PEG-PCL-SS NPs can keep stable in one week.

An in vitro drug release study was conducted to confirm the duel responsiveness of the nanoparticles to GSH and photothermal effect. GSH was added to the PBS to mimic the tumor cell microenvironment. It is important to note that as glutathione (5 mM to 10 mM) increases, DOX in the nanoparticles can be released more and more quickly (from 31.3% to 61.9%) (Fig. 3c). This is because the breakdown of the disulfide bond in the nanoparticle structure due to GSH can result in the drug release. In addition, we have found that with the photothermal effect produced by the addition of the photosensitizer IR780, the release of the drug can be greatly promoted (Fig. 3d). This experiment validated the properties of nanoparticles with controlled release manner, and we can trigger drug release with glutathione and near-infrared laser irradiation. According to previous studies, the invasive bladder cancer normally contains higher amount of glutathione. Therefore, the nanoparticles we developed can provide controlled drug release in a GSH-rich environment and potentially enhance therapeutic effects against tumors with high malignancy.

The cell cytotoxicity of the drug-loaded nanoparticles was evaluated by the MTT assay (Fig. 4a). Under the near-infrared laser irradiation, the cytotoxicity produced by the photothermal effect was significantly higher than that of the other control groups (from IR780 concentration of 0.078 μg/mL or more). The results confirmed that the nanoparticles had a good photothermal treatment effect. Both free IR780 and DOX exhibited antitumor ability in cancer cells. However, the NPs co-loaded with IR780 and DOX showed strong, synergistic therapy for cancer treatment. In the meantime, the cytotoxicity of NPs in normal cells is much less than that of cancer cells (Fig. 4a, Additional file 1: Figure S4). However, as DOX is very toxic, and the photothermal effect of IR780 is very strong, the cytotoxicity of NPs in normal cells is clearly observed. The difference of toxicity is mainly caused by the difference of cell uptake. The drug amount of cancer cells uptake is much higher than normal cells. When IR780 concentration was 1.25 μg/mL and DOX was 1.775 μg/mL, cell viability was 31.34% and 12.22% without or with laser irradiation, respectively. At the same time, it can be observed that the difference in cytotoxicity during the process of increasing DOX concentration is getting smaller and smaller, indicating that the effect of chemotherapeutic drugs begins to play a leading role as the concentration of doxorubicin increases. This is consistent with the clinical situation.

To monitor cellular uptake of DOX&IR780@PEG-PCL-SS NPs, the nanoparticles were incubated with MB-49 cancer cells, and the result was observed by fluorescence microscope. As can be seen from Fig. 4b, compared with free DOX or free IR780 group, DOX&IR780@PEG-PCL-SS NPs had more DOX and IR780 fluorescence within the cells, indicating NPs enhanced the drug uptake. This is beneficial for the photothermal and chemotherapy.

In order to verify the accumulation of nanoparticles in tumor, we investigated the biodistribution of the nanoparticle in a mouse bladder cancer model. As can be seen from Fig. 5a, free IR780 also has a certain accumulation in bladder tumors, which is the passive accumulation of the near-infrared dye itself. For the normal mouse group, there is part of NPs accumulating in the bladder region. Ex vivo imaging (the last organ is bladder for each group) showed that bladder had very few NPs compared with other organs. The nanoparticle group accumulates in the tumor, indicating that our nanoparticles have good tumor targeting. The distribution of DOX&IR780@PEG-PCL-SS NPs provides a solid foundation for further treatment. PEGylation is a common approach for improving the efficiency of drug delivery in vivo. In vivo pharmacokinetics of different nanoparticles were compared here. From the results (Additional file 1: Figure S5), there are no significant difference in half-life time (t_1/2) of PEG-PCL-SS, PEG-PCL and albumin NPs (24.18 h vs 20.63 h vs 22.37 h). The half-life time of PLGA NPs is 6.07 h, much less than other three carriers. PEGylation improved the in vivo circulation time of drug loaded NPs. Albumin is a classic drug carrier, and paclitaxel loaded albumin NPs are used in clinic [23]. The results showed that PEG-PCL-SS as a drug carrier is comparable with Albumin.

We established the orthotopic bladder cancer model in C57BL/6 mice according to our previously reported method [2]. Through small animal CT, a tumor can be observed when the bladder of the mouse is filled with urine (Fig. 5b). This indicated the successful construction of a mouse orthotopic bladder cancer model.

Changes in tumor size in a mouse bladder cancer model can be observed by In vivo imaging. One week after injection of luciferase-expressing MB49 cells, significant bioluminescence aggregation in the bladder area of mice was observed, suggesting tumor formed (Fig. 6a). After 3 weeks’ treatment, mice treated with DOX&IR780@PEG-PCL-SS NPs and near-infrared laser irradiation achieved the best anticancer effect, and the tumor growth was the slowest compared with other groups, indicating that the combined therapy can achieve synergistic inhibition effect for the bladder tumors. We then used the ROI value of fluorescence imaging to further evaluate the size of bladder tumors (Fig. 6b), and quantitatively confirmed the reduction of bladder tumor sizes after the treatment using DOX&IR780@PEG-PCL-SS NPs and near-infrared laser irradiation. Additionally, visual photos of the bladder tumors of the mice obtained in the third week (21 days) were taken by camera and the results are consistent with in vivo imaging data (Fig. 6c). Photographs of normal bladder and orthotopic bladder cancer are shown in Fig. 6c. The normal bladder wall was transparent with no solid lesions. An obvious solid lesion was observed in the bladder cancer model, showing the carcinoma invasion in all layers of the bladder wall, including the mucosa and muscular layer. This orthotopic bladder cancer model was similar to muscular invasive bladder cancer of humans in the clinic.

After the mice were sacrificed, the heart, liver, spleen, lung, kidney and bladder of the mice were collected for histological analysis. The bladder and tumor tissues were stained with H&E, TUNEL or Ki-67 to observe the apoptosis and cell proliferation in the bladder cancer tissues. The results of bladder tumor staining showed that the bladder tumor involved the whole bladder layer, and the tumor apoptosis level of the tumors from the mice treated with DOX&IR780@PEG-PCL-SS NPs combined with near-infrared laser irradiation was significantly higher than that of other experimental groups while the bladder cancer cell proliferation was less than other groups (Ki67 staining results) (Fig. 6d).

To evaluate the toxicity of the nanoparticles at the whole-body level, blood samples and major organs were harvested for serological and histological analysis. There were no obvious accumulation of nanoparticles and functional damage. 24 h after the tail vein administration of the mice, blood was obtained by eyeball blood sampling. Serological tests in mice showed that the selected nanoparticle concentration (from 0 to 2.5 mg/kg DOX, from 0 to 4 mg/kg IR780) did not identify liver and kidney damage. However, significant changes in liver and kidney function were observed after injection of high concentrations of nanoparticles (5 mg/kg DOX, 8 mg/kg IR780) (Fig. 7a–d). The major organs (heart, liver, spleen, lung, and kidney) of all the groups showed no noticeable histological changes, suggesting the nanoparticles have no toxicity to the organs and are biocompatible to be used as drug formulations (Fig. 7e).

The datasets used and analyzed during the current study are available from the corresponding author on reasonable request.