Preparation and optimization of nanoparticles
Even though EGCG and Fe3+ ions have been widely used to prepare MPNs, there were rare reports about using MPNs as carriers for delivery of BLM. Owing to the presence of metal-binding domain in BLM, Fe3+ ions could assemble with BLM in water, forming the core of nanoparticles [38, 39]. Then redundant Fe3+ ions further coordinated with EGCG at the interface of ethanol/water, composing MPNs (Fig. 1A and Additional file 1: Figure S1). We firstly investigated the proportion of three components required for the formation of BFE NPs. At beginning, the proportion of EGCG was explored by varying its input with fixed amount of BLM and Fe3+. As shown in Fig. 1B and Additional file 1: Figure S2A, when the molar ratio between BLM, EGCG and Fe3+ was set at 1:3:6, the corresponding nanoparticles exhibited the darkest color, whereas the particle size reached minimum and the zeta potential also decreased to the lowest. Similarly, the influence of the amount of Fe3+ on BFE NPs was examined. Using particle size and zeta potential as indicators, it has been further confirmed that the prepared nanoparticles were most suitable when the proportion of three components was 1:3:6 (Fig. 1C and Additional file 1: Figure S2B). Therefore, the molar ratio between BLM, EGCG and Fe3+ in the formation of BFE NPs was fixed at 1:3:6 in the following investigation.
The stability of nanoparticles is a prerequisite for subsequent application and storage. In order to simulate different biological conditions, the particle size changes of BFE NPs incubated in different media (H2O, Glu, NS, PB, and PBS) were monitored. After 24 h, BFE NPs were quite stable in both water and glucose solution, as the particle size of BFE NPs remained unchanged (Fig. 1D and E). But the particle size of BFE NPs increased exponentially in NS, PB and PBS, and sedimentation was even observed in PB and PBS. Furthermore, there was no precipitation of BFE NPs in 10 or 50% FBS-M or 100% FBS, and the particle size of nanoparticles slightly increased and then stayed steady (Additional file 1: Figure S3). Thus, we hypothesized that BFE NPs might adsorb proteins from the serum, which facilitated the stability of nanoparticles. In long-term stability study, BFE NPs were steady and remained the similar size for 7 days in the complete medium containing 10% FBS (Fig. 1F and Additional file 1: Figure S4A). In brief, BFE NPs aggregated in various salt solutions, but they exhibited colloidal stability in serum-containing solution, indicating that serum proteins might protect BFE NPs from aggregation.
Polyphenols are highly adherent and exhibit multiple interactions (e.g., hydrogen bonds, hydrophobic, and electrostatic interactions), which allow them to form robust conjugates with other substances. BSA has been widely used to modify nanoparticles to improve the stability. In order to improve the stability of BFE NPs, BFE NPs were further modified with BSA by incubation in BSA solution through surface adsorption (Fig. 1G). When the concentration of BSA reached 5 mg/mL (Fig. 1H), the nanoparticles could remain stable in PBS. Subsequently, with the concentration of BSA continually increased, the particle size of nanoparticles gradually increased. Therefore, the BSA concentration of 5 mg/mL was selected to prepare [email protected] NPs. As expected, the particle size of [email protected] NPs remained constant for 7 days in all media, including H2O, PBS and 10% FBS-M (Fig. 1I and Additional file 1: Figure S4B). The introduction of BSA endowed nanoparticles with great physiological stability and long-term stability, which laid a sufficient foundation for subsequent application.
To sum up, BLM + Fe3+ or BLM + EGCG could form nanoparticles (BF NPs or BE NPs). But only when three components were all present, nanoparticles with desired structure could be fabricated. As shown in Fig. 1J, BFE NPs which were prepared in optimal proportion displayed the particle size of 158.9 ± 1.8 nm and the zeta potential of − 38.1 ± 3.5 mV and presented a dark black appearance. The negative surface charge of BFE NPs indicated the structure of MPNs. After BSA coating on the surface of nanoparticles, [email protected] NPs remained the black appearance, while their particle size increased by ~ 15 nm (173.0 ± 1.4 nm) than BFE NPs and zeta potential was back to − 11.5 ± 1.1 mV. As a result of the masking of BSA, [email protected] NPs were less charged, which remarkably improved the stability of nanoparticles.
Characterization and spectra of nanoparticles
The morphology of nanoparticles was studied by TEM. As shown in Fig. 1K–L and Additional file 1: Figure S5, BFE NPs possessed network-like structures, which indicated the successful formation of MPNs. While the images of [email protected] NPs presented scattered particles because BSA facilitated the dispersion of nanoparticles. As shown in Additional file 1: Table S1, the EE of BLM and Fe3+ in [email protected] NPs was 65.0% and 77.2% (80.4% and 94.9% in BFE NPs), respectively, indicating this delivery system realized efficient drug packaging. In order to confirm the formation of nanoparticles, the UV–vis spectra, fluorescent spectra and FT-IR spectra were subsequently applied to analyze the formation mechanism. In Fig. 2A, the maximum absorption wavelength of BLM at 291 nm was red-shifted to 297 nm in the UV–vis spectrum of [email protected] NPs, which manifested the π-π interactions between BLM, EGCG and BSA. Furthermore, [email protected] NPs and direct mixture of EGCG + Fe3+ exhibited broad absorption in the NIR window, confirming that Fe3+-based MPNs had the ability to serve as photothermal reagents. In Fig. 2B, BLM exhibited a fluorescence emission from 330 to 480 nm with excitation wavelength at 308 nm in its fluorescent spectrum. However, the fluorescence of BLM was quenched in [email protected] NPs as a result of the formation of coordination bonds between EGCG and Fe3+. In Fig. 2C, the -OH stretching bands (3556, 3479 and 3357 cm−1) of pure EGCG were not observed in the FT-IR spectrum of [email protected] NPs, demonstrating the formation of coordination bonds. [email protected] NPs exhibited the characteristic amide I and amide II band vibrations (1648 and 1550 cm−1) of BLM and BSA, indicating the existence of BLM and BSA in nanoparticles. All of the above results proved the successful preparation of [email protected] NPs.
Self-assembly mechanism study of BFE NPs and [email protected] NPs
In order to further confirm the self-assembly mechanism of BFE NPs and [email protected] NPs, the prepared nanoparticles were dispersed into different solutions (NaCl, urea, EDTA and SDS) to determine the role of electrostatic force, hydrogen bonds, coordination bonds and hydrophobic force, respectively. In Fig. 2D, when BFE NPs were dispersed into 0.9% NaCl solution (electrostatic force-eliminating agents), a small amount of precipitation was observed, indicating there were certain electrostatic interactions within nanomedicines. Changes and precipitation were more obvious when BFE was mixed with urea solution which could deconstruct hydrogen bonds, suggesting the hydrogen bonds were involved in the formation of BFE NPs. However, it was found that SDS did not affect nanoparticles, suggesting hydrophobic force barely existed during the assembly process of BFE NPs. The most obvious change of BFE NPs was observed in appearance, where precipitate formed immediately, upon mixing with EDTA solution (coordination bonds-eliminating agents). These results implied that EDTA was the most effective treatment to disintegrate the BFE NPs and coordination force played the main force in the formation of BFE.
To sum up, we could speculate different forces that participated in the formation of nanoparticles as follow: coordination bonds > hydrogen bonds > electrostatic force ≫ hydrophobic force. Furthermore, when the [email protected] NPs were placed in the above solution, the changes were smaller than that of BFE NPs in appearance. This indicated that the presence of BSA could improve the stability of nanoparticles to a certain degree. It has been proved that the fluorescence of BLM in [email protected] NPs was quenched, owing to coordination between BLM and Fe3+ (Fig. 2B). Therefore, we further investigated the fluorescence recovery ability of BLM from [email protected] NPs by adding EDTA solution. The degradation of [email protected] NPs was supposed to induce the release of BLM, leading to fluorescence recovery. As shown in Fig. 2E, upon adding EDTA, the fluorescence of BLM gradually recovered and fluorescence intensity gradually increased with incubation time. It indicated that EDTA could destroy the structures of [email protected] NPs and lead to the release of BLM. It further confirmed that coordination force played a vital role in the self-assembly process of nanoparticles.
In vitro pH sensitive study
The [email protected] NPs was designed with the characteristics of pH-responsive degradation in an acidic environment, owing to the pH responsiveness of coordination force and hydrogen bonding. In acidic conditions, the disassemble of [email protected] NPs was accompanied by BLM release in the acidic TME. To evaluate the pH-responsive capability of [email protected] NPs, the size distribution of nanomedicines was measured firstly through dispersing them into buffer solution with pH at 6.5 and 5.5. From the results in Fig. 2F, with the extension of incubation time, the particle size of nanoparticles increased gradually in an acidic environment. The particle size of [email protected] NPs remained steady with negligible changes at pH 7.4. But at pH 6.5 and 5.5, [email protected] NPs became larger than before, indicating that the nanoparticles were pH-responsive.
Furthermore, the fluorescence recovery ability of BLM from [email protected] NPs under acidic conditions (pH 6.5 and 5.5) was also investigated. As expected, the fluorescence intensity of BLM increased gradually with incubation time at both pH values in Fig. 2G and H. Moreover, the fluorescence intensity of BLM recovered more quickly at pH 5.5 than that at pH 6.5. These results implied that [email protected] NPs could gradually dissociate and release the BLM in an acidic environment.
In vitro drug release
To accurately access the BLM release behavior from [email protected] NPs in the physiological condition, tumor sites and intracellular acidic environment, in vitro drug release tests were performed in PBS solutions with pH 7.4, pH 6.5 and pH 5.5, to simulate certain conditions. As shown in Fig. 2I, the amount of BLM released from [email protected] NPs was gradually increased as the pH of releasing medium decreased from 7.4 to 5.5. At pH 7.4, the amount of BLM released within the entire experimental period (72 h) was around 30%, while BLM released was up to 43% in PBS solution at pH 5.5. The pH sensitive release profile was mainly ascribed to the dissociation of the coordination bands in [email protected] NPs in acidic environment.
In vitro photothermal evaluation
In our previous study, it was found that Fe3+ ions-based MPNs exhibited a broad absorption in the NIR region, which indicated that the designed reagents might have a photothermal transduction effect. To test the photothermal conversion efficiency of [email protected] NPs, the temperature differences (ΔT) of [email protected] NPs solution was checked under different Fe3+ concentrations or power densities. In Fig. 2J, K and Additional file 1: Figure S6A, B, with the increase of laser intensity (from 2.0 to 3.0 W/cm2) or iron ions concentration (from 0.2 to 0.8 mM), the temperature of [email protected] NPs solution increased significantly. The temperature of [email protected] NPs with Fe3+ concentration at 0.8 mM could increase up to 48.1 ℃ with temperature change about 21 ℃ after irradiation for 10 min (808 nm laser at 2.5 W/cm2). These results suggested that [email protected] NPs could serve as effective PTAs.
To further investigate the photothermal stability of nanomedicines, BFE NPs and [email protected] NPs (0.8 mM) were irradiated for 5 cycles of laser on (808 nm laser at 2.5 W/cm2, 10 min) and laser off (10 min), respectively. After 5 cycles, the ΔT between adjacent peaks was within 0.5 ℃ according to Fig. 2L. It indicated the excellent photothermal stability of both BFE NPs and [email protected] NPs under repeated NIR laser irradiation, while coating with BSA did not affect the photothermal conversion efficiency of nanoparticles.
In vitro cytotoxicity assay
The cell viability was firstly determined by MTT assay to investigate the in vitro anti-tumor ability of [email protected] NPs. 4T1 cells were incubated with free BLM or [email protected] NPs at different BLM concentrations. As shown in Fig. 3A, both free BLM and [email protected] NPs showed weak cytotoxicity at low concentrations. The cell viability of [email protected] NPs at BLM concentration of 8 μM was 53.2%, which was lower than that of free BLM (66.5%). And the cell viability of [email protected] NPs + L (BLM: 8 μM) was 47.1%, indicating that [email protected] NPs could efficiently kill tumor cells with laser irradiation. Then, live/dead staining assay was conducted by staining cells with Calcein-AM and PI after respective treatments. Calcein-AM (green) could easily penetrate live cell membrane to mark live cells, while PI (red) could only reach the cell nucleus through the disordered membrane of dead cell. As shown in Fig. 3B, the cells which were treated with laser alone showed almost no apparent red fluorescence. More red fluorescent signals were found in the groups treated with free BLM or [email protected] NPs (BLM: 8 μM), and cells treated with [email protected] NPs + L presented obvious red fluorescence. All the results illustrated the synergistic cytotoxicity of combination therapy.
In vitro cellular uptake study
It was reported that the cellular uptake of nanomedicines was significantly influenced by their surface physicochemical characteristics. In order to understand whether the presence of BSA in our system would facilitate the cellular uptake, we evaluated the effect of BSA modification on the in vitro cellular uptake. Before that, green fluorescent dye, coumarin-6, was loaded into BFE NPs during the preparation for fluorescent observations. The internalization of BFE NPs and [email protected] NPs into 4T1 cells was observed by fluorescence microscopy. The blue area was the nuclei of 4T1 cells stained by DAPI and the green fluorescence resulted from coumarin-6 loaded nanoparticles. As shown in Fig. 3C, the amount of phagocytosed nanoparticles, no matter BFE NPs or [email protected] NPs, both increased with time, as stronger green fluorescence was observed at 6 h than that at 2 h, indicating the internalization of nanoparticles occurred in a time-dependent manner. What’s more, after incubation with BFE NPs or [email protected] NPs, the cytoplasm of 4T1 cells presented different intensities of coumarin-6 fluorescence. The fluorescence of cells treated with [email protected] NPs was much stronger than that in BFE NPs group, indicating that the surface modification of BSA could promote cellular uptake of nanoparticles.
In vitro ROS generation
It is a truism that higher than the physiological level of ROS would trigger the damage of proteins, organelles and nucleic acids, thus leading to cell apoptosis. Excessive production of ROS within cancer cells, such as superoxide anion radical (O2●−) and hydroxyl radical (•OH), is often considered to be a significant condition for killing tumor cells. The designed system was supposed to produce excess ROS in multiple directions (Fig. 3D). In combination with FeII, BLM was transformed into an activated form and could convert oxygen into hydrogen peroxide (H2O2). Highly toxic hydroxyl radicals were produced by the Fenton reactions under the high concentration of H2O2, leading to ROS amplification. Moreover, the transformation between Fe3+ ions and Fe2+ ions consumed glutathione heavily. This kind of GSH depletion could protect generated ROS from scavenging. Elevated temperature caused by PTT could further promote the production of ROS. Therefore, we evaluated the ROS generation ability of [email protected] NPs by incubation with 4T1 cancer cells. According to the fluorescence changes of a ROS-sensitive probe, 2′,7′-dichlorofluorescin diacetate (DCFH-DA), the amount of generated ROS could be confirmed. As shown in Fig. 3G, weak green fluorescence (DCF) was observed in control group or cells treated with laser, indicating that ROS produced by the metabolism of cells themselves was limited. The ROS level in 4T1 cancer cells treated with BLM alone increased slightly. It was reasonable since BLM could efficiently promote the formation of hydrogen peroxide only when catalyzed by adequate iron ions. Treating 4T1 cells with [email protected] NPs could facilitate the generation of ROS, as an increased fluorescence signal was observed in the cytoplasm. Upon laser irradiation, bright fluorescence was observed, indicating that the significantly enhanced ROS amplification effect was triggered by NIR. Furthermore, similar results were mirrored by flow cytometry analysis which were presented in Fig. 3E and F. These results implied that [email protected] NPs combined with PTT could synergistically induce ROS amplification.
In vitro MRI study of [email protected] NPs
The incorporation of Fe3+ ions enbaled [email protected] NPs to be potential MRI contrast agents. To further evaluate the contrast efficacy of [email protected] NPs, their longitudinal relaxivity (r1) and transverse relaxivity (r2) were tested firstly by scanning [email protected] NPs with different concentration gradients of Fe (0, 0.1, 0.2, 0.3, 0.4, and 0.5 mM). According to the graph data (Fig. 4A and Additional file 1: Figure S7), [email protected] NPs exhibited the r1 value of 0.96 mM−1 s−1 in water. The r2 value of [email protected] NPs was determined to be 2.41 mM−1 s−1, which was too low for [email protected] NPs to perform as T2-weighted contrast agents. But r2/r1 = 2.51 < 3, indicating [email protected] NPs were potential T1-weighted contrast agents for further application.  In Fig. 4B, it showed the T1-weighted images of [email protected] NPs at different Fe3+ concentrations, which presented positive bright contrast increasing. The MR signal was enhanced linearly with the increasing concentrations of Fe3+. [email protected] NPs dispersed in agarose gel also showed the obvious results (Additional file 1: Figure S8). The T1 value was measured by the T1 mapping images. As shown in Fig. C, [email protected] NPs could significantly shorten T1 relaxation time both in water and agarose gel, indicating they have good MR imaging ability in vitro. Then, [email protected] NPs were used for cellular MR imaging.  After incubation with nanoparticles for 4 h, the T1 value of 4T1 cells treated with [email protected] NPs was found to be significantly lower than that of cells without nanoparticles (Fig. 4D, E), indicating [email protected] NPs had the potential for further in vivo MR imaging.
In vivo MR imaging of mice
It is extremely important to accurately monitor the size and location of tumor in the course of tumor therapy. Especially for photothermal or photodynamic therapy, accurate imaging of tumors can guide the course of treatment, monitor therapeutic efficacy, and reduce unexpected damage to normal tissues. MRI has become a diagnostic and research tool in treating various tumors because of its ability of accurately delineating the detailed images of the tumor tissue. As shown in Fig. 4F, 4T1 tumor-bearing BALB/c mice were i.v. injected with [email protected] NPs to assess in vivo MR imaging ability. In Fig. 4G, compared to pre-injection, the tumor region of mice was significantly brighter after injection of [email protected] NPs, owing to the effective accumulation of [email protected] NPs at the tumor site. The contrast between the tumor tissue and surrounding normal tissue was more pronounced, making tumor boundary clearer. In Fig. 4H, [email protected] NPs was continuously enriched at the tumor site and the T1 MR signal intensity gradually increased. At 4 h post-injection, the relative T1 signal of tumor site reached the maximum, which was about 1.63 times higher than that of pre-injection. After that, the MR signal intensity gradually decreased, or even fell below the value of pre-injection since 12 h post-injection. The quantitative analysis of SNR in tumor region presented the similar results (Fig.4I). It might be caused by the increased tumor necrotic areas (red arrow represented the necrosis of tumor tissue), which indicated the cytotoxic effect of [email protected] NPs upon arrival of the tumor region.  From all these results, it could reflect that effective accumulation of [email protected] NPs at the tumor sites could favor the precise MR imaging and cause necrosis of the tumor tissue, facilitating further therapeutic applications.
Based on the above axial images, coronal MR scanning was performed to study various organs of the mice. Furthermore, the coronal T1-weighted MR images and T1 mapping images of mice showed the similar trend. As shown in Fig. 4J, after intravenous injection of [email protected] NPs, the tumor became brighter over time compared to other organs, and the average SNR of tumor gradually increased (Fig. 4K). In T1 mapping images, [email protected] NPs visibly decreased the T1 value of tumor, the T1 relaxation time was gradually shortened (Fig. 4L). In Additional file 1: Figure S9, the tumor and other organs could be clearly distinguished (the organs were marked with different colored arrows), and the SNR of different organs increase over time. Although the SNR of different organs increased over time, the relative signal ratio of tumor to other organs also increased, indicating that [email protected] NPs exhibited good enhancement effects on the signal of tumor.
Biodistribution study of [email protected] NPs
To evaluate the biodistribution of [email protected] NPs within the body, 4T1 tumor-bearing BALB/c mice were established and tested. Fluorescent dye DiR labeled [email protected] NPs or free DiR were injected into tumor-bearing BALB/c mice, respectively. The mice were sacrificed to obtain tumors and main organs at designed time intervals (8, 12 and 24 h). As shown in Fig. 5A, quite weak DiR fluorescence intensity was observed and remained the same level at all the time points in the tumor from mice intravenously injected with free DiR. It was similar trend as previous reports, which was ascribed to its weak tumor retention.  Moreover, the liver and spleen were the main accumulation organs of free DiR. By contrast, stronger fluorescence intensity was observed in the tumor from mice treated with [email protected] NPs. In Fig. 5B, quantification of fluorescence intensity indicated that the accumulative fluorescence intensity at the tumor site increased with prolonging time and reached the maximum fluorescence intensity at 12 h post-injection (Additional file 1: Figure S10). The quantitative results of relative fluorescent ratio of tumor/liver displayed the similar trend (Fig. 5C).  It was worth mention that the accumulation of [email protected] NPs in the liver and spleen was significantly reduced, indicating that our nanomedicine was able to prolong the circulation lifetime of drugs and change metabolic pathways of drugs in the body. These results implied that [email protected] NPs could accumulate in the tumor region effectively.
In vivo dose exploration of BLM
Even though BLM is an effective glycopeptide anticancer drug that could affect the cutting of single- and double-stranded DNA, the risk of pulmonary fibrosis caused by BLM is still not negligible. In order to achieve the highest anti-tumor activity of BLM while minimizing its potential side effects, before applying [email protected] NPs into further in vivo anti-tumor experiment, the optimal dosage of BLM was firstly explored. As the experimental scheme diagram of treatment shown in Fig. 5D, 4T1 tumor-bearing BALB/c mice were i.v. injected with PBS or [email protected] NPs with different concentrations (BLM: 2.5, 5 and 10 mg/kg) on day 5, 8 and 11. Both the body weight and tumor volume were measured every 2 days and tumors from mice with various treatments were separated and weighed on day 21 post-injection. As shown in Fig. 5E–H and Additional file 1: Figure S11A, compared with PBS, all the groups treated with [email protected] NPs exhibited anti-tumor effect (inhibition rate of 47.0% for 2.5 mg/kg, 61.7% for 5 mg/kg and 67.7% for 10 mg/kg) due to effective killing effect of nanoparticles on tumors.
According to the tumor growth curve, mice treated with [email protected] NPs (BLM: 5 mg/kg or 10 mg/kg) exhibited similar tumor-suppressive power, as no significant difference was observed both in the tumor volume and tumor weight. But when compared to mice treated with 2.5 mg/kg, better tumor inhibition with significantly smaller tumor size and low tumor weight was found in groups treated with 5 or 10 mg/kg. Then, the safety of nanomedicine was monitored by analyzing the weight of the mice and lung section. It was found that 10 mg/kg of BLM treatment gave rise to the obvious loss of body weight, while the weight of mice treated with 5 mg/kg remained unchanged. It might mean that [email protected] NPs (BLM: 10 mg/kg) had overrun the safe dose. The idea was further confirmed in the results of lung section by histological analysis. As shown in Fig. 5I and Additional file 1: Figure S11B, the extensive inflammation was observed in the group of 10 mg/kg, and this was also associated with widespread collagen (blue area by Masson’s trichrome staining) accumulation and alveolar structure disorder. While the group of 2.5 and 5 mg/kg presented mild inflammation, and there were no obvious pathological changes in lung structures. [email protected] NPs (BLM: 10 mg/kg) showed more severe pulmonary fibrosis of mice than other groups, which represented dose-dependent side effects. Therefore, the concentration of nanomedicine was set to [email protected] NPs (BLM: 5 mg/kg) in the following experiments.
In vivo anti-tumor efficiency of synergistic therapy
To further evaluate the combined therapeutic effects of CDT and PTT, 4T1 tumor-bearing BALB/c mice were i.v. injected with PBS, free BLM (5 mg/kg) or [email protected] NPs (BLM: 5 mg/kg) three times on day 6, 9 and 12. Half of the mice that received [email protected] NPs were further locally irradiated under NIR laser every 12 h-post injection at a power density of 2.5 W/cm2 for 2 min (Fig. 6A). Both the body weight and tumor volume were measured every 2 days and tumors and main organs from mice with various treatments were separated and weighed on day 21. As recorded in Fig. 6B–D and F, BLM and [email protected] NPs treatment presented moderate tumor inhibitory effect comparing to PBS group. The tumor inhibitory rate of BLM and [email protected] NPs were 58.4% and 69.0%, respectively. The superior anti-tumor efficiency of [email protected] NPs than free BLM was attributed to the enhanced accumulation at tumor site and the ROS amplification effect of nanomedicine. Beyond expectation, the [email protected] NPs + L group showed the eminent inhibition compared with other groups (tumor inhibition rate was calculated to be 93.7%) without obvious weight loss of mice. In Fig. 6E and Additional file 1: Figure S12, complete tumor ablation was achieved in five mice of all eight mice (5/8). During the entire experimental period, the therapeutic efficacy was maintained well and no recurrence was observed in the ablated tumor. These results demonstrated the superiority of combination therapy of chemotherapy, CDT and PTT. Histological analysis of the lung sections stained with H&E and Masson’s trichrome was conducted to assess the side effects of pulmonary fibrosis. As shown in Fig. 6G and H, severe inflammation was not observed in each group, and there were no obvious pathological changes in the lungs of all groups. In general, [email protected] NPs + Laser could achieve the desirable therapeutic effect with minimal toxic side effects.
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