{'fraction_non_alphanumeric': 0.04334738109572547, 'fraction_numerical': 0.032140045385078496, 'mean_word_length': 4.407963936889557, 'pattern_counts': {'":': 0, '<': 0, '<?xml version=': 0, '>': 0, 'https://': 0, 'lorem ipsum': 0, 'www.': 0, 'xml': 0}, 'pii_count': 0, 'substrings_counts': 0, 'word_list_counts': {'cursed_substrings.json': 0, 'profanity_word_list.json': 0, 'sexual_word_list.json': 0, 'zh_pornsignals.json': 0}}
Multi-mode biodegradable tumour-microenvironment sensitive nanoparticles for targeted breast cancer imaging

Gas-filled ultrasound (US) contrast agents easily collapse in the body, and the gas can easily overflow, which limits the effectiveness of US imaging. To address this issue, an injectable gas-generating multi-mode system was developed that carries the MR negative contrast agent Fe3O4, the fluorescent dye Cy5.5, and the CO2 releasing donor (Na2CO3). The nanoparticles can continuously generate carbon dioxide (CO2) gas in acidic tumour tissue in the body, giving the tumour a strong echo signal under ultrasonic imaging. In addition, the nanoparticles confer excellent effects for MR and fluorescence imaging of the tumour tissue. The results indicate that this pH-responsive NP system provides good effects in MR/US/fluorescent imaging. This study provides a useful reference for multi-mode tumour imaging.


Introduction
In clinical practice, microbubbles are primarily applied as ultrasound contrast agents for the real-time imaging of various organs and blood vessels [1][2][3]. Traditional ultrasound contrast agents typically consist of materials such as lipids or proteins that enclose air or perfluorocarbon gases. The gas species encapsulated in the microspheres have low stability in the blood and a short halflife because of the rapid diffusion of microbubble defects [4][5][6]. Moreover, because the particle size of the gasfilled microbubbles is usually large (approximately 1 to 8 μm), it is difficult for the microbubbles to penetrate into the host tumour environment by tissue extravasation. Therefore, the current application of micron-sized bubbles in intravascular imaging is limited [7]. Ideal ultrasound contrast agents should generally exhibit an optimal size for transport through the tissue vascular space, an adequate duration of acoustic effect, good targeting and biocompatibility, and easy excretion from the body [8,9]. The concept of "gas-generating nanoparticles" was proposed in prior research, and such nanoparticles have the potential for use in ultrasound contrast imaging [10][11][12]. These gas-generating nanoparticles are superior to the current gas-filled microbubbles in performance, and the continuously generated gas enables intense ultrasound imaging. Gas-generating nanoparticles can enhance permeation and retention, and they may stably circulate in the blood and effectively accumulate in the tumour tissue [13,14].
It remains a challenge to detect tiny and occult tumours by traditional imaging methods, such as magnetic resonance imaging (MRI), computed tomography (CT), and ultrasound, which are limited by long acquisition times, high radiation dose, and poor sensitivity [15,16]. It is necessary to integrate different imaging methods and develop multi-modal imaging technology to achieve integrate synergy for the early detection of cancer [17][18][19]. Superparamagnetic iron oxide (Fe 3 O 4 ) nanoparticles can be used as negative MRI contrast agents in T2-weighted imaging [20,21]. Fe 3 O 4 has attractive overall properties, including small particle size, strong penetrability, high magnetization, good metabolism, and relatively low toxicity [22,23]. Fe 3 O 4 contrast agents for the MRI diagnosis of early-stage cancer have been extensively studied due to their high relaxation and contrast [24][25][26]. In addition, real-time fluorescence imaging has excellent resolution and can be a valuable method for defining tumour staging, guiding tumour resection, and monitoring the treatment effects [27,28].
Herein, these nanoparticles are mainly encapsulated by poly (lactic-co-glycolic) acid (PLGA), which has been approved by the Food and Drug Administration (FDA) for use as a biosafe material [29,30]. The PLGA particles are modified with RGD peptide to enable binding to αvβ3 integrin on the surface of breast cancer cells and with Cy5.5 as a fluorescent dye for imaging in vivo, and they are encapsulated with Fe 3 O 4 to act as a T2-negative contrast agent in MRI (Scheme 1a). Due to the upregulated glycolysis in tumour tissue, which could produce more lactic acid and protons in the extracellular environment, the pH of tumour tissues (6.8-7.2) is lower than that of normal tissues (pH 7.4) [31][32][33]. Thus, we designed sodium carbonate (Na 2 CO 3 ) in the PLGA to produce CO 2 bubbles at the lower pH of tumour tissues for ultrasound imaging. To verify their promising application in tumour imaging, the comprehensive properties of these multi-mode nanoparticles for in vitro imaging were systematically characterized, including their cytotoxicity, targeting specificity, and biodistribution in tumour tissue, by three imaging modes.

Results and discussion
Synthesis and characterization of Na 2 CO 3 /Fe 3 O 4 @PLGA/ Cy5.5/RGD NPs Na 2 CO 3 /Fe 3 O 4 @PLGA/Cy5.5/RGD NPs were designed as RGD-targeted multi-mode contrast agents by encapsulating a biocompatible polymer of PLGA with Fe 3 O 4 and Na 2 CO 3 and an integrin-targeted agent via a biodegradable chemical bond (Scheme 1b).
Scheme 1 a Schematic diagrams of the function in Fe 3 O 4 /Na 2 CO 3 @PLGA/Cy5.5/cRGD NPs via targeted accumulation into the tumor and generating CO 2 bubbles in acid tumor tissues, followed by triple-modal MR/US/FI imaging of breast cancer. b Schematic illustration of the preparation of the Fe 3 O 4 / Na 2 CO 3 @PLGA/Cy5.5/cRGD NPs.
Transmission electron microscopy images showed that Na 2 CO 3 /Fe 3 O 4 @PLGA/Cy5.5/RGD NPs were clear spheres with uniformly dispersed iron oxide particles visible in the shell (Fig. 1a). The average hydrodynamic size of the NPs was measured as 117.6 nm by dynamic light scattering, and the average polydispersity index was 0.234 (Fig. 1b). The surface charge of the NPs was confirmed by zeta potential measurements to be − 21.7 mV (Fig. 1c). Fluorescence spectrum measurement revealed that Na 2 CO 3 /Fe 3 O 4 @PLGA/Cy5.5/RGD had the maximum emission wavelength at 685 nm, indicating that Cy5.5 was successfully encapsulated in the PLGA core (Fig. 1d). The saturation magnetization values for Na 2 CO 3 /Fe 3 O 4 @PLGA/Cy5.5/RGD and free Fe 3 O 4 NPs were equal to 32.6 and 42.5 emu/g, respectively (Fig. 1e). These findings indicated the superparamagnetic characteristic of the nanoparticles at room temperature. The FITR spectrum of Na 2 CO 3 /Fe 3 O 4 @PLGA/Cy5.5/RGD showed that N-H stretching vibration and -OH absorption peak appeared around 3432 cm −1 . In addition, we found an enhancement (1628 cm −1 ) of the C = O stretching vibration. Compared to that of the nontargeted NPs, the characteristic peak (the carboxyl) at 1735 cm −1 of the targeted NPs was significantly reduced. The results showed the bonding between the carboxyl group on the microsphere surface and the amino group on RGD peptide. In vitro binding of Na 2 CO 3 / Fe 3 O 4 @PLGA/Cy5.5/RGD NPs is shown in Fig. 1f.
In vitro binding of Na2CO3/Fe3O4@PLGA/Cy5.5/RGD NPs αvβ3 integrin is generally highly expressed on breast cancer tumour endothelial cells and can promote tumour metastasis [33][34][35][36]. Cellular immunofluorescence for the expression of αv integrin in MDA-MB-231 cells was much higher than that in MCF-7 cells; A549 cells served as positive controls (Fig. 2a). The cellular uptake of NPs was studied by CLSM (Fig. 2b). The Na 2 CO 3 /Fe 3 O 4 @PLGA/Cy5.5/RGD NPs showed a much higher binding rate to MD-MB-231 cells than did nontargeted NPs. The fluorescence images also revealed that Na 2 CO 3 /Fe 3 O 4 @PLGA/Cy5.5/RGD NPs bound to the cell cytoplasm, and merged images showed the same locations as the expression of αv integrin [37,38].

Cytotoxicity assay
The in vitro cytotoxicity of Na 2 CO 3 /Fe 3 O 4 @PLGA/ Cy5.5/RGD NPs was estimated in MDA-MB-231 cells using a CCK8 assay, while A549 and MCF-7 cells treated with NPs were used as controls (Fig. 2c). In the range of Fe concentrations of 5-80 μg/mL, the cell viability of A549 and MB231 cells was not significantly reduced, and both were above 70%. In contrast, MCF-7 cells showed a significant decrease in cell viability to approximately 50% at Fe concentrations higher than 40 μg/mL.

In vitro contrast imaging
We used an agar gel phantom to study the performance of Na 2 CO 3 /Fe 3 O 4 @PLGA/Cy5.5/RGD NPs in vitro at different pH values (Fig. 3a). The ultrasound contrast images of Na 2 CO 3 /Fe 3 O 4 @PLGA/Cy5.5/RGD NPs were significantly enhanced at weakly acidic pH (pH 6.8) compared with pH 7.2, likely because pH 7.2 does not produce enough CO 2 bubbles for ultrasound imaging. In contrast, when the NPs were in a weakly acidic environment, enough bubbles could be generated for ultrasound imaging. This characteristic is relevant to tumours, which exhibit high tissue heterogeneity and diverse pH levels (pH 6.8-7.2) in vivo [32,39,40]. The signal intensity of the ultrasound image was then analyzed (Fig. 3b). The signal intensity ratios of the non-targeted NP (pH = 7), non-targeted NP (PH = 5), targeted NP (PH = 7), and targeted NP (PH = 5) groups relative to the signal intensity of the blank group were 112%, 145%, 167%, and 178 ± 4%, respectively, which clearly indicates that the targeted NP group (PH = 5) had the strongest US signal.
For the MRI study in vitro, as the concentration of Fe in the Na 2 CO 3 /Fe 3 O 4 @PLGA/Cy5.5/RGD NPs increased, the T2-weighted signal intensity showed a significant decrease, indicating the possibility of these NPs for use as T2 MR contrast agents (Fig. 3c). The transverse relaxation rate (r2) of Na 2 CO 3 /Fe 3 O 4 @PLGA/ Cy5.5/RGD NPs was calculated to be 19.597 mM −1 s −1 . Although the transverse relaxation rate (r2) of Na 2 CO 3 / Fe 3 O 4 @PLGA/Cy5.5/RGD NPs is lower than that of many other MRI superparamagnetic agents, the composition of Fe 3 O 4 can increase the r2, which was 2.94 times higher than the r2 of SPIO particles used clinically.
Ultrasound contrast imaging of Na 2 CO 3 /Fe 3 O 4 @PLGA/ Cy5.5/RGD NPs To demonstrate the potential of the Na 2 CO 3 / Fe 3 O 4 @PLGA/Cy5.5/RGD NPs for ultrasound imaging in tumours, we administered a tail vein injection of Na 2 CO 3 /Fe 3 O 4 @PLGA/Cy5.5/RGD NPs to breast cancer xenograft nude mice and monitored the ultrasound images as a function of time (Fig. 4a). Before injection, images of the tumour, liver, and subcutaneous area were recorded. Immediately after injection, the area of the tumour tissues did not show any contrast enhancement. Enhancement of the tumour area was observed beginning 30 min after injection and lasted for 90 min. The in vivo ultrasound results showed that Na 2 CO 3 / Fe 3 O 4 @PLGA/Cy5.5/ RGD NPs generated enough bubbles in acidic tumour tissues to produce echogenic  reflectivity for ultrasound imaging. As a control, we also obtained images of the liver and subcutaneous tissues at different times after injection of the targeted NPs. Throughout the observation period, no significant enhancement was found in the subcutaneous injection area, and the enhancement in the liver, which decreased over time, was significantly lower than that in the tumours (Fig. 4b). This result indicates that Na 2 CO 3 / Fe 3 O 4 @PLGA/Cy5.5/RGD NPs circulating in the body at physiological pH do not produce a substantial amount of CO 2 bubbles for ultrasound contrast enhancement.

MRI of Na 2 CO 3 /Fe 3 O 4 @PLGA/Cy5.5/RGD NPs
For in vivo MRI, to demonstrate that NPs can be used for tumour-specific imaging, Na 2 CO 3 /Fe 3 O 4 @PLGA/ Cy5.5/RGD NPs were injected directly into tumours and muscles. The results showed that the tumour area exhibited a significant decrease in T2-MR contrast after injection of the targeted NPs, and the signal intensity decreased significantly from 8875 at 0 min to 5972 at 120 min after injection (Fig. 5a, b). However, with the same amount of nanoparticles injected, the subcutaneous muscle area showed a much lower T2 signal decrease. This finding demonstrates the effectiveness of Na 2 CO 3 /Fe 3 O 4 @PLGA/Cy5.5/RGD NPs with hypersensitive integrin-targeted T2-MR contrast agents for use in tumour-targeted imaging. In the tail vein injection group, T2-MR imaging also showed an obvious decrease in contrast in the tumour at 24 h post-injection, demonstrating the high tumour accumulation of Na 2 CO 3 / Fe 3 O 4 @PLGA/Cy5.5/RGD NPs (Fig. 5c, d). Moreover, decreased T2 signals were observed in the liver and kidneys, indicating that the iron ions in the NPs could be rapidly cleared from the body. Therefore, MRI revealed that the PLGA-wrapped Fe 3 O 4 nanoparticles exhibited efficient passive tumour targeting via the enhanced permeability and retention (EPR) effect, especially RGDmediated targeting, but could be decomposed and quickly excreted in vivo.

Fluorescence imaging and histology
Two hundred microliters of NPs were intravenously injected into mice for in vivo fluorescence imaging. In the group injected with RGD-targeted NPs, the fluorescence signal of Cy5.5 gradually increased in the tumour area and reached a peak at 4 h after injection, indicating that Na 2 CO 3 /Fe 3 O 4 @PLGA/Cy5.5/RGD NPs can effectively accumulate in the tumour. In the non-targeted group, NPs were distributed throughout the body after injection and rapidly cleared, and they did not accumulate in the tumour for a long period of time (Fig. 6a). The mice were then dissected, and the main organs and tumours were collected for in vitro fluorescence imaging, which revealed high tumour uptake of the targeted NPs (Fig. 6b, c). The fluorescence intensity of Cy5.5 in the tumours of mice injected with targeted NPs was 1.5 times that in mice injected with non-targeted NPs. Furthermore, tumour-specific targeting of Na 2 CO 3 / Fe 3 O 4 @PLGA/Cy5.5/RGD NPs was verified by tissue fluorescence imaging of frozen tumour sections (Fig. 7a). Immunofluorescence staining of tumour sections with antibodies against αv and β3 integrin revealed significant expression of αvβ3 integrin in tumour tissues. The fluorescence of αv and β3 integrin was merged with the Cy5.5 fluorescence of Na 2 CO 3 /Fe 3 O 4 @PLGA/Cy5.5/ RGD NPs to obtain an immunostaining image revealing colocalization. The immunofluorescence results in the tumour tissues indicated that Na 2 CO 3 /Fe 3 O 4 @PLGA/ Cy5.5/RGD NPs specifically bind to αvβ3 integrin in MB231 malignant breast cancer. Moreover, H&E staining of Na 2 CO 3 /Fe 3 O 4 @PLGA/Cy5.5/RGD NPs compared with the non-targeted group showed that all organ tissue sections had normal pathological morphology and no histopathological damage response (Fig. 7b). All the results of the above cytotoxicity and histological analysis indicated that Na 2 CO 3 /Fe 3 O 4 @PLGA/Cy5.5/RGD NPs induced no significant toxicity to major organ tissues in vivo, and their good biocompatibility can be reasonably attributed to PLGA.

Conclusions
In conclusion, the results above demonstrate a creative and successful approach for MRI of breast cancer through a magnetic targeting and a gas-generating system that is activated in the tumour microenvironment. Na 2 CO 3 /Fe 3 O 4 @PLGA/Cy5.5/RGD NPs exhibit excellent imaging performance and good biocompatibility in MR/ultrasound/fluorescent imaging modes. Our work shows the strong potential for tumour diagnosis with improved multi-modal imaging.

Materials
Poly (lactic-co-glycolic acid) (PLGA) (lactide:glycolide = 75:25, Mw = 20,000), Cyanine5.5 dye, and polyvinyl (See figure on previous page.) Fig. 2 a Confocal fluorescence images with the expression of αv integrin on MB231, A549, and Mcf-7 cells. Blue and green represent DAPI and αv fluorescence, respectively. b Confocal fluorescence images of MB231 cells incubated with targeted Fe 3 O 4 /Na 2 CO 3 @PLGA/Cy5.5/cRGD NPs and non-targeted NPs. Blue, red, and green, represent DAPI, Cy5.5, and α v fluorescence, respectively. c Relative viability of MB231 cells incubated with different concentrations of Fe 3 O 4 /Na 2 CO 3 @PLGA/Cy5.5/cRGD NPs   Fig. 4 a In vivo ultrasound imaging of tumors, livers, and subcutaneous areas at different time after injection of Fe 3 O 4 /Na 2 CO 3 @PLGA/Cy5.5/cRGD NPs. b Echo intensity rate as a function of time is calculated by tissue/blank, tissue represents the echo intensity of the tumor, liver, or subcutaneous area, blank represents the echo intensity before injection to the solution and stirred at 4°C overnight. To remove EDC, NHS, and any residual cRGD, the transparent solution was filtered by an ultrafiltration tube. Finally, Fe 3 O 4 /Na 2 CO 3 @PLGA/Cy5.5/cRGD NPs were resuspended in 1.25 mL of deionized water and stored at 4°C.

Nanoparticle characterization
The dynamic diameters and zeta potential of nanoparticles were measured by a Zetasizer Nano-ZS (Malvern Instruments, UK). The morphology of the nanoparticles was obtained using a FEI Tecnai F20 transmission electron microscope. The Cy5.5 loading was recorded by a Average signal intensity in muscle and tumor for injection of Fe 3 O 4 /Na 2 CO 3 @PLGA/Cy5.5/cRGD NPs. c T2-MR images on axial and coronal of MDA-MB-231 tumor-bearing mice before and after intravenous injection of Fe 3 O 4 /Na 2 CO 3 @PLGA/Cy5.5/cRGD NPs. d Signal intensity ratio is calculated by tissue/muscle, tissue stands for the signal intensity of the tumor, liver, and kidney before and after injection of the targeted NPs, muscle stands for the signal intensity of the muscle at the same time Hitachi F-7000 fluorescence spectrometer. FTIR was performed using a fourier transform infrared spectrometer (Alpha II, Bruker, Switzerland). A vibrating sample magnetometer (VSM, Lake Shore 7410) was applied to determine the hysteresis curve of the nanoparticles and free Fe 3 O 4 .  To assess the targeting efficacy of the nanoparticles, a cellular uptake study was performed by using confocal laser scanning microscopy (CLSM). Cells were seeded onto 35 mm glass-bottom culture dishes (MatTek, USA) at 2 × 10 4 cells mL −1 for 24 h. Then, the cells were incubated with RGD-targeted NPs (30 μg mL −1 , 0.5 mL) at pH 7.4 for 2 h, and non-targeted NPs were used as controls. After incubation, the cells were fixed with 4% paraformaldehyde for 20 min and then incubated with αv antibody. By means of colocalization, we verified the targeted binding of the nanoparticles to the integrin on the cells.

Contrast-enhanced ultrasound imaging
Ultrasound imaging of nanoparticles was performed by using a Vevo 2100 (Fujifilm Visual Sonics Inc., Canada) ultrasound system. The RGD-targeted and non-targeted NPs were added to the agarose model, and PBS was used as a control. Images were recorded in B-mode and CEUS-mode with different pH buffers of 7.2 and 6.8. The area of interest was drawn, and the average grey value was measured in B-mode images.
For in vivo ultrasound imaging, mice were anaesthetized with 2% isoflurane (Hebei Yipin Pharmaceutical Co., Ltd., China), and body temperature was maintained at 37°C with a heated pad. A total of 200 μL of RGDtargeted NPs was injected via the tail vein. Control animals received a subcutaneous injection with the same amount of NPs. Ultrasonic images were recorded using a 7-MHz transducer to continuously acquire ultrasound images of the tumours, livers, and subcutaneous areas. The acoustic focus zone was placed at the centre of the tumour with the largest cross-section, and a field of view containing the tumour and its adjacent tissue was obtained.
Magnetic resonance imaging MRI exams of Na 2 CO 3 /Fe 3 O 4 @PLGA/Cy5.5/RGD NPs were performed using a 3.0 T MR (GE Healthcare, USA) and an animal coil (RF TECH LIMITED, China). NPs with different Fe concentrations of 0.031, 0.063, 0.125, 0.25, 0.5, and 1 mM were scanned in 1 mL Eppendorf tubes, and PBS was used as a control. T2 MRI was performed for each tube using a T2-weighted FSE sequence (slice thickness of 3 mm, TR/TE 2000/74.4 ms, 8 × 8 cm FOV, and 320 × 256 matrix). The relaxivities (r2) were calculated by a linear fitting of the inverse relaxation time as a function of the Fe concentration.
For in vivo MRI, mice were randomly divided into two groups (n = 3) for MR scanning that received either (1) local injection of Na 2 CO 3 /Fe 3 O 4 @PLGA/Cy5.5/RGD NPs within subcutaneous muscle and tumour tissues or (2) tail vein injection of Na 2 CO 3 /Fe 3 O 4 @PLGA/Cy5.5/ RGD NPs. Baseline images of the mice were taken before injection of the nanoparticles. For group one, the same amount of NPs was injected into the subcutaneous and tumour tissues, and MRI scanning was performed every 30 min to record the signal transition of the tissues. For group two, tumour imaging was performed in the axial and coronal positions, and the MR parameters were the same as those used for in vitro imaging. The signal intensity (SI) in the region of interest (ROI) was measured and compared to tissue signals at different times before and after injection.

Tumour fluorescence imaging
For fluorescence imaging in vivo, an in vivo fluorescence imaging system (FX PRO, Bruker, Switzerland) was used for scanning, and the mice were randomly divided into two groups (n = 3): (1) RGD-targeted NPs and (2) nontargeted NPs. Images were captured every 30 min for a period of 4 h after the injection. Subsequently, important organs and tumours were harvested and imaged, and the distribution of fluorescence in the organs of the body was observed. Quantitative analysis of fluorescence intensity was performed using molecular imaging software (Bruker, Switzerland). These important organs then underwent H&E staining to evaluate the tissue toxicity. Frozen tumour sections were also subjected to fluorescence immunostaining with antibodies against αv integrin and β3 integrin.