Skip to main content

The Study of Enhanced High-Intensity Focused Ultrasound Therapy by Sonodynamic N2O Microbubbles


High-intensity focused ultrasound (HIFU) is a representative non-invasive method of cancer therapy, but its low therapeutic efficacy and risk of damage to surrounding normal tissue hinder its further clinical development and application. Sonodynamic therapy (SDT) kills tumor cells through reactive oxygen molecules produced by sonosensitizers during ultrasound treatment. SDT can enhance HIFU efficacy like microbubbles. In this work, we developed nanoscale N2O microbubbles (N2O-mbs) by an improved mechanical oscillation method. These microbubbles showed good biocompatibility and tumor cell binding. The sonosensitivity of the N2O-mbs was detected both extracellularly and intracellularly through the detection of reactive oxygen species generation. The toxic effects of these sonodynamic microbubbles on tumor cells and the synergistic effect on HIFU treatment were evaluated. Significant apoptosis was caused by reactive oxygen species produced by N2O-mbs under ultrasound irradiation. N2O-mbs combined with HIFU increased tumor cell necrosis and apoptosis in vitro and the coagulative necrotic volume and echo intensity in the bovine liver target area ex vivo. These sonodynamic microbubbles have been also demonstrated to efficiently inhibit tumor growth in vivo. N2O-mbs have a significant impact on the treatment and ablation effect of HIFU due to the advantages of microbubble and extraordinary sonosensitivity. This finding suggests that N2O-mbs may be a novel auxiliary agent for ultrasound that can be used to promote HIFU tumor thermal ablation.


Malignant tumors are one of the major diseases that threaten human life and health [1]. High-intensity focused ultrasound (HIFU) is a new technique for the non-invasive local ablation of tumors. HIFU has been successfully used in the treatment of benign and malignant solid tumors in the liver, kidney, pancreas, prostate, breast, bone and uterus [2, 3]. However, the inherent limitations of HIFU, such as the decay of ultrasonic energy during treatment, the weakening of energy accumulation in the target area and the damage of non-target healthy tissue reduce its therapeutic effect [4, 5]. The focal field formed by HIFU irradiation is small, usually in millimeter magnitude. It takes a long time to ablate large tumors. The extension of HIFU irradiation time will increase body temperature, even reaching 39.2 °C. As the depth of the tumor increases in the body, the energy of HIFU ablation also needs to increase [6]. These increase the risk of physical damage to the patient and reduce the efficiency and safety of HIFU treatment. Therefore, researchers have committed to finding ways to increase the therapeutic efficiency of HIFU in recent years [7,8,9]. Microbubbles could synergistically improve HIFU therapeutic efficacy [7, 10]. The gas in the microbubble belongs to the high acoustic impedance material. The microbubbles increase the scattering and reflection of the ultrasonic wave in the target area when the HIFU irradiates the area of tumor tissue [11, 12]. Microbubbles increase the temperature of the tumor target area and enhance the thermal effect of HIFU treatment by increasing the accumulation of HIFU energy in the target area [13]. In addition, microbubbles as an exogenous cavitation nucleus also reduce the tissue cavitation threshold and enhance the cavitation effect of HIFU as it passes through the blood circulation into the tumor tissue [14]. In recent years, studies have indicated that sonodynamic therapy (SDT) can synergistically enhance HIFU treatment efficacy [15, 16]. The interactions between the sonosensitizers and ultrasound produce reactive oxygen species (ROS), including singlet oxygen and hydroxyl radicals, which kill tumor cells and inhibit tumor growth via apoptosis and necrosis [17]. SDT has made great progress in the non-invasive tumor treatment filed in recent years. It enables the reduction of drug dose and HIFU irradiation power compared to those of conventional monotherapies. In order to make full use of the advantages of the two, this study combined the microbubbles and sonodynamic effect to further improve the efficacy of HIFU. Sonosensitizers are an important part of SDT [18, 19]. Most of the currently studied traditional sonosensitizers are from photosensitizers. N2O is a photosensitizer [20, 21], that produce toxic substances under ultraviolet light irradiation condition. In this study, the sonosensitivity of N2O was also initially explored. We previously found that application of N2O inhalation anesthesia in HIFU operation aggravated injury degree of tissue, including the increased thickness of abdominal and skin congestion [22]. The combined utilization of N2O and HIFU played a synergistic effect on tissue injury. But, what biological effect N2O has in HIFU treatment is unclear. N2O is a relatively stable small molecular gas with no biotransformation and no tissue specificity in cells. It can be widely used in tissue and has no toxic effect on the body [23, 24]. So, it is an attractive prospect as a sonosensitizer. In this study, nanoscale microbubbles (N2O-mbs) were prepared using lipid-wrapped N2O and C3F8. The dosage of N2O was reduced and its range of action in vivo was also effectively limited to the area of tumor tissue. The sonodynamic effect of N2O and its synergistic effect on HIFU efficacy were examined.

Materials and Methods


1,2-Dihexadecanoyl-rac-glycero-3-phosphocholine (DPPC) and 1,2-distearoyl-sn-glycero-3-phosphoethanolamine-N-[methoxy(polyethylene glycol)-2000] (DSPE-mPEG2000) were purchased from Avanti Polar Lipids (Alabaster, AL, USA). Glycerine and agarose were obtained from Sigma Aldrich (St. Louis, MO, USA). N2O and C3F8 were purchased from Chongqing Ruixin Gas Co., Ltd (China). 4′,6-Diamidino-2-phenylindole (DAPI), 1,1′-dioctadecyl-3,3,3′,3′-tetramethylindocarbocyanine perchlorate (DiI), 2′,7′-dichlorofluorescin diacetate (DCFH-DA), 3-amino,4-aminomethyl-2′,7′-difluorescein, diacetate (DAF-FM DA) and CCK-8 were purchased from Beyotime Biotechnology (Chongqing, China). Calcein-AM (CAM) and propidium iodide (PI) were obtained from Santa Cruz Biotechnology (TX, USA). Annexin V-FITC/PI were obtained from Nanjing Keygen Biotech (Nanjing, China). Singlet oxygen sensor green (SOSG) was purchased from Invitrogen (NY, USA).

Preparation of N2O-mbs and C3F8-mbs

N2O-mbs were prepared by the rotating film combined with mechanical oscillation method. We took DPPC and DSPE-PEG2000 as shell materials and N2O as the core. Briefly, 5 mg DPPC, 2 mg DSPE-PEG2000 and 10 mL chloroform were simultaneously poured into a round-bottom flask, mixed and fully dissolved by ultrasonic waves. Then, the lipid films were formed by rotary evaporator (60 min, 55 °C, 100 r/min). Next, 2 mL of 10% glycerol was added to hydrate the lipid films and prepare a suspension. 500 μL of which was added to a capsule tube. The capsule tube was capped with a rubber cap. The air in the tube was replaced with N2O and C3F8 by a gas displacement device. Then, the suspension was mechanically oscillated by a silver–mercury capsule mixer (YJT-2, Shanghai Medical Device Co., Ltd., China) for 150 s. Finally, the resulting suspension was subjected to differential centrifugation to obtain target N2O-mbs, and was centrifuged at 300 rpm for 5 min, and then centrifuged at 800 rpm for 5 min. N2O-mbs were resuspended in PBS and then stored at 4 °C for further use.

The C3F8-mbs were fabricated using the same mechanical oscillation method, as described previously [25]. DiI-labeled N2O-mbs can be prepared by adding DiI during spin film formation. It is worth mentioning that N2O has a low molecular weight and is unstable. The N2O in the microbubble easily overflows. Therefore, the half-life of the microbubble is reduced. C3F8 is a macromolecular inert gas that is widely used in the study of ultrasonic microbubble contrast agents. C3F8 can increase the stability of the microbubbles. Therefore, in this study, N2O and C3F8 (2:1) were mixed as the N2O-mbs core to increase their stability.

Fabrication and Performance Detection of N2O-mbs

The morphology and size distribution of N2O-mbs were observed under bright-field optical microscopy. The concentrations of N2O-mbs and C3F8-mbs were calculated by globulimeter according to the calculation guidelines. The average particle size and zeta potential of the N2O-mbs were determined by a dynamic laser light scattering system (Malvern Instruments, Malvern, UK). The structure and morphology of the N2O-mbs were characterized by transmission electron microscopy (TEM, Hitachi H-7600, Hitachi Ltd., Tokyo, Japan). The prepared N2O-mbs were stored at 4 °C. In order to observe the stability of N2O-mbs, the morphology and concentration were recorded on the first, second and third days. At the same time, the average particle size and zeta potential of the microbubbles were determined.

Cell Culture and Animal Model

Human breast cancer cells (MDA-MB-231; Jinxique Technology Development Co., Ltd. Chongqing, China) were passaged in the lab for fewer than 3 months after resuscitation. The cells were maintained in a 37 °C incubator with 5% CO2, using DMEM containing 10% fetal bovine serum, 50 μg/L streptomycin and 50 μg/L penicillin. When the cells reached 80% confluence, they were used for experiment.

All animal experiments were carried out according to the guidelines of Animal Ethics Committee of Chongqing Medical University. A certain number of female nude mice (4–6 weeks old; weight of 15–20 g) were purchased from Animal Experiment Center of Chongqing Medical University (Chongqing, China). For the establishment of solid tumor, MDA-MB-231 cells (1 × 106 cells/mL) suspended in normal saline (100 μL) were injected subcutaneously into the right back flank of every mouse. All tumor-bearing mice were used for therapeutic experiments when the tumor volumes reached around 150 mm3.

Intracellular Uptake and Biocompatibility Evaluation of N2O-mb

MDA-MB-231 cells in the growth phase were seeded at a density of approximately 1 × 105 cells per confocal laser scanning microscopy (CLSM) flask for 24 h. Next, 100 μL (1 × 105 bubbles/mL) of DiI-labeled N2O-mbs complete medium dilution solution was added to fill the confocal dish with medium. The dish was sealed with microplate sealers and stored inverted in an incubator, keeping the N2O-mbs in contact with the cells. After 2 h and 4 h of co-incubation, the cells were gently washed 3 times with PBS, fixed with 4% paraformaldehyde (PFA) for 20 min and stained with DAPI for 20 min. Finally, the cell-targeting behavior of N2O-mbs was observed by CLSM (Nikon A1, Japan).

The cytotoxicity of N2O-mbs was evaluated by a standard CCK-8 assay. MDA-MB-231 cells were seeded in a 96-well plate (5 × 104 cells/well) for 24 h. Next, 100 μL of different concentrations (1 × 104/mL, 1 × 105/mL, and 1 × 106/mL) of N2O-mb were added. After 24 h of incubation, CCK-8 solution (10 μL) was added to each well. Then, the MDA-MB-231 cells were cultured at 37 °C for another 2 h. Finally, the absorbance of each well was measured at 450 nm with a Bio-Tek microplate reader (Bio-Tek Instruments, Thermo Fisher Scientific, Winooski, VT, USA).

Ten healthy female nude mice approximately weighing 20 g were divided into two groups randomly. The N2O-mbs (n = 5) group were intravenously injected with N2O-mbs (200 μL, 1 × 105/mL) and the control group (n = 5) injected with normal saline (200 μL). After 21 days, the major organs (heart, liver, spleen, lung and kidney) of all mice were excised and stained with hematoxylin–eosin (H&E).

In Vitro SDT Efficiency of N2O-mbs

The method for oxygen radical detection was based on a previous report [26]. Briefly, 10 μL of SOSG (500 μM) was mixed with 2 mL of the sample solution. The treatments were grouped as follows: group C (the blank control group), PBS alone was added; N2O-mbs group, 100 μL of N2O-mbs (1 × 105/mL) in 2 mL of PBS solution was added; C3F8-mbs group, 100 μL of C3F8-mbs (1 × 105/mL) in 2 mL of PBS solution was added; LIFU group, PBS was irradiated by ultrasound (2 W/cm2; Institute of Ultrasound Imaging of Chongqing Medical Sciences, Chongqing, China) for 100 s; LIFU–N2O-mbs group, PBS with added N2O-mbs was ultrasound irradiated; LIFU–C3F8-mbs group, PBS with added C3F8-mbs was ultrasound irradiated. The experimental group treatment parameters were set as 2 W/cm2 and 100 s through the analysis and comparison of the experimental results and consultation of the literature [27, 28]. The ultrasound parameters employed for treatment purposes were set as follows: frequency, 650 kHz; focal length, 12.5 mm; pulse wave mode, 50% duty cycle; and pulse duration, 1 s. The generation of singlet oxygen (1O2) was determined by fluorescence spectrometry (Cary Eclipse, Agilent Technologies) by measuring the fluorescence intensity (λ excitation/λ emission = 504 nm/525 nm). The selection of the ultrasound intensity and duration was consistent with in vitro cell experiments.

After the generation of extracellular reactive oxygen species (ROS) was detected using the SOSG assay, the production of intracellular ROS was detected by a DCFH-DA-based ROS assay kit. MDA-MB-231 cells were seeded at a density of approximately 1 × 105 cells per CLSM flask. Then, they were randomly distributed into six groups: the control group (without treatment), the N2O-mbs only group (100 μL, 1 × 105 bubbles/mL), the C3F8-mbs only group (100 μL, 1 × 105 bubbles/mL), the LIFU only group (2 W/cm2 for 100 s), the LIFU–C3F8-mbs group, the LIFU–N2O-mbs group. After incubation for 24 h to allow cell attachment, each group was subjected to the corresponding experimental intervention described above. Then, the same amount of DCFH-DA (30 μM) was added to the corresponding dish in each group, and the dish was incubated for 20 min in the dark. The cells were then gently rinsed 3 times with PBS to remove the DCFH probe that did not enter the cell. Finally, the generation of intracellular ROS was determined by CLSM. To further verify the SDT efficiency of N2O-mbs, cells were seeded in 6-well plates, cultured for 24 h and randomly distributed into six groups, as described above. Then, the corresponding treatments were performed in each group. The cells in each group were digested and prepared into cell suspensions at appropriate concentrations and placed into a CLSM dish. Finally, the cells were scanned by CLSM after co-staining with CAM and PI dyes to differentiate dead (red) and live (green) cells. Apoptosis was detected by flow cytometry and Annexin V-FITC/PI staining. After 1 h of treatment, each group of cells was centrifuged, and the cells were collected. Following Annexin V-FITC/PI co-staining, flow cytometry (Becton–Dickinson, Franklin Lakes, NJ) detection was performed.

In Vitro Sonodynamic Effect of N2O-mbs Enhances HIFU Treatment Efficacy

A HIFU system (JC200, HIFU Technology Co., Ltd., Chongqing, China) composed of diagnostic ultrasound unit, a therapeutic ultrasound unit and a central processing system was used as described previously [29]. The HIFU parameters employed for treatment purposes were set as follows: working frequency, 0.94 MHz; focal length, 140 mm; diameter, 220 mm; and real-time diagnostic transducer frequency, 3.5 MH. The integrated transducers were submerged in degassed water. To evaluate the enhancement effect of N2O-mbs on HIFU treatment, MDA-MB-231 cells were centrifuged, 5 × 105/mL, and distributed into four groups: the control group (without treatment), The HIFU only group (125 W, 5 s), the HIFU–N2O-mbs only group, the HIFU–C3F8-mbs only group. Next, the different respective treatments were performed for each group. The treated cells were centrifuged and washed with PBS, double stained with Annexin V-FITC/PI and harvested for flow cytometry. The nitric oxide (NO) probe DAF-FM was used to detect NO in the supernatant from each treatment group. All experiments were carried out 3 times. TEM was used to identify the ultrastructural morphology of the treated cells. After each treatment, the treated cells were immediately fixed with 2% OsO4, dehydrated in a graded series of alcohol, and flatly embedded in Epon 812 (Electron Microscopy Sciences, Fort Washington, PA). Ultrathin sections (100 nm) were prepared, stained with uranyl acetate and lead citrate, and examined under an electron microscope.

Ex Vivo and In Vivo Sonodynamic Effect of N2O-mbs Enhances HIFU Ablation Efficacy

Fresh bovine liver tissues were purchased from local abattoir and used within 12 h after slaughter. Fresh ex vivo bovine liver with little connective tissue and less blood vessels was sliced into 10 cm × 5 cm × 5 cm section and degassed for 1 h at 37 °C. The bovine livers were divided into three groups: C3F8-mbs group, N2O-mbs group and PBS group. First, freshly isolated bovine liver was placed in a container containing deaerated water. Then, 200 μL (1 × 105 bubbles/mL) of microbubbles in PBS was directly injected into the bovine liver in the manner shown in Fig. 6a. Under the guidance of a diagnostic ultrasound transducer, the HIFU focal point was positioned at the injection site. Then, the therapeutic transducer was used to perform 5 s of ablation at different power (100 W, 125 W, 150 W) on the bovine liver injection site. Finally, the coagulative necrotic volume of the target area in the bovine liver tissue was calculated according to the measured maximum length, width and depth (mm) by the following equation: V (mm3) = π/6 × length × width × depth. Furthermore, the grey value of the target area before and after HIFU ablation in each group was recorded on the diagnostic ultrasound images.

Twenty tumor-bearing mice were randomly divided into four groups (n = 5 per group), including a control group (without any treatment), a HIFU–PBS group, a HIFU–C3F8-mbs group, and a HIFU–N2O-mbs group. HIFU (125 W, 5 s) ablation of tumor was applied after the mice received an intravenous injection of 200 μL of C3F8-mbs group, N2O-mbs and PBS. The HIFU ablation procedure of solid tumors was similar to that of ex vivo isolated bovine liver. Firstly, mice were anesthetized with 1% pentobarbital (8 mL/kg). The tumor site of the mouse was inoculated into a container containing deaerated water. Under the guidance of a diagnostic ultrasound transducer, the HIFU focal point was positioned at the tumor tissue. The mice body weights and the tumor volume were recorded with a 3-day interval. Finally, all mice were killed 21 days after treatment and tumor tissues were dissected from the mice and then sent for H&E, proliferating cell nuclear antigen (PCNA) staining, terminal deoxynucleotidyl transferase dUTP nick end labeling (TUNEL).

Statistical Analysis

All data were presented and analyzed with GraphPad Prism (version 7, GraphPad Software Inc., La Jolla, CA, USA). Data are expressed as the mean ± SD. Each experiment was repeated at least 3 times. Statistical analyses were performed by one-Way ANOVA with Bonferroni post-test (comparing all groups) or Dunnett post-test (comparing all groups to a control group). A value of p < 0.05 was considered statistically significant.


Characterization of N2O-mbs

The preparation of N2O-mbs by the modified mechanical oscillation method results in a highly stable milky white suspension (Fig. 1a). The N2O-mbs did not change significantly in particle size and morphology after 72 h of storage at room temperature. Under the light microscope, N2O-mbs were observed with uniform size, good dispersion and high stability (Fig. 1b). The concentration of N2O-mbs was 5.12 ± 0.45 × 108 bubbles/mL. As shown in the TEM images (Fig. 1c), the size of N2O-mbs was evenly distributed, and the mean size was was approximately 450 nm. The N2O-mb dynamic light scattering results revealed hydrodynamic diameters of 458.1 ± 17.26 nm (polydispersity index = 0.368; Fig. 1d), which was consistent with the TEM results. The potential of the N2O-mbs was − 16.2 ± 0.35 mV (Fig. 1e) (Additional file 1: Figure S1).

Fig. 1

a Photographs of N2O-mbs dispersed in deionized water; b image of N2O-mbs under bright-field optical microscopy; c transmission electron microscope image of N2O-mbs; d size distribution of N2O-mbs; e apparent zeta potential of N2O-mbs

Intracellular Uptake and Biocompatibility of N2O-mbs

The cytotoxicity of N2O-mbs against cells in vitro was investigated by the CCK-8 method. We defined the cell viability of the control group as 100%. After 24 h of incubation, the cell viability results showed no significant cytotoxicity to MDA-MB-231 cells. Even at high N2O-mb concentrations, the cell viability remained greater than 95% (Fig. 2a). The cytotoxicity of N2O-mbs in vivo on healthy nude mice was analyzed. As shown in Fig. 2b, histopathology analysis of main organs (heart, liver, spleen, lung and kidney) showed that N2O-mbs did not cause significant toxic damage to mice. These results indicated that N2O-mbs have high biocompatibility.

Fig. 2

a Cell viability was determined by CCK-8 assay; b H&E staining of the major organs (heart, liver, spleen, lung and kidney) in healthy female nude mice with or without receiving the N2O-mbs; c the images from a to d show cell in bright field, cell nuclei stained by DAPI, N2O-mbs stained by DiI, and the merged results of the three fluorescence images; scale bar = 50 μm [NS no significance, compared with control group (0 bubbles/mL)]

The intracellular uptake of N2O-mbs over prolonged incubation times (2 h and 4 h) was visualized by CLSM. The incubation of cells with DiI-labeled N2O-mbs resulted in the accumulation of a large number of N2O-mbs in the cancer cell membrane and cytoplasm. As shown in Fig. 2c, there was good colocalization of red fluorescent N2O-mbs with the blue fluorescent cells. This finding suggests that N2O-mbs are efficiently internalized into MDA-MB-231 cancer cells.

Sonodynamic Effect of N2O-mbs In Vitro

SOSG is a commonly used singlet oxygen detection probe that is highly sensitive and reliable for the detection of oxygen free radical generation. To explore the potential of N2O-mbs as a sonosensitizer, SOSG was used to detect ROS generation in vitro [30, 31]. SOSG combines with 1O2 to form SOSG-EP, which is characterized by an increase in fluorescence intensity. As shown in Fig. 3a, after ultrasonic irradiation of SOSG solution containing N2O-mbs, the fluorescence intensity value increased significantly; compared with that in the rest of the groups, the production of oxygen free radicals was significantly increased (p < 0.01).

Fig. 3

a Fluorescence spectrum of SOSG with N2O-mbs irradiated by LIFU; b cell viability was determined by CCK8 assay; c confocal images of intracellular ROS generation (green fluorescence indicates positive staining for ROS stained with DCFH-DA); d the average fluorescence intensity value (DCFH-DA) of each group calculated by Image J. (The data were shown as mean ± SD, n = 5 per group, *p < 0.05, compared with LIFU–C3F8-mbs group)

In addition to the detection of ROS generation in aqueous solution after ultrasonic irradiation of N2O-mbs, a DCFH-DA ROS assay kit was used to determine the intracellular ROS production by N2O-mbs. As shown in Fig. 3b, the positive control group demonstrated the strongest fluorescence intensity. The next strongest green fluorescence signal appeared only in the LIFU–N2O-mbs group, revealing the consequential production of ROS in the simultaneous presence of N2O-mbs and LIFU irradiation. However, no obvious fluorescence was detected in any of the remaining groups (Fig. 3c). The cell viability of the control group was defined as 100%. The CCK-8 assay results showed approximately 46% cell death in the LIFU–N2O-mbs group (Fig. 3d). The cytotoxicity of N2O-mbs in combination with LIFU was evaluated by CLSM observation of cell death after treatment. CAM was used to stain live cells with green fluorescence. PI was used to stain dead cells with red fluorescence. As shown in Fig. 4a, there were many dead cells in the LIFU–N2O-mbs group. Furthermore, the flow cytometry results showed that the apoptosis rate of the MDA-MB-231 cell group was significantly higher than that of other groups (p < 0.05) after the combined N2O-mbs with LIFU treatment (Fig. 4b). The combined C3F8-mbs with LIFU treatment did not cause obvious cell death or apoptosis. The results further indicated that extensive apoptosis and necrosis occurred in response to SDT. The flow cytometry results were consistent with those of the CLSM. These results indicate that N2O-mbs combined with LIFU induce tumor cell apoptosis in vitro (Additional file 2: Figure S2; Additional file 3: Figure S3).

Fig. 4

a Flow cytometry analysis of tumor cell apoptosis and necrosis; b confocal images of CAM/PI co-stained MDA-MB-231 cells after various treatments. The scale bars are 100 μm

In Vitro HIFU Synergistic Effect Assessment in Cancer Cells

The flow cytometry results are shown in Fig. 5a. Both N2O-mbs and C3F8-mbs increased the mortality of MDA-MB-231 cells after HIFU ablation. Furthermore, compared to HIFU-C3F8-mbs, N2O-mbs significantly increased MDA-MB-231 apoptosis (p < 0.05; Fig. 5b). The results of the NO test showed that the fluorescence intensity of the supernatant of the HIFU–N2O-mbs group was also significantly higher than that of the remaining groups (p < 0.05) (Fig. 5c). Changes in the cytoplasm and organelles were observed by TEM (Fig. 5d). The cell in the control group (without any treatment) showed complete cell morphology. Large amounts of vacuolar substances were found in the cell cytoplasm of the HIFU group. But the cells still have complete cell membranes and nuclear membranes. However, both the HIFU–N2O-mbs group and the HIFU–C3F8-mbs group showed a loss of cell membrane integrity and complete disintegration of the cell structure. It was worth mentioning that the TEM observations were only the moment in the process of cell death and apoptosis after the treatment in each group. N2O-mbs as exogenous microbubbles have an obviously synergistic effect on the HIFU treatment. In the HIFU–N2O-mbs group, the sonodynamic effect of N2O-mbs could promote more cell apoptosis. The results have been validated in both flow cytometry detection and in vivo experiment (Additional file 4: Figure S4; Additional  file 5: Figure S5)

Fig. 5

a Results of Annexin V-FITC/PI binding assay; b the average cell apoptosis rate in each group; c quantitative analysis of NO generation of N2O-mbs irradiated by HIFU; d transmission electron microscopy image of cells. The scale bars are 100 μm. (The data were shown as mean ± SD, n = 5 per group, *p < 0.05, compared with control, HIFU, HIFU–C3F8-mbs groups)

N2O-mbs as a Synergist for HIFU Therapy

After HIFU ablation of the isolated bovine liver, a grey–white coagulative necrotic region appeared in the targeted area (Fig. 6b). The average echo intensity changes in the target area before and after HIFU are shown in Fig. 6c. Compared with those of the PBS group, the target echo intensity values of the C3F8-mbs group and the N2O-mbs group were significantly increased after HIFU treatment (p < 0.05) and increased as the HIFU ablation intensity increased. The coagulative necrotic volume of the latter two groups and the echo intensity of the B-mode ultrasound images of the target area both increased as the HIFU power increased (Fig. 6d, e).

Fig. 6

a Schematic illustration of ex vivo HIFU ablation on degassed bovine livers; b photography of the targeted area in excised bovine liver after HIFU ablation; c real-time ultrasound images before and after HIFU irradiation on bovine livers at 100 W, 125 W and 150 W for 5 s; d quantitative analysis of echo intensity; e quantitative analysis of coagulative necrosis volume of the targeted area in the excised bovine liver after HIFU ablation. (The data were shown as mean ± SD, n = 5 per group, *p < 0.05, compared with 100 W, 5 s, 125 W, 5 s groups)

The synergistic effect of N2O-mbs on HIFU therapy was further verified in vivo. As shown in Fig. 7a, the digital photos of mice and corresponding tumor tissue were recorded 21 days after different treatment. Tumor growth was more effectively inhibited after N2O-mbs combined with HIFU treatment. The synergistic effect of N2O-mbs on HIFU treatment was also evaluated by H&E, PCNA, and TUNEL staining (Fig. 7b), which demonstrated that N2O-mbs combined with HIFU irradiation could cause larger scale of tumor cell necrosis as compared with HIFU–C3F8-mbs group. The cell morphology changes exhibited in HIFU–N2O-mbs were more obvious than other groups, including karyopyknosis, karyorrhexis and karyolysis, indicating the substantial necrosis of cancer cells.

Fig. 7

a Digital photos of tumor-bearing mice and ex vivo tumors 21 days after different treatments; b H&E, PCNA and TUNEL staining of tumor sections after various treatments; c the corresponding calculated tumor volume of each group after 21 days of different treatments; d body weight of tumor-bearing mice for each group. The scale bars in HE staining are 100 μm; the scale bars in TUNEL and PCNA staining are 50 μm. (The data were shown as mean ± SD, n = 5 per group, *p < 0.05, compared with HIFU-C3F8-mbs group)

In addition, the tumor volume of HIFU–N2O-mbs exhibited a more significant inhibited tendency than HIFU–C3F8-mbs within the 21 days (Fig. 7c, d).


HIFU, as a new method of oncotherapy, has been clinically recognized and has achieved notable progress in the treatment of many solid tumors [32]. The thermal effect, cavitation effect, mechanical effect and acoustic chemical effect play significant roles in killing tumor cells and causing irreversible damage to the target area tissue during HIFU ablation [33]. HIFU has limited impact on surrounding normal tissues and is essentially a non-invasive tumor treatment. However, the energy carried by the ultrasound is attenuated due to increased transmission distance, absorption by the blood flow in the target area and the blockage of bones or gas in the body during the HIFU treatment, so that the energy transferred to the target area is reduced. However, prolonging the ablation time and increasing the treatment power increases the risk of normal tissue damage, such as skin burns, neurovascular damage and other complications [34]. Therefore, it is necessary to increase the efficacy of HIFU. Many studies have confirmed that both microbubbles and SDT can improve the efficacy of HIFU [15, 16, 35]. The N2O-loaded microbubbles prepared in this study have a smaller particle size, but similar characteristics as ultrasonic microbubble contrast agents. Studies have shown that nano/microbubbles have the same imaging capability as microbubbles in vitro, but have greater capability than microbubbles in vivo [36]. So, N2O-mbs not only could be used for ultrasound guidance and localization for HIFU treatment, but also could be used as exogenous microbubbles to enhance the efficacy of HIFU (Additional file 6: Figure S6). At the same time, the sonodynamic effect of N2O-mbs could effectively improve the efficacy of HIFU. The generation of ROS after ultrasonic excitation is one of the most important factors for sonosensitizers [16]. To verify the sonosensitivity of N2O-mbs, the production of ROS in both extracellular and intracellular environments was detected in this study. The consistent result of both tests showed that N2O-mbs can generate ROS in both aqueous solution and intracellularly. Studies have also shown that gases (N2 and O2) trapped in cavitation nuclei in solution can undergo cleavage reactions and produce N and O free radicals [37, 38], as follows:

$$ {N}_2O\to {N}_2+{O}_2\kern0.50em {O}_2\to 2\bullet O\ \ \ {N}_2\to 2N.N.+ HO.\to NO+H. NO+ HO.\to HNO $$

The cavitation effect and the advantage of microbubble packaging reduce the difficulty of the N2O reaction [39]. When incubated with cells, N2O-mbs exhibit good biocompatibility. The high selectivity, high affinity and high drug loading of nanoparticles [40], as well as the active phagocytosis by cells, promote efficient N2O-mbs binding to cancer cells. The nanobubbles display increased penetration, stability and ease of cell entry or aggregation around the cells [36]. In addition, the sonoporation effect of ultrasound can effectively promote the transfer of microbubbles into cells [41].

In contrast to the traditional microbubble contrast agent C3F8-mbs, N2O-mbs have a greater inhibitory effect on cell growth after ultrasonic irradiation, which is characterized by increased intracellular ROS, decreased cell viability, and apoptosis and necrosis. These results preliminarily suggested the sonodynamic toxic effect of N2O-mbs.

In the HIFU synergy experiment, the treatment parameters in the experimental group were set to 125 W for 5 s by analyzing and comparing the experimental results and consulting the literature, which validated a low HIFU power could induce sufficient ablation effect and reduce adverse effects. The results showed that N2O-mbs increased the necrosis and advanced apoptosis of more tumor cells. N2O-mbs acted as a nanoscale microbubble synergizer and its sonodynamic effect in response to HIFU may be the reason for the different experiment results. As a microbubble, N2O-mbs increased the deposition of HIFU energy in the target area and increased the temperature of the target area and increased the thermal effect of HIFU treatment [11]. The generation of the cavitation effect is closely related to the cavitation threshold and cavitation nucleus concentration [42]. N2O-mbs were cavitation nucleus that reduce the cavitation threshold of HIFU and facilitate the cavitation effect. Therefore, N2O-mbs effectively promoted cell necrosis. As a nanoscale microbubble synergizer, N2O-mbs were lysed and generate free radicals and nitrogen oxide in response to ultrasound. Studies have confirmed that ROS are important factors in apoptosis induction [43]. It is worth noting that many kinds of free radicals can cause damage to cells. In addition to the generation of oxygen radicals, N2O can generate other types of free radicals in cleavage reactions, such as nitrogen free radicals, which contribute to the killing of tumor cells. A small amount of nitric oxide (NO) production was detected in the cell supernatant after HIFU treatment, further indicating that the N2O cleavage reaction occurred. An et al. [44] reported that NO may have an anti-tumor function, the mechanism of which involves NO attacking suspected iron enzymes that cause cells to fail to grow and divide when they are trapped. In addition, unstable NO can interact with oxygen molecules to form hydroxyl radicals (HO·) and NO2. Hydroxyl radicals are extremely cytotoxic and promote tumor cell apoptosis. NO is also an endothelium-derived relaxing factor. The generation of NO may be the reason for hyperaemia and abnormal swelling in patients during HIFU operation. In an excised bovine liver experiment, we carefully compared the echo intensity of B-mode ultrasound images, pathological changes and coagulative necrotic volume of the target area after HIFU ablation in the presence of N2O-mbs, C3F8-mbs and PBS. All of these results were consistent. Compared with PBS, N2O-mbs effectively enhanced the ablation effect of HIFU. This synergistic effect was also better demonstrated in the ablation of solid tumor in vivo, manifested by tumor cell apoptosis increased, tumor volume reduced and tumor growth inhibition. This finding further indicates that N2O-mbs may be a novel auxiliary agent for ultrasound that can be used to promote HIFU thermal tumor ablation. The synergistic effect of N2O-mbs in HIFU and the synergistic mechanism provide new ideas and theoretical practice for HIFU synergist research. But, the other related mechanisms of the synergy should be further explored. The effect of tumor ablation by HIFU combined with N2O-mbs should be further addressed.


In summary, we have developed N2O-mb nanoparticles. The characterization and biocompatibility of the N2O-mbs were determined. The sonosensitivity of N2O-mbs was examined by detecting the production of ROS in aqueous solution and intracellularly. Compared with C3F8-mbs, N2O-mbs generated ROS and promoted the apoptosis and necrosis of tumor cells, which exhibited extraordinary sonosensitivity. In the HIFU synergy experiments, the sonodynamic effects of N2O-mbs significantly increased the apoptosis and necrosis of tumor cells in vitro, and increased the coagulative necrotic volume and echo intensity in the ex vivo isolated bovine liver target area, and effectively inhibited tumor growth in vivo. These results suggested that N2O-mbs could be a new kind of sonosensitizer and a novel auxiliary agent for ultrasound therapy that can be used for the ablation of tumors by HIFU.

Availability of Data and Materials

The conclusions made in this manuscript are based on the data which are all presented and shown in this paper.



N2O microbubbles


C3F8 microbubbles


high-intensity focused ultrasound


low-intensity focused ultrasound


singlet oxygen sensor green


sonodynamic therapy




1,2-distearoyl-sn-glycero-3phosphoethanolamine-N-[methoxy(polyethylene glycol)-2000




1,1′-dioctadecyl-3,3,3′,3′-tetramethylindocarbocyanine perchlorate


2′,7′-dichlorofluorescin diacetate


3-amino,4-aminomethyl-2′,7′-difluorescein, diacetate




Cell Counting Kit-8


confocal laser scanning microscopy


transmission electron microscope


Dulbecco’s modified Eagle’s medium


fetal bovine serum


phosphate-buffered saline


deionized water


regions of interest


reactive oxygen species


nitric oxide


  1. 1.

    Siegel RL, Miller KD, Jemal A (2018) Cancer statistics. CA Cancer J Clin 68:7–30

    Google Scholar 

  2. 2.

    Hwang JH, Crum LA (2009) Current status of clinical high-intensity focused ultrasound. In: International conference of the IEEE engineering in medicine & biology society. IEEE, New York, pp 130–133

    Google Scholar 

  3. 3.

    Hsiao YH, Kuo SJ, Tsai HD, Chou MC, Yeh GP (2016) Clinical application of high-intensity focused ultrasound in cancer therapy. J Cancer 7:225–231

    CAS  Article  Google Scholar 

  4. 4.

    Ellens N, Hynynen K (2015) Frequency considerations for deep ablation with high-intensity focused ultrasound: a simulation study. Med Phys 42:4896–4910

    Article  Google Scholar 

  5. 5.

    Marinova M, Rauch M, Schild HH, Strunk HM (2015) Novel non-invasive treatment with high-intensity focused ultrasound (HIFU). Ultraschall Med 37:46–55

    Article  Google Scholar 

  6. 6.

    Wang ZB, Wu J, Fang LQ, Wang H, Li FQ, Tian YB et al (2011) Preliminary ex vivo feasibility study on targeted cell surgery by high intensity focused ultrasound (HIFU). Ultrasonics 51:369–375

    CAS  Article  Google Scholar 

  7. 7.

    Zhang X, Zheng Y, Wang Z, Huang S, Chen Y, Jiang W et al (2014) Methotrexate-loaded PLGA nanobubbles for ultrasound imaging and synergistic targeted therapy of residual tumor during HIFU ablation. Biomaterials 35:5148–5161

    CAS  Article  Google Scholar 

  8. 8.

    Alkhorayef M, Mahmoud MZ, Alzimami KS, Sulieman A, Fagiri MA (2015) High-intensity focused ultrasound (HIFU) in localized prostate cancer treatment. Pol J Radiol 80:131–141

    Article  Google Scholar 

  9. 9.

    Zou X, Wang J, Zhao H, Zhang J, Wu W, Ye B (2009) Echinococcus granulosus: protoscolicidal effect of high intensity focused ultrasound. Exp Parasitol 121:312–316

    Article  Google Scholar 

  10. 10.

    Isern J, Pessarrodona A, Rodriguez J, Vallejo E, Gimenez N, Cassadó J (2015) Using microbubble sonographic contrast agent to enhance the effect of high intensity focused ultrasound for the treatment of uterine fibroids. Ultrason Sonochem 27:688–693

    CAS  Article  Google Scholar 

  11. 11.

    Takegami K, Keneko Y, Watanabe T et al (2005) Erythrocytes, as well as microbubble contrast agents, are important factors in improving thermal and therapeutic of high-intensity focused ultrasound. Ultrasound Med Biol 31:385–390

    Article  Google Scholar 

  12. 12.

    Moyer LC, Timbie KF, Sheeran PS et al (2015) High-intensity focused ultrasound ablation enhancement in vivo via phase-shift nanodroplets compared to microbubbles. J Ther Ultrasound 3:7

    Article  Google Scholar 

  13. 13.

    Luo W, Zhou X, Ren X et al (2007) Enhancing effects of SonoVue, a microbubble sonographic contrast agent, on high intensity focused ultrasound ablation in rabbit livers in vivo. J Ultrasound Med 26:469–476

    Article  Google Scholar 

  14. 14.

    Li QY, Du JF, Yu M et al (2009) Transmission electron microscopy of VX2 liver tumors after high-intensity focused ultrasound ablation enhanced with SonoVue. Adv Ther 26:117–125

    Article  Google Scholar 

  15. 15.

    Zhang Y, Yong LJ, Luo Y, Ding XY, Xu D, Gao X et al (2019) Enhancement of HIFU ablation by sonosensitizer-loading liquid fluorocarbon nanoparticles with pre-targeting in a mouse model. Sci Rep 9:6982

    Article  CAS  Google Scholar 

  16. 16.

    Hirschberg H, Madsen SJ (2017) Synergistic efficacy of ultrasound, sonosensitizers and chemotherapy: a review. Ther Deliv 8:331–342

    CAS  Article  Google Scholar 

  17. 17.

    Giuntini F, Foglietta F, Marucco AM, Troia A, Dezhkunov NV, Pozzoli A et al (2018) Insight into ultrasound-mediated reactive oxygen species generation by various metal-porphyrin complexes. Free Radic Biol Med 121:190–201

    CAS  Article  Google Scholar 

  18. 18.

    Shibaguchi H, Tsuru H, Kuroki M, Kuroki M (2011) Sonodynamic cancer therapy: a non-invasive and repeatable approach using low-intensity ultrasound with a sonosensitizer. Anticancer Res 31:2425–2430

    Google Scholar 

  19. 19.

    Canavese G, Cauda VA, Ancona A, Racca L, Canta M, Limongi T (2018) Nanoparticle-assisted ultrasound: a special focus on sonodynamic therapy against cancer. Chem Eng J 340:155–172

    CAS  Article  Google Scholar 

  20. 20.

    Portmann RW, Daniel JS, Ravishankara AR (2012) Stratospheric ozone depletion due to nitrous oxide: influences of other gases. Philos Trans R Soc Lond 367:1256–1264

    CAS  Article  Google Scholar 

  21. 21.

    Abrahamse H, Hamblin MR (2016) New photosensitizers for photodynamic therapy. Biochem J 473:347–364

    CAS  Article  Google Scholar 

  22. 22.

    Pan MY, Liu F, Tian ZD, Xu XY (2016) Nitrous oxide triggers synergistic effects of high intensity focused ultrasound on tissue injury via reinforcing ultrasonic cavitation in tissues. Int J Clin Exp Med 9:13047–13052

    CAS  Google Scholar 

  23. 23.

    Cartwright FF (1972) Humphry Davy’s researches on nitrous oxide. Br J Anaesth 44:291–296

    CAS  Article  Google Scholar 

  24. 24.

    Leslie K, Myles P, Kasza J, Forbes A, Peyton PJ, Chan MT (2015) Nitrous oxide and serious long-term morbidity and mortality in the evaluation of nitrous oxide in the gas mixture for anaesthesia (enigma)-II trial. Anesthesiology 123:1267

    CAS  Article  Google Scholar 

  25. 25.

    Wang D, Yang K, Gao YH, Tan KB, Liu Z (2010) Preparation and characterization of a nanoscale ultrasound contrast agent. Clin Imaging 34:288–292

    Article  Google Scholar 

  26. 26.

    Chen Q, Wang X, Wang C, Feng L, Li Y, Liu Z (2015) Drug-induced self-assembly of modified albumins as nano-theranostics for tumor-targeted combination therapy. ACS Nano 9:5223–5233

    CAS  Article  Google Scholar 

  27. 27.

    Wang L, Hu YJ, Hao YW, Li L, Zheng CX, Zhao HJ (2018) Tumor-targeting core-shell structured nanoparticles for drug procedural controlled release and cancer sonodynamic combined therapy. J Control Release 286:74–84

    CAS  Article  Google Scholar 

  28. 28.

    Zhang L, Yi HJ, Song J, Huang J, Yang K, Tan B et al (2019) Mitochondria-targeted and ultrasound-activated nanodroplets for enhanced deep-penetration sonodynamic cancer therapy. ACS Appl Mater Interfaces 11:9355–9366

    CAS  Article  Google Scholar 

  29. 29.

    Yao Y, Yang K, Cao Y, Zhou X, Xu J, Liu J (2016) Comparison of the synergistic effect of lipid nanobubbles and SonoVue microbubbles for high intensity focused ultrasound thermal ablation of tumors. Peer J 4:e1716

    Article  CAS  Google Scholar 

  30. 30.

    Ruiz-González R, Bresolí-Obach R, Gulías Ò et al (2017) Nano SOSG: a nanostructured fluorescent probe for the detection of intracellular singlet oxygen. Angew Chem Int Ed 56:2885–2888

    Article  CAS  Google Scholar 

  31. 31.

    Gollmer A, Arnbjerg J, Blaikie FH, Pedersen BW, Ogilby PR (2011) Singlet oxygen sensor green®: photochemical behavior in solution and in a mammalian cell. Photochem Photobiol 87:671–679

    CAS  Article  Google Scholar 

  32. 32.

    Elhelf IAS, Albahar H, Shah U, Oto A, Almekkawy M (2018) High intensity focused ultrasound: the fundamentals, clinical applications and research trends. Diagn Interv Imaging 99:6

    Article  Google Scholar 

  33. 33.

    Haar GT (2016) Hifu tissue ablation: concept and devices. Adv Exp Med Biol 880:3–20

    Article  CAS  Google Scholar 

  34. 34.

    Jung SE, Cho SH, Jang JH, Han JY (2011) High-intensity focused ultrasound ablation in hepatic and pancreatic cancer: complications. Abdom Imaging 36:185–195

    Article  Google Scholar 

  35. 35.

    Hamano N, Negishi Y, Takatori K et al (2014) Combination of bubble liposomes and high-intensity focused ultrasound (HIFU) enhanced antitumor effect by tumor ablation. Biol Pharm Bull 37:174–177

    CAS  Article  Google Scholar 

  36. 36.

    Fan X, Wang L, Guo Y, Tong H, Li L, Ding J (2013) Experimental investigation of the penetration of ultrasound nanobubbles in a gastric cancer xenograft. Nanotechnology 24:325102

    Article  CAS  Google Scholar 

  37. 37.

    Liu L, Yang Y, Liu P, Tan W (2013) The influence of air content in water on ultrasonic cavitation field. Ultrason Sonochem 21:566–571

    Article  CAS  Google Scholar 

  38. 38.

    Schreiber F, Wunderlin P, Udert KM, Wells GF (2012) Nitric oxide and nitrous oxide turnover in natural and engineered microbial communities: biological pathways, chemical reactions, and novel technologies. Front Microbiol 3:372

    Article  Google Scholar 

  39. 39.

    Leighton TG (1995) Bubble population phenomena in acoustic cavitation. Ultrason Sonochem 2:S123–S136

    Article  Google Scholar 

  40. 40.

    Weldon C, Ji T, Nguyen MT, Rwei A, Wang W, Hao Y (2018) Nanoscale bupivacaine formulations to enhance the duration and safety of intravenous regional anesthesia. ACS Nano 13(1):18–25

    Article  CAS  Google Scholar 

  41. 41.

    Zeghimi A, Escoffre JM, Bouakaz A (2015) Role of endocytosis in sonoporation-mediated membrane permeabilization and uptake of small molecules: a electron microscopy study. Phys Biol 12:066007

    CAS  Article  Google Scholar 

  42. 42.

    Miller MW, Miller DL, Brayman AA (1996) A review of in vitro bioeffects of inertial ultrasonic cavitation from a mechanistic perspective. Ultrasound Med Biol 22:1131–1154

    CAS  Article  Google Scholar 

  43. 43.

    Zorov DB, Juhaszova M, Sollott SJ (2014) Mitochondrial reactive oxygen species (ROS) and ROS-induced ROS release. Physiol Rev 94:909–950

    CAS  Article  Google Scholar 

  44. 44.

    An HJ, Kwon KB, Cho HI, Seo EA, Ryu DG, Hwang WJ (2005) Solanum nigrum produces nitric oxide via nuclear factor-κb activation in mouse peritoneal macrophages. Eur J Cancer Prev 14:345–350

    Article  Google Scholar 

Download references


The authors greatly acknowledge the Ultrasound Molecular Imaging Research Institution of Chongqing Medical University and the Institute of Ultrasonic Engineering in Medicine of Chongqing Medical University.


This study was funded by the National Natural Science Fund of China (Grant No. 81172122).

Author information




XZ and ZT designed the experiment and analyzed the data. XZ, MZ and QW conducted the experiments and prepared the manuscript. All authors revised the final manuscript. All authors read and approved the final manuscript.

Corresponding author

Correspondence to Zedan Tian.

Ethics declarations

Competing interests

The authors declare that they have no competing interests.

Additional information

Publisher’s Note

Springer Nature remains neutral with regard to jurisdictional claims in published maps and institutional affiliations.

Supplementary information

Additional file 1: Figure S1.

Basic representation of C3F8-mbs. A. Photographs of C3F8-mbs dispersed in deionized water; B. Image of C3F8-mbs under bright-field optical microscopy; C. Transmission electron microscope image of C3F8-mbs; D. Size distribution of C3F8-mbs; E. zeta potential of C3F8-mbs.

Additional file 2: Figure S2.

Determination of optimal LIFU irradiation time. (The data were shown as mean ± SD, n = 5 per group, *p < 0.05). To Select the optimal time for ultrasound, MDA-MB-231 cells were seeded in a 96-well plate at a density of 5000 cells per well for 24 h. And then use the strength of 2 W/cm2 ultrasonic processing cells, respectively for the 50 s, 100 s, 150 s and 200 s. After the indicated treatments, CCK8 solution (10 μL) was added in each well. Then, the MDA-MB-231 cells were cultured at 37 °C, 5% CO2 cell incubation box to save. At 3 h, 6 h, 9 h and 12 h, cell viabilities were determined by CCK-8 assay. The optical density of each well was measured at 450 nm with a Bio-Tek microplate reader. Cell viability of the control group was defined as 100%. The test results show (Figure S1) that the cells viability in 50 s and 100 s groups were more than 95% at 3 h, 6 h, 9 h and 12 h after treatment, and the difference in cell viability between the two groups is not statistically significant (p > 0.05). The cell viability decreased in 150 s and 200 s groups (p < 0.01), and the survival rate was 74% in 150 s group and 55% in 200 s group. Combined with the oxygen free radicals generated condition, 100 s was selected as the optimal time of ultrasound.

Additional file 3: Figure S3.

Quantitative analysis of 1O2 generation of N2O irradiated by LIFU. (The data were shown as mean ± SD, n = 5 per group, *p < 0.05). In aqueous solution, the difference between the N2O treated with ultrasound (LIFU-N2O group) and the N2O group was not statistically significant (p > 0.05). Compared with the control group, fluorescence intensity increased only in the LIFU group and LIFU-N2O group. And the addition of N2O did not increase the generation of oxygen free radicals in the LIFU-N2O group (p > 0.05). In the LIFU group and LIFU-N2O group, a small amount of oxygen free radicals was generated, possibly only because of the stimulation of ultrasound.

Additional file 4: Figure S4.

HIFU ablation cell suspension.

Additional file 5: Figure S5.

HIFU intensity and time selection. (The data were shown as mean ± SD, n = 5 per group, *p < 0.05). The prepared MDA-MB-231 cells suspension was grouped and treated with different acoustic power (75 W, 100 W, 125 W, 150 W, 175 W, 200 W) and different time (5 s, 10 s). Cell viability was detected with CCK8 assay. After the indicated treatments, MDA-MB-231 cells were inoculated in 96-well plates, with 5 wells in each group. CCK8 solution (10 μL) was added in each well and cultured at 37 °C for another 1 h. The optical density of each well was measured at 450 nm with a Bio-Tek microplate reader. Cell viability of the control group was defined as 100%. When the time was 5 s, the cell viability rate decreased significantly when the sound power was higher than 125 W (p < 0.05), and the cell survival rate no longer changed with the increase of the sound power (p > 0.05). At the same sound power and time of 10 s, the cell survival rate of each group did not change significantly. According to the experimental conditions, 125 W and 5 s are selected as the optimal sound power and action time.

Additional file 6: Figure S6.

In vitro ultrasound imaging performance. Fifteen grams of agarose and 500 mL of deionized (DI) water were mixed at a concentration of 3%. The mixture was repeatedly heated until the agarose dissolved. Then, after cooling, the agar gel was prepared as an in vitro ultrasound imaging model. The N2O-mbs (200 μL, 1 × 105 bubbles/mL) PBS and C3F8-mbs (200 μL, 1 × 105 bubbles/mL) PBS solutions were added to the gel model. Ultrasound imaging of the microbubbles was performed on an ultrasound system (Esaote, Italy). Finally, the echo intensities of regions of interest (ROI) were were quantitatively measured by ultrasound imaging software. The in vitro N2O-mb and C3F8-mb ultrasound imaging performance analysis is shown in Figure S6. The echo intensity of the B-mode ultrasound image within the ROI was calculated by ultrasound analysis software. The target sound intensity between the N2O-mbs group and the C3F8-mbs group was not significantly different (p > 0.05).

Rights and permissions

Open Access This article is distributed under the terms of the Creative Commons Attribution 4.0 International License (, which permits unrestricted use, distribution, and reproduction in any medium, provided you give appropriate credit to the original author(s) and the source, provide a link to the Creative Commons license, and indicate if changes were made.

Reprints and Permissions

About this article

Verify currency and authenticity via CrossMark

Cite this article

Zhong, X., Zhang, M., Tian, Z. et al. The Study of Enhanced High-Intensity Focused Ultrasound Therapy by Sonodynamic N2O Microbubbles. Nanoscale Res Lett 14, 381 (2019).

Download citation


  • Nitrous oxide
  • Microbubble
  • Sonodynamic effect
  • HIFU
  • Ablation