Ultrasonic Microbubble Cavitation in Tumor Therapy: Comparison
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Please note this is a comparison between Version 2 by Sirius Huang and Version 1 by Jian Lu.

Chemotherapy has an essential role not only in advanced solid tumor therapy intervention but also in society’s health at large. Chemoresistance, however, seriously restricts the efficiency and sensitivity of chemotherapeutic agents, representing a significant threat to patients’ quality of life and life expectancy. How to reverse chemoresistance, improve efficacy sensitization response, and reduce adverse side effects need to be tackled urgently. Consequently, studies on the effect of ultrasonic microbubble cavitation on enhanced permeability and retention (EPR) have attracted the attention of researchers. Compared with the traditional targeted drug delivery regimen, the microbubble cavitation effect, which can be used to enhance the EPR effect, has the advantages of less trauma, low cost, and good sensitization effect, and has significant application prospects.

  • ultrasound
  • microbubbles
  • cavitation effect
  • EPR effect
  • tumor therapy

1. A Brief Overview of  Ultrasonic Microbubble Cavitation

The ultrasound-mediated microbubble cavitation effect refers to a series of dynamic processes such as expansion, contraction, oscillation, and violent collapse in tiny bubbles under ultrasound sonication at a specific frequency [1,2,3][1][2][3]. The physical phenomena with high temperature, high pressure, and micro-jet are induced by rapid release of instantaneous energy accompanying ultrasound intervention in bubbles after energy absorption [4,5][4][5]. The acoustic cavitation effect is commonly used to improve cancer therapy including but not limited to hepatocellular carcinoma, colon cancer, brain cancers, and prostate cancer in medical research [6,7,8,[6][7][8]9]. When ultrasound is applied to the current and emerging technique on diagnosis and treatment, the cavitation effect can improve EPR in terms of both drug release and biological effects. During the process of agent release, ultrasound can stimulate the carrier to enhance the efficiency of drug release and distribution in tissues. In terms of biological effects, the use of acoustic energy combined with the cavitation effect of microbubbles is mainly to promote the vascular permeability and extracellular material transport by membranes in tumor microenvironment (TME) [10,11,12][9][10][11]. Meanwhile, when exposed to an ultrasound field, the liquid around the microbubbles will form acoustic streaming, in which the shear stress generated by the streaming can promote the directional release of the drug from microbubbles and enhance the permeability of the drug in tissues and cell membranes (shear-induced permeability) [11][10]. These mechanical effects primarily generated by ultrasound may lead to the improvement in permeability and vascular perfusion into solid tumor tissues [13][12].

2. Ultrasonic Microbubble Cavitation Promoting Tumor Therapy by Enhancing the EPR Effect

Microbubbles are composed of less than 100 nm layers of polymers, proteins, and lipids covering the surface of a hydrophobic fluorinated gas. To increase tumor tissue specificity, ligands for specific cell surface receptors can be attached to the micro-vesicles. Microbubbles can present distinct oscillation patterns when acoustic parameters are varied. The hydrophobic microbubbles encapsulated by lipid, protein, or polymer shell gas are irradiated by ultrasound to expand, contract, oscillate, and even violently collapse, a process called cavitation. Cavitation can be divided into two forms, namely steady-state cavitation and inertial cavitation. Steady-state cavitation refers to the stable vibration of microbubbles around the resonant diameter at low sound intensities. The stable ultrasonic cavitation effect of microbubbles is usually generated under relatively low peak negative acoustic pressures. When the acoustic pressure amplitudes were further increased, ultrasonic cavitation turned into a violent collapse called inertial cavitation accompanied by shock waves and microstreaming [14,[13]15]. These effects of cavitation have been extensively applied in various domains of medical applications [16,17,18,19][14][15][16][17]. Ultrasound-mediated microbubble cavitation can enhance EPR by improving the permeability of the biological barriers in TME through a local controllable cavitation effect, enhance material exchange and transport, and achieve the therapeutic effect of increasing drug concentration in tissue cells (Figure 1). In recent decades, numerous studies have demonstrated that ultrasound-mediated cavitation of microbubbles can facilitate the delivery of anticancer drugs to tumor cells [20,21][18][19]. Due to the sound pressure of ultrasonic waves, the microbubbles will shrink and expand periodically. When the sound pressure reaches a certain threshold, the microbubble collapses [22][20]. The cavitation or explosion of microbubbles will form temporary holes in the cell membrane and blood vessel wall to enhance permeability, providing temporary and reversible channels for the transport of substances, so that therapy agents can enter the cell passively [23,24][21][22]. Xia et al. used an orthotopic prostate cancer model with acoustic cavitation to induce an increase in the therapeutic efficacy of prostate cancer by increasing membrane permeability of prostate cancer cells and facilitating the targeted delivery of immune checkpoint inhibitors to tumors in the tumor microenvironment [9][23]. Studies have shown that ultrasound could not only enhance the passive diffusion of drug, but also affect the active transport for enhancing drug uptake. Ultrasound cavitation is thought to induce changes in ion channels and molecular reaction including membrane resealing or gap restoration in different spatial and temporal scales, resulting in increased intracellular Ca2+ concentration and cytoskeletal rearrangement [25][24]. These changes discussed above could play a crucial role in stimulating the clathrin-mediated endocytosis pathway to promote drug diffusion into cells [26][25]. In addition, fluid movement caused by cavitation may also facilitate vascular perfusion according to vasodilator expression including nitric oxide induced by increased intracellular Ca2+ concentration and high shear stress from oscillating bubbles, increasing the amount of drug agent uptake by distant tumor cells [26,27,28][25][26][27].
Figure 1. Ultrasound-mediated microbubble cavitation enhances biological barriers’ permeability and material transport. High interstitial pressure aroused by lack of blood perfusion and lymphatic return in solid tumors hinders the uptake and absorption of drug agents in cells. Using ultrasound to mediate the cavitation effect of microbubbles can increase blood–tumor barrier permeability and vascular perfusion, significantly increasing the diffusion of agents and sensitizing chemoresistance.
In recent years, many studies have also confirmed that claudins and ZO-1 play an important role in the permeability regulation of biological barriers such as the blood–tumor barrier [29,30,31,32,33][28][29][30][31][32]. Studies have shown that there are a series of intercellular junctions between endothelial or epithelial cells, of which tight junctions are the most important. Between mammalian cells, tight junctions are mainly composed of transmembrane proteins (Occludin), claudins, junctional adhesive molecules (JAMs), and cytoplasmic attachment proteins (ZO family) [34,35,36][33][34][35]. Tight junctions widely exist in biological barrier structures such as intestinal mucosal epithelial cells, interstitial cells, the blood–testis barrier, and the blood–brain barrier [37,38,39,40][36][37][38][39]. Through research, Bae et al. found that the permeability of tight junctions in the barrier structure increased after physical treatment of the biological barriers, and the expression and distribution of the main components of tight junctions changed [41][40]. Through research, it was found that after intravenous injection of contrast agent microbubbles, low-frequency ultrasound irradiation can significantly increase the drug concentration in the tissue, and 24 h after the ultrasound irradiation, the drug concentration was significantly reduced, and tissue cells were observed by transmission electron microscopy. The gap between them widened and recovered after 24 h. Changes in the spatial structure of tight junctions are temporally consistent with changes in tissue barrier permeability. This indicates that tight junctions play an important role in the regulation of tissue cell permeability. Studies have shown that the tight junction protein Occludin plays an important role in the process of low-frequency ultrasound irradiation combined with contrast agent microbubbles to open the blood–tumor barrier (Figure 2). When the blood–tumor barrier is opened, the expression level of this tight junction protein decreases [42][41]. This indicates that the tight junction protein Occludin plays an important role in enhancing the permeability of tissue cells by low-frequency ultrasound irradiation combined with contrast agent microbubbles.
Figure 2. Ultrasound-mediated microbubble cavitation enhancing tumor–blood barrier permeability. The blood–tumor barrier is composed of vascular endothelial cells, basement membrane, and tumor interstitial cells. Biological barrier regulator proteins include Occludin, Claudin, JAM, ZO, and so on. Ultrasound-mediated microbubble cavitation can significantly increase local tissue tight junction protein permeability and increase drug diffusion, meanwhile, can form vascular microcirculation thrombus by further increasing ultrasound frequency to induce tumor ischemic necrosis.
Overall, ultrasound can utilize the local microbubble cavitation to enhance the EPR effect for non-invasive targeted therapy of diseases without affecting the surrounding soft tissues. The cavitation effect can achieve the passive agents’ diffusion in tissue through ameliorating the permeability of tissue and vascular barrier by sonoporation and regulate the intercellular tight junction. Similarly, it can also enhance intracellular uptake via stimulating the clathrin-mediated endocytosis pathway induced by ion channels. On the one hand, the cavitation effect can also enhance the drug delivery efficiency by inducing the releasing vasodilator to a certain extent to increase local tissue blood perfusion. The feasibility and potential of this approach might contribute to achieve better targeted delivery in the prospective fast-revolutionizing disease area.

3. Application Studies Using Ultrasonic Microbubble Cavitation on Tumor Therapy

Many studies have confirmed that ultrasound-mediated microbubble cavitation can promote drug diffusion and induce tumor-suppressive effects by enhancing EPR through improving permeability and vascular perfusion in vitro (Table 1) and in vivo (Table 2), manifested as tumor growth inhibition, increased tumor cell apoptosis and necrosis, decreased tumor angiogenesis, and decreased expression of tumor-associated proteins. Nevertheless, a profusion of adverse effects has also been reported including hemorrhage, thrombus formation, local burns, tissue necrosis, and various organ toxicities [43,44,45][42][43][44]. Thankfully, most of the serious side effects of ultrasound-assisted therapy including necrosis and hemorrhage, are concentrated in a relatively high intensity focused ultrasound which mainly exerts an acoustic thermal effect rather than cavitation effect. Thus, keeping the ultrasonic waves under a lower intensity level and shorter intervention time could induce the controllable cavitation effect without obvious cell death and thermal damage [46][45]. Overall, low-intensity ultrasound is a relatively safe non-invasive intervention strategy. It is worthwhile to expect that flexible regulation of ultrasonic intervention parameters and better protocol design can further improve cavitation effect efficacy and potential risk aversion [47][46]. Meanwhile, complex models are crucial to represent the in vivo TME better which can provide a unique opportunity to study cellular interactions and biophysical mechanisms involved which are difficult to replicate in vitro due to lacking intricate intracellular and intercellular signaling pathways. It is therefore important to use more experimental efforts to comprehend the inherent differences between in vitro and in vivo that will affect microbubble behavior for exploring effective treatment interventions.
Table 1.
 Ultrasound-mediated microbubble adjuvant drug therapy in vitro.
Cavitation Mechanism Authors Cell Type Component Intervention Outcomes after Cavitation Effect
Enhanced permeability Tinkov et al. [48]Tinkov et al. [47] Renal carcinoma cell Doxorubicin Group 1: DOX

Group 2: DOX + MBs		 Group 3: EB + US

Approximately two-fold enhanced anti-proliferative effect in DOX-loaded MBs.

DOX-loaded MBs with high affinity to the nucleus.
Group 4: EB + MBs + US US-mediated MBs cavitation can increase tumor vascular permeability.

 Enhanced permeability

Promoted drug diffusion		 Li F. et al. [49]Li F. et al. [48] Renal carcinoma cell rAAV Group 1: rAAV

Group 2: rAAV + MBs

Group 3: rAAV + US

Group 4: rAAV + UTMD		 US-mediated MBs inhibit tumor cell proliferation and induce apoptosis.

US-mediated MBs promote viral transfection approximately two-fold.
The cavitation effect promotes drug release approximately three-fold.
Enhanced permeability Tang Q. et al. [57]Tang Q. et al. [56] Hepatic cancer HSV-TK/GCV Group 1: pEGFP-KDR-TK + pEGFP-C1-AFP-TK

Group 2: pEGFP-KDR-TK + pEGFP-C1-AFP-TK + US

Group 3: pEGFP-KDR-TK + pEGFP-C1-AFP-TK + MBs + US		 US-mediated MBs can increase killing effect of HSV-TK/GCV and CD/5-FC systems on vascular and hepatoma cells.

US-mediated MBs can increase tumor vascular permeability and gene transfection efficiency.		 Enhanced permeability

Promoted drug diffusion		 Haag P. et al. [50]Haag P. et al. [49] Prostate tumor cell ODNs Group 1: MBs

Enhanced permeability

Induced tumor necrosis		 Li P. et al. [58]Li P. et al. Group 2: ODNs

Group 3: ODNs + MBs

Group 4: ODNs + US

Group 5: ODNs + MBs + US		 [57] Subcutaneous VX2 cancerBest US frequency: 1.75 MHz; best MI: 1.9.

US-mediated MBs inhibit AR protein levels by 36.23%.

US-mediated MBs promote viral transfection approximately 40-fold.
Evans Blue Group 1: EB

Group 2: EB + MBs

Group 3: EB + US

Group 4: EB + MBs + US		 US-mediated MBs can induce tumor microvasculature disruption resulting in hemorrhage, edema, and thrombosis to cause necrosis. Promoted drug uptake Yan F. et al. [51]Yan F. et al. [50] Breast cancer cell Paclitaxel and LyP-1 Peptide
Enhanced permeability Cool S.K. et al. [43]Cool S.K. et al. [42]Group 1: MBs No tumor

 ICG-liposomesGroup 2: PTX-loaded MBs

Group 3: Targeted PTX-loaded MBs		 Group 1: Drug-MBs + US

Group 2: Drug + MBs + US

Group 3: MBs + US

Group 4: Drug + USTargeted ultrasonic MBs encapsulation rate: 63%.

US for 2 min increased cell uptake approximately seven-fold.
MBs can increase ICG-liposomes loaded approximately three-fold.

US-mediated MBs increase drug release two times more.

US-mediated MBs can cause skin lesions due during microbubble collapse. Enhanced permeability

Promoted drug diffusion
Enhanced permeability

Promoted drug diffusion

Enhanced perfusion		Cochran M.C. et al. [52]Cochran M.C. et al. [51] Lin C.Y. et al. [59Breast cancer cell ]Doxorubicin and paclitaxel Lin C.Y. et al. [58]Group 1: MBs

Group 2: MBs + US

 Colon cancerGroup 3: Drug-loaded MBs DOX

Group 4: Drug-loaded MBs + US		 Group 1: DOX

Group 2: DOX + MBs

The encapsulation efficiency of PTX and DOX: 72%, 20.5%.

The payload of PTX-loaded MBs is 20 times DOX.

The anti-tumor effect increased by 80.1%.
Group 3: DOX + US

Group 4: DOX + MBs + US US-mediated MBs cavitation can increase tissue permeability and destroy tumor vessels.

US-mediated MBs can increase tumor drug uptake and inhibit growth.

US intervention time should be less than 2 min.		 Promoted drug diffusion Wang D.S. et al. [53
Enhanced permeability

Promoted drug diffusion		]Wang D.S. et al. [52] Fokong S. et al. [60]Fokong S. et al. [59Vascular endothelial tumor cell ]DNA Group 1: Cationic MBs + US Colon cancer Rhodamine-B

Coumarin-6

Group 2: Neutral MBs + US

Group 3: US

Group 4: Cationic MBs		 Group 1: MBs-Rhodamine-B

Group 2: MBs-Coumarin-6

Group 3: MBs-Rhodamine-B + US

Group 4: MBs-Coumarin-6 + USCationic MBs protect plasmid DNA from degradation.

Cationic MBs promote gene transfection approximately two-fold.
The polymer-based MBs are highly suitable for image-guided, targeted, and triggered drug delivery to tumors and blood vessels. Enhanced permeability Ren S.T. et al. [54]Ren S.T. et al. [53] Colon adenocarcinoma cell Docetaxel Group 1: DOC

Enhanced permeability

Induced tumor necrosis		Group 2: DOC + US

Group 3: MBs + US

Group 4: DOC + MBs + US		 The maximum encapsulation rate: 54.9%.

The anti-tumor effect increased approximately two-fold.
Huang P. et al. [7] Colon cancer No drug Enhanced permeability

Promoted drug diffusion		 Escoffre J.M. et al. [55]Escoffre J.M. et al. [54] Glioblastoma cell Doxorubicin Group 1: MBs + US

Group 2: DOX + MBs

Group 3: DOX + MBs + US		 US-mediated MBs significantly increased drug uptake.

Tumor cell death with US-mediated MBs was enhanced approximately three-fold.
Abbreviations: MBs, microbubbles; DOX, doxorubicin; US, ultrasound; PTX, paclitaxel; DOC, docetaxel; rAAV, recombinant adeno-associated virus; UTMD, ultrasound-targeted microbubble destruction; ODNs, oligodeoxynucleotides; MI, mechanical index; AR, androgen receptor.
Table 2.
 Ultrasound-mediated microbubble adjuvant drug therapy in vivo.
Cavitation Mechanism Authors Cell Type Component Intervention Outcomes after Cavitation Effect
Enhanced permeability Wang G. et al. [56]Wang G. et al. [55] Hepatic cancer Evans Blue Group 1: EB

Group 2: EB + MBs

Group 1: MBs


Group 2: US


Group 3: MBs + US
US-mediated MBs inhibit tumor growth and metastasis.

US-mediated MBs destroy tumor cell nucleus and microvascular.

US-mediated MBs decreases the expression of CD31.
Abbreviations: EB, Evans Blue; MBs, microbubbles; DOX, doxorubicin; US, ultrasound; HSV-TK/GCV, Herpes simplex virus-thymidine kinase/ganciclovir; KDR, kinase insert domain receptor; 5-FC, 5-fluorocytosine; TK, thymidine kinase; pEGFP, enhanced green fluorescent protein plasmid; ICG, indocyanine green; PBCA, poly (butyl cyanoacrylate).

Although applications of acoustic cavitation have realized significant progress, there are still many difficulties and challenges which require further efforts to explore more suitable delivery systems and effective efficacy. Firstly, the particle size of microbubbles remains a key factor affecting localized drug accumulation and cavitation effects in tumors. Therefore, we need to develop a new process to solve the situation that the cavitation effect is weakened due to the low accumulation of microbubbles around the tumor tissue caused by the unsuitable particle size of microbubbles. Secondly, with the emergence of multifunctional drug delivery systems, the structure with membrane shells continues to present complex trends. We need to reduce the adverse effects of membrane shell material, particle size, and targeted modification type on the cavitation effect in the complex and variable TME for achieving the controllability and stability of the targeted microbubble-loading system between different individuals with finally attaining the standardized application in clinical intervention. Of course, due to the different research directions of each scholar, there are also differences in the parameters they used. We need more efforts to verify the effects of ultrasound intervention time, irradiation time interval, ultrasound frequency, sound intensity, microbubble size, drug dose, and concentration on the therapeutic efficacy of the disease. Meanwhile, the integration of multiple technologies needs to be carried out, including protein-membrane-targeted modification, photothermal, magnetic field, radiation, free radicals, gene interference, immunotherapy, etc., to comprehensively enhance the anti-tumor efficacy. Absolutely, the safety of the delivery vehicle is also an issue that closer attention should be paid to. Although many studies have confirmed the high histocompatibility of microbubbles, more research is still needed in the future to further confirm the potential harm caused by long-term accumulation in the body.

At present, there are still many problems to be solved in the treatment of tumors with low-frequency ultrasound combined with microbubbles, but it is undeniable that this technology has shown great clinical application value as a safe, effective, easy-to-operate, and targeted non-invasive treatment method. With the development of technology, this promising non-invasive tumor treatment method will be widely used in clinical practice.

References

  1. Inui, A.; Honda, A.; Yamanaka, S.; Ikeno, T.; Yamamoto, K. Effect of ultrasonic frequency and surfactant addition on microcapsule destruction. Ultrason. Sonochem. 2021, 70, 105308.
  2. Li, M.; Lan, B.; Sankin, G.; Zhou, Y.; Liu, W.; Xia, J.; Wang, D.; Trahey, G.; Zhong, P.; Yao, J. Simultaneous Photoacoustic Imaging and Cavitation Mapping in Shockwave Lithotripsy. IEEE Trans. Med. Imaging 2020, 39, 468–477.
  3. Suslick, K.S.; Eddingsaas, N.C.; Flannigan, D.J.; Hopkins, S.D.; Xu, H. The Chemical History of a Bubble. Acc. Chem. Res. 2018, 51, 2169–2178.
  4. Yildirim, A.; Blum, N.T.; Goodwin, A.P. Colloids, nanoparticles, and materials for imaging, delivery, ablation, and theranostics by focused ultrasound (FUS). Theranostics 2019, 9, 2572–2594.
  5. Ye, L.; Zhu, X.; He, Y.; Wei, X. Ultrasonic cavitation damage characteristics of materials and a prediction model of cavitation impact load based on size effect. Ultrason. Sonochem. 2020, 66, 105115.
  6. Daecher, A.; Stanczak, M.; Liu, J.B.; Zhang, J.; Du, S.; Forsberg, F.; Leeper, D.B.; Eisenbrey, J.R. Localized microbubble cavitation-based antivascular therapy for improving HCC treatment response to radiotherapy. Cancer Lett. 2017, 411, 100–105.
  7. Huang, P.T.; You, X.D.; Pan, M.Q.; Li, S.Y.; Zhang, Y.; Zhao, Y.Z.; Wang, M.H.; Hong, Y.R.; Pu, Z.X.; Chen, L.R.; et al. A novel therapeutic strategy using ultrasound mediated microbubbles destruction to treat colon cancer in a mouse model. Cancer Lett. 2013, 335, 183–190.
  8. Wang, F.; Dong, L.; Liang, S.M.; Wei, X.X.; Wang, Y.L.; Chang, L.S.; Guo, K.; Wu, H.W.; Chang, Y.Q.; Yin, Y.L.; et al. Ultrasound-triggered drug delivery for glioma therapy through gambogic acid-loaded nanobubble-microbubble complexes. Biomed. Pharm. 2022, 150, 113042.
  9. Liu, T.; Li, M.; Tang, J.; Li, J.; Zhou, Y.; Liu, Y.; Yang, F.; Gu, N. An acoustic strategy for gold nanoparticle loading in platelets as biomimetic multifunctional carriers. J. Mater. Chem. B 2019, 7, 2138–2144.
  10. Stride, E.; Coussios, C. Nucleation, mapping and control of cavitation for drug delivery. Nat. Rev. Phys. 2019, 1, 495–509.
  11. Athanassiadis, A.G.; Ma, Z.C.; Moreno-Gomez, N.; Melde, K.; Choi, E.; Goyal, R.; Fischer, P. Ultrasound-Responsive Systems as Components for Smart Materials. Chem. Rev. 2022, 122, 5165–5208.
  12. Rapoport, N. Ultrasound-mediated micellar drug delivery. Int. J. Hyperth. 2012, 28, 374–385.
  13. Sankin, G.N.; Simmons, W.N.; Zhu, S.L.; Zhong, P. Shock wave interaction with laser-generated single bubbles. Phys. Rev. Lett. 2005, 95, 034501.
  14. Chen, H.; Kreider, W.; Brayman, A.A.; Bailey, M.R.; Matula, T.J. Blood vessel deformations on microsecond time scales by ultrasonic cavitation. Phys. Rev. Lett. 2011, 106, 034301.
  15. Bang, J.H.; Suslick, K.S. Applications of ultrasound to the synthesis of nanostructured materials. Adv. Mater. 2010, 22, 1039–1059.
  16. Fernandez Rivas, D.; Prosperetti, A.; Zijlstra, A.G.; Lohse, D.; Gardeniers, H.J. Efficient sonochemistry through microbubbles generated with micromachined surfaces. Angew. Chem. Int. Ed. Engl. 2010, 49, 9699–9701.
  17. Kwan, J.J.; Graham, S.; Myers, R.; Carlisle, R.; Stride, E.; Coussios, C.C. Ultrasound-induced inertial cavitation from gas-stabilizing nanoparticles. Phys. Rev. E Stat. Nonlin. Soft Matter Phys. 2015, 92, 023019.
  18. Escoffre, J.M.; Piron, J.; Novell, A.; Bouakaz, A. Doxorubicin delivery into tumor cells with ultrasound and microbubbles. Mol. Pharm. 2011, 8, 799–806.
  19. Grainger, S.J.; Serna, J.V.; Sunny, S.; Zhou, Y.; Deng, C.X.; El-Sayed, M.E. Pulsed ultrasound enhances nanoparticle penetration into breast cancer spheroids. Mol. Pharm. 2010, 7, 2006–2019.
  20. Marmottant, P.; Bouakaz, A.; de Jong, N.; Quilliet, C. Buckling resistance of solid shell bubbles under ultrasound. J. Acoust. Soc. Am. 2011, 129, 1231–1239.
  21. van Wamel, A.; Kooiman, K.; Harteveld, M.; Emmer, M.; ten Cate, F.J.; Versluis, M.; de Jong, N. Vibrating microbubbles poking individual cells: Drug transfer into cells via sonoporation. J. Control. Release 2006, 112, 149–155.
  22. Mehier-Humbert, S.; Bettinger, T.; Yan, F.; Guy, R.H. Plasma membrane poration induced by ultrasound exposure: Implication for drug delivery. J. Control. Release 2005, 104, 213–222.
  23. Xia, H.; Yang, D.; He, W.; Zhu, X.; Yan, Y.; Liu, Z.; Liu, T.; Yang, J.; Tan, S.; Jiang, J.; et al. Ultrasound-mediated microbubbles cavitation enhanced chemotherapy of advanced prostate cancer by increasing the permeability of blood-prostate barrier. Transl. Oncol. 2021, 14, 101177.
  24. Park, J.; Fan, Z.; Deng, C.X. Effects of shear stress cultivation on cell membrane disruption and intracellular calcium concentration in sonoporation of endothelial cells. J. Biomech. 2011, 44, 164–169.
  25. Qin, P.; Han, T.; Yu, A.C.H.; Xu, L. Mechanistic understanding the bioeffects of ultrasound-driven microbubbles to enhance macromolecule delivery. J. Control. Release 2018, 272, 169–181.
  26. Eggen, S.; Afadzi, M.; Nilssen, E.A.; Haugstad, S.B.; Angelsen, B.; Davies Cde, L. Ultrasound improves the uptake and distribution of liposomal Doxorubicin in prostate cancer xenografts. Ultrasound Med. Biol. 2013, 39, 1255–1266.
  27. Qiu, S.F.; Li, D.X.; Wang, Y.G.; Xiu, J.C.; Lyu, C.Y.; Kutty, S.; Zha, D.G.; Wu, J.F. Ultrasound-Mediated Microbubble Cavitation Transiently Reverses Acute Hindlimb Tissue Ischemia through Augmentation of Microcirculation Perfusion Via the Enos/No Pathway. Ultrasound Med. Biol. 2021, 47, 1014–1023.
  28. Ji, C.; Wang, L.; Dai, R.; Shan, L.; Yang, H.; Zhu, H.; Meng, Q. Hyperthermia exacerbates the effects of cathepsin L on claudin-1 in a blood-brain barrier model in vitro. Brain Res. 2016, 1631, 72–79.
  29. Cai, H.; Liu, W.; Xue, Y.; Shang, X.; Liu, J.; Li, Z.; Wang, P.; Liu, L.; Hu, Y.; Liu, Y. Roundabout 4 regulates blood-tumor barrier permeability through the modulation of ZO-1, Occludin, and Claudin-5 expression. J. Neuropathol. Exp. Neurol. 2015, 74, 25–37.
  30. Ma, J.; Wang, P.; Liu, Y.; Zhao, L.; Li, Z.; Xue, Y. Kruppel-like factor 4 regulates blood-tumor barrier permeability via ZO-1, occludin and claudin-5. J. Cell Physiol. 2014, 229, 916–926.
  31. Wang, F.; Song, X.; Zhou, M.; Wei, L.; Dai, Q.; Li, Z.; Lu, N.; Guo, Q. Wogonin inhibits H2O2-induced vascular permeability through suppressing the phosphorylation of caveolin-1. Toxicology 2013, 305, 10–19.
  32. Martin, T.A.; Mason, M.D.; Jiang, W.G. HGF and the regulation of tight junctions in human prostate cancer cells. Oncol. Rep. 2014, 32, 213–224.
  33. Tang, L.; Zhang, C.Y.; Yang, Q.; Xie, H.; Liu, D.D.; Tian, H.B.; Lu, L.X.; Xu, J.Y.; Li, W.Y.; Xu, G.X.; et al. Melatonin maintains inner blood-retinal barrier via inhibition of p38/TXNIP/NF-kappa B pathway in diabetic retinopathy. J. Cell. Physiol. 2021, 236, 5848–5864.
  34. Liao, J.Z.; Li, Q.W.; Lei, C.Q.; Yu, W.L.; Deng, J.C.; Guo, J.Y.; Han, Q.Y.; Hu, L.M.; Li, Y.; Pan, J.Q.; et al. Toxic effects of copper on the jejunum and colon of pigs: Mechanisms related to gut barrier dysfunction and inflammation influenced by the gut microbiota. Food Funct. 2021, 12, 9642–9657.
  35. Poplawska, M.; Dutta, D.; Jayaram, M.; Chong, N.S.; Salifu, M.; Lim, S.H. Genes modulating intestinal permeability and microbial community are dysregulated in sickle cell disease. Ann. Hematol. 2022, 101, 1009–1013.
  36. Cheng, C.Y.; Mruk, D.D. The Blood-Testis Barrier and Its Implications for Male Contraception. Pharmacol. Rev. 2012, 64, 16–64.
  37. Rose, E.C.; Odle, J.; Blikslager, A.T.; Ziegler, A.L. Probiotics, Prebiotics and Epithelial Tight Junctions: A Promising Approach to Modulate Intestinal Barrier Function. Int. J. Mol. Sci. 2021, 22, 6729.
  38. Kaminsky, L.W.; Al-Sadi, R.; Ma, O.M. IL-1 beta and the Intestinal Epithelial Tight Junction Barrier. Front. Immunol. 2021, 12, 767456.
  39. Sasson, E.; Anzi, S.; Bell, B.; Yakovian, O.; Zorsky, M.; Deutsch, U.; Engelhardt, B.; Sherman, E.; Vatine, G.; Dzikowski, R.; et al. Nano-scale architecture of blood-brain barrier tight-junctions. Elife 2021, 10, e63253.
  40. Bae, M.J.; Lee, Y.M.; Kim, Y.H.; Han, H.S.; Lee, H.J. Utilizing Ultrasound to Transiently Increase Blood-Brain Barrier Permeability, Modulate of the Tight Junction Proteins, and Alter Cytoskeletal Structure. Curr. Neurovasc. Res. 2015, 12, 375–383.
  41. Shang, X.; Wang, P.; Liu, Y.; Zhang, Z.; Xue, Y. Mechanism of low-frequency ultrasound in opening blood-tumor barrier by tight junction. J. Mol. Neurosci. 2011, 43, 364–369.
  42. Cool, S.K.; Geers, B.; Roels, S.; Stremersch, S.; Vanderperren, K.; Saunders, J.H.; De Smedt, S.C.; Demeester, J.; Sanders, N.N. Coupling of drug containing liposomes to microbubbles improves ultrasound triggered drug delivery in mice. J. Control. Release 2013, 172, 885–893.
  43. Goertz, D.E. An overview of the influence of therapeutic ultrasound exposures on the vasculature: High intensity ultrasound and microbubble-mediated bioeffects. Int. J. Hyperth. 2015, 31, 134–144.
  44. Kuijpers, M.J.; Gilio, K.; Reitsma, S.; Nergiz-Unal, R.; Prinzen, L.; Heeneman, S.; Lutgens, E.; van Zandvoort, M.A.; Nieswandt, B.; Egbrink, M.G.; et al. Complementary roles of platelets and coagulation in thrombus formation on plaques acutely ruptured by targeted ultrasound treatment: A novel intravital model. J. Thromb. Haemost 2009, 7, 152–161.
  45. Song, F.Y.; Gao, H.; Li, D.Y.; Petrov, A.V.; Petrov, V.V.; Wen, D.S.; Sukhorukov, G.B. Low intensity focused ultrasound responsive microcapsules for non-ablative ultrafast intracellular release of small molecules. J. Mater. Chem. B 2021, 9, 2384–2393.
  46. Tu, L.; Liao, Z.; Luo, Z.; Wu, Y.L.; Herrmann, A.; Huo, S. Ultrasound-controlled drug release and drug activation for cancer therapy. Exploration 2021, 1, 20210023.
  47. Tinkov, S.; Winter, G.; Coester, C.; Bekeredjian, R. New doxorubicin-loaded phospholipid microbubbles for targeted tumor therapy: Part I--Formulation development and in-vitro characterization. J. Control. Release 2010, 143, 143–150.
  48. Li, F.; Jin, L.; Wang, H.; Wei, F.; Bai, M.; Shi, Q.; Du, L. The dual effect of ultrasound-targeted microbubble destruction in mediating recombinant adeno-associated virus delivery in renal cell carcinoma: Transfection enhancement and tumor inhibition. J. Gene Med. 2014, 16, 28–39.
  49. Haag, P.; Frauscher, F.; Gradl, J.; Seitz, A.; Schafer, G.; Lindner, J.R.; Klibanov, A.L.; Bartsch, G.; Klocker, H.; Eder, I.E. Microbubble-enhanced ultrasound to deliver an antisense oligodeoxynucleotide targeting the human androgen receptor into prostate tumours. J. Steroid. Biochem. Mol. Biol. 2006, 102, 103–113.
  50. Yan, F.; Li, X.; Jin, Q.; Jiang, C.; Zhang, Z.; Ling, T.; Qiu, B.; Zheng, H. Therapeutic ultrasonic microbubbles carrying paclitaxel and LyP-1 peptide: Preparation, characterization and application to ultrasound-assisted chemotherapy in breast cancer cells. Ultrasound Med. Biol. 2011, 37, 768–779.
  51. Cochran, M.C.; Eisenbrey, J.; Ouma, R.O.; Soulen, M.; Wheatley, M.A. Doxorubicin and paclitaxel loaded microbubbles for ultrasound triggered drug delivery. Int. J. Pharm. 2011, 414, 161–170.
  52. Wang, D.S.; Panje, C.; Pysz, M.A.; Paulmurugan, R.; Rosenberg, J.; Gambhir, S.S.; Schneider, M.; Willmann, J.K. Cationic versus neutral microbubbles for ultrasound-mediated gene delivery in cancer. Radiology 2012, 264, 721–732.
  53. Ren, S.T.; Liao, Y.R.; Kang, X.N.; Li, Y.P.; Zhang, H.; Ai, H.; Sun, Q.; Jing, J.; Zhao, X.H.; Tan, L.F.; et al. The antitumor effect of a new docetaxel-loaded microbubble combined with low-frequency ultrasound in vitro: Preparation and parameter analysis. Pharm. Res. 2013, 30, 1574–1585.
  54. Escoffre, J.M.; Mannaris, C.; Geers, B.; Novell, A.; Lentacker, I.; Averkiou, M.; Bouakaz, A. Doxorubicin liposome-loaded microbubbles for contrast imaging and ultrasound-triggered drug delivery. IEEE Trans. Ultrason. Ferroelectr. Freq. Control 2013, 60, 78–87.
  55. Wang, G.; Zhuo, Z.; Xia, H.; Zhang, Y.; He, Y.; Tan, W.; Gao, Y. Investigation into the impact of diagnostic ultrasound with microbubbles on the capillary permeability of rat hepatomas. Ultrasound Med. Biol. 2013, 39, 628–637.
  56. Tang, Q.; He, X.; Liao, H.; He, L.; Wang, Y.; Zhou, D.; Ye, S.; Chen, Q. Ultrasound microbubble contrast agent-mediated suicide gene transfection in the treatment of hepatic cancer. Oncol. Lett. 2012, 4, 970–972.
  57. Li, P.; Zhu, M.; Xu, Y.; Zhao, Y.; Gao, S.; Liu, Z.; Gao, Y.H. Impact of microbubble enhanced, pulsed, focused ultrasound on tumor circulation of subcutaneous VX2 cancer. Chin. Med. J. 2014, 127, 2605–2611.
  58. Lin, C.Y.; Li, J.R.; Tseng, H.C.; Wu, M.F.; Lin, W.L. Enhancement of focused ultrasound with microbubbles on the treatments of anticancer nanodrug in mouse tumors. Nanomedicine 2012, 8, 900–907.
  59. Fokong, S.; Theek, B.; Wu, Z.; Koczera, P.; Appold, L.; Jorge, S.; Resch-Genger, U.; van Zandvoort, M.; Storm, G.; Kiessling, F.; et al. Image-guided, targeted and triggered drug delivery to tumors using polymer-based microbubbles. J. Control. Release 2012, 163, 75–81.
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