1, Wayne Brisbane¹, Stella Whang², Yak-Nam Wang³, Kayla Gravelle², Venu Pillarisetty⁴, W. Conrad Liles⁵, Vera Khokhlova³, Michael Bailey³, Tatiana D. Khokhlova², Joo Ha Hwang²

¹Department of Urology, University of Washington, Seattle, Washington, USA; ²Department of Gastroenterology, University of Washington, Seattle, Washington, USA; ³Center for Industrial and Medical Ultrasound, University of Washington, Seattle, Washington, USA; ⁴Department of Surgery, University of Washington, Seattle, Washington, USA; ⁵Department of Medicine, University of Washington, Seattle, Washington, USA

Correspondence: George R. Schade

in vivo. We characterized the long-term immune response to BH RCC tumor ablation in a ratmodel.

2, Aaron Prodeus^{1, 2}, Jean Gariepy^{1, 2}, Kullervo Hynynen^{1, 2}, David Goertz^{1, 2}

¹University of Toronto, Toronto, Ontario, Canada; ²Sunny brook Research Institute, Toronto, Ontario, Canada

Correspondence: Sharshi Bulner

1, Tsang-Wei Tu¹, Scott R. Burks¹, Bobbie K. Lewis¹, Joseph A. Frank^1,2

¹Radiology and Imaging Sciences, National Institutes of Health, Bethesda, Maryland, USA; ²National Institute of Biomedical Imaging and Bioengineering, National Institutes of Health, Bethesda, Maryland, USA

Correspondence: Kee W. Jang

^1,2, Jeremy Vion^1,2_, Loïc DAUNIZEAU^1,2, Christopher Bawiec², Guillaume BOUCHOUX^{1, 3}, Nicolas Sénégond⁴, Jean-Yves Chapelon^1,2, Alexandre CARPENTIER^3,5

¹LabTAU, INSERM, U1032, Lyon, Rhone-Alpes, France; ²Univ Lyon, Université Lyon 1, Lyon, F-69003, France; ³CarThera Research Team, Brain and Spine Institute, Paris, France; ⁴Vermon SA, Tours, France; ⁵Department of Neurosurgery, Assistance Publique, Hopitaux de Paris, Pitie Salpetriere, Paris, France

Correspondence: William Apoutou N'Djin

in vivo on 10 pigs and monitored under real-time multi-planar magnetic resonance thermometry (MRT) (Fig. 1).

in vivo. Further investigations are ongoing to improve the robustness of the CMUTdevices and increase the treatment volumes. This project was supported by CarThera, the French National Research Agency (ANR, 2010) and Single InterministerialFund (FUI, 2013).

O20 Real-time HIFU beam imaging using beamforming in an ultrasound scanner

Kazuhiro Matsui¹, Françoise CHAVRIER^{2, 4}, Takashi Azuma³, Ichiro Sakuma^{1, 5}, William Apoutou N'Djin^{2, 4}, Rémi Souchon^2,4

¹Engineering, The University of Tokyo, Tokyo, Japan; ²LabTAU, INSERM unité 1032, Lyon, France; ³Medicine, The University of Tokyo, Tokyo, Japan; ⁴Univ Lyon, Université Lyon 1, Lyon, France; ⁵Medical Device Development and Regulation Research Center, Tokyo, Japan

Correspondence: Kazuhiro Matsui

The object of this study is to provide a method for imaging, in real time, the HIFU beam inside an acoustically propagative medium using beamforming in an ultrasound scanner.Novelty and advantagesThe novelty of the method can be found in its implementation of beamforming in an ultrasound scanner, which is analogous to the backward reconstruction using time reversal. The advantage of this method is its real-time imaging capability owing to digital parallel processing of the scanner. Further advantage is simplicity of the imaging system without requiring additional equipment aside from an ultrasound scanner and an ultrasound array serving as a time-reversal mirror.

via plane-wave beamforming. Evaluations: The feasibility of the method was evaluated using either the time-reversal reconstruction or the beamforming reconstruction, with and without HIFU beam aberrations. First, in the experiment in water without HIFU beam aberrations, performance of the method was demonstrated in comparison with the reference field obtained by numerical calculation of the forward propagation using the Rayleigh integral and hydrophone scanning. Then, in the experiment with HIFU beam aberrations induced by heterogeneous hydrogel, HIFU beam visibility was evaluated with referred to the HIFU pressure field measured by hydrophone scanning.

Burks S, Nagle M, Kim S, Milo B, Frank J. A90 Low-intensity ultrasound prolongs lifetimes of transplanted mesenchymal stem cells. J Ther Ultrasound. 2016; 4(Suppl 1):31. Available from: https://jtultrasound.biomedcentral.com/articles/10.1186/s40349-016-0076-5

O22 Impact of microbubble-enhanced radiofrequency ablation of rabbit liver

Zhong Chen, Xueyan Qiao

Department of Ultrasound, Xinqiao Hospital, The Third Military Medical University, Chongqing, China

Correspondence: Zhong Chen

Dai H, Chen F, Yan S, Ding X, Ma D, Wen J, Xu D, Zou X. In Vitro and In Vivo Investigation of High-Intensity Focused Ultrasound (HIFU) Hat-Type Ablation Mode. Med Sci Monit. 2017; 23:3373-3382. Available from: https://www.medscimonit.com/abstract/index/idArt/902528 DOI: 10.12659/MSM.902528

O24 Image-based predicition of focusing gain in situ using dual-mode ultrasound arrays

Brogan T. McWilliams, Dalong Liu, Emad S. Ebbini

Electrical Engineering, University of Minnesota, Minneapolis, Minnesota, USA

Correspondence: Brogan T. McWilliams

in situ utilizing simplified propagation models and calibration power measurements.

in vitro setup used to provide a validation for the image-based approach. In particular, an acoustic power meter (Omega, Ohmic instruments Easton, MD) was modified to allow the measurement of the insertion loss due to a slab of tissue-mimicking phantom between the DMUA and the tip of the cone (treated as the target). The TM phantom was fabricated from animal skin bovine gelatine, graphite,1-propanol, glutaraldehyde, and deionized water. Absorption of the phantom is predominately due to the presence of graphite and was determined to be 0.6 and 1.0dB/cm/MHz for two 4-mm disk-shaped slaps. Two modes of the imaging were used to characterize the FUS beam propagation through the tissue: 1) Synthetic-aperture(SA) imaging, which provides larger field of view (FoV) to characterize the propagation medium, and 2) Single-transmit focus (STF), which provides specific feedback about the interactions between the FUS beam and the tissue in its path to the target. The STF imaging is performed using the same beamforming parameters of the intended therapeutic HIFU beam, but at diagnostic levels and with sub-microsecond pulse duration. HIFU was applied at 4 different frequencies (2.4 to 4.2 MHz in stepsof 0.6 MHz). HIFU shots of 1-sec durations were used and repeated 4 times. SA and STF images were collected before, during and after the application of therapeutic HIFU. The STF frame rate was 400 fps, which was helpful to fully characterize the incidence of cavitation and/or instability in the power measurement.

in vitro at multiple frequencies. The method has been applied for the estimation of the focusing gain in vivo. As described, STF imaging of the phantom slab allowed for measuring the beam dimensions and the FUS interaction with the tissue and could be used in future studies to extract details of an inhomogeneous medium to provide accurate estimates of the focusing gain (or heating rate). Further validation of the calculated heating rate will be performed in vivo by measuringtemperature with thermocouples in the vicinity of the focus.

O25 An automatic approach to lesion planning for robotic HIFU

Tom Williamson, Scott Everitt, Ranjaka De Mel, Sunita Chauhan

Mechanical and Aerospace Engineering, Monash University, Melbourne, Victoria, Australia

Correspondence: Tom Williamson

in situ’ in variousorgans. At this stage, the neoplasm is generally spherical in shape while, conventionally, focused ultrasound (FUS) treatment involves ‘raster’ scanning the formation ofthe HIFU lesions in the ROI, an approach that will generally not conform to the spherical tumor geometry. This may lead to two major undesirable effects: large gaps or overlaps at the tumor margins (physical spacing isn’t optimized) and between individual lesions, or significant ‘lesion-to-lesion’ interaction creating uncertainty in the shape, size and extent of the subsequent lesions due to the remnant effect of previously laid lesions. Furthermore, the gaps between adjacent lesions may have a seeding effect, leading to further growth of malignancies due to the untreated sections. To avoid lesion interactions, several authors suggested a pre-defined time delay betweenlesions or change in exposure parameters. The former results in unnecessary treatment delays while the latter involves capacious real-time computations for optimizing the treatment (dynamically computing thermal dose) as well as remotely and frequently switching on/off high power equipment. In order to overcome these deficiencies, we propose a method for determining the optimal lesion arrangement within any arbitrary tumor size and shape, based on an extension of the bubble packing algorithm first described by Shimada in 1995 [1]. The original algorithm was extended to allow lesions to take any arbitrary position andorientation within the specified tumor volume, and evaluated on spherical and ellipsoidal tumor models.

1, Jonathan Caloone¹, Anthony Kocot¹, Cyril Huissoud²

¹LabTAU - U1032, INSERM, Lyon, Rhône Alpes, France; ²CHU Croix Rousse, LYON, France

Correspondence: David Melodelima

ex vivo model. The effectiveness of this HIFU device applied to the perfused placental unit must be studied in a preclinical animal study under conditions similar to those in humans before starting a clinical trial. Here, we report a feasibility study using a monkey model of pregnancy. The 3 objectives of this work were (i) to evaluate the feasibility and reproducibility of HIFU lesions in the placenta of pregnant monkeys 2,1, Raj Aravalli¹, Emad S. Ebbini¹

¹Electrical and Computer Engineering, University of Minnesota, Minneapolis, Minnesota, USA; ²Siemens, Seattle, Washington, USA

Correspondence: Dalong Liu

1, Christian Aurup¹, Carlos J. Sierra Sánchez¹, Julien Grondin¹, Wenlan Zheng¹, Vincent Ferrera², Elisa E. Konofagou^1,3

¹Biomedical Engineering, Columbia University, New York, New York, USA; ²Neuroscience, Columbia University, New York, New York, USA, ³Radiology, Columbia University, New York, New York, USA

Correspondence: Shih-Ying Wu

in vivo in preparation for clinical trials.

in vivo experiments, for the first time the noninvasive FUS treatment was achieved within 30 min outside the MRI system for primates, and targeting flexibility allowed BBB opening in both the peripheral cerebral cortex and deeply-seated subcortical structures with the use of a free-guide arm and the inflatable bladder system of the FUS transducer to couple with the scalp. Moreover, the achieved targeting accuracy were proximal to the predicted 2-mm limit in simulation. The accuracy in the awake animal setting (3.0 mm) was found to be comparable to the sedate animal setting (3.2 mm), which was higher compared to the frame-based stereotaxis due to the improvement of lateral positioning of the animal, and the focal shift in the acoustic beam path was due to the skull distortion. On the other hand, real-time cavitation mapping was performed with neuronavigation guidance during the entire sonication, with the frequency spectra data showed a dramatic increase of the cavitation signal (harmonics and ultraharmonics) after injecting microbubbles. The acoustic mapping provided real-time spatial monitoring during the sonication and successfully confirmed the location of BBB opening. Finally, in all the experiments performed, no acute damage such as hemorrhage (SWI) or edema (T2-weighted imaging) was detected upon radiologic examination 2 h after sonication.

in vitro that these limitations may be due to the conventional ultrasound sequences used to disrupt the BBB. These sequences consist of long-pulses emitted at a slow rate and generate a mixture of both desired and undesired cavitation activities. We have recently developed and tested a new low pressure rapid short-pulse (RaSP) sequence in vivo efficiency and safety of ultrasound-mediated drug delivery to the brain.

in vivo in C57BL/6 mice would improve the efficiency and safety of brain drug delivery. We compared our RaSP sequence (peak-negative pressure: 400 kPa; pulse length (PL): 5 cycles; pulse repetition frequency (PRF): 1.25 kHz; burst length: 10 ms) to the current gold standard, conventional sequence at the same acoustic pressure (PL: 10,000 cycles; PRF: 0.5 Hz; burst length: 10 ms). Fluorescently-tagged (Texas Red) 3 kDa dextran and microbubbles were intravenously injected in mice while sonicating the left hippocampus with a 1 MHz focused ultrasound transducer. A 7.5 MHz passive cavitation detector captured the microbubble acoustic emissions. The relative dose and distribution of the drug were quantified by calculating the normalised optical density (NOD, average increase in fluorescence in the targeted area normalised by the control) and the coefficient of variation (COV, standard deviation over the average fluorescence intensity in the targeted region). Safety was assessed by haematoxylin and eosin (H&E) histological staining.

Nappoli A, Zaccagna F, Catocci G, Giulia B, Caliolo G, Andrani F, Catalano C. Magnetic resonance guided focused ultrasound surgery (MRgFUS) treatment of osteoid osteoma: a prospective development study. J Ther Ultrasound. 2015; 3(Suppl 1): O44. Available from: https://jtultrasound.biomedcentral.com/articles/10.1186/2050-5736-3-S1-O44

O32 Transoesophageal HIFU for cardiac ablation: experiments on beating hearts

Paul Greillier¹, Bénédicte Ankou², Ali Zorgani¹, Francis Bessière², Fabrice Marquet³, Julie Magat³, Sandrine Melot-Dusseau⁴, Romain Lacoste⁴, Bruno Quesson³, Mathieu Pernot⁵, Philippe Chevalier², Cyril Lafon^{1, 6}

¹LabTau - U1032, INSERM, LYON, Rhône, France; ²Hôpital Louis-Pradel, Lyon, France; ³IHU-LIRYC - CHU Bordeaux, Pessac, France; ⁴Station de primatologie -CNRS- UPS846, Rousset, France; ⁵Institut Langevin - Ondes et Images - ESPCI ParisTech, CNRS UMR 7587, Paris, France; ⁶University of Virginia, Charlottesville, Virginia, USA

Correspondence: Paul Greillier

Greillier P, Ankou B, Bessière, Zorgani A, Pioche M, Kwiecinski W, Magat J, Melot-Dusseau S, Lacoste R, Quesson B, Pernot M, Catheline S, Chevalier P, Lafon C. A75 Trans esophageal HIFU for cardiac ablation: first experiment in non-human primate. J Ther Ultrasound. 2016; 4(Suppl 1):31. Available from: https://jtultrasound.biomedcentral.com/articles/10.1186/s40349-016-0076-5

O33 In-vivo investigation of the combination of focused ultrasound and radiotherapy, using photoacoustic imaging as aplanning and monitoring tool

Marcia M. Costa, Anant Shah, Ian Rivens, Tuathan O'Shea, Carol Box, Jeff Bamber, Gail ter Haar

Radiotherapy and Imaging, The Institute of Cancer Research, Sutton, UK

Correspondence: Marcia M. Costa

1, Takashi Azuma¹, Kosuke Minamihata², Satoshi Yamaguchi¹, Shinya Yamahira¹, Etsuko Kobayashi¹, Mariko Iijima¹, Yoshikazu Shibasaki¹, TeruyukiNagamune¹, Ichiro Sakuma¹

¹The University of Tokyo, Tokyo, Japan; ²Kyushu University, Fukuoka, Japan

Correspondence: Ayumu Ishijima

1. Kawabata K et al. Jpn J Appl Phys 2005; 44: 4548.

2. Ishijima A et al. Ultrasonics 2016; 69: 97–105.

3. Lee YH et al. Biochem Biophys Res Commun 2013; 441: 1011–1017.

4. Wang CH et al. Biomaterials 2012; 33: 1939–1947.

O35 Dual mode time reversal cavity for US shockwave therapy and 3D imaging

J. Robin^1,2, B. Arnal¹, M. Tanter¹, M. Pernot¹

¹Institut Langevin, Paris, France; ²Université Paris 7, Paris, France

Correspondence: J. Robin

[1] Arnal et al, Appl Phys Lett, 101 1-5, 2012

[2] Robin et al, IEEE IUS, 2015

[3] Sarvazyan et al, Acoust Phys 55 630–7, 2009

[4] Luong et al, Sci Rep 6 36096, 2016

[5] Montaldo et al, Appl Phys Lett 2004 (No Image Selected)

O36 The effects of steroids on the myocardial reduction induced by myocardial cavitation-enabled therapy (MCET)

Y. I. Zhu¹, X. Lu², C. Dou², D. L. Miller², O. D. Kripfgans^{2, 1}

¹O.D. Kripfgans, Biomedical Engineering, University of Michigan, Ann Arbor, Michigan, USA; ²Department of Radiology, University of Michigan, Ann Arbor, Michigan, USA

Correspondence: Y. I. Zhu

in vivo model for HCM. Under ketamin/zylazine IP anesthesia, contrast agent was infused at a rate of 5μL/min/kg (tail vein catheter). The shaved and depilated left thorax was aimed at with a cardiac phased array (10S, Vivid 7, GE Healthcare) to center on the left ventricular myocardium. In this arrangement a 19 mm diameter single element therapy transducer was co-aligned to aim at a registered region of interest in the field of view of the 10S array. For therapy 10-cycle tone bursts at 1.5 MHz, 4 repetitions at 0.25 ms pulse interval, i.e. 4.0 kHz PRF, were sent every 8 heartbeats, aligned with trigger end systole (RR/3, using ECG gating). Peak negative free field pressures of 4 MPa were used to induce cavitation for 10 min. Therapy and sham therapy groups were followed up with MP administered at 0, 3, 6 and 24 hours after ultrasound exposure. Specifically, 30 mg/kg was chosen as high dose while 1 mg/kg was used as low dose alternative. Myocardial wall thickness 24 hours after therapy, measured from echocardiography was used to gauge the effect of initial myocardial swelling. White blood cell count was carried out 24 hours after therapy. Hearts were removed after 4 weeks and examined for evidence of the MP treatment effect. Histological sections with Masson’s trichrome staining were quantitatively analyzed for extent of fibrosis, i.e. tissue scarring.

Imaging protocol was: TR=600ms, TE=36ms, slice thickness=5mm, resolution=1.6*1.6mm2, matrix=54*128, EPI factor=9. Acquisition time=8.4s. Two sets of images with opposite polarity of DEG were used to quantify the displacement in each measurement. Ten measurements of ARFI were scanned before and immediately after HIFU sonication. T-test was used to determine whether tissue displacements have significantly changed. Temperature rise was monitored by GREduring HIFU sonication. The protocol was: TR=29ms, TE=10ms with the same FOV and resolution. The ambient temperature was 19°C. T2w image was acquired after HIFU sonication with TR=5000ms, TE=89ms, resolution=0.8*0.8 mm2, matrix=108*256.

p = 0.18 from 1, Xue Feng¹, Helen L. Sporkin¹, Jeff Elias², Kim Butts-Pauly³, Craig H. Meyer¹

¹Biomedical Engineering, University of Virginia, Charlottesville, Virginia, USA; ²Neurological Surgery, University of Virginia Hospital, Charlottesville, Virginia, USA; ³Radiology, Stanford University, Palo Alto, Virginia, USA

Correspondence: Steven P. Allen

[1] Plata et al. “A feasibility study on monitoring the evolution of apparent diffusion coefficient decrease during thermal ablation,” Med. Phys., 42(8), 5130–5137, 2015

[2] Smith et al. “Reduced field of view MRI with rapid, B1-robust outer volume suppression,” Magn. Reson. Med., 67(5), 1316–1323, 2012.

O41 Selection of MR-HIFU hyperthermia treatment sites based on MR thermometry evaluation in healthy volunteers

Satya V.V.N. Kothapalli¹, Michael Altman², Ari Partanen³, Lifei Zhu¹, Galen Cheng¹, H. Michael Gach², William Straube², Dennis Hallahan², Hong Chen^1,2

¹Biomedical Engieering, Washington University in Saint Louis, Saint Louis, Missouri, USA; ²Department of Radiation Oncology, Washington University in St. Louis, Saint Louis, Missouri, USA; ³Clinical Science MR Therapy, Philips, Andover, Massachusetts, USA

Correspondence: Satya V.V.N. Kothapalli

in vitro and intravascular bioeffects. Therefore, our study investigated the behaviors of ADV-Bs in vessels and tissue triggered by ultrasound (US), and then evaluated the feasibility of using intertissue ADV-Bs to treat resistant tumor cells by physical damage.

in vitro to deliver drugs into cells. Through these studies, it was discovered that several mechanisms of trans-membrane drug delivery exist and that they are highly dependent on the acoustic parameters, microbubble conditions, and the cell-type used. Despite promising results from these study, the advancement from single cell-bubble interactions to clinical use has not been made. This gap in development is largely because the underlying mechanism of trans-membrane drug delivery under high flow condition and for a large population of cells, remains poorly understood and poorly controlled. Our study explores the ultrasound and microbubble-mediated trans-membrane drug delivery efficiency and safety to a monolayer of endothelial cells using a state-of-theart physiologically-relevant cultivation system under different ultrasound exposure conditions. In the end, we will evaluate the critical question on whether safe transmembrane drug delivery can be achieved in such a complex, physiologically relevant environment.

1,2, Melissa Lin², Eric O'Neill², Oliver D. Kripfgans^{2, 1}, Renny T. Franceschi^{3, 4}, Andrew J. Putnam⁴, Mario L. Fabiilli^{1, 2}

¹Applied Physics Program, University of Michigan, Ann Arbor, Michigan, USA; ²Department of Radiology, University of Michigan, Ann Arbor, Michigan, USA; ³School of Dentistry, University of Michigan, Ann Arbor, Michigan, USA; ⁴Department of Biomedical Engineering, University of Michigan, AnnArbor, Michigan, USA

Correspondence: Alexander Moncion

in vivo model via CD31 immunohistochemical staining on days 7 and 14.

ex vivo. The ability to non-invasively stimulate and inhibit the PNS with FUS would allow clinicians an alternative therapeutic modality to treat peripheral neuropathy, as current treatment procedures can generate systemic side effects or require invasive procedures. In this study, we aim to show that FUS can elicit excitatory effects targeting the PNS and generate downstream physiological responses.

ex vivo mouse limbs alongside the sciatic nerve and exposed to FUS stimulation. A force balance was used to determine the acoustic radiation force generated by the transducer to estimate the tissue deformation in the focal region. To confirm neural activity at the single-unit level, a via FUS was shown capable of eliciting both observable leg twitching and measurable EMG responses when using the following FUS parameters: 0.2-5.7 MPa, 35-100% DC (continuous wave), 0.1-1kHz PRF, 0.8-10.5 ms stimulation duration. Increasing the pressure and DC raised the average peak-to-peak EMG response along with the success rate (Fig. 1). Varying the PRF or stimulation duration did not have a significant effect on response. Both delay and peak-to-peak EMG responses for FUS stimulation were found to be comparable to direct electrical stimulation of the sciatic nerve. Mice stimulated with efficacious parameters did not display any significant deviation in behavior compared to the control group or baseline values. The blinded histology study did not detect any damage for the stimulated group, only for the positive control. In in vivo. This demonstrates that FUS can be a non-invasive alternative to conventional therapeutic methods. Specific FUS parameters has been identified for successful and safe stimulation. Future work to explore the potential mechanisms of generation of the action potential will dictate the FUS parameters to translate this technique to clinical applications.

O46 The safety and feasibility of high intensity focused ultrasound in treatment of resistant hypertension

P. You

State Key Laboratory of Ultrasound Engineering in Medicine Co-founded by Chongqing and the Ministry of Science and Technology,Chongqing Key Laboratory of Ultrasound in Medicine and Engineering,College of Biomedical Engineering,Chongqing Medical University, Chongqing, China

1,2

¹The College of Biomedical Engineering, Chongqing Medical University, Chongqing, Chongqing, China; ²Haifu Hospital of the First Hospital Affiliated Hospital, Chongqing Medical University, Chongqing, China

1,2, A. Dupre^{1, 2}, Y. Chen², D. Perol², J. Vincenot^1, M. Rivoire^{1, 2}

¹LabTAU - U1032, INSERM, Lyon, Rhône Alpes, France; ²Centre Leon Berard, Lyon, France

Correspondence: D. Melodelima

Melodelima D, Dupre A, Vincenot J, Chen Y, Perol D, Rivoire M. A49 Clinical experience of intra-operative High Intensity Focused Ultrasound in patients with colorectal liver metastases. Results of a Phase II study. J Ther Ultrasound. 2016; 4(Suppl 1):31. Available from: https://jtultrasound.biomedcentral.com/articles/10.1186/s40349-016-0076-5.

O49 Catheter-directed thrombolysis of deep vein thrombosis enhanced by intraclot microbubbles and ultrasound: A clinical study

Q. Zhu¹, S. GAO¹, G. Dong², M. Guo¹, F. XIE³

¹Department of Ultasound, XinQiao Hospital,Third Military Medical University, Chongqing, China; ²Department of Ultrasound, The First Affiliated Hospital of Zhengzhou University, Zhengzhou, Henan, China; ³Internal Medicine Cardiology, University of Nebraska Medical Center, Omaha, NE, China

Correspondence: Q. Zhu

S. Yeo¹, Y. Kim^{2, 3}, H. Lim^{3, 4}, H. Rhim³, S. Jung^{4, 5}, N. Hwang⁵

¹Radiology, University Hospital of Cologne, Cologne, Germany; ²Radiology, Mint Hospital, Seoul, Korea; ³Radiology and Center for Imaging Science, Samsung Medical Center, Seoul, Korea; ⁴Health Sciences and Technology, SAIHST, Sungkyunkwan University, Seoul, Korea; ⁵Biostatistics and Clinical Epidemiology Center, Research Institute for Future Medicine, Samsung Medical Center, Seoul, Korea

Correspondence: S. Yeo

1, G. G. Powathil², P. Ziegenhein¹, J. Ijaz³, I. Rivens¹, M. Chaplain⁴, U. Oelfke¹, G. ter Haar¹

¹Joint Department of Physics, The Institute of Cancer Research, Sutton, UK; ²Swansea University, Swansea, UK; ³Bristol University, Bristol, UK; ⁴St. Andrew's University, St. Andrews, UK

Correspondence: S. C. Brueningk

in vitro FUS experiments, (2) to verify FUS simulation using measured temperature distributions, (3) to predict the cellular effects of combination treatments.

via mitotic catastrophe. The CAM was compared to results from experiments designed to characterise the response of HCT116 cells [1] G. Powathil et al., Semin Cancer Biol, (30, p.13–20), 2015 [2] B. Clarke, Ultrasound Med Biol, (21, p. 353–363), 1995