Integrated ultrasound and magnetic resonance imaging for simultaneous temperature and cavitation monitoring during focused ultrasound therapies

Arvanitis, Costas D.; McDannold, Nathan

doi:10.1118/1.4823793

Cited by 64 publications

(57 citation statements)

References 79 publications

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“…However, the information obtained from a single-element PCD is fundamentally limited due to the inherent trade-off between the volume of sensitivity and spatial specificity of the device. The use of multielement arrays, combined with passive beamforming algorithms borrowed from other fields, [45][46][47][48] has been shown to overcome this limitation and enable spatial mapping of cavitation activity during the application of FUS in both in vitro [49][50][51][52][53][54][55][56][57][58][59][60][61][62] and in vivo [63][64][65][66][67] settings. The integration of passive imaging during mechanicalbased FUS brain therapies would make the procedures practical, by providing a method for real-time treatment monitoring and control.…”

Section: Introductionmentioning

confidence: 99%

“…[69][70][71][72] One approach to utilizing passive imaging in the brain could be to image through these windows using a narrowaperture array. 64,65 However, due to the superior resolution afforded by large apertures while employing passive imaging techniques, 48 an implementation with an array covering the entire skull surface would be optimal.…”

Section: Introductionmentioning

confidence: 99%

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Experimental demonstration of passive acoustic imaging in the human skull cavity using CT‐based aberration corrections

Jones

O’Reilly

Hynynen³

2015

Medical Physics

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Purpose: Experimentally verify a previously described technique for performing passive acoustic imaging through an intact human skull using noninvasive, computed tomography (CT)-based aberration corrections Jones et al. [Phys. Med. Biol. 58, 4981-5005 (2013)]. Methods: A sparse hemispherical receiver array (30 cm diameter) consisting of 128 piezoceramic discs (2.5 mm diameter, 612 kHz center frequency) was used to passively listen through ex vivo human skullcaps (n = 4) to acoustic emissions from a narrow-band fixed source (1 mm diameter, 516 kHz center frequency) and from ultrasound-stimulated (5 cycle bursts, 1 Hz pulse repetition frequency, estimated in situ peak negative pressure 0.11-0.33 MPa, 306 kHz driving frequency) Definity™ microbubbles flowing through a thin-walled tube phantom. Initial in vivo feasibility testing of the method was performed. The performance of the method was assessed through comparisons to images generated without skull corrections, with invasive source-based corrections, and with water-path control images. Results: For source locations at least 25 mm from the inner skull surface, the modified reconstruction algorithm successfully restored a single focus within the skull cavity at a location within 1.25 mm from the true position of the narrow-band source. The results obtained from imaging single bubbles are in good agreement with numerical simulations of point source emitters and the authors' previous experimental measurements using source-based skull corrections O'Reilly et al. [IEEE Trans. Biomed. Eng. 61, 1285-1294]. In a rat model, microbubble activity was mapped through an intact human skull at pressure levels below and above the threshold for focused ultrasound-induced blood-brain barrier opening. During bursts that led to coherent bubble activity, the location of maximum intensity in images generated with CT-based skull corrections was found to deviate by less than 1 mm, on average, from the position obtained using source-based corrections. Conclusions: Taken together, these results demonstrate the feasibility of using the method to guide bubble-mediated ultrasound therapies in the brain. The technique may also have application in ultrasound-based cerebral angiography. C 2015 American Association of Physicists in Medicine.

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Section: Introductionmentioning

confidence: 99%

Section: Introductionmentioning

confidence: 99%

Experimental demonstration of passive acoustic imaging in the human skull cavity using CT‐based aberration corrections

Jones

O’Reilly

Hynynen³

2015

Medical Physics

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“…Several imaging and sensing modalities have been proposed for noninvasive temperature monitoring during thermal therapies, including ultrasound imaging, magnetic resonance imaging, and optoacoustic (photoacoustic) imaging and sensing. [5][6][7] The potential advantages of optoacoustic temperature imaging techniques reside in enhanced spatial resolution, temperature sensitivity, and faster data acquisition. [8][9][10] During the past decade, optoacoustic imaging has attracted significant attention from researchers and clinicians due to its success in a variety of biomedical applications that involve high resolution deep tissue imaging of optical absorbers (blood, water, and near infrared contrast agents) unattainable with other modalities.…”

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confidence: 99%

Red blood cell as a universal optoacoustic sensor for non-invasive temperature monitoring

Петрова

Oraevsky

Ermilov

2014

Applied Physics Letters

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Optoacoustic (photoacoustic) temperature imaging could provide improved spatial resolution and temperature sensitivity as compared to other techniques of non-invasive thermometry used during thermal therapies for safe and efficient treatment of lesions. However, accuracy of the reported optoacoustic methods is compromised by biological variability and heterogeneous composition of tissues. We report our findings on the universal character of the normalized temperature dependent optoacoustic response (ThOR) in blood, which is invariant with respect to hematocrit at the isosbestic point of hemoglobin. The phenomenon is caused by the unique homeostatic compartmentalization of blood hemoglobin exclusively inside erythrocytes. On the contrary, the normalized ThOR in aqueous solutions of hemoglobin showed linear variation with respect to its concentration and was identical to that of blood when extrapolated to the hemoglobin concentration inside erythrocytes. To substantiate the conclusions, we analyzed optoacoustic images acquired from the samples of whole and diluted blood as well as hemoglobin solutions during gradual cooling from þ37 to À15 C. Our experimental methodology allowed direct observation and accurate measurement of the temperature of zero optoacoustic response, manifested as the sample's image faded into background and then reappeared in the reversed (negative) contrast. These findings provide a framework necessary for accurate correlation of measured normalized optoacoustic image intensity and local temperature in vascularized tissues independent of tissue composition. Temperature monitoring of live tissue is an important technique that provides feedback information needed for guidance of thermal therapies, such as laser interstitial thermotherapy, high-intensity focused ultrasound, radio frequency ablation, and cryoablation. 1-3 Temperature readings collected in real time around the treated areas help warranting safety and efficiency of the therapeutic procedure. 4 Noninvasive temperature monitoring is unanimously preferred among the clinicians, especially when there are crucial requirements to minimize collateral thermal damage to the adjacent normal tissues and zones of innervation. Several imaging and sensing modalities have been proposed for noninvasive temperature monitoring during thermal therapies, including ultrasound imaging, magnetic resonance imaging, and optoacoustic (photoacoustic) imaging and sensing. [5][6][7] The potential advantages of optoacoustic temperature imaging techniques reside in enhanced spatial resolution, temperature sensitivity, and faster data acquisition. [8][9][10] During the past decade, optoacoustic imaging has attracted significant attention from researchers and clinicians due to its success in a variety of biomedical applications that involve high resolution deep tissue imaging of optical absorbers (blood, water, and near infrared contrast agents) unattainable with other modalities. [11][12][13] The premium quality of optoacoustic images, as compared to other imagin...

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“…21,22 Given the wide-ranging applicability of HIFU, numerous extracorporeal and intracorporeal (e.g. transrectal, transuretral, intravascular, interstitial etc.)…”

Section: Mri-guided Focused Ultrasound Surgery Principles and Technomentioning

confidence: 99%

MRI-guided focused ultrasound surgery in musculoskeletal diseases: the hot topics

Bazzocchi¹,

Napoli²,

Sacconi³

et al. 2016

BJR

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MRI-guided focused ultrasound surgery (MRgFUS) is a minimally invasive treatment guided by the most sophisticated imaging tool available in today's clinical practice. Both the imaging and therapeutic sides of the equipment are based on non-ionizing energy. This technique is a very promising option as potential treatment for several pathologies, including musculoskeletal (MSK) disorders. Apart from clinical applications, MRgFUS technology is the result of long, heavy and cumulative efforts exploring the effects of ultrasound on biological tissues and function, the generation of focused ultrasound and treatment monitoring by MRI. The aim of this article is to give an updated overview on a "new" interventional technique and on its applications for MSK and allied sciences

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Integrated ultrasound and magnetic resonance imaging for simultaneous temperature and cavitation monitoring during focused ultrasound therapies

Cited by 64 publications

References 79 publications

Experimental demonstration of passive acoustic imaging in the human skull cavity using CT‐based aberration corrections

Experimental demonstration of passive acoustic imaging in the human skull cavity using CT‐based aberration corrections

Red blood cell as a universal optoacoustic sensor for non-invasive temperature monitoring

MRI-guided focused ultrasound surgery in musculoskeletal diseases: the hot topics

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