This work was supported by the National Institutes of Health (R01-EB014496). The authors would like to thank Iason Apostolakis for his contribution to the experiments.

Ce protocole a été approuvé par le soin et l&#39;utilisation des animaux Commission institutionnelle de l&#39;Université Columbia. Tout l&#39;acquisition et le traitement des données ont été effectuées en utilisant l&#39;environnement Matlab. 1. expérimental <ol><li> Dégazer un ex vivo canine échantillon de foie pendant 90 min. Mettez l&#39;échantillon de foie dans un réservoir rempli d&#39;dégazé Phosphate Buffered Solution (Figure 1). Fixer l&#39;échantillon de foie sur un absorbeur acoustique avec des aiguilles aux extrémités du foie. </li><li> Insérez un 64 élément, 0,32 mm hauteur, 2,5 MHz fréquence centrale réseau phasé (imagerie) à travers un trou circulaire situé dans le centre d&#39;un réseau hémisphérique transducteur HIFU 93-élément (thérapeutique) à 4,5 MHz fréquence centrale, 70 mm de profondeur focale et 1,7 mm x 0,4 mm de taille focal 11. Alignez les deux transducteurs co-axialement et fixer le transducteur d&#39;imagerie dans le transducteur thérapeutique avec vis de réglage. <ol><li> Couvrir le transducteur HIFU avec AVolume contrôlée membrane de polyuréthane remplie d&#39;eau qui coule dégazé pour le refroidir. Monter la sonde sur un 3-D positionneur commandé par ordinateur. </li></ol></li><li> Connecter le transducteur HIFU à un générateur de fonction 25 Hz envoi d&#39;une forme d&#39;onde sinusoïdale modulée en amplitude à 500 mV d&#39;amplitude maximale. Connecter le transducteur d&#39;imagerie à ultrasons d&#39;un système entièrement programmable à l&#39;aide du logiciel Matlab. Note: Un logiciel associé au système à l&#39;aide d&#39;ultrasons et l&#39;environnement Matlab doit être installé sur l&#39;ordinateur connecté au système. Un amplificateur 50 dB RF et un réseau d&#39;adaptation doit être placé entre le transducteur HIFU et le générateur de fonction pour amplifier respectivement la puissance et adapter l&#39;impédance. </li><li> Créer une grille polaire, en utilisant Matlab, en commençant à 50 mm de la surface de la matrice et de 40 mm de profondeur dans la direction radiale d&#39;un pas de 9,625 um spatiale et de 90 ° dans la direction azimutale avec 128 lignes et dont l&#39;origine est la focus de l&#39;onde divergente. Définir la source de l&#39;onde divergente 10,24 mm (la moitié de la taille de l&#39;ouverture) derrière la surface de la matrice et centrée dans la direction latérale. <ol><li> Créer une grille cartésienne, en utilisant Matlab, en commençant à 50 mm de la surface de la matrice et de 40 mm de profondeur dans la direction axiale avec un pas spatial de 9,625 um et 20 mm de largeur dans la direction latérale de 64 lignes pour l&#39;onde plane. Définir la source de l&#39;onde plane sur la surface de la matrice. Pour chaque grille, calculer le temps à partir de la source de chaque point de la grille et à l&#39;arrière de chaque élément de la matrice. </li></ol></li><li> Entrez &quot;ReconMat_DW&quot; pour faire diverger imagerie d&#39;onde ou &quot;ReconMat_PW&quot; pour l&#39;imagerie par onde plane dans la fenêtre de commande Matlab et appuyez sur &quot;Entrée&quot; pour créer une matrice de reconstruction associée à un algorithme de retard et sommation standard pour chaque grille. Appliquer l&#39;algorithme de retard et sommation à chaque vecteur de la base standard et récupérer les élémen non-zérosts de la matrice résultante 11. Allouer les éléments non nuls obtenus à partir de la matrice résultante de la matrice creuse à l&#39;endroit correspondant. Enregistrer la matrice de reconstruction sur le disque dur de l&#39;ordinateur. Remarque: Le divergente et les méthodes d&#39;ondes planes utilisent deux matrices distinctes de reconstruction. <ol><li> Cast la matrice de reconstruction d&#39;une matrice de GPU. Entrez &quot;SetUpP4_2Flash_4B_streaming_DW&quot; pour faire diverger imagerie d&#39;onde ou &quot;SetUpP4_2Flash_4B_streaming_PW&quot; pour l&#39;imagerie par onde plane dans la fenêtre de commande Matlab et appuyez sur &quot;Entrée&quot; pour créer un fichier de configuration pour l&#39;acquisition de données de canal à ultrasons en utilisant le script associé avec le réseau phasé et fournies par le fabricant de l&#39;échographe. Nommez le fichier de configuration &quot;P4-2Flash_DivergingWave.mat&quot; pour faire diverger imagerie des vagues et &quot;P4-2Flash_PlaneWave.mat&quot; pour l&#39;imagerie d&#39;onde plane. Note: Un logiciel commercial doit être installé sur l&#39;ordinateur to lancer la reconstruction matrice creuse à une matrice de GPU. </li></ol></li><li> Synchroniser le système à ultrasons avec le générateur de fonction à l&#39;aide d&#39;un déclencheur externe de sorte que l&#39;acquisition de données échographiques de cadence élevée du foie commence en même temps que HIFU. </li><li> Ouvrez Matlab. Exécutez le script de configuration &quot;SetUpP4_2Flash_4B.m&quot; fournies par le fabricant du système d&#39;échographie d&#39;utiliser l&#39;imagerie en mode B. Nommez le fichier de configuration créé: &quot;P4-2Flash_4B_Bmode.mat&quot;. Utilisez la commande &quot;VSX&quot; et quand &quot;Nom du fichier .mat à traiter:&quot; est invité, entrez le nom du fichier de configuration &quot;P4-2Flash_4B_Bmode.mat&quot;. Déplacez les deux transducteurs et utilisez l&#39;affichage en mode B qui est apparu sur l&#39;écran d&#39;ordinateur pour les positionner dans la région ciblée du foie à l&#39;ablation. Cibler une région d&#39;environ 1 cm sous la surface du foie pour éviter une forte atténuation ultrasonore due à l&#39;absorption. Enregistrer une image classique en mode B du foie sur l&#39;ordinateur. Note:Ici nous avons effectué des ablations HIFU à 11 endroits différents dans deux échantillons de foie en déplaçant les transducteurs avec le positionneur 3-D pour chaque ablation. </li></ol> 2. Ultrason d&#39;acquisition de données <ol><li> Ouvrez Matlab. Utilisez la commande &quot;VSX&quot; et quand &quot;Nom du fichier .mat à traiter:&quot; est invité, entrez le nom du fichier de configuration &quot;P4-2Flash_DivergingWave.mat&quot; pour faire diverger imagerie d&#39;onde ou &quot;P4-2Flash_PlaneWave.mat&quot; pour onde plane imagerie. Démarrez le HIFU et l&#39;appliquer pendant 2min de la région ciblée. </li><li> Acquérir les données de canal RF à 1000 images par seconde pendant 2 min à l&#39;aide des ondes divergentes. Alternativement, acquérir les données de canal RF à 1000 images par seconde pendant 2 min en utilisant des ondes planes. </li><li> Transférer les données vers un ordinateur hôte toutes les 200 trames via un câble PCI Express. Sinon, pour le streaming en temps réel, d&#39;acquérir les données de canal RF à 167 images par seconde pendant 2 min à l&#39;aide des ondes planes et transfer les données à un ordinateur hôte tous les 2 cadres. Remarque: Les méthodes d&#39;imagerie avec jeu de 200 images fournit une haute résolution temporelle dans chaque jeu, mais créer des écarts entre chaque série et est approprié pour le traitement hors ligne. La méthode d&#39;imagerie à 167 fps avec une résolution temporelle inférieure, mais ne crée pas de lacunes à travers toute la durée de l&#39;ablation et est approprié pour le streaming en temps réel. </li><li> Fonte de la matrice de données de canal RF à une seule matrice de précision GPU avec Matlab. Multiplier la matrice de données de canal RF par la matrice de reconstruction pour obtenir les données RF 11 reconstruits. </li></ol> 3. Déplacement Imaging <ol><li> Créer un Butterworth filtre passe-bas 6 e de commande à 4 MHz fréquence de coupure en utilisant le System Toolbox DSP de Matlab. Appliquer ce filtre passe-bas pour les données RF reconstruits pour filtrer la composante 4,5 MHz HIFU. </li><li> Estimer le déplacement axial entre les images consécutives en utilisant 1-D normalisée corrélation croiséeavec une longueur 3.1mm-fenêtre et 90% de recouvrement. </li><li> Créer un Butterworth filtre passe-bas 6 e de l&#39;ordre à 100 Hz fréquence de coupure en utilisant le System Toolbox DSP de Matlab. Appliquer ce filtre passe-bas pour les données de déplacement temporel utilisant Matlab pour récupérer la composante de fréquence de 50 Hz-oscillatoire. </li><li> Définir une région d&#39;intérêt (ROI) sous la région focale à -6 dB (1,7 x 0,4 mm dans de l&#39;eau) et situé à 70 mm de la surface du transducteur. Extraire les données de déplacement dans ce ROI. Estimer le déplacement rapport signal sur bruit (SNR d) à la région focale après 2 min de l&#39;ablation comme le rapport entre le déplacement moyenne et l&#39;écart type du déplacement dans le ROI. </li><li> Extraire le signal de déplacement temporel de 50 Hz à la mise au point à partir des données de la matrice de déplacement. Convertir le signal de déplacement temporel au foyer en un son audible en utilisant Matlab. </li></ol>

<ol>
	<li>Al-Bataineh, O., Jenne, J., Huber, P. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Clinical+and+future+applications+of+high+intensity+focused+ultrasound+in+cancer.">Clinical and future applications of high intensity focused ultrasound in cancer.</a> Cancer Treat Rev. 38, 346-353 (2012).</li><li>Dewhirst, M. W., Viglianti, B. L., Lora-Michiels, M., Hanson, M., Hoopes, P. J. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Basic+principles+of+thermal+dosimetry+and+thermal+thresholds+for+tissue+damage+from+hyperthermia.">Basic principles of thermal dosimetry and thermal thresholds for tissue damage from hyperthermia.</a> Int J Hyperthermia. 19, 267-294 (2003).</li><li>Napoli, A., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=MR-guided+high-intensity+focused+ultrasound:+current+status+of+an+emerging+technology.">MR-guided high-intensity focused ultrasound: current status of an emerging technology.</a> Cardiovasc Intervent Radiol. 36, 1190-1203 (2013).</li><li>Gudur, M. S., Kumon, R. E., Zhou, Y., Deng, C. X. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=High-frequency+rapid+B-mode+ultrasound+imaging+for+real-time+monitoring+of+lesion+formation+and+gas+body+activity+during+high-intensity+focused+ultrasound+ablation.">High-frequency rapid B-mode ultrasound imaging for real-time monitoring of lesion formation and gas body activity during high-intensity focused ultrasound ablation.</a> IEEE Trans Ultrason Ferroelectr Freq Control. 59, 1687-1699 (2012).</li><li>Jensen, C. R., Cleveland, R. O., Coussios, C. C. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Real-time+temperature+estimation+and+monitoring+of+HIFU+ablation+through+a+combined+modeling+and+passive+acoustic+mapping+approach.">Real-time temperature estimation and monitoring of HIFU ablation through a combined modeling and passive acoustic mapping approach.</a> Phys Med Biol. 58, 5833-5850 (2013).</li><li>Mariani, A., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Real+time+shear+waves+elastography+monitoring+of+thermal+ablation:+in+vivo+evaluation+in+pig+livers.">Real time shear waves elastography monitoring of thermal ablation: in vivo evaluation in pig livers.</a> J Surg Res. 188, 37-43 (2014).</li><li>Bing, K. F., Rouze, N. C., Palmeri, M. L., Rotemberg, V. M., Nightingale, K. R. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Combined+ultrasonic+thermal+ablation+with+interleaved+ARFI+image+monitoring+using+a+single+diagnostic+curvilinear+array:+a+feasibility+study.">Combined ultrasonic thermal ablation with interleaved ARFI image monitoring using a single diagnostic curvilinear array: a feasibility study.</a> Ultrason Imaging. 33, 217-232 (2011).</li><li>Athanasiou, A., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Breast+lesions:+quantitative+elastography+with+supersonic+shear+imaging--preliminary+results.,+Radiology.">Breast lesions: quantitative elastography with supersonic shear imaging--preliminary results., Radiology.</a> 256, 297-303 (2010).</li><li>Maleke, C., Konofagou, E. 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The authors declare that they have no competing financial interests.

Surveillance en temps réel des lésions HIFU est important pour assurer la livraison appropriée et efficace lésion. Comme les formes de lésion, le tissu se raidit et son amplitude de mouvement sous excitation diminue. Application HIFU dans une région des résultats de tissu en une force de rayonnement acoustique qui induit un déplacement des tissus. La variation relative de déplacement est un substitut de la variation relative de la rigidité des tissus. Cette technique présente l&#39;avantage de contrôler lés...

High Intensity Focused Ultrasound (HIFU) is a technique that generates temperature elevation at the focal region and can be used to ablate cancerous tissue 1. Temperature elevation at the focus causes thermal lesions in the tissue 2. In order to avoid overtreating a region and to reduce treatment duration, it is imperative to reliably monitor the ablation. Magnetic resonance-guided focused ultrasound (MRgFUS) is the main technique used in clinic to guide and monitor HIFU treatment 3. MRI provides high spatial resolution images of the treated region with tissue displacement or thermal dose but has a frame rate of 0.1-1 Hz and is costly. Several ultrasound-based techniques such as B-mode imaging 4, passive acoustic mapping 5, shear wave imaging 6 and acoustic radiation force impulse 7 have been developed to guide and monitor thermal ablation. However, B-mode imaging and passive acoustic mapping do not provide imaging of mechanical properties of the ablated region which is useful to the operator to improve lesion delivery. 
Shear wave imaging and acoustic radiation force impulse can both characterize the elasticity of the tissue by measuring acoustic radiation force-induced displacements 7,8. However, in both methods, the HIFU treatment is typically interrupted to monitor the ablation. Our group has developed a technique called Harmonic Motion Imaging for Focus Ultrasound (HMIFU) which can monitor the HIFU treatment with ultrasound without stopping the ablation9,10. Briefly, a HIFU transducer sends an amplitude-modulated wave to the region to ablate while simultaneously generating an oscillatory motion in the focal region. A co-axially aligned ultrasound transducer is used to image this oscillation. The magnitude of the induced motion is related to the stiffness of the tissue.
To ensure proper lesion delivery, the temporal resolution of real-time monitoring is of key interest in ablation guidance. Recently, our group has shown real-time streaming of displacement at a frame rate up to 15 Hz, imaged with diverging waves in a narrow field of view and using a fast image reconstruction method 11. Several beamforming techniques can be used to image the displacements. A large field of view can be obtained with diverging wave imaging by changing the delay profile but the axial direction is not aligned with the HIFU beam on the lateral regions and the wave is attenuated due to geometric spreading in the lateral direction, which can affect the quality of the displacement estimation. In contrast, the lateral field of view for plane wave is upper bounded by the active aperture but the axial direction is aligned with the HIFU beam at the focus and there is no geometric spreading in the lateral direction. Depending on the type of application, one or the other imaging method can be selected. The objectives of this protocol are to show how plane wave imaging can provide real-time streaming of displacements images using HMIFU during ablation and to compare the quality of the motion estimation between diverging and plane wave imaging.

<table border="0" cellpadding="0" cellspacing="0">
	<colgroup>
		<col />
		<col />
		<col />
		<col />
	</colgroup>
	<tbody>
		<tr>
			<td>P4-2 Phased array</td>
			<td>ATL</td>
			<td></td>
			<td></td>
		</tr>
		<tr>
			<td>H-178 HIFU transducer</td>
			<td>Sonic Concepts</td>
			<td></td>
			<td></td>
		</tr>
		<tr>
			<td>3-D positioner</td>
			<td>Velmex Inc.</td>
			<td></td>
			<td></td>
		</tr>
		<tr>
			<td>AT33522A function generator</td>
			<td>Agilent Technologies</td>
			<td></td>
			<td></td>
		</tr>
		<tr>
			<td>V-1 ultrasound system</td>
			<td>Verasonics</td>
			<td></td>
			<td></td>
		</tr>
		<tr>
			<td>3100L RF amplifier</td>
			<td>ENI</td>
			<td></td>
			<td></td>
		</tr>
		<tr>
			<td>Matching network</td>
			<td>Sonic Concepts</td>
			<td></td>
			<td></td>
		</tr>
		<tr>
			<td>Degasing system</td>
			<td>Sonic Concepts</td>
			<td></td>
			<td></td>
		</tr>
		<tr>
			<td>Programming software</td>
			<td>Matlab</td>
			<td></td>
			<td></td>
		</tr>
		<tr>
			<td>Jacket software package</td>
			<td>Accelereyes</td>
			<td></td>
			<td></td>
		</tr>
	</tbody>
</table>

real-time monitoring of high intensity focused ultrasound (hifu) ablation of in vitro canine livers using harmonic motion imaging for focused ultrasound (hmifu)

Mouvement harmonique Imaging pour ultrasons focalisés (HMIFU) est une technique qui peut effectuer et de surveiller ultrasons focalisés de haute intensité (HIFU) ablation. Un mouvement oscillatoire est généré au foyer d&#39;une fréquence centrale transducteur HIFU 93-élément et 4,5 MHz en appliquant un signal modulé en amplitude à 25 Hz en utilisant un générateur de fonction. Un transducteur d&#39;imagerie 64 et 2,5 MHz élément de pression de crête est 68kPa confocale placée au centre du transducteur HIFU pour acquérir les fréquences radioélectriques (RF) des données de canal. Dans ce protocole, la surveillance en temps réel de l&#39;ablation thermique utilisant HIFU avec une puissance acoustique de 7 W sur foies canins in vitro est décrite. HIFU traitement est appliqué sur le tissu pendant 2 min et la région ablation est imagé en temps réel en utilisant l&#39;imagerie divergentes ou onde plane jusqu&#39;à 1000 images / seconde. La matrice de données de canal RF est multipliée par une matrice creuse pour la reconstruction de l&#39;image. Le champ reconstruit de vue est de 90 ° pour wa divergentve et 20 mm pour l&#39;imagerie d&#39;onde plane et les données sont échantillonnées à 80 MHz. La reconstruction est exécutée sur un Graphical Processing Unit (GPU) afin de l&#39;image en temps réel à un taux de 4,5 trame d&#39;affichage. 1-D normalisée de corrélation croisée des données reconstruit haute fréquence est utilisé pour estimer les déplacements axiaux dans la région focale. L&#39;ampleur du déplacement de crête à crête à la profondeur focale diminue au cours de l&#39;ablation thermique qui dénote la rigidification du tissu en raison de la formation d&#39;une lésion. Le déplacement rapport signal sur bruit (SNR d) à la zone de convergence pour onde plane était 1,4 fois plus élevé que pour la vague divergente montrant que l&#39;imagerie d&#39;onde plane semble produire un meilleur déplacement des cartes de qualité pour HMIFU que divergentes imagerie d&#39;onde.

Le streaming en temps réel des IHM déplacement durant HIFU ablation peut être obtenu en utilisant l&#39;imagerie à ondes divergents et avion. La figure 2 est une capture d&#39;écran de la vidéo montrant affichage en temps réel de la force de rayonnement acoustique de déplacement induit utilisant l&#39;imagerie par onde plane in vitro canines foies en cours de traitement HIFU . Les déplacements sont diffusées en temps réel sur l&#39;écran de l&#39;ordinateur à un taux de tr...

Watch this Scientific Journal Video about Real-time Monitoring of High Intensity Focused Ultrasound HIFU Ablation of In Vitro Canine Livers Using Harmonic Motion Imaging for Focused Ultrasound HMIFU a

Real-time Monitoring of High Intensity Focused Ultrasound HIFU Ablation of In Vitro Canine Livers Using Harmonic Motion Imaging for Focused Ultrasound HMIFU

This article describes real-time monitoring of HIFU ablation in canine liver with high frame rate ultrasound imaging using diverging and plane wave imaging. Harmonic Motion Imaging for Focused Ultrasound is used to image the decrease of acoustic radiation force induced displacement in the ablated region.

Suivi en temps réel de haute intensité ultrasons focalisés (HIFU) Ablation de<em&gt; In Vitro</em&gt; Canine Livers Utilisation mouvement harmonique Imaging pour ultrasons focalisés (HMIFU)

Harmonic Motion Imaging for Focused Ultrasound (HMIFU) is a technique that can perform and monitor high-intensity focused ultrasound (HIFU) ablation. An ...

real-time-monitoring-high-intensity-focused-ultrasound-hifu-ablation

Research

JoVE Journal

Bioengineering

Real-time Monitoring of High Intensity Focused Ultrasound (HIFU) Ablation of In Vitro Canine Livers Using Harmonic Motion Imaging for Focused Ultrasound (HMIFU)

9.9K vues.  Columbia University. This article describes real-time monitoring of HIFU ablation in canine liver with high frame rate ultrasound imaging using diverging and plane wave imaging. Harmonic Motion Imaging for Focused Ultrasound is used to image the decrease of acoustic radiation force induced displacement in the ablated region.

Vidéo: Real-time Monitoring of High Intensity Focused Ultrasound HIFU Ablation of In Vitro Canine Livers Using Harmonic Motion Imaging for Focused Ultrasound HMIFU

Contrast Ultrasound Targeted Treatment of Gliomas in Mice via Drug-Bearing Nanoparticle Delivery and Microvascular Ablation

We are developing minimally-invasive contrast agent microbubble based therapeutic approaches in which the permeabilization and/or ablation of the microvasculature are controlled by varying ultrasound pulsing parameters.  Specifically, we are testing whether such approaches may be used to treat malignant brain tumors through drug delivery and microvascular ablation.  Preliminary studies have been performed to determine whether targeted drug-bearing nanoparticle delivery can be facilitated by the ultrasound mediated destruction of "composite" delivery agents comprised of 100nm poly(lactide-co-glycolide) (PLAGA) nanoparticles that are adhered to albumin shelled microbubbles. We denote these agents as microbubble-nanoparticle composite agents (MNCAs). When targeted to subcutaneous C6 gliomas with ultrasound, we observed an immediate 4.6-fold increase in nanoparticle delivery in MNCA treated tumors over tumors treated with microbubbles co-administered with nanoparticles and a 8.5 fold increase over non-treated tumors. Furthermore, in many cancer applications, we believe it may be desirable to perform targeted drug delivery in conjunction with ablation of the tumor microcirculation, which will lead to tumor hypoxia and apoptosis. To this end, we have tested the efficacy of non-theramal cavitation-induced microvascular ablation, showing that this approach elicits tumor perfusion reduction, apoptosis, significant growth inhibition, and necrosis. Taken together, these results indicate that our ultrasound-targeted approach has the potential to increase therapeutic efficiency by creating tumor necrosis through microvascular ablation and/or simultaneously enhancing the drug payload in gliomas.

Insonation of microbubbles is a promising strategy for tumor ablation at reduced time-averaged acoustic powers, as well as for the targeted delivery of therapeutics. The purpose of the present study is to develop low duty cycle ultrasound pulsing strategies and nanocarriers to maximize non-thermal microvascular ablation and payload delivery to subcutaneous C6 gliomas.

L&#39;échographie de contraste ciblées traitement des gliomes chez la souris via la livraison de drogue nanoparticules-Bearing et l&#39;ablation microvasculaire

We are developing minimally-invasive contrast agent microbubble based therapeutic approaches in which the permeabilization and/or ablation of the ...

Recherche

Bio-ingénierie

Decellularization and Recellularization of Whole Livers

The liver is a complex organ which requires constant perfusion for delivery of nutrients and oxygen and removal of waste in order to survive1. Efforts to recreate or mimic the liver microstructure with grounds up approach using tissue engineering and microfabrication techniques have not been successful so far due to this design challenge. In addition, synthetic biomaterials used to create scaffolds for liver tissue engineering applications have been limited in inducing tissue regeneration and repair in large part due to the lack of specific cell binding motifs that would induce the proper cell functions2. Decellularized native tissues such blood vessels3and skin4on the other hand have found many applications in tissue engineering, and have provided a practical solution to some of the challenges. The advantage of decellularized native matrix is that it retains, to an extent, the original composition, and the microstructure, hence enhancing cell attachment and reorganization5.
In this work we describe the methods to perform perfusion-decellularization of the liver, such that an intact liver bioscaffold that retains the structure of major blood vessels is obtained. Further, we describe methods to recellularize these bioscaffolds with adult primary hepatocytes, creating a liver graft that is functional in vitro, and has the vessel access necessary for transplantation in vivo.

Perfusion decellularization is a novel technique to produce whole liver scaffolds that retains the organ's extracellular matrix composition and microarchitecture. Herein, the method of preparing whole organ scaffolds using perfusion decellularization and subsequent repopulation with hepatocytes is described. Functional and transplantable liver grafts can be generated using this technique.

Décellularisation et Recellularization des foies entiers

The liver is a complex organ which requires constant perfusion for delivery of nutrients and oxygen and removal of waste in order to survive1. Efforts to ...

Induction of Adhesion-dependent Signals Using Low-intensity Ultrasound

In multicellular organisms, cell behavior is dictated by interactions with the extracellular matrix. Consequences of matrix-engagement range from regulation of cell migration and proliferation, to secretion and even differentiation. The signals underlying each of these complex processes arise from the molecular interactions of extracellular matrix receptors on the surface of the cell. Integrins are the prototypic receptors and provide a mechanical link between extracellular matrix and the cytoskeleton, as well as initiating some of the adhesion-dependent signaling cascades. However, it is becoming increasingly apparent that additional transmembrane receptors function alongside the integrins to regulate both the integrin itself and signals downstream. The most elegant of these examples is the transmembrane proteoglycan, syndecan-4, which cooperates with &alpha;5&beta;1-integrin during adhesion to fibronectin. In vivo models demonstrate the importance of syndecan-4 signaling, as syndecan-4-knockout mice exhibit healing retardation due to inefficient fibroblast migration1,2. In wild-type animals, migration of fibroblasts toward a wound is triggered by the appearance of fibronectin that leaks from damaged capillaries and is deposited by macrophages in injured tissue. Therefore there is great interest in discovering strategies that enhance fibronectin-dependent signaling and could accelerate repair processes.
The integrin-mediated and syndecan-4-mediated components of fibronectin-dependent signaling can be separated by stimulating cells with recombinant fibronectin fragments. Although integrin engagement is essential for cell adhesion, certain fibronectin-dependent signals are regulated by syndecan-4. Syndecan-4 activates the Rac1 protrusive signal3, causes integrin redistribution1, triggers recruitment of cytoskeletal molecules, such as vinculin, to focal adhesions4, and thereby induces directional migration3. We have looked for alternative strategies for activating such signals and found that low-intensity pulsed ultrasound (LIPUS) can mimic the effects of syndecan-4 engagement5. In this protocol we describe the method by which 30 mW/cm2, 1.5 MHz ultrasound, pulsed at 1 kHz (Fig. 1) can be applied to fibroblasts in culture (Fig. 2) to induce Rac1 activation and focal adhesion formation. Ultrasound stimulation is applied for a maximum of 20 minutes, as this combination of parameters has been found to be most efficacious for acceleration of clinical fracture repair6. The method uses recombinant fibronectin fragments to engage &alpha;5&beta;1-integrin, without engagement of syndecan-4, and requires inhibition of protein synthesis by cycloheximide to block deposition of additional matrix by the fibroblasts., The positive effect of ultrasound on repair mechanisms is well documented7,8, and by understanding the molecular effect of ultrasound in culture we should be able to refine the therapeutic technique to improve clinical outcomes.

This protocol describes the stimulation of cultured fibroblasts with low-intensity pulsed ultrasound, which drives focal adhesion formation and Rac1 activation by mimicking engagement of the transmembrane matrix receptor, syndecan-4. This approach allows investigation of a successful clinical technique at the cellular level, thereby providing opportunities for refinement of the therapy.

L&#39;induction de signaux d&#39;adhésion dépendant de l&#39;aide ultrasons à faible intensité

In multicellular organisms, cell behavior is dictated by interactions with the extracellular matrix. Consequences of matrix-engagement range from ...

Wideband Optical Detector of Ultrasound for Medical Imaging Applications

Optical sensors of ultrasound are a promising alternative to piezoelectric techniques, as has been recently demonstrated in the field of optoacoustic imaging. In medical applications, one of the major limitations of optical sensing technology is its susceptibility to environmental conditions, e.g. changes in pressure and temperature, which may saturate the detection. Additionally, the clinical environment often imposes stringent limits on the size and robustness of the sensor. In this work, the combination of pulse interferometry and fiber-based optical sensing is demonstrated for ultrasound detection. Pulse interferometry enables robust performance of the readout system in the presence of rapid variations in the environmental conditions, whereas the use of all-fiber technology leads to a mechanically flexible sensing element compatible with highly demanding medical applications such as intravascular imaging. In order to achieve a short sensor length, a pi-phase-shifted fiber Bragg grating is used, which acts as a resonator trapping light over an effective length of 350 &#181;m. To enable high bandwidth, the sensor is used for sideway detection of ultrasound, which is highly beneficial in circumferential imaging geometries such as intravascular imaging. An optoacoustic imaging setup is used to determine the response of the sensor for acoustic point sources at different positions.

Optical detection of ultrasound is impractical in many imaging scenarios because it often requires stable environmental conditions. We demonstrate an optical technique for ultrasound sensing in volatile environments with miniaturization and sensitivity levels appropriate for optoacoustic imaging in restrictive scenarios, e.g. intravascular applications.

Wideband détecteur optique des ultrasons pour les applications d&#39;imagerie médicale

Optical sensors of ultrasound are a promising alternative to piezoelectric techniques, as has been recently demonstrated in the field of optoacoustic ...

Universal Hand-held Three-dimensional Optoacoustic Imaging Probe for Deep Tissue Human Angiography and Functional Preclinical Studies in Real Time

The exclusive combination of high optical contrast and excellent spatial resolution makes optoacoustics (photoacoustics) ideal for simultaneously attaining anatomical, functional and molecular contrast in deep optically opaque tissues. While enormous potential has been recently demonstrated in the application of optoacoustics for small animal research, vast efforts have also been undertaken in translating this imaging technology into clinical practice. We present here a newly developed optoacoustic tomography approach capable of delivering high resolution and spectrally enriched volumetric images of tissue morphology and function in real time. A detailed description of the experimental protocol for operating with the imaging system in both hand-held and stationary modes is provided and showcased for different potential scenarios involving functional and molecular studies in murine models and humans. The possibility for real time visualization in three dimensions along with the versatile handheld design of the imaging probe make the newly developed approach unique among the pantheon of imaging modalities used in today&#8217;s preclinical research and clinical practice.

We provide herein a detailed description of the experimental protocol for imaging with a newly developed hand-held optoacoustic (photoacoustic) system for three-dimensional functional and molecular imaging in real time. The demonstrated powerful performance and versatility may define new application areas of the optoacoustic technology in preclinical research and clinical practice.

Universal à main en trois dimensions optoacoustique sonde d&#39;imagerie pour Deep Tissue angiographie humain et des études précliniques fonctionnels en temps réel

The exclusive combination of high optical contrast and excellent spatial resolution makes optoacoustics (photoacoustics) ideal for simultaneously ...

Eye Irritation Test (EIT) for Hazard Identification of Eye Irritating Chemicals using Reconstructed Human Cornea-like Epithelial (RhCE) Tissue Model

To comply with the Seventh Amendment to the EU Cosmetics Directive and EU REACH legislation, validated non-animal alternative methods for reliable and accurate assessment of ocular toxicity in man are needed. To address this need, we have developed an eye irritation test (EIT) which utilizes a three dimensional reconstructed human cornea-like epithelial (RhCE) tissue model that is based on normal human cells. The EIT is able to separate ocular&#160;irritants and corrosives (GHS Categories 1 and 2 combined) and those that do not require labeling (GHS No Category). The test utilizes two separate protocols, one designed for liquid chemicals and a second, similar protocol for solid test articles. The EIT prediction model uses a single exposure period (30 min for liquids, 6 hr for solids) and a single tissue viability cut-off (60.0% as determined by the MTT assay). Based on the results for 83 chemicals (44 liquids and 39 solids) EIT achieved 95.5/68.2/ and 81.8% sensitivity/specificity and accuracy (SS&#38;A) for liquids, 100.0/68.4/ and 84.6% SS&#38;A for solids, and 97.6/68.3/ and 83.1% for overall SS&#38;A. The EIT will contribute significantly to classifying the ocular irritation potential of a wide range of liquid and solid chemicals without the use of animals to meet regulatory testing requirements. The EpiOcular EIT method was implemented in 2015 into the OECD Test Guidelines as TG 492.

Eye Irritation Test EIT for Hazard Identification of Eye Irritating Chemicals using Reconstructed Human Cornea-like Epithelial RhCE Tissue Model

We have developed an eye irritation test which utilizes a three dimensional reconstructed human cornea-like epithelial (RhCE) tissue model. The test is able to discriminate between ocular irritant and corrosive materials (GHS Categories 1 and 2 combined) and those that do not require labeling (GHS No Category).

Irritation des yeux Test (IET) pour l&#39;identification des dangers des produits chimiques irritants oculaires utilisant épithélial (RHCE) Tissue modèle reconstruit humain Cornea-like

To comply with the Seventh Amendment to the EU Cosmetics Directive and EU REACH legislation, validated non-animal alternative methods for reliable and ...

Real Time Monitoring of Intracellular Bile Acid Dynamics Using a Genetically Encoded FRET-based Bile Acid Sensor

F&#246;rster Resonance Energy Transfer (FRET) has become a powerful tool for monitoring protein folding, interaction and localization in single cells. Biosensors relying on the principle of FRET have enabled real-time visualization of subcellular signaling events in live cells with high temporal and spatial resolution. Here, we describe the application of a genetically encoded Bile Acid Sensor (BAS) that consists of two fluorophores fused to the farnesoid X receptor ligand binding domain (FXR-LBD), thereby forming a bile acid sensor that can be activated by a large number of bile acids species and other (synthetic) FXR ligands. This sensor can be targeted to different cellular compartments including the nucleus (NucleoBAS) and cytosol (CytoBAS) to measure bile acid concentrations locally. It allows rapid and simple quantitation of cellular bile acid influx, efflux and subcellular distribution of endogenous bile acids without the need for labeling with fluorescent tags or radionuclei. Furthermore, the BAS FRET sensors can be useful for monitoring FXR ligand binding. Finally, we show that this FRET biosensor can be combined with imaging of other spectrally distinct fluorophores. This allows for combined analysis of intracellular bile acid dynamics and i) localization and/or abundance of proteins of interest, or ii) intracellular signaling in a single cell.

We provide a detailed protocol to study bile acid dynamics in living cells using a genetically encoded BAS FRET sensor. This Bile Acid Sensor represents a unique tool to study (regulation of) bile acid transport and FXR activation in a wide range of cell types.

Surveillance en temps réel des intracellulaire des acides biliaires Dynamics en utilisant un capteur acides biliaires base-FRET codées génétiquement

F&#246;rster Resonance Energy Transfer (FRET) has become a powerful tool for monitoring protein folding, interaction and localization in single cells. ...

Proper Positioning and Restraint of a Rat Hind Limb for Focused High Resolution Imaging of Bone Micro-architecture Using In Vivo Micro-computed Tomography

The use of in vivo micro-computed tomography (&#181;CT) is a powerful tool which involves the non-destructive imaging of internal structures at high resolutions in live animal models. This allows for repeated imaging of the same rodent over time. This feature not only reduces the total number of rodents required in an experimental design and thereby reduces the inter-subject variation that can arise, but also allows researchers to assess longitudinal or life-long responses to an intervention. To acquire high quality images that can be processed and analyzed to more accurately quantify outcomes of bone micro-architecture, users of in vivo &#181;CT scanners must properly anesthetize the rat, and position and restrain the hind limb. To do this, it is imperative that the rat be anesthetized to a level of complete relaxation, and that pedal reflexes are lost. These guidelines may be modified for each individual rat, as the rate of isoflurane metabolism can vary depending on strain and body size. Proper technique for in vivo &#181;CT image acquisition enables accurate and consistent measurement of bone micro-architecture within and across studies.

Proper Positioning and Restraint of a Rat Hind Limb for Focused High Resolution Imaging of Bone Micro-architecture Using In Vivo Micro-computed Tomography

This paper instructs users of in vivo micro-computed tomography (&#181;CT) scanners how to anesthetize, correctly position and restrain the hind limb of a rat for minimal movement during high-resolution imaging of the tibia. The result is high quality images that can be processed to accurately quantify bone micro-architecture.

Le positionnement et la retenue d’une patte de Rat pour l’imagerie ciblée haute résolution des os à l’aide de la micro-architecture In Vivo Micro-computed Tomography

The use of in vivo micro-computed tomography (&#181;CT) is a powerful tool which involves the non-destructive imaging of internal structures at high ...

Hand-held Clinical Photoacoustic Imaging System for Real-time Non-invasive Small Animal Imaging

Translation of photoacoustic imaging into the clinic is a major challenge. Handheld real-time clinical photoacoustic imaging systems are very rare. Here, we report a combined photoacoustic and clinical ultrasound imaging system by integrating an ultrasound probe with light delivery for small animal imaging. We demonstrate this by showing sentinel lymph node imaging in small animals along with minimally invasive real-time needle guidance. A clinical ultrasound platform with access to raw channel data allows the integration of photoacoustic imaging leading to a handheld real-time clinical photoacoustic imaging system. Methylene blue was used for sentinel lymph node imaging at 675 nm wavelength. Additionally, needle guidance with dual modal ultrasound and photoacoustic imaging was shown using the imaging system. Depth imaging of up to 1.5 cm was demonstrated with a 10 Hz laser at a photoacoustic imaging frame rate of 5 frames per second.

A clinical handheld photoacoustic imaging system will be demonstrated for real-time non-invasive small animal imaging.

À main photoacoustique clinique, système d’imagerie pour l’imagerie animale petit Non invasif en temps réel

Translation of photoacoustic imaging into the clinic is a major challenge. Handheld real-time clinical photoacoustic imaging systems are very rare. Here, ...

Focused Ion Beam Lithography to Etch Nano-architectures into Microelectrodes

With advances in electronics and fabrication technology, intracortical microelectrodes have undergone substantial improvements enabling the production of sophisticated microelectrodes with greater resolution and expanded capabilities. The progress in fabrication technology has supported the development of biomimetic electrodes, which aim to seamlessly integrate into the brain parenchyma, reduce the neuroinflammatory response observed after electrode insertion and improve the quality and longevity of electrophysiological recordings. Here we describe a protocol to employ a biomimetic approach recently classified as nano-architecture. The use of focused ion beam lithography (FIB) was utilized in this protocol to etch specific nano-architecture features into the surface of non-functional and functional single shank intracortical microelectrodes. Etching nano-architectures into the electrode surface indicated possible improvements of biocompatibility and functionality of the implanted device. One of the benefits of using FIB is the ability to etch on manufactured devices, as opposed to during the fabrication of the device, facilitating boundless possibilities to modify numerous medical devices post-manufacturing. The protocol presented herein can be optimized for various material types, nano-architecture features, and types of devices. Augmenting the surface of implanted medical devices can improve the device performance and integration into the tissue.

We have shown that the etching of nano-architecture into intracortical microelectrode devices may reduce the inflammatory response and has the potential to improve electrophysiological recordings. The methods described herein outline an approach to etch nano-architectures into the surface of non-functional and functional single shank silicon intracortical microelectrodes.

Lithographie focalisée de faisceau d'ion à Etch Nano-architectures dans des microélectrodes

With advances in electronics and fabrication technology, intracortical microelectrodes have undergone substantial improvements enabling the production of ...