WO2014076674A2 - Réduction de fouillis d'échos en place pour imagerie photo-acoustique - Google Patents

Réduction de fouillis d'échos en place pour imagerie photo-acoustique Download PDF

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Publication number
WO2014076674A2
WO2014076674A2 PCT/IB2013/060206 IB2013060206W WO2014076674A2 WO 2014076674 A2 WO2014076674 A2 WO 2014076674A2 IB 2013060206 W IB2013060206 W IB 2013060206W WO 2014076674 A2 WO2014076674 A2 WO 2014076674A2
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varying
image
excitation
images
location
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WO2014076674A3 (fr
Inventor
Todd Nicholas ERPELDING
Haixin Ke
Hua Xie
Lihong Wang
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Koninklijke Philips NV
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Koninklijke Philips NV
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0093—Detecting, measuring or recording by applying one single type of energy and measuring its conversion into another type of energy
    • A61B5/0095—Detecting, measuring or recording by applying one single type of energy and measuring its conversion into another type of energy by applying light and detecting acoustic waves, i.e. photoacoustic measurements

Definitions

  • the present invention relates to photoacoustic imaging and, more particularly, to averaging photoacoustic images.
  • Photoacoustic (PA) imaging is a non-ionizing and noninvasive hybrid imaging technique that can measure strong optical absorption contrasts with high ultrasonic spatial resolution at depths beyond the optical diffusion limit. Both image resolution and depth are highly scalable with the ultrasonic frequency. Since ultrasonic scattering is 2-3 orders of magnitude less than optical scattering on the basis of per unit path length, photoacoustic imaging can break through the fundamental limitation of existing pure optical imaging. Photoacoustic imaging relies on the photoacoustic effect to generate pressure waves that can be detected by ultrasound array transducers. Typically, a short laser pulse illuminates tissue leading to optical absorption, rapid heating and thermoelastic expansion to produce pressure waves.
  • photoacoustic imaging is highly compatible with ultrasound imaging.
  • the same detection mechanism greatly simplifies spatial registration between photoacoustic and ultrasound images.
  • Photoacoustic imaging is an emerging modality that could expand the scope of diagnostic ultrasonography into new clinical applications, such as image-guided sentinel lymph node biopsy, breast cancer diagnosis, and therapy monitoring.
  • the preferred implementation for photoacoustic imaging is the so-called reflection mode, which is most similar to hand-held ultrasonography.
  • reflection mode photoacoustic imaging both the light source and the ultrasound transducer are placed in close proximity on the skin surface.
  • a typical photoacoustic transducer is designed with an optical fiber bundle bifurcated to flank both sides of the ultrasound array transducer. Photoacoustic waves are received by the ultrasound transducer in the same geometry as pulse-echo ultrasound.
  • Photoacoustic imaging extends the imaging depths beyond the optical diffusion limit while maintaining ultrasonic spatial resolution. It enables clinical applications at depths and/or spatial resolutions that would be impossible with pure optical imaging techniques.
  • background clutter signals that degrade image contrast.
  • One source of background clutter is from optical absorption near the skin surface (blood vessels, melanin), launching acoustic waves that are backscattered to the transducer from acoustic inhomogeneities in tissue.
  • Jaeger et al. describe a method for clutter reduction based on tissue shear deformation and motion-compensated signal averaging ("Improved Contrast Deep).
  • the Jaeger study presents a method that depends on tissue deformation and is therefore anatomy specific, unusable for example on the rib cage.
  • Axial deformation is an alternative proposed in the Jaeger study, and preferable in that coupling gel can be used, but is still anatomy specific. Both forms of deformation yield varying results clinician to clinician and instance to instance.
  • a medical image acquiring device repeatedly photoacoustically images an intracorporeal spatial location that is common image to image. This is done by varying the ultrasound transducer acquisition location, light excitation, or both, image to image so that averaging of the images serves to decorrelate background clutter that exists in the images, of the spatial location, individually.
  • a computer program embodied within a computer readable medium as described below, or, alternatively, embodied within a transitory, propagating signal has instructions executable by a processor for performing a plurality of acts, from among which is the act of: repeatedly photoacoustically imaging an intracorporeal spatial location that is common image to image, varying at least one of ultrasound transducer acquisition location, and light excitation, image to image so that averaging of the images serves to decorrelate background clutter that exists in the images, of said spatial location, individually.
  • a photoacoustic apparatus that has an array of multiple ultrasound transducer elements is configured for forming receiving apertures at different positions along the array and for, based on what is temporally a single pulse of light and based on imaging acquisition by ones of the apertures that is responsive to the pulse, performing spatial compounding to produce a photoacoustic frame from the single pulse.
  • Fig. 1 is a set of schematic diagrams of respectively an exemplary
  • photoacoustic medical image acquiring device and a particular embodiment, in accordance with the present invention
  • Fig. 2 is a schematic and conceptual diagram of another particular
  • Fig. 3 is a schematic diagram of a face view of an exemplary photoacoustic medical image acquiring device, with side views of different embodiments for the probe, in accordance with the present invention.
  • Fig. 1 depicts, by way of illustrative and non-limitative example, a photoacoustic (PA) medical image acquiring device 100.
  • the device 100 includes an imaging probe 102, such as an integrated photoacoustic -ultrasound imaging probe, and a processor 103. It further includes a pulsed light source (not shown), typically of pulse length less than 20 nanosecond (ns), such as a high-energy laser, for illuminating body tissue and exciting PA waves. Also included is an elongated light delivery system 104 extending from the light source to, and into, the imaging probe 102.
  • the light delivery system 104 includes an optical fiber bundle 106 and optionally, for example, optical components that couple light into the fiber optic bundle.
  • the probe 102 includes an ultrasound transducer 108, here implemented with a linear array or matrix array.
  • the probe 102 also includes a patient- interface surface 110, as part of its housing 112, for contacting a body 114 of a medical subject such as a patient, human or animal.
  • the patient- interface surface 110 has a light- emitting location 115.
  • the two bifurcated 116 legs of the fiber bundle 106 flank both elevational 118 sides of the transducer 108, and terminate near the patient-interface surface 110 in two, respective, spaced-apart excitation sources 120.
  • the fiber optic bundle 106 is made up of multiple sub-bundles arranged in parallel. The sub-bundles are each bifurcated 116, the parallel arrangement extending the legs laterally 122 on each elevational 118 side of the transducer 108.
  • a single laser shot is used to reconstruct one photoacoustic imaging frame 123.
  • Light is strongly scattered in biological tissue, so one laser shot can illuminate a broad region that covers the imaging field of view.
  • Modern ultrasound systems have multichannel, parallel data acquisition. So the photoacoustic imaging frame rate is usually limited by the laser repetition rate. Pulsed lasers with repetition rates of 30-50 Hz or higher can offer frame rates with minimal motion between consecutive frames.
  • the transducer 108 has an array 124, here a linear array although it may be a matrix array.
  • the transducer 108 has a number of active receiving, or "receive”, apertures 125, with each aperture typically comprising multiple transducer elements 126 of the array 124, such as eight.
  • the active receiving apertures 125 corresponding to an image acquisition location of the transducer 108, span the transducer laterally 122. They may also overlap, by half the aperture length, for example.
  • the apertures 125 receive in parallel the
  • radiofrequency (RF) data returning as a result of the laser pulse.
  • the acquisition location is the location, with respect to the probe 102, at which the PA wave is sensed on the transducer 108.
  • Fig. 1 Two different positions 127 are shown in Fig. 1 for respective apertures, which may correspond to an aperture translation along the array 124.
  • the desired or "true" PA signal is elicited by a light pulse 128 whose spatial spreading 129 begins upon leaving the excitation sources 120, denoted in Fig. 1 with the boxed number "1."
  • the single light pulse 128 is temporally a single light pulse despite its issuance from two spatially different excitation sources 120, since the issuance from the two sources is simultaneous.
  • the light passes through skin 130 of the patient and is absorbed by a PA target at a location 132 within the body 114.
  • the resulting thermoelastic expansion of the target represented in Fig. 1 by the concentric dotted lines, generates an acoustic wave that results in the desired PA signal being received by the transducer 108.
  • the differential strength and differential timing of the signal with respect to elements 126 of the set of one or more active receiving apertures 125 allows for the creation of a PA image 123 representative of the nature and location of PA targets within the field of view of the transducer 108.
  • optical absorption near a skin surface 134 is caused by melanin and superficial blood vesselsl36. Specifically, the optical absorption leads to photoacoustic waves that propagate directly 138 to the receiving apertures 125 and propagate into deeper tissue of the body 114, as well. As the photoacoustic waves propagate into the tissue, acoustic scatterers generate echoes, which are backscattered to the transducer 108. Both the directly coupled PA waves and backscattered "PA echoes" generate background clutter signals that degrade photoacoustic image contrast. These signals are not random, but rather deterministic and are therefore not effectively reduced by simple signal averaging. The signals appear spatially over the individual PA image 123 as areas of false brightness or intensity.
  • the clutter signal amplitude can be reduced, but not eliminated, by choosing an optical wavelength with low surface absorption. However, it is difficult to overcome the strong optical fluence at the skin surface and high melanin levels from skin pigmentation.
  • wavelength selection may not be good option for imaging many light- absorbing targets or PA contrast agents.
  • the fiber optic bundle 106 is, at the excitation sources 120, rocked angularly back and forth laterally.
  • the rocking is with respect to the probe 102.
  • the rocking is performed along the imaging plane of the linear array 124 or, for three-dimensional imaging, along the central lateral imaging plane of the matrix array.
  • Multiple PA images 123 e.g., ten, are acquired over the course of each angular rotation as represented by the two-headed arrow 140.
  • the probe 102 which may be applied manually is likewise kept stationary, i.e., in place, during rotation.
  • the rocking can be accomplished mechanically by means of a motor (not shown), within the probe 102, that is controlled by the processor 103.
  • the fiber optic bundle 106 can, at excitation sources 120 for example, be
  • the acquisition location varying entails the active receiving aperture(s) 125 being moved with respect to the probe 102.
  • the light-emitting location 115 on the patient-interface surface 110 of the probe 102 is stationary with respect to the probe.
  • the movement of the aperture(s) 125 can therefore be regarded also as with respect to the light-emitting location 115.
  • the aperture movement is done in the current example by rocking the transducer 108 back and forth laterally, i.e., along the imaging plane of the linear array 124 or, for three-dimensional imaging, along the central lateral imaging plane of the matrix array.
  • transducer-rocking versions There are a number of transducer-rocking versions. In each example presented herein below, the transducer is separated from the skin surface by a distance. That gap is filled by coupling fluid, coupling gel or a compliant gel standoff.
  • the probe 102 is configured with a fluid-fillable enclosure (not shown) in which the transducer is fixed for rotational, i.e., rocking, movement, the fluid serving as a coupling medium.
  • the fluid if containing water or an aqueous solution, is degassed, an example of which is provided in U.S. Patent Publication No.
  • the fluid may also include mineral oils or hydro-gels.
  • the fluid cools the probe 102 and the patient's skin in contact with the probe.
  • the rocking varies the image acquisition location, while not varying the light excitation, as illustrated by example in Fig. 2.
  • the active receiving aperture 125 or multiple currently active receiving apertures, are rocked while light delivery is not varied.
  • the common intracorporeal spatial location 132 is imaged responsively one-to-one to the laser shots fired during a rotational swing.
  • the transducer 108 has an ultrasound-receiving surface 204, i.e., "transducer surface”, denoted in Fig. 2 by the line of alternating short and long line segments.
  • transducer surface denoted in Fig. 2 by the line of alternating short and long line segments.
  • B-mode acquisition is interleaved, i.e., alternated, with PA acquisition, so that, for example, each PA frame is immediately followed by a corresponding B-mode frame acquired with the same transducer orientation.
  • an extracorporeal structure 212 is employed for determining any in -plane displacement of the transducer 108.
  • the extracorporeal structure 212 can be elongated, locationally fixed with respect to the probe during acquisition of the B-mode images and equivalently with respect to the axis of rotation, and disposed parallel, or otherwise transverse, to the axis.
  • the extracorporeal structure 212 should be distinctively echogenic, like metal. Since the rotational axis can be regarded as normal to the sheet of Fig.
  • the extracorporeal structure 212 such as a wire, appears in the imaging plane of a linear array 124, for example, as a point target.
  • the point target within the B-mode image can be estimated by speckle tracking which is performed automatically and without the need for user intervention.
  • the device 100 identifies, in the B-mode image, a fixed, i.e., motionless, landmark, such as a vein or bone, within the anatomy, which can be done from a few preliminary frame to frame pattern matching comparisons. From the spatial relationship between the point target and the landmark, the in-plane displacement, if any, is determinined. If the device 100 is used for imaging parts of the anatomy that are motionless, the landmark is not needed.
  • the position of the point target with respect to the anatomy indicates the in-plane displacement if any.
  • This can entail co-registering the differently oriented B-mode images by pattern-matching on the anatomy.
  • a skin surface orientation relative to the transducer surface 204 can be determined automatically and without the need for user intervention.
  • a rotational angle 216 between the skin surface 134 and the transducer surface 204 is measured.
  • a rigid transformation model can be derived for application to each PA image 208 to register it with respect to the reference imaging geometry which is usually set at the central transducer position
  • the instant scheme has the advantage of easy image registration for aligning individual component images. In particular, local motion tracking for each pixel in the entire imaging plane is not needed.
  • the wire 212 may alternatively reside in a compliant stand-off pad that is usable in lieu of coupling gel, the pad being firmly attached to the probe housing.
  • the extracorporeal structure 212 is separate from the probe 102, and is held stationary with respect to the skin surface 134 instead of with respect to the probe. This alleviates the need to find a motionless structure as a landmark in the case of moving anatomy.
  • the wire, or other extracorporeal structure 212 may be fixed to, and suspended in, a water bath or the stand-off pad. Inadvertent motion while holding the probe is not transferred to the water bath or pad, since the latter remain stationary.
  • the angular rocking may be elevational.
  • the probe 102 can be configured to, in another way, vary the image acquisition location.
  • the probe 102 may, for example, be configured for other movement of the transducer 108, such as translation, that provides a different viewing angle.
  • An example is a translational rocking back and forth, laterally or elevationally.
  • the frame 123 is acquired in response to a single issued light pulse 128.
  • all of the elements 126 of the array 124 simultaneously sense the RF data generated in reaction to excitation by the light pulse 128.
  • Different apertures 127 overlapping as described above, provide the viewpoint variation.
  • a photoacoustic apparatus that has an array 124 of multiple ultrasound transducer elements 126 is configured for forming receiving apertures 127 at different positions along the array and for, based on what is temporally a single pulse of light 128 and based on imaging acquisition by ones, or all, of the apertures that is responsive to the single pulse, performing spatial compounding to produce a photoacoustic frame 123 from the single pulse.
  • images that are reconstructed from different apertures 127 are spatially compounded.
  • frame acquisition and processing is rapid, and background clutter is reduced as in the previously described embodiments.
  • the optimal aperture translation step based on pulse-echo ultrasound imaging, should be equal to approximately half its length in the lateral direction.
  • a displacement between consecutively adjacent active receiving apertures 125 might be set at four elements.
  • the optimum aperture displacement for photoacoustic imaging can be derived from auto-correlation analysis. Since the translation of the active receiving aperture 125 is controlled by the ultrasound device 100, PA images 123 acquired at different aperture positions can be accurately registered and the overlapping area can be averaged together to form the final compound image.
  • Spatial compounding can be expanded from a one-dimensional to a two-dimensional array 124 for more flexibility in aperture selection and translation. This embodiment enjoys the same advantage of easy image registration for aligning individual component images, in comparison to the technique in the Jaeger study.
  • the acquisition location varying entails the active receiving aperture 125 being moved electronically, more generally with respect to the probe 102 and for example with respect to the light-emitting location 115 on the patient-interface surface 110 of the probe, in synchrony with repeated PA imaging.
  • the movement with respect to the probe 102 serves as an alternative form of varying the acquisition location while not varying the light excitation.
  • this embodiment repeatedly photoacoustically images the common intracorporeal spatial location 132 in the course of performing the PA excitation- acquisition sequence so that the target is viewed from different angles.
  • the device 100 is configured for varying the acquisition location by electronically translating the aperture 125, the location varying being likewise performed in synchrony with the repeated imaging.
  • the device 100 can be modified in different ways to vary the light excitation.
  • an integrated photoacoustic-ultrasound imaging probe configured for varying light excitation without varying acquisition location incorporates light delivery into the probe housing or has light delivery attached to the probe.
  • Signal averaging is performed over multiple frames to reduce background clutter.
  • an integrated photoacoustic-ultrasound imaging probe 300 may include in addition, or instead of, an optical fiber bundle 302 (the constituent sub-bundles 304 being shown in Fig. 3), free space optics 306 and/or a light guide (or "light pipe") 308.
  • the optical beam pattern is moved slightly, for example via translation 310, rotation 312 and/or vibration 314, relative to an ultrasound array 316 of a transducer of the probe 300 during imaging.
  • a motor (not shown) is incorporated within the probe to provide the movement.
  • the movement of the optical beam is such that consecutive imaging frames provide substantial clutter reduction. A sufficient amount of movement can be derived empirically.
  • the excitation varying entails moving excitation sources 318 which are disposed near an output end 320 of a light delivery system 322.
  • this may involve moving, e.g., further apart or closer together, PA image to PA image a pair of curved mirrors 324, 326 that receive light input from a bifurcated deflection mirror 328 illuminated by a laser 330.
  • Movement image to image may alternate movement together with movement apart with each subsequent image, but need not do so and may, for example, transition by degrees of movement in one direction for a while.
  • the light travels a path 331 indicated by the parallel- stem arrows.
  • the device includes an optical mask 332, an engineered diffuser 334, or the both the mask and the diffuser.
  • the excitation varying entails spatially altering a beam 336 by physically moving 337, via a motor and PA image to PA image, the mask 332 and/or diffuser 334 into and out of the light path, entirely or to varying degrees.
  • One or both of the beam altering components 332, 334 can be disposed either at a distal end 338 of the light delivery system 322; or a proximal end 342 of the light delivery system 322, for example at an input side of the fiber bundle or light guide after the connection of the laser 330 and before entry into the probe 300.
  • any combination of the components 332, 334 can be disposed at either the distal or proximal end.
  • Disposal at the proximal end 342 has the advantage that the component 332, 334 need not be made part of the probe 300 whose design is limited by more factors than those of the part of the device 100 on the other side of the cable.
  • An alternative embodiment switches 344 the optical illumination between the two fiber bundles placed on opposite sides of the ultrasound array 316.
  • two separate, spaced-apart fiber bundles rather than a single, bifurcated fiber bundle can be used.
  • a fast scanning mirror galvanometer can be used to switch the input beam from one fiber bundle to the next fiber bundle on consecutive laser shots.
  • an active state with respect to illumination is switched from one source of the excitation to another source of the excitation, the two sources being spaced apart.
  • the switching toggles back and forth between two such sources.
  • the final photoacoustic image displayed can be taken as the geometric mean of the two images acquired with the right and left fiber bundles separately. Equivalently, the arithmetic mean of logarithmic values of the two images may be taken.
  • An example of varying both the light excitation and the acquisition location, image to image would be toggling back and forth between the two separate fiber bundle branches or sources image to image while also translating an active receiving aperture 125 image to image.
  • a medical image acquiring device repeatedly photoacoustically images an intracorporeal spatial location that is common image to image, varying at least one of ultrasound transducer acquisition location, and light excitation, image to image so that averaging of the images serves to decorrelate background clutter that exists in the images, of the spatial location, individually.
  • the varying of one may be in the absence of the other, and may entail movement.
  • the movement may be of an optical fiber bundle, a light guide or free space optics, as by rotation, translation or vibration. It may be of an optical mask or engineered diffuser, or it may entail toggling between active states of two spaced apart, separate optical fiber branches near the probe surface. If the movement pertains instead to acquisition location, it may imply translation of the active receive aperture, or rotation of the transducer as in the imaging plane in which case co-registering of the images may use synchronous B-mode images to detect skin orientation and a landmark.
  • a computer program can be stored momentarily, temporarily or for a longer period of time on a suitable computer-readable medium, such as a floppy disk, a magnetic hard disk drive, a solid-state medium such as a solid state hard disk, flash memory, a USB thumb drive, read-only memory (ROM), an optical storage medium such as an optical disk, and a magneto-optical disk.
  • a suitable computer-readable medium such as a floppy disk, a magnetic hard disk drive, a solid-state medium such as a solid state hard disk, flash memory, a USB thumb drive, read-only memory (ROM), an optical storage medium such as an optical disk, and a magneto-optical disk.
  • optical disks include compact disks (CD) and digital versatile disks (DVD), for example CD-ROM, CD-RW, CD-R, DVD-ROM, DVD- RW, or DVD-R disks.
  • Such a computer-readable medium is non-transitory only in the sense of not being a transitory, propagating signal
  • a single processor or other unit may fulfill the functions of several items recited in the claims.
  • the mere fact that certain measures are recited in mutually different dependent claims does not indicate that a combination of these measures cannot be used to advantage.

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Abstract

L'invention concerne un dispositif d'acquisition d'image médicale (100), qui de manière répétée représente, de façon photo-acoustique, un emplacement spatial intracorporel (132) qui est commun d'image à image, en faisant varier au moins l'un d'un emplacement d'acquisition de transducteur ultrasonore et d'une excitation de lumière, d'image à image, de telle sorte qu'une moyenne des images sert à décorréler le fouillis d'échos d'arrière-plan qui existe dans les images de l'emplacement spatial, individuellement. La variation de l'un peut être réalisée en l'absence de l'autre et peut entraîner un déplacement. Le déplacement peut être celui d'un faisceau de fibres optiques, d'un guide de lumière ou d'une optique sans fil, tel que par rotation (140), translation ou vibration. Il peut être celui d'un masque optique ou d'un diffuseur artificiel, ou il peut entraîner un basculement entre des états actifs de deux branches de fibre optique séparées et espacées près de la surface de sonde. Si le déplacement se rapporte, à la place, à l'emplacement d'acquisition, il peut impliquer la translation de l'ouverture de réception active (127), ou la rotation du transducteur dans le plan d'imagerie, auquel cas l'enregistrement simultané des images peut utiliser des images de mode B synchrones pour détecter une orientation de la peau et un repère.
PCT/IB2013/060206 2012-11-16 2013-11-18 Réduction de fouillis d'échos en place pour imagerie photo-acoustique Ceased WO2014076674A2 (fr)

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Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP3090682A1 (fr) 2015-05-08 2016-11-09 Universiteit Twente Réduction d'artéfacts en imagerie thermoacoustique et photoacoustique

Citations (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20050154309A1 (en) 2003-12-30 2005-07-14 Liposonix, Inc. Medical device inline degasser

Family Cites Families (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP5697361B2 (ja) * 2010-04-26 2015-04-08 キヤノン株式会社 光音響波測定装置

Patent Citations (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20050154309A1 (en) 2003-12-30 2005-07-14 Liposonix, Inc. Medical device inline degasser

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
M JAEGER ET AL.: "Improved Contrast Deep Optoacoustic Imaging Using Displacement-Compensated Averaging: Breast Tumor Phantom Studies", PHYS. MED. BIOL., vol. 56, 2011, pages 5889 - 5901

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP3090682A1 (fr) 2015-05-08 2016-11-09 Universiteit Twente Réduction d'artéfacts en imagerie thermoacoustique et photoacoustique
WO2016182435A1 (fr) 2015-05-08 2016-11-17 Universiteit Twente Réduction d'artefacts en imagerie photo-acoustique et thermoacoustique

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