[go: up one dir, main page]

WO2009130647A1 - Imagerie de microvasculature à mouvement compensé - Google Patents

Imagerie de microvasculature à mouvement compensé Download PDF

Info

Publication number
WO2009130647A1
WO2009130647A1 PCT/IB2009/051604 IB2009051604W WO2009130647A1 WO 2009130647 A1 WO2009130647 A1 WO 2009130647A1 IB 2009051604 W IB2009051604 W IB 2009051604W WO 2009130647 A1 WO2009130647 A1 WO 2009130647A1
Authority
WO
WIPO (PCT)
Prior art keywords
frame
frames
sequence
contrast
blood vessels
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Ceased
Application number
PCT/IB2009/051604
Other languages
English (en)
Inventor
Cecile Dufour
Olivier Gerard
Thomas Gauthier
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Koninklijke Philips NV
Original Assignee
Koninklijke Philips Electronics NV
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Koninklijke Philips Electronics NV filed Critical Koninklijke Philips Electronics NV
Publication of WO2009130647A1 publication Critical patent/WO2009130647A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/48—Diagnostic techniques
    • A61B8/483—Diagnostic techniques involving the acquisition of a 3D volume of data
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/46—Ultrasonic, sonic or infrasonic diagnostic devices with special arrangements for interfacing with the operator or the patient
    • A61B8/461—Displaying means of special interest
    • A61B8/463—Displaying means of special interest characterised by displaying multiple images or images and diagnostic data on one display
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/48—Diagnostic techniques
    • A61B8/481—Diagnostic techniques involving the use of contrast agents, e.g. microbubbles introduced into the bloodstream
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/52—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/5215—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data
    • A61B8/5238—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data for combining image data of patient, e.g. merging several images from different acquisition modes into one image
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/52—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/5269—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving detection or reduction of artifacts
    • A61B8/5276—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving detection or reduction of artifacts due to motion
    • G—PHYSICS
    • G06—COMPUTING OR CALCULATING; COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T7/00—Image analysis
    • G06T7/20—Analysis of motion
    • G—PHYSICS
    • G06—COMPUTING OR CALCULATING; COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T7/00—Image analysis
    • G06T7/30—Determination of transform parameters for the alignment of images, i.e. image registration
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S7/00—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00
    • G01S7/52—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00
    • G01S7/52017—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00 particularly adapted to short-range imaging
    • G01S7/52053—Display arrangements
    • G01S7/52057—Cathode ray tube displays
    • G01S7/52071—Multicolour displays; using colour coding; Optimising colour or information content in displays, e.g. parametric imaging
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S7/00—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00
    • G01S7/52—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00
    • G01S7/52017—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00 particularly adapted to short-range imaging
    • G01S7/52077—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00 particularly adapted to short-range imaging with means for elimination of unwanted signals, e.g. noise or interference
    • G—PHYSICS
    • G06—COMPUTING OR CALCULATING; COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T2207/00—Indexing scheme for image analysis or image enhancement
    • G06T2207/10—Image acquisition modality
    • G06T2207/10132—Ultrasound image
    • G—PHYSICS
    • G06—COMPUTING OR CALCULATING; COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T2207/00—Indexing scheme for image analysis or image enhancement
    • G06T2207/30—Subject of image; Context of image processing
    • G06T2207/30004—Biomedical image processing

Definitions

  • the present invention relates to an ultrasonic diagnostic imaging method, in particular motion compensated imaging method for imaging micro -vascular systems with contrast agents.
  • the invention also relates to a corresponding computer program product and ultrasonic diagnostic apparatus.
  • Ultrasonic contrast agents enable clinicians to image and quantify structures and functions in the body which are not otherwise readily seen or measured.
  • the ability of ultrasonic contrast agents to resonate nonlinearly when excited with ultrasound can produce a strong harmonic response, enabling clear segmentation of vessels infused with the contrast agent.
  • a sharply defined image can be produced by disrupting the microbubbles of the contrast agent with high mechanical index (MI) ultrasound as described in US patent 5,456,257.
  • MI mechanical index
  • vascular structures involved are tiny, micro -vascular structures with individual vessels conducting minute amounts of blood flow at very low rates of flow. It would be desirable to be able to use contrast enhanced ultrasound to image and delineate such difficult to detect micro -vascular structures.
  • a first sequence of frames i.e. a succession of B-mode frames, of the object (e.g. the liver) in which the contrast agent has been injected, and a second sequence of frames depicting the path followed by the microbubbles (contrast agent) in the tiny vessels.
  • the object e.g. the liver
  • the contrast agent contrast agent
  • the invention overcomes this issue and provides a new ultrasonic diagnostic method.
  • ultrasound is used to image micro-vascular structures with the aid of a contrast agent.
  • the harmonic response of the contrast agent reduces clutter, and temporal persistence is used to discern the structure of the micro-vasculature by delineating the track of microbubbles through the tiny vessels.
  • an ultrasound imaging method for visualising blood vessels containing contrast agent comprising the following steps performed by an ultrasonic diagnostic apparatus: acquiring a first sequence of data frames, the sequence containing an object to be analyzed; compensating movement of the object; computing contrast agent paths visualising the blood vessels in the object; and - generating a second sequence of data frames by aligning the positions of the computed paths with the position of the moving object contained in the first sequence of data frames.
  • the present invention provides readable vasculatures for both steady and moving tissues, possibly blended with moving colour Doppler data and/or tissue data.
  • the moving object is blurred, or if it is not blurred it is not moving, i.e. it is static, whereas in the present invention the moving objects are clear and not blurred.
  • the contrast agent also shows clear paths in the frames of the second sequence.
  • an ultrasonic diagnostic apparatus for visualising blood vessels containing contrast agent, the apparatus comprising means for: acquiring a first sequence of data frames, the sequence containing a moving object to be analyzed;
  • FIG.l illustrates in block diagram form an ultrasonic diagnostic imaging system constructed in accordance with the principles of the present invention
  • FIG.2 illustrates in block diagram form details of the image processor of FIG.1 in accordance with a first embodiment of the present invention
  • FIG.3 is a flow chart illustrating a first imaging method in accordance with the first embodiment of the present invention
  • FIG.4 illustrates in block diagram form details of the image processor of FIG.1 in accordance with a second embodiment of the present invention.
  • FIG.5 is a flow chart illustrating a second imaging method in accordance with the second embodiment of the present invention.
  • a probe 101 includes an array transducer 103 which transmits ultrasound beams into a subject and receives echoes from along the beam directions in response to the transmit beams, all under control of a beamformer 105. Echo signals produced by the beamformer are demodulated into quadrature I, Q components by a quadrature bandpass (QBP) filter 107.
  • Quadrature bandpass filters are well known in the art such as those described in US patent 09/693,059, entitled “Ultrasonic Harmonic Flash Suppression".
  • the echo samples are coupled to an echo processor 109 where the samples are processed for B mode display by amplitude detection and log compression.
  • the echo samples are also coupled to a flow processor 111 where they are used for Doppler estimation as described in US patents 5,386,830, 6,036,643 and 6,095,980.
  • the processed echo and flow signals are coupled to an image processor 113 where they are scan converted into the desired image format and displayed on a display 115 either separately or combined.
  • a sequence of two or three dimensional images may be stored in an image buffer 117 where they may be replayed for more detailed study, or processed by rendering to form a two or three dimensional image sequence.
  • FIG.2 shows in block diagram form the image processor 113 of FIG.l in accordance with the first embodiment of the present invention.
  • contrast frames Io, Ii, h- - -I n are received and fed into a scan converter 201 which converts received contrast frames into a desired display format in step 303, such as a rectangular or sector shaped image.
  • the converted images or frames are then fed into a motion estimation unit 202 and into first motion compensation unit 203 to perform first motion compensation (step 305), also known as image registration or image alignment, prior to the inter-frame high pass filtering (step 307).
  • the motion estimation unit 202 estimates in step 304 motion between two consecutive contrast image frames and then this information is input to the first motion compensation unit 203.
  • Motion compensation from frame to frame can reduce the blurring of tissue/transducer motion and will lead to a more effective temporal filter.
  • the first motion compensation unit 203 spatially aligns, based on the motion information, the current input contrast frame /ggi with the previous input contrast frame /ggi_; to obtain the spatially aligned frame I n (I n .]) which is thus motion compensated.
  • This alignment can be carried out for instance by using a method described in a publication entitled "The Engineer's Guide to Motion Compensation” by John Watkinson, published by Snell & Wilcox Ltd. Durford Mill, Petersfield, Hampshire.
  • X(Y) means that X is spatially aligned with Y.
  • the aligned frame I n (I n .]) then enters an inter-frame high pass filter (HPF in FIG.2) 205.
  • the inter- frame high pass filter 205 is a temporal filter that may take the form of an FIR filter, an HR filter or a frame-to-frame differentiator which filters successive images on a pixel-by-pixel basis. Spatially corresponding pixels which are the same from frame to frame, such as pixels of stationary tissue, will produce a low-or zero-level output.
  • the temporal high pass filter 205 is sensitive to some degree of probe motion.
  • One way to reduce unwanted effects from probe motion is by harmonic flash suppression, as described in the aforementioned US patent 09/693,059.
  • Another approach, which may be used separately or in conjunction with flash suppression, is to perform motion compensation as explained above prior to the inter-frame high pass filtering, as shown in FIG.2.
  • the inter-frame high pass filter 205 thus reduces signals from stationary and quasi- stationary objects such as tissue and produces display level signals from moving microbubbles in the vasculature. More specifically, in step 307 the temporal high pass filter 205 filters / spirit_; and I n (I n .]) to obtain a difference frame D n .
  • the difference frame D n corresponds to new bubbles present in the current frame compared to the previous frame / spirit_;.
  • the high pass filtering comprises performing frame-to- frame subtraction on a spatial basis of temporally different images.
  • the current contrast frame / spirit can be stored in the image buffer 117.
  • the output from the image buffer 117 is connected to the motion estimation unit 202 so that the stored / trademark can be used when estimating motion between / admir + ; and / formulate.
  • step 311 the second motion compensation unit 207 aligns D n with a previous persistent frame P n .] to obtain D n (P n .]). In other words, the alignment is done between the difference frame D n and the previous persistent frame P n .]. This operation corresponds to a second motion compensation.
  • D n (P n .]) is needed to avoid visual artefacts in the vasculature represented by the current persistence frame P n . If this alignment is not done, the vasculature would give misleading information to the user.
  • D n is in the same reference position as / admir_;, but it is not in the same reference position as P n .]. This also means that D n is not in the same reference position as P n .]. For this reason, D n needs to be aligned with iV;.
  • the aligned frame D n is fed into a post processor 209, which performs in step 313 image processing tasks such as thresholding, noise reduction, or frame-to-frame speckle tracking.
  • the aligned difference frame D n is then applied to a persistence processor 211 which sustains a temporal sequence of detected microbubbles in the image.
  • the persistence processor 211 calculates in step 315 the current persistent frame P n from P n ⁇ 1 and D n (P n _;).
  • the persistence processor 211 can have a time constant for the persistence of a displayed microbubble which is greater than zero and as great as one. As the individual microbubble detection events build up (persist) in the image over time, the morphology of the tiny blood vessels through which they are passing becomes visible.
  • the persistence processor 211 can be operated with a high time constant, showing the continual passage of microbubbles through blood vessels and a continual buildup of the flow structure on the screen.
  • the persistence processor 211 can also be given a lower time constant so that microbubble events will slowly decay away with time.
  • the user is given a reset control 212 to reset the persistence to black at the start of an acquisition sequence or after a high time constant sequence has filled the screen with microbubble events or after tissue or transducer motion. It may further be desirable to combine the transmission of a high MI transmit frame with the reset control 212, causing the reset of the persistence processor 211 to coincide with a high energy frame which strongly disrupts the microbubbles currently in the image region.
  • step 316 the current persistent frame P n can be stored in a persistence frame buffer 213.
  • the output of this buffer is connected to the persistence processor 211 and to the second motion compensation unit 207.
  • a first post-persistence processor 214 aims to align prior to display the persistent frame P n with frame / Struktur, by applying motion compensation, for instance a global rigid deformation. This processing leads to the generation of P n (I n ).
  • This alignment allows the microvasculature image, represented by the current persistent frame P n , to be synchronized with the current contrast frame / political, This operation improves the dynamic behaviour of the micro vascular imaging (MVI) image construction, and thus the visual comfort of the user.
  • MVI micro vascular imaging
  • the second post-persistence processor 215 aims to improve the image quality of the aligned persistent frame P n (I n ). It may perform image processing such as edge enhancement or segmentation/thresholding.
  • the processed contrast image may be blended with a conventional 2D echo image.
  • 2D can be understood to cover also 3D depending on the properties of the probe used.
  • the contrast image may also be segmented and applied as a colour overlay over the 2D echo image in step 321 as indicated by the blend/overlay processor 217. After these operations the obtained image can be displayed to the user in step 323.
  • step 321 is merely optional and it may also be left out.
  • the tracks of microbubbles shown in persistent frames can be used to calculate the absolute velocity of blood flow through the micro -vasculature.
  • the bubbles can be seen to move a finite amount between frames along the curved paths of the micro -vasculature. Since the scale of the pixel density relative to the anatomy being displayed is known, the distance travelled by a microbubble over a period of frames can be measured in an image. From the knowledge of the frame rate (in frames per second) and the distance a microbubble has moved, the absolute velocity of the flow through the micro -vasculature can be calculated.
  • this region of interest located in the centre of the first image, i.e. frame Io, is under focus of the clinician.
  • the invention proposes in a further aspect that an implicit ROI is located at the centre of the first image, having dimension coping as much as possible with ultrasound scanning. This area is proposed to be centred. Its shape can be:
  • the invention also proposes to select the first frame of the sequence, i.e. frame Io as support for ROI delineation.
  • This implicit ROI might, however, not be appropriate: it could be too small or too large. It also could be the case that the first frame of the sequence might not correspond to the best viewpoint. Hence some ways to modify the implicit ROI, or to delineate a better defined ROI, are proposed (step 325) to the user:
  • the size of the implicit ROI can be enlarged or reduced. Its most adequate location can be set. - If still not satisfactory, the clinician could define himself its ROI.
  • a circular/spherical ROI is, however, foreseen to be the most suitable and easiest protocol to define a ROI dedicated to MVI.
  • the centre of the ROI can be located by one click, and an implicit radius can be proposed.
  • the clinician can increase or reduce this radius by using simple buttons (+/- slider, mouse with a scroll wheel, etc.).
  • the user interaction protocol is made available via a user interface.
  • FIG.2 the only difference is that in FIG.4 there is no second motion compensation unit 207. Also in the flow chart most of the steps are identical to the steps shown in the flow chart of
  • step 203 the first image registration unit 203 operates differently in the second embodiment as in the first embodiment.
  • step 203 referring to the flow chart of FIG.5, in step
  • step 505 current frame / solo is aligned with the previous persistent frame P n .] to obtain I n (P n .]).
  • step 507 the HPF 205 is then applied on I n (P n .]) and I n .](P n .2) to obtain a difference frame D n , which is by nature aligned with P n .].
  • step 509 I n (P n .]) is stored in the image buffer 117. In this embodiment there could be a further output from the image buffer 117 to connect this buffer back to the high pass filter 205. As the motion compensation is computationally expensive, I n (P n .]) is saved so that it can be used to calculate the next difference frame, i.e.
  • Both the first and second embodiments need at least one alignment, namely the alignment done by the first motion compensation unit 203 and preferably the storage of I n .].
  • Advantage of the first embodiment over the second embodiment is in memory consumption: the second embodiment additionally stores I n (P n .]).
  • Advantage of the second embodiment over the first embodiment is in computation time: the first embodiment needs to perform an additional alignment done by the second motion compensation unit 207.
  • the present invention can be generalised so that the method can be considered to comprise the following steps performed by an ultrasonic diagnostic apparatus: acquiring a first sequence of data frames, the sequence containing a moving object to be analyzed; compensating the movement of the object; computing contrast agent paths visualising the blood vessels in the object; and - generating a second sequence of data frames by aligning positions of the computed paths with the position of the moving object contained in the first sequence of data frames.
  • the first sequence of data frames corresponds to the image contrast frames / admir.
  • the second sequence represents P n (I n ) corresponding to the persistent frames that are aligned and displayed, e.g. on a screen, together with the contrast image frames.
  • the generating and computing steps are performed only when all the frames of the frame sequence in question have been dealt with in a corresponding previous step.
  • the generating and computing steps are performed as soon as at least two frames of the frame sequence have been dealt with in a corresponding previous step.
  • the computing step only starts when the compensation step has been carried for all the frames of the first sequence. Similarly, the computing step only starts when the computing step has been carried out for all the frames.
  • the algorithm performs only one time the compensation, computation, and generation steps.
  • the computing step starts when the compensation step has been carried for two successive frames of the first sequence.
  • the same principle applies to the next steps.
  • the compensation, computation, and generation steps are performed several times in a loop.
  • the invention equally relates to a computer program product that is used to store computer program code for implementing any of the method steps as described above when loaded and run on computer means of the ultrasonic diagnostic apparatus.
  • the computer program may be stored/distributed on a suitable medium supplied together with or as a part of other hardware, but may also be distributed in other forms, such as via the Internet or other wired or wireless telecommunication systems.
  • the invention equally relates to an integrated circuit that is arranged to perform any of the method steps in accordance with the embodiments of the invention. While the invention has been illustrated and described in detail in the drawings and foregoing description, such illustration and description are to be considered illustrative or exemplary and not restrictive; the invention is not restricted to the disclosed embodiments. Other variations to the disclosed embodiments can be understood and effected by those skilled in the art in practicing the claimed invention, from a study of the drawings, the disclosure and the appended claims. For instance, the motion estimation could be done prior to the scan conversion. Actually, the whole process, i.e. the motion estimation, as well as MVI construction, could be done prior to the scan conversion.
  • the scan conversion can thus be performed, for instance, after the first motion compensation or after the high pass filtering. It is also possible to combine the operations of the persistence processor 211, 1 st post persistence processor 214 and the 2 nd post persistence processor 215 into a single processor or into two processors. In the above examples, two consecutive frames were processed, but it is also possible that every third or fourth, etc. frame is processed instead. This would save some processing power, while not necessarily leading into considerably worse outcome.
  • the word "comprising” does not exclude other elements or steps, and the indefinite article "a” or “an” does not exclude a plurality. A single processor or other unit may fulfil the functions of several items recited in the claims. The mere fact that different features are recited in mutually different dependent claims does not indicate that a combination of these features cannot be advantageously used. Any reference signs in the claims should not be construed as limiting the scope of the invention.

Landscapes

  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Physics & Mathematics (AREA)
  • Radiology & Medical Imaging (AREA)
  • Medical Informatics (AREA)
  • Veterinary Medicine (AREA)
  • Biophysics (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Pathology (AREA)
  • Public Health (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • General Health & Medical Sciences (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • Computer Vision & Pattern Recognition (AREA)
  • Theoretical Computer Science (AREA)
  • General Physics & Mathematics (AREA)
  • Hematology (AREA)
  • Multimedia (AREA)
  • Ultra Sonic Daignosis Equipment (AREA)

Abstract

La présente invention porte sur un procédé et sur un appareil pour une imagerie par ultrasons de vaisseaux sanguins avec l'aide d'un agent de contraste. Les emplacements de microbulles de l'agent de contraste sont détectés dans une série d'images à mesure que les microbulles se déplacent à travers les vaisseaux sanguins. L'invention fournit des vasculatures lisibles par utilisation de compensation de mouvement pour à la fois des tissus stables et mobiles, possiblement mélangés avec des données de Doppler de couleur mobile et/ou des données de tissu.
PCT/IB2009/051604 2008-04-24 2009-04-17 Imagerie de microvasculature à mouvement compensé Ceased WO2009130647A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US4749208P 2008-04-24 2008-04-24
US61/047,492 2008-04-24

Publications (1)

Publication Number Publication Date
WO2009130647A1 true WO2009130647A1 (fr) 2009-10-29

Family

ID=40720049

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/IB2009/051604 Ceased WO2009130647A1 (fr) 2008-04-24 2009-04-17 Imagerie de microvasculature à mouvement compensé

Country Status (1)

Country Link
WO (1) WO2009130647A1 (fr)

Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2015097634A (ja) * 2013-11-19 2015-05-28 株式会社東芝 超音波診断装置及び超音波診断装置用のプログラム
CN112566559A (zh) * 2018-07-11 2021-03-26 皇家飞利浦有限公司 具有像素外推图像增强的超声成像系统
WO2021084060A1 (fr) * 2019-11-01 2021-05-06 Koninklijke Philips N.V. Systèmes et procédés d'imagerie vasculaire
US20220071596A1 (en) * 2019-01-03 2022-03-10 Koninklijke Philips N.V. Systems and methods for contrast enhanced imaging

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20020040189A1 (en) * 1995-10-10 2002-04-04 Michalakis Averkiou Ultrasonic perfusion measurement using contrast agents
US20030204142A1 (en) * 2002-04-26 2003-10-30 Koninklijke Philips Electronics N.V. Contrast-agent enhanced color-flow imaging
US20030229285A1 (en) * 2002-06-11 2003-12-11 Simpson David Hope Ultrasonic diagnostic micro-vascular imaging
US20040225218A1 (en) * 2003-05-06 2004-11-11 Siemens Medical Solutions Usa, Inc. Identifying clinical markers in spatial compounding ultrasound imaging
US20080306382A1 (en) * 2007-06-05 2008-12-11 Siemens Medical Solutions Usa, Inc. Adaptive clinical marker preservation in spatial compound ultrasound imaging

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20020040189A1 (en) * 1995-10-10 2002-04-04 Michalakis Averkiou Ultrasonic perfusion measurement using contrast agents
US20030204142A1 (en) * 2002-04-26 2003-10-30 Koninklijke Philips Electronics N.V. Contrast-agent enhanced color-flow imaging
US20030229285A1 (en) * 2002-06-11 2003-12-11 Simpson David Hope Ultrasonic diagnostic micro-vascular imaging
US20040225218A1 (en) * 2003-05-06 2004-11-11 Siemens Medical Solutions Usa, Inc. Identifying clinical markers in spatial compounding ultrasound imaging
US20080306382A1 (en) * 2007-06-05 2008-12-11 Siemens Medical Solutions Usa, Inc. Adaptive clinical marker preservation in spatial compound ultrasound imaging

Cited By (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2015097634A (ja) * 2013-11-19 2015-05-28 株式会社東芝 超音波診断装置及び超音波診断装置用のプログラム
CN112566559A (zh) * 2018-07-11 2021-03-26 皇家飞利浦有限公司 具有像素外推图像增强的超声成像系统
US20210255321A1 (en) * 2018-07-11 2021-08-19 Koninklijke Philips N.V. Ultrasound imaging system with pixel extrapolation image enhancement
US11953591B2 (en) * 2018-07-11 2024-04-09 Koninklijke Philips N.V. Ultrasound imaging system with pixel extrapolation image enhancement
US20220071596A1 (en) * 2019-01-03 2022-03-10 Koninklijke Philips N.V. Systems and methods for contrast enhanced imaging
WO2021084060A1 (fr) * 2019-11-01 2021-05-06 Koninklijke Philips N.V. Systèmes et procédés d'imagerie vasculaire
US12478348B2 (en) 2019-11-01 2025-11-25 Koninklijke Philips N.V. Systems and methods for vascular imaging

Similar Documents

Publication Publication Date Title
US11969286B2 (en) Systems and methods for automatic detection and visualization of turbulent blood flow using vector flow data
US6676606B2 (en) Ultrasonic diagnostic micro-vascular imaging
JP7232195B2 (ja) 血管内の壁せん断応力の同時視覚化及び定量化のためのシステム及び方法
US6659953B1 (en) Morphing diagnostic ultrasound images for perfusion assessment
EP3905960B1 (fr) Systèmes et procédés d'imagerie à amélioration de contraste
JP4594610B2 (ja) 超音波画像処理装置及び超音波診断装置
US6620103B1 (en) Ultrasonic diagnostic imaging system for low flow rate contrast agents
US9008387B2 (en) Method and apparatus for processing ultrasound images
JP3402703B2 (ja) 超音波診断装置
US20090187106A1 (en) Synchronized combining for contrast agent enhanced medical diagnostic ultrasound imaging
US12343211B2 (en) Ultrasound image analyzing apparatus for quantifying contrast agent stagnation
JP2019534103A (ja) 造影剤流の肝灌流を特徴付けるシステム及び方法
CN109982643A (zh) 用于解剖结构、功能和血液动力学成像的三模式超声成像
US11403732B2 (en) Ultrasound super resolution imaging
CN117769392A (zh) 超分辨率超声成像
US20090148018A1 (en) Image segmentation technique for displaying myocardial perfusion that does not show the microbubbles in the cardiac chambers
WO2009130647A1 (fr) Imagerie de microvasculature à mouvement compensé
WO2015124388A1 (fr) Visualisation adaptative de mouvement en imagerie 4d médicale
US20090204003A1 (en) Tracking selection for medical diagnostic ultrasound imaging
US8657750B2 (en) Method and apparatus for motion-compensated ultrasound imaging
US9480403B2 (en) Medical imaging system and method for generating a blended cine loop
US12167937B2 (en) Methods and systems for live image acquisition
Mor‐Avi et al. Power Doppler imaging as a basis for automated endocardial border detection during left ventricular contrast enhancement
JP2024519328A (ja) 超解像度超音波イメージング
WO2025248069A1 (fr) Procédé et appareil d'imagerie de microscopie de localisation ultrasonore ultrarapide 3d

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 09733941

Country of ref document: EP

Kind code of ref document: A1

NENP Non-entry into the national phase

Ref country code: DE

122 Ep: pct application non-entry in european phase

Ref document number: 09733941

Country of ref document: EP

Kind code of ref document: A1