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WO2016055902A1 - Imagerie ultrasonore tridimensionnelle par intersection de balayage 2d - Google Patents

Imagerie ultrasonore tridimensionnelle par intersection de balayage 2d Download PDF

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Publication number
WO2016055902A1
WO2016055902A1 PCT/IB2015/057435 IB2015057435W WO2016055902A1 WO 2016055902 A1 WO2016055902 A1 WO 2016055902A1 IB 2015057435 W IB2015057435 W IB 2015057435W WO 2016055902 A1 WO2016055902 A1 WO 2016055902A1
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Prior art keywords
images
image
sequence
ultrasound
probe
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Ceased
Application number
PCT/IB2015/057435
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English (en)
Inventor
Yinhui DENG
David Hope Simpson
Canxing XU
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Koninklijke Philips NV
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Koninklijke Philips NV
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Publication of WO2016055902A1 publication Critical patent/WO2016055902A1/fr
Anticipated expiration legal-status Critical
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Classifications

    • 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
    • G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
    • G01S15/88—Sonar systems specially adapted for specific applications
    • G01S15/89—Sonar systems specially adapted for specific applications for mapping or imaging
    • G01S15/8906—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques
    • G01S15/8993—Three dimensional imaging systems
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/42—Details of probe positioning or probe attachment to the patient
    • A61B8/4245—Details of probe positioning or probe attachment to the patient involving determining the position of the probe, e.g. with respect to an external reference frame or to the patient
    • A61B8/4254—Details of probe positioning or probe attachment to the patient involving determining the position of the probe, e.g. with respect to an external reference frame or to the patient using sensors mounted on the probe
    • 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
    • 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
    • G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
    • G01S15/88—Sonar systems specially adapted for specific applications
    • G01S15/89—Sonar systems specially adapted for specific applications for mapping or imaging
    • G01S15/8906—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques
    • G01S15/8909—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration
    • G01S15/8915—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration using a transducer array
    • G01S15/8918—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration using a transducer array the array being linear
    • 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
    • G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
    • G01S15/88—Sonar systems specially adapted for specific applications
    • G01S15/89—Sonar systems specially adapted for specific applications for mapping or imaging
    • G01S15/8906—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques
    • G01S15/8909—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration
    • G01S15/8915—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration using a transducer array
    • G01S15/892—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration using a transducer array the array being curvilinear
    • 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
    • G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
    • G01S15/88—Sonar systems specially adapted for specific applications
    • G01S15/89—Sonar systems specially adapted for specific applications for mapping or imaging
    • G01S15/8906—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques
    • G01S15/8934—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a dynamic transducer configuration
    • G01S15/8936—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a dynamic transducer configuration using transducers mounted for mechanical movement in three dimensions
    • 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
    • G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
    • G01S15/88—Sonar systems specially adapted for specific applications
    • G01S15/89—Sonar systems specially adapted for specific applications for mapping or imaging
    • G01S15/8906—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques
    • G01S15/8934—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a dynamic transducer configuration
    • G01S15/8938—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a dynamic transducer configuration using transducers mounted for mechanical movement in two dimensions
    • G01S15/894—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a dynamic transducer configuration using transducers mounted for mechanical movement in two dimensions by rotation about a single axis
    • 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
    • G01S7/52085—Details related to the ultrasound signal acquisition, e.g. scan sequences
    • 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
    • G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
    • G01S15/88—Sonar systems specially adapted for specific applications
    • G01S15/89—Sonar systems specially adapted for specific applications for mapping or imaging
    • G01S15/8906—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques
    • G01S15/8909—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration
    • G01S15/8915—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration using a transducer array
    • G01S15/8925—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration using a transducer array the array being a two-dimensional transducer configuration, i.e. matrix or orthogonal linear arrays
    • 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
    • G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
    • G01S15/88—Sonar systems specially adapted for specific applications
    • G01S15/89—Sonar systems specially adapted for specific applications for mapping or imaging
    • G01S15/8906—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques
    • G01S15/8934—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a dynamic transducer configuration
    • G01S15/8945—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a dynamic transducer configuration using transducers mounted for linear mechanical movement
    • 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
    • G01S7/5206—Two-dimensional coordinated display of distance and direction; B-scan display
    • G01S7/52065—Compound scan display, e.g. panoramic imaging

Definitions

  • This invention relates to medical ultrasound imaging and, in particular, to three dimensional ultrasonic imaging by intersecting scanning of a region of interest.
  • Ultrasonic imaging can be used to produce two dimensional or three dimensional images of a region of interest.
  • Premium ultrasound systems conventionally are capable of operating with probes having two dimensional transducer arrays which can be operated in a phased mode to steer transmit and receive beams over a three dimensional region of the body.
  • Such solid state probes can acquire beams steered over a three dimensional region which are used to form three dimensional images in real time.
  • Two dimensional array probes can also be used to produce static images of extended volumes referred to as panoramic images as described in U.S. patent 8,539,838 (Yoo et al . ) The probe shown in this patent can be moved along the surface of the body with a row of transducers extending normal to the direction of travel continuously
  • an ultrasonic imaging system and method are described in which manual freehand 2D image scanning is performed using a ID array probe, a mechanically swept single piston transducer probe, or a row of elements of a 2D array probe.
  • a 2D array whether one row of elements or more than one row of elements is used is not significant as long as a sequence of 2D images is acquired where each image plane in each sequence is formed in a fixed location and orientation relative to the transducer.
  • the inventive technique is designed specifically to operate without the need for a priori knowledge of the exact orientation or spacing of the 2D images in any of the sequences, although the technique can also be performed with a priori knowledge.
  • a region of interest can be scanned by at least two intersecting sweeps of images.
  • the present invention can be used generally if sweeps (2 or more) intersect in such a manner that the lines of intersection of the sweeps, taken together, are not all parallel.
  • a region of interest can be scanned at least twice in approximately orthogonal directions to acquire two sets of approximately parallel planes, or in three or more different directions to acquire three or more sets of image planes, which spatially intersect each other.
  • the line or lines of intersection of images from the two sets of image planes are then found and the intersecting images fitted together in
  • FIGURE 1 provides an example ultrasound system in accordance with an embodiment of the present invention.
  • FIGURE 2 illustrates in perspective two
  • FIGURE 3 illustrates the two intersecting
  • FIGURE 4 illustrates a grid showing how an assumed line of intersection of two images can fail to be an actual line of intersection of the two images by reason of nonlinear motion of the probe during scanning.
  • FIGURE 5 illustrates the translation needed for one line of image data of one image to bring it into registration with the same image data in an
  • FIGURE 6 illustrates the actual alignment of one set of approximately parallel images with an image which is approximately orthogonal to the approximately parallel images .
  • FIGURE 7 illustrates a response surface of function values for unknown variables in an iterative 3D image reconstruction technique of the present invention .
  • the present invention includes an ultrasound system which produces a three dimensional image of a region of interest.
  • the ultrasound system can include an ultrasound probe having, e.g., a one dimensional array of transducer elements.
  • a first frame sequence buffer, coupled to the ultrasound probe can be configured to store a first sequence of ultrasound images, such as spatially offset two dimensional images as the probe is moved in a first direction.
  • a second frame sequence buffer, coupled to the ultrasound probe can be configured to store a second sequence of
  • ultrasound images such as spatially offset two
  • An image line registration processor coupled to receive images from the first and second frame sequence buffers, can be configured to identify a common line of intersection of an image of one buffer with an image of the other buffer.
  • a 3D volume buffer coupled to the image line registration processor, can be configured to store the image data of images found to have one or more lines of intersection by the image line registration processor.
  • a display coupled to the 3D volume buffer, can be configured to produce a three dimensional image based on the intersecting sweeps of the ultrasound probe.
  • An ultrasound probe 11 contains a one dimensional transducer array 12.
  • the array is a curved linear array which scans a sector image when the face of the probe is pressed into acoustic contact with the body.
  • the linear array may also be a straight linear array or a single row of a two dimensional array transducer.
  • the probe is connected by a T/R switch 14 to a transmit beamformer 16 and a receive beamformer 18.
  • transmit beamformer actuates predetermined groups of elements at specifically related times to transmit beams in desired directions over an image plane and the receive beamformer steers and focuses receive beams in response to those transmission events.
  • the receive beams are filtered and may undergo other signal
  • the detected signals may be amplitude detected tissue signals or Doppler detected signals from moving substances such as blood flow.
  • a series of ad acent receive beams are stored in a frame buffer 24 from which they will be further processed into a planar image frame as described below.
  • the ultrasound system 10 of the present invention can be configured to determine an approximate position of the ultrasound probe 11 in space.
  • the ultrasound probe can include position sensors to determine the probe's position in space.
  • position sensors can be used, such as accelerometers , gyroscopes, and/or electromagnetic field sensors.
  • electromagnetic instrument tracking system or other similar system may be used alone or in combination with the ultrasonic diagnostic imaging system to determine the probe position.
  • the electromagnetic tracking system uses electromagnetic field generators and
  • sensors to determine the location of an object in space.
  • the location may be determined in relation to a fixed plane, an ultrasound probe, and/or other reference point.
  • An electromagnetic tracking system that may be used is the PercuNav system by Philips®.
  • an electromagnetic tracking and navigation system may be used, such as the PercuNav system, elements of which are shown in Figure 1.
  • the electromagnetic tracking and navigation system has a field generator 46 which generates an electromagnetic field permeating a surrounding space of the probe during imaging.
  • Sensors 44 are located on the probe 12 which interact with the electromagnetic field and produce signals used to calculate the position and orientation of the image plane of the probe. This calculation is done by a coordinate generator 42 of the system, which is shown receiving signals representing the position and orientation of the image plane, and further receiving signals from the field generator 46 to which the coordinate generator 42 is also coupled for field registration purposes.
  • the electromagnetic tracking and navigation system can be controlled via operator control signals from the control panel 30.
  • the present invention includes methods for producing a three dimensional ultrasound image by freehand scanning.
  • the methods can include, for example, moving an ultrasound probe containing a one dimensional array of transducer elements in a first direction while acquiring a first sequence of spatially offset images from a region of interest.
  • the first direction can be generally orthogonal to the plane of an image produced by the array.
  • the methods can include storing the first sequence of images.
  • Another step of the methods can include moving the ultrasound probe in a second direction while acquiring a second sequence of spatially offset images from a region of interest.
  • the probe can be moved in intersecting sweeps in the first and second directions such that at least one image in the first sequence intersects at least one image in the second sequence.
  • intersecting sweeps can be generally orthogonal, e.g., the first direction can be generally orthogonal to the second direction.
  • the methods can include storing the second sequence of images, and/or processing an image from the first sequence with an image of the second sequence to identify at least one common line of intersection of the two image.
  • the methods can include processing additional images from both sequences to identify one or more lines of intersection of each additional image with one or more lines of previously processed images to form a three dimensional grid of intersecting images.
  • a step of the methods can include processing the three dimensional grid of intersecting images to produce a three
  • first frame sequence buffer 32 The probe is moved so that the images received during its motion will sweep through a region of interest.
  • the user touches a control on the user interface 30 to condition the frame sequence buffer to begin storing images.
  • the control is touched again to inform the buffer that the first sequence is complete. Any identical images stored at the beginning and the end of the sweep before and after the probe has moved may be identified by image matching and discarded. Since the probe is moved in a given direction the
  • the probe is slid or rocked in a second direction (e.g., an approximately orthogonal direction) to acquire a second sequence of images.
  • the second sequence of images will also be in an spaced relationship (e.g., approximately parallel) by reason of the rocking or sliding motion but in an
  • the second sequence of images is stored in a second frame sequence buffer 34.
  • the user interface 30 is used as before to command the second frame sequence buffer when to start and stop storing acquired images. Images stored in the two frame sequence buffers are then spatially registered by detecting the image line of intersection of an image of one sequence to an image of the other sequence by an image line
  • This registration is based upon the image content such as the features or speckle pattern of each image.
  • the registered grid of planar images is stored in a 3D volume buffer 38. Spaces between the planes of the registered images may then be filled in by scan conversion using scan
  • the data of the 3D volume image can thus be converted to uniform density in all three dimensions
  • the 3D dataset is then rendered into a 3D image by volume renderer 28 for display on an image display 40.
  • accurately spaced image planes of the scanned volume can be produced, enabling quantitative distance, area and volume measurements to be made of a scanned organ (e.g., a kidney) or a mass, so that the dimensions of the organ or mass can be quantitatively measured.
  • User control of the ultrasound system is provided by a user interface 30.
  • FIGURE 2 illustrates how the image registration process may begin.
  • the center frame of each sequence is initially selected for registration on the assumption that, if the frame acquisition were perfect, the two center frames of the two orthogonal sequences would intersect at their center line.
  • FSi- c is the center image frame of the first frame sequence
  • FS 2 is the center image frame of the second frame sequence. Since the orientation of the images from the respective sequences is approximately orthogonal, one frame will spatially intersect the other at a common line of intersection Li . If the scanning were done in perfect alignment the line of intersection Li would be the aligned center lines of each image. But since the sequences were acquired by manual hand scanning, it is not, as can be seen from the tilt of line Li and its position at the tops of the images.
  • the line of intersection Li of the first two images selected for processing is generally the most exhaustive to determine because it can have virtually any
  • a pixel matching process such as block matching used in
  • panoramic imaging may be employed to compare and try to align a line of pixels of one image with a line of pixels in the other image.
  • the degree of match of one line with another may not be perfect because the two images were acquired at different times and the anatomy images may have changed due to bodily function or movement or other effects. Hence a degree of match less than 100% should be used to ascertain matching lines of intersection.
  • the location of the common line Li is noted and used to initially estimate the positions of other intersecting images as shown in FIGURE 3.
  • FIGURE 3 In this example the two image sequences have been acquired by rocking the probe or sliding it in an arc as indicated by arrow R for the second sequence. This motion will cause the respective images to be approximately parallel but differently angularly tilted by a differential angle ⁇ as shown for images 61, 62, 63, FS 2 64, 65, and 66 of the second sequence.
  • the magnitude of the assumed differential angle ⁇ is predicated up the knowledge that a rocking motion was used to scan the region of interest which can be
  • the angular increment ⁇ is not exact, of course, but provides a starting point from which the search for the line of intersection of each second sequence image and the first sequence image FSi- c .
  • intersection c is shown in relation to a pixel grid 80 for purposes of illustration. Line c is seen to
  • FIGURE 5 illustrates how the line of intersection matching process proceeds for two intersecting image planes FS i- n and FS2-n of the two sequences.
  • Image FS i- n has a line of image content indicated at 70 which is shown as a row of circles at the current line of intersection of the two images. But this same line of image content 70' is at a different planar location in the second image 70' which is not in alignment at this orientation. When a search is made for this image content in the second image, it is seen that the lines of image content are not
  • the spacing to the line of intersection with an adjacent image may be increased or decreased from the nominal pixel spacing in the common image, in which case the pixel spacing in the common image can be stretched or compressed (warped) to maintain the geometric accuracy of the intervening image region.
  • the final alignment may not be the initially assumed alignment shown in FIGURE 3, but the pattern of alignment shown in FIGURE 6.
  • Other images of the first sequence may now be registered to common lines of intersection with the second sequence images until all of the images of both sequences have been registered with each other,
  • the spacing between the image planes of the grid may then be filled in by
  • volume rendering rendered into a 3D volume image by volume rendering and the image viewed dynamically by dynamic parallax display.
  • the two scanning sequences have a common constraint, which is that each has been applied to the same target anatomy or region of interest in 3D space.
  • unknown variable parameters that prevent an accurate reconstruction of the target of interest by use of just one sequence. Assume that values are randomly chosen for uncertain parameter sets of the two sequences, ⁇ 1 for one sequence and ⁇ 2 for the other sequence. Using the chosen values, a
  • the reconstruction be a full reconstruction of the entire target volume.
  • the reconstructed data can be just the image information that shares the same spatial coordinates, the lines of intersection Li of the two image sequences. Since the original scan plane data are discrete, interpolation may be needed in each image to obtain the exactly intersecting lines. This interpolation can be extended, if desired, to interpolate data for a full reconstruction of the target of interest. For example, a direct reconstruction of the 3D volume data of each image sequence with additional interpolated lines can be performed and then a comparison of the results is made. It can be seen that the reconstructed lines of intersection denote the data information for comparison once some parameter sets for the scanned sequences are chosen . The next step is to perform a comparison to see whether the reconstructed lines of intersection of each scanning sequence are similar.
  • comparison is to directly use one reconstructed data set minus the other reconstructed data set, then sum the difference directly.
  • Another method is to sum the square of the difference of the two data sets.
  • ⁇ denotes the spatial uncertainty parameter of the current data
  • Distis a distance metric used to evaluate the data constraints .
  • FIGURE 7 illustrates the result of this kind of search known as a "grid search”. From FIGURE 7 it can be seen that the function values of different parameter combinations build up a surface called a "response surface". In the response surface the location with the minimum value is the optimal value of the parameters, which are [4,8] in this example.
  • Another way to obtain the optimal solution is to first obtain several values of sampled points on the response surface. Then, based on a spatial shape assumption, an effort is made to reconstruct the response surface and find the location of the minimum value on the
  • This iterative method is a global optimization, which can be performed by a number of methods, such as hardy multi-quadratics and kriging- function based methods, among others.
  • the computer program instructions may also cause at least some of the operational steps to be performed in parallel.
  • steps may also be performed across more than one processor, such as might arise in a multi-processor computer system.
  • one or more processes may also be performed concurrently with other processes, or even in a different sequence than illustrated without departing from the scope or spirit of the invention.
  • the computer program instructions can be stored on any suitable computer-readable hardware medium
  • RAM random access memory
  • ROM read-only memory
  • EEPROM electrically erasable programmable read-only memory
  • flash memory electrically erasable programmable read-only memory
  • CD-ROM compact disc-read only memory
  • DVD digital versatile disks
  • the present invention can include a system having instructions thereon, which when executed, cause the system to perform the following steps: moving an ultrasound probe containing a one dimensional array of transducer elements in a first direction while acquiring a first sequence of spatially offset images from a region of interest; storing the first sequence of images; moving the ultrasound probe in a second direction while acquiring a second sequence of
  • spatially offset images from a region of interest wherein at least one image in the first sequence intersects at least one image in the second sequence; storing the second sequence of images; processing an image from the first sequence with an image of the second sequence to identify at least one common line of intersection of the two images; processing additional images from both sequences to identify one or more lines of intersection of each additional image with one or more lines of previously processed images to form a three dimensional grid of intersecting images; and processing the three dimensional grid of intersecting images to produce a three dimensional ultrasound image of a region of interest.

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Abstract

L'invention concerne un système à ultrasons (10) qui comprend une sonde (11) avec un transducteur de réseau unidimensionnel (12) qui est basculé ou glissé à travers le corps dans deux directions orthogonales pour acquérir deux séquences d'images plates à décalage par élévation balayées à travers la même région d'intérêt. Une image d'une première séquence est traitée avec une ou plusieurs images de l'autre séquence pour trouver une ligne d'intersection commune avec une ou plusieurs images de l'autre séquence. Une fois que toutes les images d'intersection ont été traitées pour trouver leurs lignes d'intersection avec d'autres images sensiblement orthogonales, une grille de type pour caisse alvéolée d'images a été identifiée. Les espaces d'élévation entre les images peuvent être remplis par une conversion de balayage et les données d'image traitées pour former une image tridimensionnelle de la région d'intérêt.
PCT/IB2015/057435 2014-10-09 2015-09-29 Imagerie ultrasonore tridimensionnelle par intersection de balayage 2d Ceased WO2016055902A1 (fr)

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