Classifications

• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
  • A61B8/08—Clinical applications
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
  • A61B8/54—Control of the diagnostic device
• • 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
• • 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
  • G01S15/8995—Combining images from different aspect angles, e.g. spatial compounding
• • 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

Definitions

• This disclosure relates to ultrasound imaging and more particularly to systems and methods for spatial compounding using linear arrays and even more specifically to phased arrays.
• Spatial compounding is a method of creating an ultrasound image by compiling multiple views acquired at different angles. Each view is obtained from multiple lines of sight at different angles. This is a departure from traditional ultrasound imaging that used a single line of sight perpendicular to the scanhead face. The views from the multiple angles are combined to create a single image, thereby reinforcing real- tissue information and suppressing random artifacts. Spatial compounding has resulted in a reduction in speckle noise artifacts; shadowing artifacts and image-degrading artifacts. In addition, such compounding, which is also known as compound imaging, results in improvements in: contrast resolution; needle visualization; tissue contrast resolution; fine-structure delineation; interface/border continuity and lateral edge detection.
• Some systems use a method where information from both the transmit and the receive beam steering is processed to produce images from multiple view angles.
• the multiple images are aligned and combined to form an image. Images that are created using both transmit and receive information are typically superior to images consisting of receive information only.
• phased arrays which, for example, can have 64, 128 (or if desired, any other number) elements.
• all of the array elements 64 or 128, must be selectively pulsed to form the wavefront for each scan line.
• Each scan line has its own unique angle with respect to the transducer face in the sector format.
• the geometry of each ray is independent of the geometry from other rays.
• Electronic focusing is required for both transmitting energy into the subject as well as for receiving the energy reflected back from the target.
• a phased array typically has a linear geometry, but the shape of the images produced are usually sectors similar to those produced by curved arrays.
• image data corresponding to the different views must be resampled, or geometrically aligned to a common set of coordinates, before they are combined.
• the symmetry of the beams i.e, they are equally spaced in angle
• spatial compounding for phased arrays is much more complicated because the beams are typically not equally spaced.
• each ray has a unique geometry
• the resampling of each ray is also unique to that ray.
• each beam requires a unique table for registration. Therefore, a very large amount of computation and/or very large tables are required to register the image data from the different views.
• the present invention is directed to a system and method which makes a phased array look like a curved array for purposes of performing spatial compounding calculations.
• the phased array is treated as though it were a curved array by creating both a virtual apex and a virtual radius of curvature. Based on this transformation, standard spatial-compounding resampling tables can be used just as they are with curved arrays.
• certain data is removed prior to the actual display. This removed data represents data generated by virtual prior to the physical skin line of the phased array.
• FIGURE 1 shows one schematic illustration of an embodiment of a the operational theory of image generation using a curved array in accordance with the prior art
• FIGURE 2 shows one schematic illustration of an embodiment of a the operational theory of image generation using a phased array in accordance with one aspect of the invention
• FIGURE 3 shows one embodiment of a method for constructing a virtual apex and employing the concepts herein;
• FIGURE 4 shows one embodiment of a sonographic system that can employ the concepts discussed herein;
• FIGURE 5 shows one alternative embodiment.
• FIGURE 1 shows one schematic illustration 10 of an embodiment of a the operational theory of image generation using a curved array in accordance with the prior art.
• FIGURE 1 shows one method for spatially compounding beams formed along a curved array. This technique is well-known in the art and can be accomplished, for example, using concepts discussed in the above-identified U.S. Patent Application No. 11/749,319.
• Curved array 102 has apex 100 and radius of curvature 101.
• Unsteered ray 11, emanating from apex 100 is perpendicular to the array surface, which in one embodiment can be ceramic.
• This ray also called a beam
• This ray is steered left (11 SL) and steered right (11 SR) as discussed in the P35 application to paint the target, such as target 110 below skin line 103 of the subject.
• This trio of beams (as well as many others as are desired) can be moved anywhere along aperture 102 to form the different look directions that need to be acquired for spatial compounding.
• the beam can be moved anywhere that is perpendicular to surface 102 of the scan head and the resampling computations are identical for beams at any one of those locations. This then results in a minimal amount of information that must be stored in order to resample properly formed beam data for subsequent conversion into pixel images for display to a user. Once resampled, the data from the various steered rays can be combined and scan-converted to produce spatial compounded images.
• FIGURE 2 shows one schematic illustration 20 of an embodiment of the operational theory of image generation using a phased array in accordance with one aspect of the invention.
• rays from the surface (scan head) of a phased array such as from scan head 204, which typically has elements arranged along a line, are mathematically calculated as if they emanate from apex 200.
• apex 200 becomes a virtual apex having virtual radius of curvature 201 with virtual scan head 202 and virtual skin line 203.
• a beam such as beam 21 can be constructed that is nernendicular to virtual surface 202.
• Beam 21 can be steered left (21SL) and steered right (21SR) to focus on all or a part of target 210 which is located within a subject below actual skin line 205 which is displaced from actual scan head 204 by the thickness of the lens.
• beam steering pivot point 206 and virtual radius of curvature need not coincide with virtual ceramic 202 used for beamforming, and also note that the virtual skin line need not be tangent to the actual skin line.
• phased array is leveraged off of the calculations made for curved arrays since the different look directions are not tied to the physical ceramic structure of the phased array scan head.
• a modification that must be made to use phased arrays in this manner is to take into account that while a virtual apex and radius is being used, the ultrasound beam emanates from the true skin line rather than from the virtual skin line.
• the data acquired corresponding to the region between the virtual skin line and true skin line is meaningless and is not displayed.
• the symmetry of the virtual curved array construct avoids requiring unique resampling tables for each beam; a single table is used for all beams. Without this, time-consuming calculations and/or very large tables would be required
• Rays 21 U, 21 SL and 21 SR are the rays the system uses for imaging the target. As noted above, while only three such lines are shown, any number of rays can be used. These rays represent the center of the beam and only data coming from those portions of the respective beams that are below the actual skin line (within the subject) are used for the ultimate image presentation. However, since the calculation for compounding of the various rays is made before the virtual data is removed, the calculations are easier and faster to make thereby allowing a linear array, such as a phased array, to be used for quickly moving targets such as for cardiac imaging applications.
• a linear array such as a phased array
• FIGURE 3 shows one embodiment 30 of a method for constructing a virtual apex 303 given the length of the phased array 301 and the desired field of view 302.
• the virtual apex determines the virtual radius. Note that, as will be discussed, more than one virtual apex can be used, if desired, or the virtual scanhead properties could be computed to meet different requirements.
• Process 304 transmits energy along rays to the target within the subject and receives energy along rays back as in a curved array. The calculated virtual radius of curvature has been substituted for the actual radius of curvature of the curved array.
• Process 305 performs compounding, such as spatial compounding, on the received rays as is done with the curved arrays using the fact that the tables required to register the steered and unsteered beam data are the same for all rays.
• Process 306 then removes the virtual data by, for example, by discarding the data acquired prior to the actual skin line.
• “prior to skin line” means data that is collected earlier in time than is data from the signal as it enters the skin line.
• data is recorded that would correspond to times before the ultrasound beam is emitted from the scanhead. This is required to make the phased array look like a curved array, but it means that the data (i.e., the data collected prior to the skin line) is not valid and should not be displayed.
• the data to be removed depends upon timing and necessarily on scanhead orientation. The system knows which data to discard from the geometry of the problem. This can be a look-up in a table, if desired. Note that while the data to be discarded is carried along for calculation purposes (so that the problem being solved is the same as for a curved array), it is removed at the end of the process.
• Process 307 converts the remaining compounded data to pixel space.
• Process 308 then displays the pixel space data as an image on a screen or other read-out mechanism.
• FIGURE 4 shows one embodiment 40 of an implementation of the concepts discussed herein. Controller 41 generates the transmit sequence as well as the steerage angle for the beams in conjunction with beamformer 42 and analog transmitter/receiver 43.
• Controller 41 can comprise, for example, one or more processors that perform the ray angle adjustment or the ordinate location control for the respective rays of each time frame.
• the output of transmitter/receiver 43 supplies the transmit signals to transducer array 44.
• Transducer 44 receives a sequence of rays reflected from a subject which are used to form an image.
• each steer angle there are 128 rays for each steer angle (the rays are numbered in an example firing sequence using three steers) in each time differentiated frame.
• the returned signal for each fired ray is received by array 44 and communicated via analog transmitter/receiver 43 to receive beamformer 45.
• the output of the receive beamformer is a digitally sampled and beamformed ray.
• This ray is then filtered and detected by component 46 and sent to compounding engine 47 for compounding.
• Each collection of similarly steered rays are resampled (aligned), scan converted into a common grid and buffered by the compounding engine and stored in buffer memory 48.
• the compounding engine computes a weighted average for each common sample in the buffer memory for the given frame of ultrasound data.
• the compounded data is then sent from the compounding engine to the scan converter 49 for processing for display 400.
• FIGURE 5 shows one alternative embodiment 30 in which more than one virtual apex is created.
• Multiple virtual apices may be used instead of or in conjunction with multiple steer angles for compounding. That is, different views for spatial compounding may be obtained by steering rays at different angles, by employing rays with different virtual apices, or both, as desired.
• virtual apex 500 has virtual ceramic 502 and virtual skin line 503.
• Virtual skin line 503 is not tangent to actual skin line 205 of the subject.
• the virtual ceramics 202 and 502 need not touch and thus rays 510 and 210 need not intersect at a common point of the respective virtual ceramic lines.
• compounding of the beams can occur after scan conversion to pixel space, if desired. Also, it is possible to acquire an entire frame along a single look direction before acquiring data along another look direction and then compounding the looks.

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• Engineering & Computer Science (AREA)
• Physics & Mathematics (AREA)
• Remote Sensing (AREA)
• Radar, Positioning & Navigation (AREA)
• Health & Medical Sciences (AREA)
• Life Sciences & Earth Sciences (AREA)
• Acoustics & Sound (AREA)
• General Physics & Mathematics (AREA)
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• Molecular Biology (AREA)
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• Measurement Of Velocity Or Position Using Acoustic Or Ultrasonic Waves (AREA)

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• 2007
  • 2007-09-12 US US11/854,373 patent/US8137278B2/en active Active
• 2008
  • 2008-09-05 JP JP2010524932A patent/JP5452491B2/ja active Active
  • 2008-09-05 EP EP08830904.2A patent/EP2187813B1/en active Active
  • 2008-09-05 WO PCT/US2008/075367 patent/WO2009035916A1/en not_active Ceased
  • 2008-09-05 CN CN200880106592.8A patent/CN101868184B/zh active Active
  • 2008-09-05 CN CN201610225786.6A patent/CN105997139B/zh active Active
• 2013
  • 2013-12-27 JP JP2013272077A patent/JP5894571B2/ja active Active

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