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WO1999030617A1 - Procede et systeme d'imagerie de diagnostic par ultrasons avec cadence d'images amelioree - Google Patents

Procede et systeme d'imagerie de diagnostic par ultrasons avec cadence d'images amelioree Download PDF

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Publication number
WO1999030617A1
WO1999030617A1 PCT/US1998/026879 US9826879W WO9930617A1 WO 1999030617 A1 WO1999030617 A1 WO 1999030617A1 US 9826879 W US9826879 W US 9826879W WO 9930617 A1 WO9930617 A1 WO 9930617A1
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WO
WIPO (PCT)
Prior art keywords
receive
beams
transmit
fundamental
region
Prior art date
Application number
PCT/US1998/026879
Other languages
English (en)
Inventor
David J. Napolitano
Christopher R. Cole
Gregory L. Holley
Original Assignee
Acuson Corporation
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 Acuson Corporation filed Critical Acuson Corporation
Priority to AU22002/99A priority Critical patent/AU2200299A/en
Publication of WO1999030617A1 publication Critical patent/WO1999030617A1/fr

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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
    • 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
    • G01S7/52023—Details of receivers
    • G01S7/52036—Details of receivers using analysis of echo signal for target characterisation
    • G01S7/52038—Details of receivers using analysis of echo signal for target characterisation involving non-linear properties of the propagation medium or of the reflective target
    • G01S7/52039—Details of receivers using analysis of echo signal for target characterisation involving non-linear properties of the propagation medium or of the reflective target exploiting the non-linear response of a contrast enhancer, e.g. a contrast agent
    • 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
    • G01S15/8977—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using special techniques for image reconstruction, e.g. FFT, geometrical transformations, spatial deconvolution, time deconvolution
    • 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
    • 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
    • G01S7/52095—Details related to the ultrasound signal acquisition, e.g. scan sequences using multiline receive beamforming
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • 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
    • G01S15/8959—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using coded signals for correlation purposes

Definitions

  • This invention relates to medical diagnostic ultrasonic imaging methods and systems, and in particular to improvements to such systems that allow an increased frame rate.
  • multiple transmit beams are fired along the same ultrasound line.
  • Examples of such applications include two-pulse techniques that use phase inversion subtraction to enhance harmonic image components, synthetic aperture techniques, synthetic spectrum techniques, and sequential focus techniques.
  • the requirement for multiple transmit pulse firings on each ultrasound line results in a substantial reduction in frame rate.
  • Chapmar. U.S. Patent 5,632,277 discloses an ultrasound imaging system that employs phase inversion subtraction to enhance the image.
  • two transmit ultrasonic pulses which differ in phase by 180° are focused in the same beam direction.
  • the echo signals associated with these pulses are stored and then summed.
  • Linear echoes destructively interfere in this summation due to the 180° phase difference between the two transmitted ultrasonic pulses.
  • Non-linear echoes do not destructively interfere to the same extent, because the phases associated with non-linear echoes no longer differ by 180°. In this way, the amplitude of the non-linear echoes can be increased relative to the amplitude of the linear echoes in the summed signal.
  • the system disclosed in the Chapman patent suffers from the disadvantage that two ultrasonic pulses must be directed along each beam direction, and this requirement reduces the frame rate by a factor of two.
  • Cole U.S. Patent 5,617,862 discusses a system that coherently sums receive beams along the same steering direction to achieve a synthetic aperture.
  • the disclosed system also results in a substantial reduction in frame rate.
  • the reductions in frame rate discussed above are inevitable in the disclosed systems, and in many cases the frame rate may fall to clinically unacceptable levels.
  • the multiple firing techniques discussed above reduce frame rate in discrete steps. For example, when two transmit beam firings are required for each transmit beam direction, the frame rate is reduced by a factor of two as compared to conventional single transmit beam operation. It would be advantageous to have a technique whereby a continuous trade off could be made between selected performance factors and the resulting frame rate when employing various multiple-pulse modes of operation.
  • preferred embodiments described below transmit a plurality of spatially distinct ultrasonic transmit beams into a region.
  • a plurality of pre-detection receive beams are received from the region, each receive beam associated with a respective one of the transmit beams.
  • the transmit and receive beams include beams of at least first and second types.
  • the first and second types of beams differ in at least one scan parameter other than transmit and receive line geometry, and can for example differ in phase, aperture, frequency or focus.
  • Pre-detection receive beams associated with spatially distinct ones of the transmit beams are then preferably combined in a coherent manner.
  • the first and second types of beams alternate on a line-by-line or group-of-lines by group-of-lines basis. It is the coherent combination that synthesizes the desired feature such as two-pulse cancellation, synthetic aperture, synthetic spectrum, or multiple focus.
  • This approach allows a continuous tradeoff between performance and frame rate by adjustment of the scan line density. For example, if the same scan line density is used in both the normal mode and one of the alternating line modes described above, there is no frame rate loss.
  • Figure 1 is a block diagram of an ultrasonic imaging system that incorporates a presently preferred embodiment of this invention.
  • Figure 2 is a flow chart of a portion of a method practiced by the system of Figure 1.
  • Figures 3 and 4 are schematic diagrams illustrating the formation of a composite signal in two alternative embodiments in which a single receive beam is acquired for each transmit beam.
  • Figures 5 through 8 are waveform diagrams illustrating the operation of the method shown in Figure 3.
  • Figure 11 is a diagram showing the spacing of a set of transmit beams generated by the system of Figure 1 as compared to the Nyquist spacing.
  • Figures 12 and 13 are schematic diagrams of the methods of Figures 3 and 9, respectively.
  • Figure 14 is a schematic diagram showing transmit apertures utilized in an alternating line aperture embodiment of this invention.
  • Figures 15-19 are schematic diagrams showing receive apertures used in various alternating line aperture embodiments of this invention.
  • Figure 20 is a flow chart showing an alternating line focus embodiment of this invention.
  • Figure 21 is a flow chart showing an alternating line frequency embodiment of this invention.
  • Figure 22 is a graph showing frequency characteristics of the embodiment of Figure 21.
  • Figure 23 is a flow chart of an additional embodiment of this invention.
  • Figure 1 shows a schematic view of an ultrasonic imaging system 10 that incorporates a presently preferred embodiment of this invention that provides alternating line phase.
  • the system 10 includes a transmit beamformer 12 that is coupled to a phased transducer array 14 by a multiplexer 16.
  • the multiplexer 16 also couples the transducer array 14 to a receive beamformer 18.
  • the transmit beamformer 12 in part operates as a conventional transmit beamformer to generate a set of transmit signals for the individual transducers included in the transducer array 14.
  • the transmit beamformer 12 can include a waveform generator 20 that applies a suitably shaped ultrasonic pulse to a focus delay 22.
  • the focus delay 22 provides conventional steering delays by any suitable combination of delays, phase shifts and phase rotati ⁇ ns.
  • the focus delays are selected to cause ultrasonic signals from the transducer array 14 to constructively interfere at a selected transmit focus along a selected transmit beam direction.
  • an exemplary transmit beam T1 is shown.
  • the transmit beamformer 12 additionally includes a phase inverter 24 that is controlled by a controller 26.
  • the phase inverter 24 is active only for every other transmit beam.
  • transmit beams T1 , T3,... are transmitted with positive polarity
  • transmit beams T2, T4, T6,... are transmitted with inverted or negative polarity.
  • the receive beamformer 18 can operate in a single beam mode, in which a single receive beam is acquired for each transmit beam, or in a multiple receive beam mode, in which multiple receive beams are acquired in association with each transmit beam.
  • each receive beam is spatially aligned with the associated transmit beam, while in the multiple receive beam mode each of the receive beams is spatially offset from the respective transmit beam.
  • two receive beams R1a and R1b are shown in association with the transmit beam T1.
  • the transmit beams including the transmit beam T1 are directed into a region R of the subject, and the receive beams R1a, R1b are associated with echoes from the region R.
  • the receive beamformer 18 applies appropriate delays and phase rotations to coherently sum receive signals from the transducer array 14 to create the desired receive beams along desired directions. These receive beams are applied to a line buffer 28 that stores the receive beams for further processing. In this embodiment, the line buffer 28 stores the receive beams coherently. That is, sufficient timing or phase information is preserved, or sufficient phase corrections were made to allow the interference effects discussed below to be obtained consistently. Selected receive beams associated with multiple, spatially distinct transmit beams are applied to a summer 30 for summation to form a composite signal C that is applied to an image processor 32.
  • the image processor 32 forms a conventional image such as .' ⁇ B mode image and presents this image on a display 34.
  • Figure 2 provides a flowchart of a portion of a method practiced by the system of Figure 1.
  • the system transmits a first transmit beam of positive polarity in a first direction in step 40, and receives and stores one or more first receive beams associated with this first transmit beam in step 42. Then the transmit beamformer transmits a second transmit beam of negative polarity in a second direction in step 44.
  • the second transmit beam is usually adjacent to the first transmit beam.
  • One or more second receive beams associated with the second transmit beam are received and stored in step 46, and selected ones of the first and second receive beams are summed in step 48 to generate a composite signal, which is supplied to the image processor in step 50.
  • Figure 3 illustrates the method of Figure 2 diagrammatically.
  • the X direction proceeds from left to right, and transmit and receive beams of differing azimuthal positions are plotted at differing X coordinates.
  • Reference numerals 40-50 have been used in Figure 3 to designate portions of Figure 3 that correspond to the correspondingly numbered steps of Figure 2. Note that the first and second receive beams R1 , R2 that are summed in step 48 are associated with spatially distinct transmit beams T1
  • FIG. 4 shows another embodiment of the method of this invention which includes steps 40-46 as described above.
  • a third transmit beam T3 (positive polarity) is transmitted along a third spatially distinct direction in step 52, and a corresponding receive beam R3 is acquired in step 54.
  • the receive beams R1 , R2, R3 are all aligned with the corresponding transmit beams T1 , T2, T3 and are all spatially distinct.
  • These three receive beams R1 , R2, R3 are summed in step 56 using summing values [1 , 2, 1] as shown in Figure 4 to generate a composite signal C1 that is applied to the image processor in step 58.
  • Figures 5-8 diagrammatically illustrate the benefits obtained with the methods of Figures 2-4.
  • Figure 5 shows the ultrasonic waveform associated with the positive polarity transmit beams T1 , T3 in solid lines and th ., inverted or negative polarity ultrasonic waveform associated with transmit pulse T2 in dotted lines.
  • the inverted polarity pulse differs from the positive polarity pulse by phase inversion or a phase shift of 180°.
  • the ultrasonic pulse shown in Figure 5 is an amplitude modulated sinusoid, and the sinusoid has a fundamental wavelength ⁇ ? .
  • the pulses shown in Figure 5 represent the fundamental components 80, 82 of the transmit beams T1 and T2, respectively.
  • Figure 5 can also be taken as a representation of the fundamental components 84, 86 of the receive beams R1, R2, respectively, assuming a different amplitude scale.
  • the fundamental components 84, 86 of the receive beams are created by linear echoes of the fundamental components 80, 82 of the ultrasonic transmit beams, and the fundamental component 84 of the receive beam R1 is 180° out of phase with respect to the fundamental component 86 of the receive beam R2 .
  • Figure 6 schematically shows the summation of the fundamental components 84, 86 of the receive beams R1 , R2 . Because the fundamental components 84, 86 are substantially equal in amplitude, and because they differ in phase by 180°, the fundamental components 84, 86 of the receive beams R1 , R2 destructively interfere to a substantial extent.
  • the harmonic components 88, 90 of the receive beams R1 , R2 are created by non-linear effects, they are not characterized by a phase shift of 180°.
  • the harmonic components 88, 90 are second harmonic components having a wavelength ⁇ equal to one-half of ⁇ ? .
  • the harmonic receive components 88, 90 have substantially the same phase, and when summed they constructively interfere as shown in Figure 8.
  • Figures 9 and 10 relate to multiple receive beam embodiments of this invention.
  • a first transmit beam T1 (of positive polarity) is transmitted along a first azimuthal direction in step 60, and two associated receive beams R1a, R1b are acquired in step 62.
  • the receive beams R1a, R1b are offset spatially on respective sides of the transmit beam T1.
  • a second transmit beam T2 (of negative polarity) is transmitted along a second transmit direction, spatially distinct from the first transmit direction of the transmit beam T1.
  • Two corresponding receive beams R2a, R2b are acquired in step 66, and two spatially aligned receive beams R1b, R2a are added together in step 68. Note that the summed receive beams R1b, R2a are spatially aligned along the azimuthal direction, but that they are associated with spatially distinct transmit beams T1 , T2, respectively.
  • the summing step 68 generates a composite signal C1 that is applied to the image processor in step 70.
  • Figure 9 shows a modified form of the method of Figure 9, in which steps 60-66 are performed as described previously.
  • the summing step 72 sums a total of four receive beams R1a, R1b, R2a, R2b to produce the composite signal C1' that is applied to the image processor in step 74.
  • the illustrated methods are repeated as further transmit beams are fired and further receive beams are acquired.
  • Figure 12 shows the manner in which the method of Figure 3 can be used with multiple transmit beams that traverse the region of interest.
  • four transmit beams T1-T4 of alternating polarity are used to acquire associated receive beams R1-R4 that are summed as shown to produce composite signals C1-C3.
  • three composite signals CI-C3 are acquired using only four transmit events.
  • Figure 13 shows t..&. manner in which the method of Figure 9 can be used with transmit beams that traverse the region of interest.
  • the advantage of fundamental component rejection is obtained without any substantial penalty in frame rate, since the summed receive signals are associated with spatially distinct transmit beams.
  • the receive beams associated with a single transmit beam may be combined to produce an intermediate combined beam aligned with the respective transmit beam.
  • This intermediate combined beam does not provide cancellation of fundamental or harmonic components, but it may be useful in various frequency compounding techniques.
  • FIG 11 schematically shows an array of transmit beams T1-T7 that can be used in the methods described above.
  • the focal range RF is illustrated, and the separation between adjacent transmit beams is indicated by the symbol SB.
  • the Nyquist spacing i.e. the beam spacing required for Nyquist sampling
  • the beam spacing SB is equal to the Nyquist spacing SN
  • an associated azimuthal resolution and level of fundamental component suppression will be obtained. If the transmit beams are positioned more closely together such that the ratio SB/SN is less than one, the level of fundamental suppression will be improved in the composite signals at the expense of increased time to acquire a frame of image data.
  • the ratio SB SN can be made greater or less than one-half.
  • the ratio S B SN can be made greater than one such that the azimuthal dimension is sampled with a spacing greater than the Nyquist spacing SN. In this case, the time required to acquire a frame is reduced, but the level of suppression of the fundamental component in the composite signal is reduced. Relationships between the beam spacing SB and the Nyquist spacing SN described above can be applied either at the focal range RF or ranges spaced from the focal range RF.
  • the fundamental components of the receive beams in general will not be perfectly cancelled due to the fact that the associated transmit beams are spatially distinct, and therefore the phase difference between the fundamental components of the summed receive beams will often be substantially different than 180° such as 180° ⁇ 30° or 180° ⁇ 45°.
  • the method described above allows a trade-off between frame rate and degree of fundamental rejection in the composite signal.
  • the positive and negative polarity ultrasound lines can approach each other by increasing line density and thereby increasing the rejection of the fundamental component in the composite signal.
  • the alternating line phase embodiments described above alternate the polarity of the phase of the transmit beam across scan lines. Coherent combination of the pre-detection receive beams cancels fundamental signals and enhances second harmonic signals, thereby allowing an increase in axial resolution. This technique offers a tradeoff between additional rejection of the fundamental component and frame rate as a function of the selected line density. When operated at Nyquist line spacing, the alternating line phase technique described above can provide additional rejection at up to two times the frame rate of conventional two-pulse techniques.
  • the alternating line phase techniques can be used (1) to create combined beams that cancel fundamental components and enhance even harmonic components, as described above (by adding the respective receive beams), or (2) to create combined beams that cancel even harmonic components and enhance fundamental components (by subtracting the respective receive beams).
  • two different combined beams may be generated from a single set of receive beams, one combined beam emphasizing even harmonic components and the other combined beam emphasizing odd harmonic components.
  • Such combined beams can be compounded to reduce speckle effects.
  • receive signals Y1 , Y2 associated with differently- phased transmit beams T1 , T2 may be combined by addition (to emphasize the even harmonic components) or by subtraction (to emphasize the fundamental components).
  • Other combinations of Y1 and Y2 are possible, as described for example in Bradley U.S. Patent Application Serial No. 60/095,768, filed August 7, 1998, assigned to the assignee of this invention and hereby incorporated by reference in its entirety.
  • the combined signal Zn can take the form
  • Zn
  • Zi corresponds to the first harmonic compcr ent;
  • Z 2 corresponds to a compounded combination of the fundamental and first harmonic components.
  • combining is intended broadly to encompass both linear and nonlinear combinations, including the examples set out above as well as other useful combinations of receive signals or beams.
  • alternating line phase techniques described above can be implemented using a SequoiaTM ultrasonic imaging system available from Acuson Corporation, Mountainview, California, using an
  • the SequoiaTM imaging system can be programmed with the following scan parameters, transmit f number - 1.85 transmit apodization - half circle receive f number - 1.00 receive apodization - uniform transmit center frequency - 3.5 MHz receive center frequency - 7.0 MHz transmit focus - 25 mm receive focus - 10-25 mm Or course, all of these parameters can readily be modified as desired, depending on the application.
  • the transmit aperture, the receive aperture, or both can be alternated across scan lines. Coherent combination of at least two of the pre-detection receive beams forms a synthetic aperture sum which may increase lateral resolution.
  • the alternate apertures may be left/right, inside/outside, even/odd elements of the transducer, or other variations.
  • transmit beams T1-T4 and receive beams R1-R4 can be created in the geometry shown in Figure 12 discussed above. Adjacent receive beams R1-R2, R2-R3, R3-R4 can be combined to produce composite beams C1 , C2 and C3.
  • the system 10 of Figure 1 can be used to implement these alternating line embodiments.
  • the transmit beams T1 -T4 can be all of the same polarity, rather than of alternating polarity as described above in conjunction with Figure 12.
  • the transmit beams can be provided with a transmit aperture 100 that is centered on the origin 102 of the respective transmit beam. As the origins 102 shift laterally for successive transmit beams, the transmit apertures 100 are shifted in a similar manner.
  • the receive beams can be considered to be of two types which alternate across the region being imaged. These two types differ in receive aperture.
  • receive beams of the first type R1, R3, Certainly are acquired with a receive aperture 104 at the left side of the transducer
  • receive beams of the second type R2, R4, ...) are acquired with a receive aperture 106 at the right side of the transducer.
  • the left and right receive apertures 104, 106 may translate across the face of the transducer to follow the origin of the respective receive beams, as shown in Figure 16.
  • Figure 16 shows one of the receive apertures wrapping from right to left in receive line R2, though such wrapping is not required.
  • Figure 17 and 18 relate to alternative embodiments in which the receive aperture is divided into an inside portion 108 and two outside portions 110.
  • the receive beams of the first type are acquired using the inside receive aperture 108
  • receive beams of the second type are acquired using the outside receive aperture 110.
  • the inside and outside receive apertures 108, 110 can be moved across the face of the transducer so as to remain centered on the origin of the respective receive lines, with or without wrapping.
  • apertures may be used for the two or more receive apertures associated with respective receive beams.
  • even transducer elements may be used for a first receive aperture 108 for receive beams of the first type
  • odd transducer elements may be used for a second receive aperture 110 for receive beams of the second type.
  • the receive beams that are combined to create the composite beams are of differing types, and the combined beams are therefore characterized by a synthetic aperture that includes signal information associated with multiple apertures (e.g., left/right, inside/outside, or even/odd) in the various embodiments discussed above.
  • the Acuson SequoiaTM ultrasonic imaging system can be used with an Acuson 8L5 transducer to implement the alternating line aperture embodiments described above.
  • the following scan parameters can be used: transmit f number 2.0 transr.. ' .L apodization half circle receive f number 1.0 receive apodization uniform transmit focus 25 mm receive focus 10-25 mm
  • the transmit aperture may also be varied between the first and second types of receive beams, and in some cases more than two types of beams will be appropriate.
  • three different receive apertures can be provided, and three receive beams (one from each aperture type) can be coherently summed to create a synthetic aperture combined beam.
  • the location of the transmit focus is alternated across scan lines.
  • Coherent combination of the associated receive beams forms a composite beam with improved transmit depth of field at higher frame rates as compared to standard sequential focusing methods, in which multiple segmented portions of an image are acquired with separate respective transmit beams are stitched together.
  • Figure 20 shows a schematic view of a beam acquisition method similar to that of Figure 12.
  • the transmit focus 112, 114 is indicated by a dark triangle.
  • transmit beams of the first type T1, T3, ...) are characterized by a relatively distant transmit focus 112
  • transmit beams of the second type T2, T4, ...) are characterized by a relatively shallow transmit focus 114.
  • Receive beams R1-R2, R2-R3, R3-R4, ... are combined, and in each case the combined receive beams are associated with transmit beams of the first type as well as transmit beams of the second type.
  • the resulting composite beams C1, C2, C3 ... have an improved transmit depth of field.
  • FIG. 21 shows an embodiment of this invention in which the receive lines of the first type (R1 , R3, ...) are acquired with a frequency of operation f1 , while receive beams of a second type (R2, R4, ...) are acquired with a frequency of operation f2.
  • Adjacent receive beams of the first and second type are coherently combined to produce composite beams C1, C2, C3, ... having an increased bandwidth, as shown in Figure 22.
  • the bandwidth of the receive beams of the first and second types are shown at 115, 116, respectively, and the bandwidth of the composite beams is shown at 117. This advantage of a large bandwidth for the composite beams is obtained at a high frame rate.
  • the alternating line frequency embodiments can also implement a multiple receive beam acquisition scheme similar to that of Figure 13, in which multiple receive beams are acquired in response to each respective transmit beam.
  • inventions of this invention transmit a set of ultrasonic transmit beams into a region, including in some cases spatially aligned transmit beams.
  • Fundamental components of selected transmit beams are characterized by a phase difference of 180°.
  • Ultrasonic receive beams are acquired from the region, and multiple receive beams are associated with each respective one of the transmit beams. At least two receive beams are summed to form a composite signal, and the phase difference in the fundamental transmit components is effective to cause fundamental components of the receive beams to destructively interfere to a greater extent than harmonic components of the receive beams. In some embodiments, three or more receive beams are summed to form the composite signal.
  • the system of Figure 1 can be used to practice the methods of Figures 9 and 10 with spatially aligned transmit beams.
  • Figure 23 shows a flowchart of another embodiment of the method of this invention.
  • a first transmit beam T1 (positive polarity) is transmitted along a first azimuthal direction in step 140, and in step 142 two spatially distinct receive beams R1a, R1b are received.
  • receive beams R1a and R1b are offset on respective sides of the azimuthal direction of the transmit beam T1.
  • a second transmit beam T2 (negative polarity) is transmitted along the same azimuthal direction as transmit beam T1, and in step 146 two receive beams R2a, R2b are received.
  • receive beams R1a, R2a are spatially aligned and receive beams R1b, R2b are spatially aligned.
  • step 148 spatially aligned receive beams R1a, R2a are summed and spatially aligned receive beams R1b, R2b are separately summed to form composite signals C1 , C2 respectively.
  • step 150 the composite signals C1 , C2 are applied to the image processor.
  • both transmit phase and receive aperture are alternated among beams, using either sequential or simultaneous alternation techniques.
  • left and right receive apertures are alternated with a positive transmit polarity phase over two scan lines, and then left and right receive apertures are alternated with negative transmit polarity over the next two scan lines, and all four scan lines are coherently summed to create the composite beam.
  • a positive transmit polarity pulse/left (or inside or even element) receive aperture configuration is alternated with a negative transmit polarity pulse/right (or outside or odd element) receive aperture, and two scan lines are coherently summed to create the composite beam.
  • Simultaneous alteration techniques are preferred for two or more alternating parameters if there is little or no interaction between or among the parameters.
  • the line density controls the resulting performance level and frame rate.
  • each of the proposed modes and combinations described above can be programmed to have the same frame rate advantage; however, performance can be improved since common receive lines can be coincident yet multiple coincident transmit lines are avoided to eliminate any unnecessary decrease in the frame rate. This can offer advantages when tissue motion is an issue, as in cardiology applications.
  • selected pre-detection receive beams are coherently combined.
  • Coherent combination is discussed extensively in the above-identified U.S. Patent 5,667,373, assigned to the assignee of this invention, and the entirety of the disclosure of this patent is hereby incorporated by reference for its teaching regarding alternative forms of coherent combination.
  • the methods described above can be used both in situations where a non-linear contrast agent is introduced into the region of interest as well as in situations in which the region of interest is maintained free of added non-linear contrast agent.
  • the methods described above can be used during a medical diagnostic examination session in which the subject is maintained free of added non-linear contrast agent during the entire session. ln this case, the harmonic components described above are generated by natural processes associated with the propagation of ultrasound through body tissues.
  • the transmit beamformer 12 and the receive beamformer 18 can be made to operate using any suitable architecture, including both analog and digital architectures.
  • the beamformers 12, 18 can also be of the simultaneous multi-beam transmit-multi beam receive, particularly where simultaneous transmit beams are widely spaced.
  • the transducer array 14 can be a one-dimensional, 1.5 dimensional or 2 dimensional array, flat or curved, and of either constant or varying thickness.
  • the transmit beams can be formed of transmit waveforms of the widest variety of shapes including unipolar and bipolar pulses, with or without smoothly rising and falling envelopes. Sinusoidal, square wave or multi-level square wave techniques can be used.
  • the waveform generator 20 and the focus delay 22 can vary widely in complexity and sophistication.
  • the phase inverter 24 can operate in an analog or digital fashion, and it can be implemented by delays, phase rotations or phase inversions.
  • the controller 26 can be included as part of the transmit beamformer 12; alternately the phase inverter 24 can be implemented separately from the transmit beamformer 12. The controller 26 may control the phase inverter 24 without controlling other e!:,ments of the system.
  • the line buffer 28 and the summer 30 can be implemented as analog or digital systems, and the line buffer 28 may correspond to a digital memory for multiple receive beams.
  • the methods described above can be implemented over a full frame of image data or part of a frame, and they can be used with a wide variety of ultrasonic imaging signals including B mode signals, Doppler signals and the like. Though the examples described above emphasize second harmonic components, this invention is not limited to use with second harmonic signals.
  • harmonic is intended broadly to encompass any non-linear echo signal, including sub-harmonics, fractional harmonics and integral harmonics of 2 and greater.
  • the present invention can be used with any suitable scan line geometry, including sector, Vector®, and parallel beam geometries, for example.
  • scan parameter is intended broadly to encompass transmit and/or receive parameters other than beam steering direction and beam origin.
  • spatially distinct is intended broadly to encompass transmit lines that are spatially distinct in azimuth, in elevation, or both. With respect to the embodiments described above that utilize transmit beams which are entirely spatially distinct from one another, it may be desirable to fire additional transmit beams which are spatially aligned with previously fired transmit beams.

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  • Engineering & Computer Science (AREA)
  • Physics & Mathematics (AREA)
  • Radar, Positioning & Navigation (AREA)
  • Remote Sensing (AREA)
  • Computer Networks & Wireless Communication (AREA)
  • General Physics & Mathematics (AREA)
  • Acoustics & Sound (AREA)
  • Nonlinear Science (AREA)
  • Ultra Sonic Daignosis Equipment (AREA)

Abstract

L'invention concerne un système (10) d'imagerie médicale de diagnostic par ultrasons qui capte des faisceaux de réception à partir de faisceaux (40) d'émission spatialement distincts. Les faisceaux de réception sont alternés entre au moins un premier et un second type (42, 46) sur la largeur de la région visualisée. Le premier et le second type de faisceaux de réception diffèrent en au moins un paramètre de balayage autre que la géométrie des lignes d'émission et de réception. Ils peuvent par exemple présenter une différence au niveau de la phase d'émission, de l'ouverture d'émission ou de réception, de la fréquence de réseau ou du foyer d'émission. Les faisceaux de réception de prédétection associés à des faisceaux d'émission spatialement distincts (comprenant au moins un faisceau du premier type et au moins un faisceau du second type) sont de préférence combinés (48) de manière cohérente. On peut ainsi utiliser des techniques d'inversion de phase à deux impulsions, des techniques d'ouverture synthétique, des techniques de fréquence synthétique et des techniques de focalisation synthétique tout en réduisant sensiblement le ralentissement de la cadence d'image habituellement associé à ces techniques.
PCT/US1998/026879 1997-12-18 1998-12-18 Procede et systeme d'imagerie de diagnostic par ultrasons avec cadence d'images amelioree WO1999030617A1 (fr)

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US99353397A 1997-12-18 1997-12-18
US08/993,533 1997-12-18
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Cited By (9)

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US6186950B1 (en) 1999-11-04 2001-02-13 Atl Ultrasound Ultrasonic pulse inversion harmonic separation with reduced motional effects
US6193662B1 (en) 1999-02-17 2001-02-27 Atl Ultrasound High frame rate pulse inversion harmonic ultrasonic diagnostic imaging system
US6228031B1 (en) * 1999-02-17 2001-05-08 Atl Ultrasound High frame rate ultrasonic diagnostic imaging systems with motion artifact reduction
US6315723B1 (en) 1999-10-08 2001-11-13 Atl Ultrasound Ultrasonic diagnostic imaging system with synthesized transmit focus
US6432056B1 (en) 1999-10-08 2002-08-13 Atl Ultrasound Ultrasonic diagnostic imaging system with high frame rate synthetic transmit focus
EP1249208A1 (fr) * 2000-11-15 2002-10-16 Aloka Co., Ltd. Dispositif de diagnostic ultrasonore
USRE43048E1 (en) 1995-10-10 2011-12-27 Advanced Technology Laboratories, Inc. Ultrasonic diagnostic imaging with harmonic contrast agents
WO2015191871A1 (fr) * 2014-06-11 2015-12-17 The Johns Hopkins University Système à ultrasons à ouverture synthétique
EP3017767A1 (fr) * 2014-11-06 2016-05-11 Samsung Medison Co., Ltd. Appareil de diagnostic ultrasonique et son procédé de contrôle

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Cited By (12)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
USRE43048E1 (en) 1995-10-10 2011-12-27 Advanced Technology Laboratories, Inc. Ultrasonic diagnostic imaging with harmonic contrast agents
US6193662B1 (en) 1999-02-17 2001-02-27 Atl Ultrasound High frame rate pulse inversion harmonic ultrasonic diagnostic imaging system
US6228031B1 (en) * 1999-02-17 2001-05-08 Atl Ultrasound High frame rate ultrasonic diagnostic imaging systems with motion artifact reduction
US6315723B1 (en) 1999-10-08 2001-11-13 Atl Ultrasound Ultrasonic diagnostic imaging system with synthesized transmit focus
US6432056B1 (en) 1999-10-08 2002-08-13 Atl Ultrasound Ultrasonic diagnostic imaging system with high frame rate synthetic transmit focus
US6186950B1 (en) 1999-11-04 2001-02-13 Atl Ultrasound Ultrasonic pulse inversion harmonic separation with reduced motional effects
EP1249208A1 (fr) * 2000-11-15 2002-10-16 Aloka Co., Ltd. Dispositif de diagnostic ultrasonore
EP1249208A4 (fr) * 2000-11-15 2005-05-04 Aloka Co Ltd Dispositif de diagnostic ultrasonore
WO2015191871A1 (fr) * 2014-06-11 2015-12-17 The Johns Hopkins University Système à ultrasons à ouverture synthétique
US10349917B2 (en) 2014-06-11 2019-07-16 The Johns Hopkins University Synthetic aperture ultrasound system
EP3017767A1 (fr) * 2014-11-06 2016-05-11 Samsung Medison Co., Ltd. Appareil de diagnostic ultrasonique et son procédé de contrôle
US10012724B2 (en) 2014-11-06 2018-07-03 Samsung Medison Co., Ltd. Ultrasonic diagnostic apparatus and method of controlling the same

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