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WO2012035472A1 - Quantification de déformation de tissu dans des images d'élastographie ultrasonore - Google Patents

Quantification de déformation de tissu dans des images d'élastographie ultrasonore Download PDF

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Publication number
WO2012035472A1
WO2012035472A1 PCT/IB2011/053938 IB2011053938W WO2012035472A1 WO 2012035472 A1 WO2012035472 A1 WO 2012035472A1 IB 2011053938 W IB2011053938 W IB 2011053938W WO 2012035472 A1 WO2012035472 A1 WO 2012035472A1
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WO
WIPO (PCT)
Prior art keywords
strain
roi
probe
curve
image
Prior art date
Application number
PCT/IB2011/053938
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English (en)
Inventor
Alwyn Patrick D'sa
Junzheng Man
Original Assignee
Koninklijke Philips Electronics N.V.
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 N.V. filed Critical Koninklijke Philips Electronics N.V.
Publication of WO2012035472A1 publication Critical patent/WO2012035472A1/fr

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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
    • A61B8/485—Diagnostic techniques involving measuring strain or elastic properties
    • 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
    • G01S7/52042—Details of receivers using analysis of echo signal for target characterisation determining elastic properties of the propagation medium or of the reflective target
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/08—Detecting organic movements or changes, e.g. tumours, cysts, swellings
    • A61B8/0825—Detecting organic movements or changes, e.g. tumours, cysts, swellings for diagnosis of the breast, e.g. mammography
    • 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
    • A61B8/467—Ultrasonic, sonic or infrasonic diagnostic devices with special arrangements for interfacing with the operator or the patient characterised by special input means
    • A61B8/469—Ultrasonic, sonic or infrasonic diagnostic devices with special arrangements for interfacing with the operator or the patient characterised by special input means for selection of a region of interest
    • 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
    • G01S7/52073—Production of cursor lines, markers or indicia by electronic means
    • 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
    • G01S7/52074—Composite displays, e.g. split-screen displays; Combination of multiple images or of images and alphanumeric tabular information

Definitions

  • This invention relates to medical diagnostic ultrasound systems and, in particular, to ultrasound systems which assess the stiffness of tissue regions in the body by elastography .
  • Elastography is the assessment of the elastic properties of tissue in the body. It has been found that the stiffness of tissue in the body can give an indication of whether the tissue may be malignant or benign.
  • the female breast for instance, can contain a variety of different lumps, cysts, and other growths, some of which may be malignant and some of which may be benign.
  • ultrasound is frequently used to assess tissue characteristics to determine whether to biopsy suspect tissue.
  • Elastography can be performed to determine whether the breast contains softer or harder (stiffer) regions. Since stiffer tissue correlates more greatly with malignant masses, the identification of regions of stiffer tissue can indicate a need to make a definitive diagnosis by biopsy.
  • a problem posed by elastography is the need to accurately and reproducibly measure quantifiable properties of tissue non-invasively within the body. This means that the properties of the target tissue cannot be measured directly at the site of the tissue, but only through measurements made at the surface of the body through intervening tissues.
  • Poisson's ratio is the ratio, when a sample is stretched or
  • Young's modulus which is a measure of stiffness, and is defined as the ratio of the
  • the stress component at target tissue is generally unknown and difficult to measure non- invasively .
  • strain deformation
  • strain of a reference point can be used to normalize strain of a target region.
  • a strain ratio between normal tissue and tumor can indicate their relative stiffness, assuming similar pressure between two regions within a
  • tissue stiffness is quantified by acquiring and analyzing a sequence of strain (elastography) images as the compressive force applied to the body is varied.
  • the sequence of strain images is used to compute a curve or profile of the strain rate variation over a time interval of compressive force variance.
  • the strain rate data is then used to compute a curve or profile of total (cumulative) strain over the time interval of compressive force variance.
  • the maximum or peak values of total (cumulative) strain curves are repeatable even though the technique used to apply the compressive force may vary from one procedure to another .
  • FIGURE 1 illustrates in block diagram form an ultrasonic diagnostic imaging system constructed in accordance with the principles of the present
  • FIGURE 2 illustrates the steps of a method for producing a quantified measure of manually induced strain .
  • FIGURE 3 illustrates an ultrasound image of a region of interest (ROI) of a target tissue mass in a tissue-mimicking phantom.
  • ROI region of interest
  • FIGURE 4 illustrates one of a plurality of elastography images of the ROI obtained during image acquisition as a variable pressure is applied to compress the target with an ultrasound probe.
  • FIGURE 5 illustrates instantaneous mean strain and strain rate versus time curves calculated from the elastogram data of an identified ROI.
  • FIGURES 5-8 the B mode ultrasound image of the ROI is shown on the left of the image display and the elastogram is displayed on the right.
  • FIGURE 6 illustrates total (cumulative) strain versus time curves for hard (stiff) tissue and softer background tissue.
  • FIGURE 7 illustrates strain rate versus time curves produced from image data acquired during rapid tissue compression.
  • FIGURE 8 illustrates total (cumulative) strain versus time curves calculated using the rapidly acquired compression data of FIGURE 7.
  • An ultrasound probe 10 has an array transducer 12 for transmitting ultrasound waves to and receiving echoes from a region of the body.
  • the array is shown in block diagram form.
  • transducer can be a one-dimensional array of
  • transducer elements or a two-dimensional array of transducer elements for scanning a two dimensional image field or a three dimensional image field in the body.
  • the elements of the array transducer are driven by a transmit beamformer 16 which controls the steering, focusing and penetration of transmit beams from the array.
  • a receive beamformer 18 receives echoes from the transducer elements and combines them to form coherent echo signals from points in the image field.
  • the transmit and receive beamformers are coupled to the transducer array elements by transmit/receive switches 14 which protect sensitive receive circuitry during transmission.
  • a beamformer controller 20 synchronizes and controls the operation of the beamformers.
  • the received echo signals are demodulated into quadrature (I and Q) samples by a quadrature bandpass (QBP) filter 22.
  • the QBP filter can also provide band limiting and bandpass filtering of the received signals.
  • the received signals may then undergo further signal processing such as harmonic separation and frequency or spatial compounding by a signal processor 24.
  • the processed echo signals are applied to a detector 25 which performs amplitude detection of the echo signals by the equation ( I 2 + Q 2 ) 112 for a B mode processor 26, and to a Doppler processor 28 for Doppler phase detection of tissue motion at points in the image field.
  • the outputs of the B mode processor 26 and the Doppler processor 28 are coupled to a frame memory or buffer 30 for storage.
  • the frame memory stores consecutive scans of the image field on a spatial basis for the calculation of strain by a strain estimator 32 from the frame-to-frame
  • strain is calculated as a spatial derivative of
  • radiofrequency (r.f.) or baseband I and Q data may also be calculated from amplitude-detected (B mode) or tissue Doppler data.
  • Any form of strain calculation such as strain, the ratio of lateral to axial strain, and strain velocity estimation may be employed.
  • the echoes received at a common point in consecutive frames may be correlated to estimate displacement at the point. If no motion is present at the point, the echoes from consecutive frames will be the same. If motion is present, the echoes will be different and the motion vector indicates the displacement.
  • US Pat. 6,558,324 (Von Behren et al . ) describes both amplitude and phase sensitive techniques for estimating strain and employs speckle tracking for strain estimation through block matching and correlation.
  • the tissue displacement is caused by varying the pressure applied to the body by the probe.
  • Any other type of compression source can alternatively be used, including mechanical vibration or acoustic radiation force impulse.
  • compression applied by varying the force of the probe against the body is preferred as it requires no additional devices or special pulse transmissions.
  • Another reason for the preference of strain estimation with phase-sensitive techniques is that the slight motion produced by small, virtually imperceptible motion occurring while holding a probe against the body can be sensed and used to estimate strain by the strain estimator 32.
  • the strain estimator 32 produces an estimated strain value at each point in the image field which are spatially arranged to form a strain image or elastogram.
  • a sequence of such elastograms are produced from successive images acquired during probe pressure variation and stored as time-sequential strain images of the image field at 34.
  • the strain image data is coupled to a strain rate curve calculator 36.
  • the calculator 36 produces a strain rate curve in a two-step process, first producing an instantaneous mean strain curve for an ROI, then scaling this data by the system pulse repetition frequency (PRF) to produce a strain rate versus time curve.
  • PRF system pulse repetition frequency
  • the strain rate data is applied to a total (cumulative) strain curve calculator 38, which produces a total strain curve that yields a
  • the B mode and strain image are coupled to an image processor 42, as well as the calculated curves, for production of images on a display 50.
  • FIGURE 2 illustrates a method for producing a quantified measure of tissue stiffness in accordance with the present invention using the ultrasound system of FIGURE 1.
  • the ultrasound probe 10 is placed against the body over an ROI and pressed against the body with a varying force to cause deformation of the tissue of the underlying ROI.
  • the pressure of the probe can be gradually increased so that the tissue within the ROI is fully deformed with the application of maximum reasonable force, or a maximum force can be applied, then decreased
  • the ultrasound system is triggered to store a sequence of elastography images in the frame buffer 30.
  • Triggering can be done by the equivalent techniques of triggering the start of storage in the buffer, or running the images through the buffer continuously as a first-in, first-out buffer, then triggering the buffer to stop running and retain the immediately preceding sequence of images in the buffer.
  • the frame buffer can store up to twenty seconds of continuous image frames as the tissue is variably compressed with the probe. It is customary to acquire and store the images in a side- by-side format where the ultrasound image is displayed on the left of the screen and the
  • elastography image is displayed on the right or in a single image display format where the elastography image is overlaid on top of the ultrasound image.
  • the clinician may review the image frames stored in the buffer and delete (trim) frames acquired prior to or after the probe pressure was variably applied. For example, if several seconds elapsed during triggered acquisition before the clinician started to increase the probe pressure, frames acquired during that time may be eliminated from storage.
  • elastogram images are produced from the sequence of images stored in the buffer. From the elastogram images and also the B mode images, the clinician identifies an ROI at 66 for which stiffness is to be quantified. This may be done by placing a ROI delineator of the desired size and shape, such as a circle, over a tissue mass seen in the elastogram image. Alternatively the ROI may be identified by tracing its outline by freehand tracing.
  • the outline of the ROI may be placed slightly inside the apparent boundary of the mass to capture only suspect tissue and no normal tissue in the ROI for the subsequent stiffness measurement.
  • the ROI tracks the motion of the tissue mass from frame-to-frame to compensate for tissue motion resulting from patient breathing, probe movement, etc. during image acquisition.
  • a mean instantaneous strain curve is calculated from the strain data encompassed within the identified ROI.
  • a strain rate curve is calculated from the mean strain data.
  • the total (cumulative) strain curve is computed and displayed for the duration of the tissue pressure variation.
  • FIGURE 3 shows a two-dimensional B mode ultrasound image of a region of a phantom which contains a hard (stiff) tissue- mimicking target 80.
  • the circular hard target 80 is barely visible against the simulated normal
  • the clinician has placed small calipers at the top and bottom of the hard target to measure its size which, in this example is 1.12 cm as shown below the image.
  • the clinician triggers acquisition to store a sequence of elastography images as pressure is gradually applied with the probe. As the probe pressure is continually
  • the white bar 82 below the image begins to fill with color or extend to the right as the acquired elastography images fill the image buffer.
  • the buffer bar 82 indicates the remaining capacity of the buffer and hence the time remaining during which images can be acquired and stored as pressure is varied.
  • a marker 84 moves along the buffer bar 82 to indicate the location in the image sequence of the image currently displayed on the screen.
  • each strain image indicates the net deformation of tissue at each point in the image from one frame to the next.
  • this can be done in a variety of ways, such as by integrating the velocity (Doppler phase shift) values for common points between successive images or identifying the
  • FIGURE 4 An elastogram 86, overlaid over the B mode image, is shown in FIGURE 4 with the hard target 88 shown as a different color than that of the background tissue surrounding it.
  • FIGURE 5 shows two circles 88' and 90 which identify ROIs in the elastogram 86 at the top of the screen. To the left of the elastogram 86 is the corresponding B mode image.
  • the circle 90 identifies the hard tissue mass in the image and encompasses most of the pixels of the mass.
  • the circle 90 identifies an ROI of normal tissue to the left of the mass.
  • Mean instantaneous strain curves 92 and 94 are shown for the pixel values encompassed in the ROI circles for the sequence of elastograms. This is done by summing and averaging all of the strain values (pixel color values) in the ROI for each elastogram in the sequence, then expressing the change from one frame to the next as a percentage.
  • the tissue points in a ROI had a mean location of 1.00 cm in one frame and a mean location of 1.04 cm in the next frame
  • the percentage change from one frame to the next would be 0.04 cm divided by 1.00 cm times 100% which yields a 4% change.
  • the scaled curves are of the same shape as those of FIGURE 5 but of larger values of the percentage change in strain per second, or the strain rate as a function of time as shown by the x-axis in FIGURE 5.
  • the curves 92 and 94 for the ROIs show peak values at the time of maximum applied probe pressure, and decline thereafter as the probe pressure is
  • the normal tissue total strain curve 98 reaches a plateau level of around 7.8%, and the hard tissue total strain curve reaches a plateau level of around 3.4%.
  • deformation of the hard ROI and the normal tissue is dependent upon the relative elasticity of their respective materials and is quantified by these measures .
  • FIGURES 7 and 8 illustrate that the total
  • FIGURE 7 shows the pressure applied with the probe for a very short duration
  • FIGURE 7 the probe pressure is applied in a span of about one second and then maintained, compared with the five seconds of pressure increase seen in FIGURE 5.
  • the strain rate curves 192 and 194 in FIGURE 7 are seen to rapidly rise, then fall, as the probe pressure is applied and maintained at its maximum level.
  • the resultant total strain curves 196 and 198 are calculated for the hard and normal tissues as shown in FIGURE 8, it is seen that each curve quickly rises as pressure is applied and thereafter maintains its maximum
  • the present invention may be implemented on an ultrasound cart as part of the ultrasound image acquisition and processing system, or may be

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Abstract

L'invention porte sur un système d'imagerie de diagnostic ultrasonore qui acquiert une séquence d'images d'élastographie (élastogrammes) à l'aide d'une sonde puisque la sonde est utilisée pour faire varier la pression et comprimer une région d'intérêt (ROI) d'une masse anatomique à l'intérieur du corps. Une région d'intérêt est identifiée dans l'une des images de la séquence acquise d'élastogrammes. Le changement moyen de déformation d'une trame d'image à la suivante à l'intérieur de la région d'intérêt est calculé sur l'intervalle sur lequel la région d'intérêt est comprimée de manière variable, par exemple, d'un niveau minimal de départ de pression à un niveau maximal final. Ce résultat intermédiaire est utilisé pour produire la vitesse de déformation. La déformation totale ou cumulée est ensuite calculée sur l'intervalle de compression pour produire une courbe ou un profil de la déformation totale dans la ROI. Le niveau final de la courbe ou du profil de déformation totale est une mesure de la rigidité du tissu de la ROI.
PCT/IB2011/053938 2010-09-16 2011-09-09 Quantification de déformation de tissu dans des images d'élastographie ultrasonore WO2012035472A1 (fr)

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US61/383,646 2010-09-16

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Cited By (14)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN102626327A (zh) * 2012-04-26 2012-08-08 声泰特（成都）科技有限公司 基于接收端空间复合的超声弹性成像及压力反馈方法
WO2014013366A1 (fr) * 2012-07-18 2014-01-23 Koninklijke Philips N.V. Procédé et système de traitement de données d'imagerie ultrasonore
US8971990B2 (en) 2012-12-21 2015-03-03 General Electric Company Systems and methods for nonlinear elastography
CN104470443A (zh) * 2012-07-18 2015-03-25 皇家飞利浦有限公司 用于处理超声成像数据的方法和系统
JP2018020107A (ja) * 2016-07-22 2018-02-08 東芝メディカルシステムズ株式会社 解析装置及び解析プログラム
WO2020172636A3 (fr) * 2019-02-22 2020-10-22 California Institute Of Technology Systèmes et procédés de tomographie photoacoustique (pact)
US11020006B2 (en) 2012-10-18 2021-06-01 California Institute Of Technology Transcranial photoacoustic/thermoacoustic tomography brain imaging informed by adjunct image data
US11029287B2 (en) 2011-02-11 2021-06-08 California Institute Of Technology Multi-focus optical-resolution photoacoustic microscopy with ultrasonic array detection
US11137375B2 (en) 2013-11-19 2021-10-05 California Institute Of Technology Systems and methods of grueneisen-relaxation photoacoustic microscopy and photoacoustic wavefront shaping
US11369280B2 (en) 2019-03-01 2022-06-28 California Institute Of Technology Velocity-matched ultrasonic tagging in photoacoustic flowgraphy
US11530979B2 (en) 2018-08-14 2022-12-20 California Institute Of Technology Multifocal photoacoustic microscopy through an ergodic relay
US11592652B2 (en) 2018-09-04 2023-02-28 California Institute Of Technology Enhanced-resolution infrared photoacoustic microscopy and spectroscopy
US11672426B2 (en) 2017-05-10 2023-06-13 California Institute Of Technology Snapshot photoacoustic photography using an ergodic relay
US11986269B2 (en) 2019-11-05 2024-05-21 California Institute Of Technology Spatiotemporal antialiasing in photoacoustic computed tomography

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Cited By (18)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US12050201B2 (en) 2011-02-11 2024-07-30 California Institute Of Technology Multi-focus optical-resolution photoacoustic microscopy with ultrasonic array detection
US11029287B2 (en) 2011-02-11 2021-06-08 California Institute Of Technology Multi-focus optical-resolution photoacoustic microscopy with ultrasonic array detection
CN102626327A (zh) * 2012-04-26 2012-08-08 声泰特（成都）科技有限公司 基于接收端空间复合的超声弹性成像及压力反馈方法
US11020094B2 (en) 2012-07-18 2021-06-01 Koninklijke Philips N.V. Method and system for processing ultrasonic imaging data
WO2014013366A1 (fr) * 2012-07-18 2014-01-23 Koninklijke Philips N.V. Procédé et système de traitement de données d'imagerie ultrasonore
CN104470443A (zh) * 2012-07-18 2015-03-25 皇家飞利浦有限公司 用于处理超声成像数据的方法和系统
RU2636262C2 (ru) * 2012-07-18 2017-11-21 Конинклейке Филипс Н.В. Способ и система для обработки данных ультразвуковой визуализации
US11020006B2 (en) 2012-10-18 2021-06-01 California Institute Of Technology Transcranial photoacoustic/thermoacoustic tomography brain imaging informed by adjunct image data
US8971990B2 (en) 2012-12-21 2015-03-03 General Electric Company Systems and methods for nonlinear elastography
US11137375B2 (en) 2013-11-19 2021-10-05 California Institute Of Technology Systems and methods of grueneisen-relaxation photoacoustic microscopy and photoacoustic wavefront shaping
JP2018020107A (ja) * 2016-07-22 2018-02-08 東芝メディカルシステムズ株式会社 解析装置及び解析プログラム
JP7043193B2 (ja) 2016-07-22 2022-03-29 キヤノンメディカルシステムズ株式会社 解析装置、超音波診断装置、及び解析プログラム
US11672426B2 (en) 2017-05-10 2023-06-13 California Institute Of Technology Snapshot photoacoustic photography using an ergodic relay
US11530979B2 (en) 2018-08-14 2022-12-20 California Institute Of Technology Multifocal photoacoustic microscopy through an ergodic relay
US11592652B2 (en) 2018-09-04 2023-02-28 California Institute Of Technology Enhanced-resolution infrared photoacoustic microscopy and spectroscopy
WO2020172636A3 (fr) * 2019-02-22 2020-10-22 California Institute Of Technology Systèmes et procédés de tomographie photoacoustique (pact)
US11369280B2 (en) 2019-03-01 2022-06-28 California Institute Of Technology Velocity-matched ultrasonic tagging in photoacoustic flowgraphy
US11986269B2 (en) 2019-11-05 2024-05-21 California Institute Of Technology Spatiotemporal antialiasing in photoacoustic computed tomography

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