Surgery – Diagnostic testing – Detecting nuclear – electromagnetic – or ultrasonic radiation
Reexamination Certificate
1999-11-26
2001-08-21
Lateef, Marvin M. (Department: 3737)
Surgery
Diagnostic testing
Detecting nuclear, electromagnetic, or ultrasonic radiation
C600S447000
Reexamination Certificate
active
06277075
ABSTRACT:
FIELD OF THE INVENTION
This invention generally relates to ultrasound imaging of the human anatomy for the purpose of medical diagnosis. In particular, the invention relates to methods and apparatus for imaging blood vessel structures, and more particularly, to signal processing algorithms for visualization of blood movement for use in ultrasound imaging systems.
BACKGROUND OF THE INVENTION
Conventional color flow imaging, including “angio” or “power Doppler imaging” (referred to hereinafter as “flow imaging”), produces one image from a sequence of transmitted pulses (a packet), typically in the range of 5-15 pulses for each scan line in the image. Slowly moving muscular tissue produces lower Doppler shift in the received signal than signal from moving blood, and efficient clutter filters are designed to suppress the clutter signal to a level much lower than the signal from blood. The signal power after clutter filtering is used to detect points in the image where blood is present. An alternative is to display the signal power as an image (angio or power Doppler) to visualize blood vessels. In order to get reliable detection, substantial temporal and spatial averaging is used, thus limiting the dynamic variation, as well as spatial resolution (bleeding). This averaging process suppresses the spatial speckle pattern in the signal amplitude.
Conventional ultrasound blood flow imaging is based on detection and measurement of the Doppler shift created by moving scatterers. This Doppler shift is utilized to suppress the signal from slowly moving muscular tissue, in order to detect the presence of blood, and is also used to quantify the actual blood velocity in each point of an ultrasound image. Unfortunately, the Doppler frequency shift is only sensitive to the velocity component along the ultrasonic beam; possible velocity components transverse to the beam are not detected or measurable from the received signal Doppler spectrum. In standard color flow imaging, the Doppler shift is estimated from the received signal generated by a number of transmitted pulses, and coded in a color scale. In some situations, the blood flow direction can be measured from the vessel geometry, but this is difficult to do in an automatic way, especially when the vessel geometry is not clearly visible in the image. Standard color flow imaging often gives confusing blood velocity visualization; e.g., in a curved blood vessel the Doppler shift, and therefore also the color, is changing along the vessel due to change in the angle between the blood velocities and the ultrasonic beam, even though the velocity magnitude is constant. In power Doppler (also called the angio mode) this problem is solved by discarding the measured Doppler shift from the display.
There is considerable interest in measuring the transverse velocity component in ultrasound flow imaging, and a number of methods have been proposed. Compound scanning from two different positions was disclosed by Fox in “Multiple crossed-beam ultrasound Doppler velocimetry,” IEEE Trans. Sonics Ultrason., Vol.
25
, pp. 281-286, 1978. Compound scanning from two different positions gives two velocity components, but there are practical problems with the large-aperture transducer, the time lag between the measurement of the two components, and the limited field of view. In accordance with a method disclosed by Newhouse et al. in “Ultrasound Doppler probing of flows transverse with respect to beam axis,” IEEE Trans. Biomed. Eng., Vol.
34
, pp. 779-789, October 1987, the transit time through the ultrasound beam is measured, which is reflected in an increased bandwidth of the Doppler signal. This method has very low accuracy, does not yield flow direction, and will only work in regions with rectilinear and laminar flow. Two-dimensional speckle tracking methods based on frame-to-frame correlation analysis have been proposed by Trahey et al. in “Angle independent ultrasonic detection of blood flow,” IEEE Trans. Biomed. Eng., Vol. 34, pp. 965-967, December 1987. This method can be used both for the RF signal and the amplitude-detected signal. Coherent processing of two subapertures of the transducer to create lateral oscillations in the received beam pattern has been described by Jensen et al. in “A new method for estimation of velocity vectors,” IEEE Trans. Ultrason., Ferroelect., Freq. Contr., Vol. 45, pp. 837-851, May 1998, and by Anderson in “Multi-dimensional velocity estimation with ultrasound using spatial quadrature,” IEEE Trans. Ultrason., Ferroelect., Freq. Contr., Vol. 45, pp. 852-861, May 1998. This method gives quantitative lateral velocity information, including the sign. The main drawback of this method is poor lateral resolution, which limits its use for imaging.
There is a need for a method of ultrasound imaging which gives the system user a correct perception of the blood flow direction and magnitude, and which is also useful to separate true blood flow from wall motion artifacts.
SUMMARY OF THE INVENTION
In ultrasound imaging, the returned echoes are processed coherently. In the images there are variations in the intensity due to constructive and destructive interference of the sound waves scattered back from a large number of scatterers. These variations in the intensity is often termed the “speckle pattern”. When there is a slight displacement of the scatterers (red blood cells), there will be a corresponding displacement of the speckle pattern. By enhancing the speckle pattern from moving scatterers and display a stream of such images, an intuitive display of the blood flow is obtained.
The present invention comprises a method and an apparatus for imaging blood motion by preserving, enhancing and visualizing speckle pattern movement, which is related to the blood cell movement in the blood vessels. This method will be referred to herein as “blood motion imaging” (BMI). Speckle pattern movement gives the user a correct perception of the blood flow direction and magnitude, and is also useful to separate true blood flow from wall motion artifacts. In this way, the system operator can see the blood flowing in the image, although no attempt is made to measure the lateral velocity component. However, the lateral velocity component may be derived indirectly by combining an angle measurement derived from the speckle motion with the radial velocity component obtained from the Doppler frequency shift.
In the preferred embodiments of the invention, image frames of signal samples (i.e., raw acoustic data) are continuously acquired. The data input for signal processing are the beamformed and complex-demodulated I/Q data samples. Alternatively, the processing can be performed on the real-valued RF data without complex demodulation. A continuous stream of data frames, each the result of one scan, is available for processing. For each position in the scan plane (as used herein, “position” means one depth range from one beam), a respective time sequence of signal samples is available for processing. This signal is first high-pass filtered. Following the high-pass filter, a speckle signal is formed. One way of forming the speckle signal is by calculating the squared magnitude (i.e., power) of the high-pass-filtered signal (I/Q or RF). This speckle signal is then subjected to a nonlinear scale conversion to form a blood motion imaging (BMI) signal for display. An example of the nonlinear scale conversion is logarithmic compression followed by gain and dynamic range adjustment.
The motion of the blood scatterers creates a corresponding movement of the speckle pattern in the images from frame to frame, showing both radial and lateral movement. For continuous acquisition, the time between each of these frames equals the pulse repetition time (1/PRF). In order to visualize the motion, the display frame rate must be reduced substantially, e.g., from 1 kHz to 30 Hz. For real-time display, much data must be discarded, but for slow motion replay, a larger fraction or all of the recorded frames can be used. To get a sufficiently high PRF, the frame rate should be maxi
Bjaerum Steinar
Torp Hans Garmann
Cabou Christian G.
Flaherty Dennis M.
GE Medical Systems Global Technology Company LLC
Lateef Marvin M.
Patel Maulin
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