KR102022143B1 - Ultrasound system and method for adaptively compensating spectral downshift of signals - Google Patents
Ultrasound system and method for adaptively compensating spectral downshift of signals Download PDFInfo
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Abstract
An ultrasound system and method for adaptively compensating for spectral downshift of a signal is disclosed. The ultrasound system includes an ultrasound probe and a processor. The ultrasound probe transmits an ultrasound signal to the object and receives an ultrasound echo signal from the object. The processor forms a complex baseband signal comprising the same phase component signal and a quadrature phase component signal based on the ultrasonic echo signal, determines the phase shift and phase dispersion based on the complex baseband signal, and determines the phase shift and phase dispersion. The demodulated baseband signal is filtered by a dynamic filter to adaptively compensate for the spectral downshift of the ultrasonic echo signal.
Description
TECHNICAL FIELD The present disclosure relates to ultrasonic systems, and more particularly, to ultrasonic systems and methods for adaptively compensating for spectral downshift of a signal.
Ultrasound systems are widely used in the medical field to obtain information about objects of interest within an object. The ultrasound system may provide high resolution images of the subject in real time using high frequency sound waves, without the need for a surgical operation to directly incision the subject. Ultrasound systems have non-invasive and nondestructive properties and are widely used in the medical field.
The ultrasound system transmits an ultrasound signal to the object and receives an ultrasound signal (ie, an ultrasound echo signal) reflected from the object. In addition, the ultrasound system performs a beamforming process on the ultrasonic echo signal to form a received focus signal, performs a quadrature demodulation on the received focused signal to form a complex baseband signal, and complex complex An ultrasound image of the object is formed based on the band signal.
In general, when an ultrasound signal propagates to an object, the ultrasound signal is attenuated by the medium of the object. Due to the attenuation of the ultrasonic signal, a spectral (frequency) downshift occurs in the ultrasonic echo signal reflected from the medium of the object. Spectral downshift of the ultrasonic echo signal degrades the performance of orthogonal demodulation and degrades the image quality of the ultrasonic image.
To compensate for the spectral downshift of the ultrasonic echo signal, dynamic quadrature demodulation is used which dynamically adjusts the demodulation frequency and the cutoff frequency of the filter. However, dynamic orthogonal demodulation compensates for the spectral downshift of the ultrasound echo signal under the assumption that the medium in the object is uniform and the attenuation coefficients of the ultrasound echo signal are the same. Therefore, the dynamic orthogonal demodulation compensates for the spectral downshift even for the ultrasonic echo signal of the medium having a non-constant attenuation coefficient, thereby degrading the quality of the ultrasonic image.
The present disclosure provides an ultrasound system and method for forming a complex baseband signal based on an ultrasound echo signal from an object, and adaptively compensating for spectral downshift of the ultrasound echo signal based on the complex baseband signal.
In one embodiment, the ultrasound system includes an ultrasound probe and a processor. The ultrasound probe is configured to transmit an ultrasound signal to the object and receive an ultrasound echo signal from the object. The processor forms a complex baseband signal comprising the same phase component signal and a quadrature phase component signal based on the ultrasonic echo signal, determines the phase shift and phase dispersion based on the complex baseband signal, and determines the phase shift and phase dispersion. And filter the complex baseband signal by a dynamic filter to adaptively compensate for the spectral downshift of the ultrasonic echo signal based on that.
In another embodiment, a method for adaptively compensating for spectral downshift includes transmitting an ultrasound signal to an object and receiving an ultrasound echo signal from the object, and in-phase component signal and quadrature based on the ultrasound echo signal. Forming a complex baseband signal comprising a phase component signal, determining a phase shift and phase dispersion based on the complex baseband signal, and spectrally down the ultrasonic echo signal based on phase shift and phase dispersion Filtering the complex baseband signal by a dynamic filter to adaptively compensate for the shift.
According to the present disclosure, it is possible to determine (predict) the phase shift and the phase dispersion based on the ultrasonic echo signal of the object, and adaptively compensate for the spectral downshift of the ultrasonic echo signal based on the determined phase shift and the phase dispersion. Can be. Therefore, the image quality of the ultrasound image may be prevented from changing according to the attenuation coefficient of the medium in the object.
1 is a block diagram schematically showing the configuration of an ultrasound system according to an embodiment of the present disclosure.
2 is a block diagram schematically illustrating a configuration of a processor according to an embodiment of the present disclosure.
3 is a block diagram schematically illustrating a configuration of a signal processing unit according to a first embodiment of the present disclosure.
4 is a block diagram schematically illustrating a configuration of a complex baseband signal forming unit according to a first embodiment of the present disclosure.
5 shows examples of phase shift, phase dispersion, smoothed phase shift and smoothed phase dispersion in accordance with a first embodiment of the present disclosure;
6 is a block diagram schematically illustrating a configuration of a signal processing unit according to a second embodiment of the present disclosure.
7 is a block diagram schematically illustrating a configuration of an upmixing processing unit according to a second embodiment of the present disclosure.
Hereinafter, embodiments of the present disclosure will be described with reference to the accompanying drawings. As used herein, the term "unit" refers to software or hardware components such as software, field-programmable gate arrays (FPGAs), and application specific integrated circuits (ASICs). However, "part" is not limited to hardware and software. The "unit" may be configured to be in an addressable storage medium, and may be configured to play one or more processors. Thus, as an example, "parts" means components such as software components, object-oriented software components, class components, and task components, and processors, functions, properties, procedures, subroutines, program code. Includes segments, drivers, firmware, microcode, circuits, data, databases, data structures, tables, arrays, and variables. Functions provided within components and "parts" may be combined into a smaller number of components and "parts" or further separated into additional components and "parts".
1 is a block diagram schematically showing the configuration of an
The
The
The
The
The
2 is a block diagram schematically illustrating a configuration of a
The
The
The
The
The
3 is a block diagram schematically illustrating a configuration of the
4 is a block diagram schematically illustrating a configuration of the complex baseband
The
The complex baseband
The complex baseband
Referring back to FIG. 3, the
The
According to an exemplary embodiment, the
Here, Δφ represents a phase shift, Im {} represents an imaginary part of a signal (for example, a Fourier transform signal), Re {} represents a real part of a signal (for example, a Fourier transform signal), and R (1 ) Represents one-lag autocorrelation.
In addition, as illustrated in FIG. 5A, the
Here, σ 2 represents phase dispersion, R (0) represents zero-lag autocorrelation, and R (1) represents original lag autocorrelation.
The
In one embodiment, the
The
In one embodiment, the
Where B represents the bandwidth of the band pass filter,
Denotes the smoothed phase dispersion.In addition, the
Where ω c represents the cutoff frequency of the band pass filter, B represents the bandwidth of the band pass filter,
Represents the smoothed phase shift, Denotes the smoothed phase dispersion.The
The
6 is a block diagram schematically illustrating a configuration of a
The
In one embodiment, the
In addition, the
The
The
7 is a block diagram schematically illustrating a configuration of an upmixing unit 540 according to a second embodiment of the present disclosure. The
The
The
The
The
The
Referring back to FIG. 6, the
In one embodiment, the
In one embodiment, the
In addition, the
Where ω c, LPF represents the cutoff frequency of the LTV low pass filter, B represents the bandwidth of the LTV low pass filter,
Denotes the smoothed phase dispersion.The
While specific embodiments have been described, these embodiments are presented by way of example and should not be construed as limiting the scope of the disclosure. The novel methods and apparatus of the present disclosure may be embodied in a variety of other forms and furthermore, various omissions, substitutions and changes in the embodiments disclosed herein are possible without departing from the spirit of the present disclosure. The claims appended hereto and their equivalents should be construed to include all such forms and modifications as fall within the scope and spirit of the disclosure.
100: ultrasonic system 110: control panel
120: ultrasonic probe 130: processor
140: storage unit 150: display unit
210: transmitting unit 220: transmission and reception switch
230: receiving unit 240: signal forming unit
250: signal processor 260: image forming unit
310, 610 complex baseband signal generator
320: signal conversion unit
330 and 620: phase information determiner
340 and 630: spatial filtering unit
350, 650: dynamic filtering unit
360: signal inverse converter
410: orthogonal demodulator
411: cosine function multiplier 412: sine function multiplier
420: Low pass filtering unit 421: First low pass filter
420: second low pass filter 430: decimation unit
431: First decimation unit 432: Second decimation unit
640: upmixing unit
710: First upmix cosine function multiplier
720: first upmixing sine function multiplier
730: second upmix cosine function multiplier
740: second upmixing sine function multiplier
750: first adder 760: second adder
Claims (35)
An ultrasound probe configured to transmit an ultrasound signal to an object and receive an ultrasound echo signal from the object;
Form a complex baseband signal comprising an equal phase component signal and a quadrature phase component signal based on the ultrasonic echo signal, determine a phase shift and phase dispersion based on the complex baseband signal, and determine the phase shift and the phase A processor configured to filter the complex baseband signal by a dynamic filter to adaptively compensate for the spectral downshift of the ultrasonic echo signal based on variance
Ultrasound system comprising a.
A signal converter configured to perform a Fourier transform on the complex baseband signal to form a Fourier transform signal;
A phase information determiner configured to determine the phase shift and the phase dispersion based on the Fourier transform signal;
A spatial filtering unit configured to perform a smoothing process on the phase shift and the phase dispersion;
A dynamic filtering unit configured to form the band pass filter based on the smoothed phase shift and the phase dispersion, and to filter the Fourier transform signal by the band pass filter;
A signal inverse transform unit configured to perform an inverse Fourier transform on the Fourier transform signal filtered by the band pass filter
Ultrasound system comprising a.
(Mathematical formula)
Calculated by the above equation,
Δφ represents the phase shift, Im {} represents the imaginary part of the Fourier transform signal, Re {} represents the real part of the Fourier transform signal, and R (1) represents one-lag autocorrelation. Indicating ultrasound system.
(Mathematical formula)
Calculated by the above equation,
σ 2 represents the phase dispersion, R (0) represents zero-lag autocorrelation, and R (1) represents one lag autocorrelation.
Determine a bandwidth of the band pass filter based on the smoothed phase dispersion,
Determine a cutoff frequency of the bandpass filter based on the bandwidth and the smoothed phase shift,
And form the bandpass filter based on the bandwidth and the cutoff frequency.
(Mathematical formula)
Calculated by the above equation,
B represents the bandwidth, Is an ultrasonic system representing the smoothed phase dispersion.
(Mathematical formula)
Calculated by the above equation,
ω c represents the cutoff frequency, B represents the bandwidth, Represents the smoothed phase shift, Is an ultrasonic system representing the smoothed phase dispersion.
A phase information determiner configured to determine the phase shift and the phase dispersion based on the complex baseband signal;
A spatial filtering unit configured to perform a smoothing process on the phase shift and the phase dispersion;
An upmixing unit configured to perform an upmixing process on the complex baseband signal based on the smoothed phase shift;
A dynamic filtering unit configured to form the low pass filter based on the smoothed phase dispersion and to filter the complex baseband signal upmixed by the low pass filter
Ultrasound system comprising a.
(Mathematical formula)
Calculated by the above equation,
Δφ represents the phase shift, Im {} represents the imaginary part of the complex baseband signal, Re {} represents the real part of the complex baseband signal, and R (1) represents one lag autocorrelation.
(Mathematical formula)
Calculated by the above equation,
σ 2 represents the phase dispersion, R (0) represents zero lag autocorrelation, and R (1) represents one lag autocorrelation.
A first upmixing cosine function multiplier configured to multiply a cosine function by the same phase component signal based on the smoothed phase shift to form a first upmixing signal;
A first upmixing sine function multiplier configured to multiply a sine function by the same phase component signal based on the smoothed phase shift to form a second upmixing signal;
A second upmixing cosine function multiplier configured to multiply a cosine function by the quadrature phase component signal based on the smoothed phase shift to form a third upmixing signal;
A second upmixing sine function multiplier configured to multiply a sine function by the quadrature phase component signal based on the smoothed phase shift to form a fourth upmixing signal;
A first adder coupled to the first upmix cosine function multiplier and the second upmix sine function multiplier, the first adder configured to add the first upmix signal and the fourth upmix signal;
A second adder coupled to the first upmixing sine function multiplier and the second upmixing cosine function multiplier and configured to add the second upmixing signal and the third upmixing signal
Ultrasound system comprising a.
Determine a bandwidth of the low pass filter based on the smoothed phase dispersion,
Determine a cutoff frequency of the low pass filter based on the bandwidth,
An ultrasonic system configured to form the low pass filter based on the bandwidth and the cutoff frequency.
(Mathematical formula)
Calculated by the above equation,
B represents the bandwidth, Is an ultrasonic system representing the smoothed phase dispersion.
(Mathematical formula)
Calculated by the above equation,
ω c, LPF represents the cutoff frequency, B represents the bandwidth, Is an ultrasonic system representing the smoothed phase dispersion.
Transmitting, by an ultrasonic probe of an ultrasonic system, an ultrasonic signal to an object and receiving an ultrasonic echo signal from the object;
Forming, by the processor of the ultrasonic system, a complex baseband signal comprising an equal phase component signal and a quadrature phase component signal based on the ultrasonic echo signal;
Determining, by the processor, phase shift and phase dispersion based on the complex baseband signal;
Filtering, by the processor, the complex baseband signal by a dynamic filter to adaptively compensate for the spectral downshift of the ultrasonic echo signal based on the phase shift and the phase dispersion.
How to include.
Performing a Fourier transform on the complex baseband signal to form a Fourier transform signal;
Determining the phase shift and the phase dispersion based on the Fourier transform signal
How to include.
(Mathematical formula)
Calculated by the above equation,
Δφ represents the phase shift, Im {} represents the imaginary part of the Fourier transform signal, Re {} represents the real part of the Fourier transform signal, and R (1) represents one-lag autocorrelation. How to indicate.
(Mathematical formula)
Calculated by the above equation,
σ 2 represents the phase dispersion, R (0) represents zero-lag autocorrelation, and R (1) represents one lag autocorrelation.
Performing a smoothing process on the phase shift and the phase dispersion;
Forming the band pass filter based on the smoothed phase shift and the phase dispersion;
Filtering the Fourier transform signal by the band pass filter;
Performing an inverse Fourier transform on the Fourier transform signal filtered by the band pass filter
How to include.
Determining a bandwidth of the band pass filter based on the smoothed phase dispersion;
Determining a cutoff frequency of the band pass filter based on the bandwidth and the smoothed phase shift;
Forming the band pass filter based on the bandwidth and the cutoff frequency
How to include.
(Mathematical formula)
Calculated by the above equation,
B represents the bandwidth, Represents the smoothed phase dispersion.
(Mathematical formula)
Calculated by the above equation,
ω c represents the cutoff frequency, B represents the bandwidth, Represents the smoothed phase shift, Represents the smoothed phase dispersion.
(Mathematical formula)
Calculated by the above equation,
Δφ represents the phase shift, Im {} represents the imaginary part of the complex baseband signal, Re {} represents the real part of the complex baseband signal, and R (1) represents one lag autocorrelation.
(Mathematical formula)
Calculated by the above equation,
σ 2 represents the phase dispersion, R (0) represents zero lag autocorrelation, and R (1) represents one lag autocorrelation.
Performing a smoothing process on the phase shift and the phase dispersion;
Performing an upmixing process on the complex baseband signal based on the smoothed phase shift;
Forming the low pass filter based on the smoothed phase dispersion;
Filtering the upmixed complex baseband signal by the lowpass filter.
How to include.
Multiplying a cosine function by the same phase component signal based on the smoothed phase shift to form a first upmix signal;
Multiplying a sine function by the same phase component signal based on the smoothed phase shift to form a second upmix signal;
Multiplying a cosine function by the quadrature phase component signal based on the smoothed phase shift to form a third upmix signal;
Multiplying a sinusoidal function by the quadrature phase component signal based on the smoothed phase shift to form a fourth upmix signal;
Adding the first upmix signal and the fourth upmix signal;
Adding the second upmix signal and the third upmix signal
How to include.
Determining a bandwidth of the low pass filter based on the smoothed phase dispersion;
Determining a cutoff frequency of the low pass filter based on the bandwidth;
Forming the low pass filter based on the bandwidth and the cutoff frequency
How to include.
(Mathematical formula)
Calculated by the above equation,
B represents the bandwidth, Represents the smoothed phase dispersion.
(Mathematical formula)
Calculated by the above equation,
ω c, LPF represents the cutoff frequency, B represents the bandwidth, Represents the smoothed phase dispersion.
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Citations (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6110116A (en) | 1994-08-05 | 2000-08-29 | Acuson Corporation | Method and apparatus for receive beamformer system |
US6248071B1 (en) | 2000-01-28 | 2001-06-19 | U-Systems, Inc. | Demodulating wide-band ultrasound signals |
JP4646808B2 (en) | 2003-12-02 | 2011-03-09 | 株式会社日立メディコ | Ultrasonic diagnostic equipment |
US20150045666A1 (en) | 2013-08-09 | 2015-02-12 | Sonowise, Inc. | Systems and Methods for Processing Ultrasound Color Flow Mapping |
JP5801956B2 (en) | 2012-05-21 | 2015-10-28 | 古野電気株式会社 | Propagation velocity measuring device, propagation velocity measuring program, and propagation velocity measuring method |
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Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6110116A (en) | 1994-08-05 | 2000-08-29 | Acuson Corporation | Method and apparatus for receive beamformer system |
US6248071B1 (en) | 2000-01-28 | 2001-06-19 | U-Systems, Inc. | Demodulating wide-band ultrasound signals |
JP4646808B2 (en) | 2003-12-02 | 2011-03-09 | 株式会社日立メディコ | Ultrasonic diagnostic equipment |
JP5801956B2 (en) | 2012-05-21 | 2015-10-28 | 古野電気株式会社 | Propagation velocity measuring device, propagation velocity measuring program, and propagation velocity measuring method |
US20150045666A1 (en) | 2013-08-09 | 2015-02-12 | Sonowise, Inc. | Systems and Methods for Processing Ultrasound Color Flow Mapping |
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