Method and apparatus for ultrasound imaging using acoustic impedance reconstruction

• US 6,200,266 B1
• Filed: 03/31/1999
• Issued: 03/13/2001
• Est. Priority Date: 03/31/1998
• Status: Expired due to Fees

• Current Assignee: Case Western Reserve University, Medsonics US Incorporated
• Original Assignee: Case Western Reserve University
• Inventors: Izatt, Joseph, Shokrollahi, Nima, Tobocman, William, Roth, Sanford
• Primary Examiner(s): Lateef, Marvin M.
• Assistant Examiner(s): Imam, Ali M.
• Application Number:
  US09/282,215
• Time in Patent Office: 713 Days
• Field of Search: 600/438, 600/443, 600/447, 600/448, 73/602
• US Class Current: 600/438
• CPC Class Codes: A61B 8/0858 involving measuring tissue layers, e.g. skin, interfaces
• CPC Class Codes: A61B 8/13 Tomography A61B8/10, A61B8/12 take precedence; tomography for radiation diagnosis A61B6/02
• CPC Class Codes: G01S 15/8993 Three dimensional imaging systems
• CPC Class Codes: G01S 7/52036 using analysis of echo signal for target characterisation
• CPC Class Codes: G01S 7/52046 Techniques for image enhancement involving transmitter or receiver image enhancement by image data processing G06T5/00
• CPC Class Codes: G01S 7/52061 Plan position indication (PPI display); C-scan display
• CPC Class Codes: G01S 7/52069 Grey-scale displays

Abstract

An ultrasound imaging system employs acoustic impedance reconstruction to produce high-resolution images of anatomical structures, which are virtually free of speckle. Determination of the acoustic impedance profile involves prefiltering of the incident ultrasound signal and the ultrasound signal reflected from the specimen to be imaged. A time domain window function is applied to both the incident and reflected signals, and an N-point FFT is computed for both the digitized incident and reflected signals to obtain the incident and reflected spectrums. A complex division of the reflected spectrum by the incident spectrum is performed to obtain the transfer function. A window function having a sharp, low-frequency cutoff is applied to the transfer function prior to performing an inverse FFT to obtain the estimated impulse response. The acoustic impedance of individual A-scans is calculated from the impulse response using the plane wave Born approximation, involving integration and exponentiation of the estimated impulse response. By mechanically or electronically scanning the transducer along a line, a series of A-scan acoustic impedance profiles are calculated and used to produce a two-dimensional, grey-scale B-scan image.

Claims

1. An ultrasound imaging system, comprising:

a transducer adapted to emit an incident ultrasonic signal toward a specimen, said transducer receiving a reflection of the incident ultrasonic signal from the specimen and generating an electrical signal which represents a reflected ultrasonic signal;

a signal processor which reconstructs an acoustic impedance of a portion of the specimen through which the reflected ultrasonic signal passes by;

computing a Fourier transform of the electrical signal which represents the reflected ultrasonic signal to obtain a reflected signal spectrum;

dividing the reflected signal spectrum by a spectrum of the incident ultrasonic signal to obtain a transfer function;

applying a frequency-domain window function having a sharp, low-frequency cutoff to the transfer function;

computing an inverse Fourier transform of the windowed transfer function to obtain an impulse response; and

calculating the acoustic impedance from the impulse response; and

an imaging device adapted to form an image of the specimen in accordance with the reconstructed acoustic impedance.

2. The system according to claim 1, wherein said signal processor calculates the acoustic impedance by integrating and exponentiating the impulse response in accordance with a plane wave Born approximation.

3. The system according to claim 1, wherein said window function reduces to zero a magnitude of a DC component of the transfer function.

4. The system according to claim 3, wherein the magnitude of at least one of a lowest frequency component above the DC component of the transfer function, a second lowest frequency component of the transfer function and a third lowest frequency component of the transfer function is unattenuated by the window function.

5. The system according to claim 4, wherein a magnitude of the lowest frequency component of the transfer function is unattenuated by the window function.

6. The system according to claim 1, wherein the window function is a rectangular filter having a sharp, high-frequency cutoff corresponding to a high-frequency end of a bandwidth of said transducer.

7. The system according to claim 1, wherein the window function smoothly approaches zero at a high-frequency end, such that magnitudes of high-frequency components of the transfer function are gradually attenuated to zero with increasing frequency.

8. The system according to claim 1, wherein said signal processor applies a time domain pre-window to the electrical signal prior to computing the Fourier transform of the electrical signal.

9. The system according to claim 8, wherein the time domain pre-window is a Hamming window.

10. The system according to claim 1, further comprising a scan controller configured to control said transducer to emit a sequence of incident ultrasonic signals which respectively travel along adjacent lines within the specimen, said signal processor reconstructing an acoustic impedance corresponding to each of the incident ultrasonic signals.

11. The system according to claim 10, wherein said transducer is a phased-array of transducer elements, wherein a direction of each of the incident ultrasonic signals is controlled by a relative phase of individual ultrasonic signals emitted by the transducer elements.

12. The system according to claim 11, wherein said transducer is controllable by said scan controller to scan in at least one of the following scanning formats:

linear;

steered linear, sector, and circular.

13. The system according to claim 10, further comprising a movable platform on which said transducer is mounted, said scan controller effecting scanning by displacing said movable platform.

14. The system according to claim 10, wherein said scan controller controls said transducer to scan in a plane of the specimen, said imaging device forming a two-dimensional B-scan image of the specimen.

15. The system according to claim 1, wherein said imaging device produces a three-dimensional image of the specimen.

16. The system according to claim 1, wherein said signal processor reconstructs the acoustic impedance in real time.

17. The system according to claim 16, wherein said imaging device updates the image of the specimen in real time.

18. The system according to claim 1, wherein the incident ultrasonic signal emitted by said transducer has a center frequency in the range between 3 and 5 MHz, inclusive, the incident ultrasonic signal imaging a field of view in a depth dimension of approximately 8 mm.

19. The system according to claim 1, wherein said imaging device includes at least one of a display and a printer.

20. The system according to claim 1, further comprising:

a memory adapted to store image information derived from the acoustic impedance reconstructed by said signal processor.

21. The system according to claim 1, further comprising:

a transmitter for transmitting image information to a remote location over at least one of;

a fiber optic medium, a wire and free space.

22. A method of generating an ultrasound image, comprising the steps of:

a) emitting an incident ultrasonic signal toward a specimen;

b) receiving a reflection of the incident ultrasonic signal from the specimen and generating an electrical signal which represents a reflected ultrasonic signal;

c) computing a Fourier transform of the electrical signal which represents the reflected ultrasonic signal to obtain a reflected signal spectrum;

d) dividing the reflected signal spectrum by a spectrum of the incident ultrasonic signal to obtain a transfer function;

e) applying a frequency-domain window function having a sharp, low-frequency cutoff to the transfer function;

f) computing an inverse Fourier transform of the windowed transfer function to obtain an impulse response;

g) calculating an acoustic impedance profile from the impulse response; and

h) forming an image of the specimen in accordance with the acoustic impedance profile.

23. The method according to claim 22, wherein step f) includes integrating and exponentiating the impulse response in accordance with a plane wave Born approximation to obtain the acoustic impedance.

24. The method according to claim 22, wherein step e) includes reducing to zero a magnitude of a DC component of the transfer function.

25. The method according to claim 24, wherein step e) includes not attenuating a magnitude of at least one of:

a lowest frequency component above the DC component of the transfer function, a second lowest frequency component of the transfer function and a third lowest frequency component of the transfer function.

26. The method according to claim 25, wherein step e) includes not attenuating a magnitude of the lowest frequency component of the transfer function.

27. The method according to claim 22, wherein the window function applied in step e) is a rectangular filter having a sharp, high-frequency cutoff corresponding to a high-frequency end of the incident ultrasonic signal.

28. The method according to claim 22, wherein the window function applied in step e) smoothly approaches zero at a high-frequency end, such that magnitudes of high-frequency components of the transfer function are gradually attenuated to zero with increasing frequency.

29. The method according to claim 22, further comprising the step of:

i) applying a time domain pre-filter to the reflected electrical signal prior to computing the Fourier transform of the reflected electrical signal.

30. The method according to claim 22, further comprising the step of:

i) effecting a scan by repeating steps a) through g) along a plurality of different, adjacent paths within the specimen, wherein step h) includes forming an image using the acoustic impedance calculated for each of the plurality of paths.

31. The method according to claim 30, wherein step i) includes controlling a direction of the incident ultrasonic signal by setting relative phases of a phased-array of transducer elements.

32. The method according to claim 31, wherein step i) includes scanning in at least one of the following scanning formats:

linear;

steered linear, sector, and circular.

33. The method according to claim 30, wherein step i) includes mechanically displacing a transducer to effect scanning.

34. The method according to claim 30, wherein the plurality of paths form a plane in the specimen, and wherein step h) includes forming a two-dimensional B-scan image of the specimen.

35. The method according to claim 22, wherein step h) includes forming a three-dimensional image of the specimen.

36. The method according to claim 22, wherein steps c) through h) are performed in real time.

37. The method according to claim 22, wherein step a) includes emitting the incident ultrasonic signal having a center frequency in the range between 3 and 5 MHz, inclusive.

38. The method according to claim 22, further comprising the steps of:

i) prior to step h), determining whether the acoustic impedance profile meets a predetermined requirement;

j) when the acoustic impedance profile fails to meet the predetermined requirement, constraining values of certain components of the acoustic impedance profile;

k) computing amplitudes of low frequency components of the transfer function below the sharp, low-frequency cutoff from the constrained values of the certain components of the acoustic impedance profile;

l) repeating steps f), g), i), j) and k) at most L times, where L is a positive integer, or until the acoustic impedance profile meets the predetermined requirement in step i).

39. The method according to claim 38, wherein:

the predetermined requirements is that the value of all of the components of the acoustic impedance profile be at least 1.0; and

step j) includes;

dividing the acoustic impedance profile into N regions, where N is an integer greater than 1;

for each region, identifying a component of the acoustic impedance profile having a minimum value within the region;

for each region, if the minimum value is less than 1.0, constraining the value of the identified component in the region to a value no less than 1.0.

40. The method according to claim 22, further comprising the step of:

i) prior to step f), adjusting amplitudes of components of the transfer function to compensate for attenuation caused by intervening tissue.

41. An ultrasound imaging system, comprising:

a transducer adapted to emit an incident ultrasonic signal toward a specimen, said transducer receiving a reflection of the incident ultrasonic signal from the specimen and generating an electrical signal which represents a reflected ultrasonic signal;

a signal processor which reconstructs an acoustic impedance of a portion of the specimen through which the reflected ultrasonic signal passes by;

a) computing a Fourier transform of the electrical signal which represents the reflected ultrasonic signal to obtain a reflected signal spectrum;

b) dividing the reflected signal spectrum by a spectrum of the incident ultrasonic signal to obtain a transfer function;

c) applying a frequency-domain window function having a sharp, low-frequency cutoff to the transfer function;

d) computing an inverse Fourier transform of the windowed transfer function to obtain an impulse response;

e) calculating an acoustic impedance profile from the impulse response;

f) determining whether the acoustic impedance profile meets a predetermined requirement;

g) when the acoustic impedance profile fails to meet the predetermined requirement, constraining values of certain components of the acoustic impedance profile;

h) computing amplitudes of low-frequency components of the transfer function below the sharp, low-frequency cutoff from the constrained values of the certain components of the acoustic impedance profile; and

i) repeating steps d) through h) at most L times, where L is a positive integer, or until the acoustic impedance profile meets the predetermined requirement in step f); and

an imaging device adapted to form an image of the specimen in accordance with the acoustic impedance profile.

42. The apparatus according to claim 41, wherein:

the predetermined requirements include the requirement that the value of all of the components of the acoustic impedance profile be at least 1.0; and

step g) includes;

dividing the acoustic impedance profile into N regions, where N is an integer greater than 1;

for each region, identifying a component of the acoustic impedance profile having a minimum value within the region;

for each region, if the minimum value is less than 1.0, constraining the value of the identified component in the region to a value no less than 1.0.