Ultrasonic method and apparatus for imaging and characterization of bodies

• US 4,063,549 A
• Filed: 12/22/1975
• Issued: 12/20/1977
• Est. Priority Date: 12/22/1975
• Status: Expired due to Term

• Current Assignee: Technicon Instruments Corporation (Bayer AG)
• Original Assignee: Technicon Instruments Corporation (Bayer AG)
• Inventors: Beretsky, Irwin, Lichtenstein, Bernard
• Primary Examiner(s): Howell, Kyle L.
• Application Number:
  US05/643,732
• Time in Patent Office: 729 Days
• Field of Search: 128/2 V, 128/2 R, 128/2.05 Z, 128/2.1 Z, 73/67.1, 73/67.9
• US Class Current: 600/443
• CPC Class Codes: A61B 8/00 Diagnosis using ultrasonic, sonic or infrasonic waves imaging of objects using sonar G01S15/00
• CPC Class Codes: G01N 29/0609 Display arrangements, e.g. colour displays indicating or recording in connection with measuring in general G01D
• CPC Class Codes: G01N 29/0645 Display representation or displayed parameters, e.g. A-, B- or C-Scan
• CPC Class Codes: G01S 15/8977 using special techniques for image reconstruction, e.g. FFT, geometrical transformations, spatial deconvolution, time deconvolution
• CPC Class Codes: Y02A 90/10 Information and communication technologies [ICT] supporting adaptation to climate change, e.g. for weather forecasting or climate simulation

Abstract

Method and apparatus are provided for the determination of the Raylographic information of a body part which is ensonified by acoustical energy pulses by a particularly precisely focused acoustical focusing system to produce acoustical energy echo pulses which are detected in coherent manner. Fourier transformation of the pulses from the time to the frequency domain enables frequency domain deconvolution to provide the impulse response with minimization of mathematical instabilities and distortion of the frequency domain impulse response. Noise extraction and spatial deconvolution filtering are included to respectively maximize signal to noise ratio and minimize distortive effects of body part surface non-orthogonality and combine with the above to provide for particular stability in the overall results and attendant increase in the axial resolution of Raylographic display and in the overall resolution of body part image displays.

Claims

1. In a method for the non-invasive examination of body parts through the selective ensonification of at least a portion of a body part with acoustical energy pulses to produce acoustical energy echo pulses, and the detection and processing of said echo pulses to indicate the relative specific acoustic impedance of the thusly ensonified body part, the steps of, transforming said echo pulses from the time domain to the frequency domain throughout a predetermined frequency range, deconvolving said echo pulses in the frequency domain to determine the impulse responses in the frequency domain of the ensonified body part at a plurality of frequencies within said frequency range, and determining the impulse responses of the ensonified body part in the time domain by transformation of said impulse responses from the frequency domain to the time domain.

2. In a method as in claim 1 wherein, said transformations are complex Fourier transformations.

3. In a method as in claim 1 wherein, the ensonification of said body part comprises the coherent transmission of said acoustical energy pulses, and the detection of said acoustical energy echo pulses is coherent to preserve both the amplitude and phase information which is inherent in said pulses.

4. In a method as in claim 1 further comprising, the steps of successively ensonifying said body part along a plurality of spaced generally parallel planes to provide indicia of the relative specific acoustic impedance thereof along each of said planes, and concomitantly displaying said indicia on a CRT or like display device in skew display mode to provide an image of said body part.

5. In a method as in claim 1 further comprising, the steps of, successively ensonifying said body part along a plurality of acurately displaced generally radial planes to provide indicia of the relative specific acoustic impedance thereof along each of said planes, and concomitantly displaying said indicia on a CRT or like display device in intensity display mode to provide a tomographic image of said body part.

6. In a method as in claim 1 wherein, the deconvolution of said echo pulses comprises, the steps of, detecting said ensonifying energy pulses, and transforming said ensonifying energy pulses from the time domain to the frequency domain.

7. In a method as in claim 6 wherein, said transformations are complex Fourier transformations, and the deconvolution of said echo pulses comprises, stabilizing said impulse responses in the frequency domain by replacing unstable values of the complex representations of said ensonifying energy pulses in the frequency domain with substitutional values which are calculated from said complex representations to minimize distortion of said impulse response thereby.

8. In a method as in claim 6 wherein, said transformations are complex Fourier transformations, and the deconvolution of said echo pulses is accomplished in accordance with the following equation:

##EQU6## wherein;

Y_I (ω

) is the imaginary component of the echo pulses in the frequency domain,

X_r (ω

) is the real component of the ensonifying energy pulses in the frequency domain,

Y_r (ω

) is the real component of the echo pulses in the frequency domain,

X_i (ω

) is the imaginary component of the ensonifying energy pulses in the frequency domain, and

H(ω

) is the impulse response of the body part in the frequency domain.

9. In a method as in claim 8 wherein, in the event of coincident zero values for X_R (ω

) and X_I (ω

) at the same frequency ω

, substitutional values for one or the other thereof are calculated through use of the X_R (ω

) or X_I (ω

) values at the adjacent frequencies ω

of interest, and said substitutional values are utilized in lieu of said zero X_R (ω

) or X_I (ω

) value in the equation to prevent the equation denominator from going to zero while minimizing distortion of the provided H(ω

) values.

10. A method as in claim 9 wherein, the determination of which of the coincident zero values of X_R (ω

) and X_R (ω

) is to be substituted for is made by calculating the respective first and second derivatives of X_R (ω

) and X_I (ω

) at the frequency ω

at which the coincident zero values appear by use of the respective values of X_R (ω

) and X_I (ω

) at the adjacent frequencies ω and

substituting for that component which exhibits a zero or near zero first derivative and a finite second derivative.

11. In a method as in claim 9 wherein, the calculation of the substitutional value is effected by averaging the summation of the values of the component to be substituted for at the adjacent frequencies ω

of interest.

12. A method as in claim 10 wherein, the calculation of the substitutional value is effected by averaging the summation of the values of the component to be substituted for at the adjacent frequencies ω

of interest.

13. A method as in claim 1 further comprising, the steps of, spatially deconvolving said impulse responses in the frequency domain to minimize the distortive effects of non-orthogonally disposed portions of said body part on said impulse responses.

14. In a method as in claim 13, wherein, said spatial deconvolution comprises the complex division of said impulse responses in the frequency domain by a spatial transfer function which is calculated in accordance with said non-orthogonality.

15. In a method as in claim 12 further comprising, the steps of, spatially deconvolving said impulse responses in the frequency domain to minimize the distortive effects of non-orthogonally disposed portions of said body part, said spatial deconvolution comprising the complex division of said impulse responses in the frequency domain by a spatial transfer function which is calculated in accordance with said non-orthogonality.

16. In a method as in claim 6 further comprising, the steps of, complexly multiplying the real and imaginary components H_R (ω

) and H_I (ω

) of the impulse response H(ω

) in the frequency domain by the same weighting factor which is variable in accordance with the power spectrum of the ensonifying energy pulses to maximize the signal to noise ratio.

17. In a method as in claim 7 wherein, the ensonification of said body part comprises the coherent transmission of said acoustical energy pulses, and the detection of said acoustical energy pulses is coherent to preserve both the amplitude and phase information in said pulses.

18. In a method as in claim 15 further comprising, the steps of, complexly multiplying the real and imaginary components H_R (ω

) and H_I (ω

) of the impulse response H(ω

) in the frequency domain by the same weighting factor which is variable in accordance with the power spectrum of the ensonifying energy pulses to maximize the signal to noise ratio.

19. In apparatus for the non-invasive examination of body parts through the selective ensonification of at least a portion of a body part with acoustical energy pulses to produce acoustical energy echo pulses, and the detection and processing of said echo pulses to indicate the relative specific acoustic impendance of the thusly ensonified body part, the improvements comprising, means for transforming said echo pulses from the time domain to the frequency domain throughout a predetermined frequency range, means for deconvolving said echo pulses in the frequency domain to determine the impulse responses in the frequency domain of the ensonified body part at a plurality of frequencies within said frequency range, and means for determining the impulse response of the ensonified body part in the time domain by transformation of said impulse responses from the frequency domain to the time domain.

20. In apparatus as in claim 19 wherein, said transformation means comprise Fast Fourier Transforms.

21. In apparatus as in claim 19 wherein, the ensonification of said body part by acoustical energy pulses is effected by coherent pulse transmission means, and the detection of the resultant echo pulses is effected by coherent pulse detection means to preserve both the amplitude and phase information which is inherent in said echo pulses.

22. In apparatus as in claim 19, further comprising, means for successively ensonifying said body part along a plurality of spaced, generally parallel planes to provide indicia of the relative specific acoustic impedance thereof along each of said planes, and CRT or like display means for concomitantly displaying said indicia in skew display mode to provide an image of said body part.

23. In apparatus as in claim 19, further comprising, means for successively ensonifying said body part along a plurality of arcuately displaced, generally radial planes to provide indicia of the relative specific acoustic impedance thereof along each of said planes, and CRT or like display means for concomitantly displaying said indicia in intensity display mode to provide a tomographic image of said body part.

24. In apparatus as in claim 19 wherein, said deconvolution means comprise means for detecting said ensonifying energy pulses, and means for transforming the same from the time to the frequency domain.

25. In apparatus as in claim 19 wherein, said means for deconvolving said echo pulses further comprise, means for stabilizing said impulse responses in the frequency domain by replacing unstable values of the complex representations of said ensonifying energy pulses in the frequency domain with substitutional values which are calculated from said complex representations to minimize distortion of said impulses responses thereby.

26. In apparatus as in claim 19 wherein, said deconvolution means comprise a deconvolution filter which is operable in accordance with the following equation:

##EQU7## Wherein;

X_R (ω

) is the real component of the ensonifying energy pulses in the frequency domain,

Y_r (ω

) is the real component of the echo pulses in the frequency domain,

X_i (ω

) is the imaginary component of the ensonifying energy pulses in the frequency domain,

Y_i (ω

) is the imaginary component of the echo pulses in the frequency domain, and

H(ω

) is the impulse response of the body part in the frequency domain.

27. In apparatus as in claim 26 wherein, said deconvolution means further comprise comparator and logic circuit means which are respectively operatively connected to said deconvolution filter and are operable, in the event of coincident zero values for X_R (ω

) and X_I (ω

) at the same frequency ω

, to calculate a substitutional value for one or the other thereof through use of the respective X_R (ω

) and X_I (ω

) values at the adjacent frequencies ω

of interest, and to apply said substitutional value to said deconvolution filter in lieu of said zero X_R (ω

) or X_I (ω

) value in the equation to prevent the equation denominator from going to zero while minimizing distortion of the provided H(ω

) values.

28. In apparatus as in claim 19, further comprising means for spatially deconvolving said impulse responses in the frequency domain to minimize the distortive effects of non-orthogonally disposed portions of said body part on said impulse responses.

29. In apparatus as in claim 28 wherein, said spatial deconvolution means comprise a spatial deconvolution filter which is operable to complexly divide said impulse responses in the frequency domain by a spatial transfer function which is calculated in accordance with said non-orthogonality.

30. In apparatus as in claim 27, further comprising, means for spatially deconvolving said impulse responses in the frequency domain to minimize the distortive effect of non-orthogonally disposed portions of said body part, said spatial deconvolution means comprising a spatial deconvolution filter which is operable to complexly divide said impulse responses in the frequency domain by a spatial domain by a spatial transfer function which is calculated in accordance with said non-orthogonality.

31. In apparatus as in claim 19, further comprising, noise extraction filter means operatively connected to said deconvolution means and operable to complexly multiply the real and imaginary components H_R (ω

) and H_I (ω

) of the impulse response H(ω

) in the frequency domain by the same weighting factor which is variable in accordance with the power spectrum of the ensonifying energy pulses to maximize the signal to noise ratio.

32. In apparatus as in claim 30, further comprising, noise extraction filter means operatively connected to said deconvolution means and operable to complexly multiply the real and imaginary components H_R (ω

) and H_I (ω

) of the impulse response H(ω

) in the frequency domain by the same weighting factor which is variable in accordance with the power spectrum of the ensonifying energy pulses to maximize the signal to noise ratio.

33. In apparatus as in claim 19 wherein, the ensonification of said body part with acoustical energy pulses and the detection of the resultant echo pulses are effected by an acoustical focusing system, said system comprising, a substantially elliptical acoustical reflector having a smooth reflecting surface which forms an acoustical aperture, a convex receiver/projector transducer spaced from said reflector and disposed in substantial alignment with the major axis of the reflector within the field of said acoustical aperture, said transducer comprising a substantially spherical surface facing said reflector and having a radius of curvature R, said acoustical reflector having first and second spaced acoustical focal points, said transducer being located between said second focal point and said reflector and being so disposed relative to said reflector that the center of the radius of curvature R is substantially coincident with said first acoustical focal point.

34. In apparatus as in claim 33 wherein, the distance along the major axis of the reflector between said first and second focal points is substantially equal to the distance along said major axis from said first focal point to said reflector.

35. In apparatus as in claim 33 wherein, said reflector comprises a plurality of piezoelectric means disposed immediately to the side of the reflecting surface remote from said transducer and operable to receive said acoustical energy echo pulses in lieu of said transducer, delay line means operatively connected to each of said piezoelectric means and operable to delay the electrical signals generated thereby in response to said acoustical energy echo pulses, whereby said acoustical system may be dynamically focused to re-locate said second focal point through adjustment of said delay line means.