Method and apparatus for adaptive focusing in a medical ultrasound imaging apparatus

• US 4,817,614 A
• Filed: 08/19/1987
• Issued: 04/04/1989
• Est. Priority Date: 08/20/1986
• Status: Expired due to Term

• Current Assignee: Siemens AG
• Original Assignee: Siemens AG
• Inventors: Haerer, Wolfgang, Eschenbacher, Heinz, Hassler, Dietrich
• Primary Examiner(s): Jaworski, Francis J.
• Assistant Examiner(s): Manuel, George
• Application Number:
  US07/087,046
• Time in Patent Office: 594 Days
• Field of Search: 128/660, 73/602, 73/597, 73/625, 73/645-648
• US Class Current: 600/441
• CPC Class Codes: G01H 17/00 Measuring mechanical vibrations or ultrasonic, sonic or infrasonic waves, not provided for in the preceding groups see provisionally also G01H1/00
• CPC Class Codes: G01N 29/0645 Display representation or displayed parameters, e.g. A-, B- or C-Scan
• CPC Class Codes: G01S 15/8927 using simultaneously or sequentially two or more subarrays or subapertures
• CPC Class Codes: G01S 15/8977 using special techniques for image reconstruction, e.g. FFT, geometrical transformations, spatial deconvolution, time deconvolution
• CPC Class Codes: G01S 7/52049 using correction of medium-induced phase aberration
• CPC Class Codes: G01S 7/5205 Means for monitoring or calibrating
• CPC Class Codes: G01S 7/5206 Two-dimensional coordinated display of distance and direction; B-scan display

Abstract

A sectional plane of the examination subject is first scanned by focused ultrasound transmission beams in an adaptation phase. Disturbing effects from the reflected echo signals which are caused by the inhomogenities in the tissue are thereby measured. In this adaptation phase, correction values for the delay time of the signals of the elemental transducers of the ultrasound array in comparison to the standard focusing are also derived from the measured values. In a following B-image imaging phase, the delay times of the active aperture are then varied dependent on the correction values during the emission and/or during reception. The disturbing effects are thereby compensated. A method and apparatus are disclosed which are especially well-suited for linear array systems and for patients having inhomogeneous tissues.

Claims

1. A method for generating an ultrasound B-image of an examination subject having acoustic inhomogeneities using an ultrasound array having a plurality of transducer elements, each transducer element having a variable delay associated therewith, including a delay used for a standard focusing of said ultrasound array, said method comprising the steps of:

scanning a sectional plane of said examination subject with focused ultrasound beams from said ultrasound array in an adaptation phase;

measuring, in said adaptation phase, echo signals reflected by said examination subject using a selected active aperture, said echo signals being disturbed by the acoustic inhomogeneities in said examination subject;

calculating correction values for the delay of each of said element in said ultrasound array from the delays used for said standard focusing based on the measured values obtained in said adaptation phase; and

scanning said examination subject with said ultrasound array using the delays calculated based on said correction values and the delays used for said standard focusing to compensate for said disturbances caused by said acoustic inhomogeneities to obtain further echo signals; and

generating a standard B-image from said further echo signals.

2. A method as claimed in claim 1, wherein the step of calculating said correction values is further defined by cross-correlation the echo signals from said transducer elements of said ultrasound array.

3. A method as claimed in claim 2, wherein the step of cross-correlating is further defined by cross-correlating echo signals of two neighboring transducer elements in said ultrasound

4. A method as claimed in claim 2, wherein the step of cross-correlating is further defined by the steps of:

grouping said transducer elements of said ultrasound array into a plurality of groups; and

cross-correlating the echo signals from neighboring groups of transducers in said ultrasound array.

5. A method a claimed in claim 2, wherein the step of calculating said correction values is further defined by the steps of:

identifying the time shift value of the maximum of said cross-correlation;

generating a distribution of transit-time differences by comparing said time shift value to an expected value for a homogeneous examination subject; and

after scanning the entirety of said sectional plane, deriving said measuring values from said distribution and calculating said correction values therefrom.

6. A method as claimed in claim 1, wherein the step of calculating said correction values is further defined by calculating correction values by averaging.

7. A method as claimed in claim 6, comprising the additional step of tilting said ultrasound array with respect to said examination subject in said adaptation phase.

8. A method as claimed in claim 5, comprising the additional step of:

aligning the time shift values from said transducer elements when calculating said correction values; and

subsequently averaging said correction values.

9. A method as claimed in claim 1, wherein said adaptation phase is repeated through a selected number of iterations, with the correction values obtained from one iteration being used for transmitting said ultrasound beams in an immediately following iteration.

10. An apparatus for generating an ultrasound B-image of an examination subject having acoustic inhomogeneities comprising:

an ultrasound array having a plurality of transducer elements, each transducer element having means connected thereto for variably setting a delay for that transducer, including a delay for standard focusing of said ultrasound array;

means for scanning said examination subject with ultrasound beams generated by said ultrasound array with said delays for standard focusing;

means for processing ultrasound echo signals reflected by said examination subject using a selected active aperture and for generating a standard B-image therefrom;

means for scanning a sectional plane of said examination subject with focused ultrasound beams from said array in an adaptation phase;

means for measuring echo signals reflected by said examination subject in said adaptation phase disturbed by the acoustic inhomogeneities in said examination subject;

means for calculating correction values for the delay of each element in said ultrasound array from the delays used for said standard focusing based on the measured values obtained in said adaptation phase; and

means for scanning said examination subject with said ultrasound array based on said correction values and the delays used for said standard focusing for compensating for said disturbances caused by said acoustic inhomogeneities.

11. An apparatus as claimed in claim 10, wherein said means for calculating said correction values is a means for cross-correlating the echo signals from said transducer elements of said ultrasound array.

12. A apparatus as claimed in claim 11, wherein said means for cross-correlating is a means for cross-correlating echo signals of two neighboring transducer elements in said ultrasound

13. An apparatus as claimed in claim 11, further comprising means for grouping said transducer elements of said ultrasound array into a plurality of groups, and wherein said means for cross-correlating is a means for cross-correlating the echo signals from neighboring groups of transducers in said ultrasound array.

14. An apparatus as claimed in claim 11, wherein said means for calculating said correction values comprises:

means for identifying a time shift value of the maximum of the output of said means for cross-correlating;

means for generating a distribution of transit-time differences including means for comparing said time shift value to an expected value for an homogeneous examination subject; and

means for deriving said measured values from said distribution and for calculating said correction values therefrom.

15. An apparatus as claimed in claim 10, wherein said means for calculating said correction values includes means for averaging.

16. An apparatus as claimed in claim 15, wherein said means for calculating said correction values includes means for aligning added time shift values from said transducer elements when calculating said correction values and means for subsequently averaging said correction values after aligning.

17. An apparatus as claimed in claim 10, further comprising means for tilting said ultrasound array with respect to said examination subject in said adaptation phase.

18. An apparatus as claimed in claim 10, further comprising control means for repeating said adaptation phase through a selected number of iterations, with the correction values obtained for one iteration being used for transmitting said ultrasound beams in an immediately following iternation.

19. An apparatus as claimed in claim 10, further comprising means for averaging a plurality of scans of said examination subject, and means for selectively varying the duration of said adaptation phase to control the number of scans used in said means for averaging.

20. An apparatus as claimed in claim 10, further comprising means for selecting the depth region in said examination subject from which said echo signals are reflected.