U.S. patent application number 11/160915 was filed with the patent office on 2007-01-18 for ultrasound imaging beam-former apparatus and method.
This patent application is currently assigned to UNIVERSITY OF VIRGINIA PATENT FOUNDATION. Invention is credited to Travis N. Blalock, John A. Hossack, William F. Walker.
Application Number | 20070016022 11/160915 |
Document ID | / |
Family ID | 32777004 |
Filed Date | 2007-01-18 |
United States Patent
Application |
20070016022 |
Kind Code |
A1 |
Blalock; Travis N. ; et
al. |
January 18, 2007 |
ULTRASOUND IMAGING BEAM-FORMER APPARATUS AND METHOD
Abstract
In some illustrative embodiments, an incoming signal from a
transducer in an ultrasound imaging beam-former apparatus is
applied to an in-phase sample-and-hold and a quadrature
sample-and-hold. The quadrature sample-and-hold may be clocked a
quarter period behind the in-phase sample-and-hold. The output of
the sample-and-holds are applied to in-phase and quadrature
analog-to-digital converters. A magnitude calculator receives the
in-phase and quadrature digital values, and outputs a magnitude. A
phase calculator receives the in-phase and quadrature digital
values, and outputs a phase. An apodizer applies a difference
between an amplitude of the outgoing signal and the magnitude and
applies a first illumination to a image point in substantial
proportion to the difference, and a phase rotator applies a second
illumination to the image point in substantial proportion to the
phase.
Inventors: |
Blalock; Travis N.;
(Charlottesville, VA) ; Walker; William F.;
(Barboursville, VA) ; Hossack; John A.;
(Charlottesville, VA) |
Correspondence
Address: |
NOVAK DRUCE & QUIGG, LLP
1300 EYE STREET NW
400 EAST TOWER
WASHINGTON
DC
20005
US
|
Assignee: |
UNIVERSITY OF VIRGINIA PATENT
FOUNDATION
1224 West Main Street Suite 1-110
Charlottesville
VA
|
Family ID: |
32777004 |
Appl. No.: |
11/160915 |
Filed: |
July 14, 2005 |
Current U.S.
Class: |
600/437 |
Current CPC
Class: |
G01S 15/8959 20130101;
G01S 7/5208 20130101; A61B 8/145 20130101; A61B 8/4483 20130101;
A61B 8/5207 20130101; A61B 8/00 20130101; G01S 7/52034 20130101;
A61B 8/4494 20130101; G01S 7/52085 20130101; A61B 8/4488 20130101;
A61B 8/461 20130101; G01S 15/8995 20130101; G01S 7/52028 20130101;
G10K 11/346 20130101; G01S 15/8915 20130101 |
Class at
Publication: |
600/437 |
International
Class: |
A61B 8/00 20060101
A61B008/00 |
Foreign Application Data
Date |
Code |
Application Number |
Jan 14, 2004 |
WO |
PCT/US04/00887 |
Claims
1. An ultrasound imaging beam-former apparatus, comprising: a
signal generator for producing an outgoing signal; a transducer for
converting said outgoing signal to outgoing ultrasound and for
converting at least a portion of said outgoing ultrasound that is
reflected to an incoming signal, said incoming signal having a
period; and a signal receiver for processing said incoming signal,
said signal receiver comprising: an in-phase sample-and-hold
connected receivably to said transducer for sampling said incoming
signal at an incoming time and outputting an in-phase amplitude of
said incoming signal at substantially said incoming time; a
quadrature sample-and-hold connected receivably to said transducer
for sampling said incoming signal at substantially one-quarter of
said period after said incoming time, said quadrature
sample-and-hold outputting a quadrature amplitude of said incoming
signal at substantially one-quarter of said period after said
incoming time; a phase calculator connected receivably to said
in-phase sample-and-hold and said quadrature sample-and-hold for
receiving said incoming time, said in-phase amplitude, and said
quadrature amplitude and outputting a phase; and a phase rotator
for applying an illumination to said image point in substantial
proportion to said phase.
2. The ultrasound imaging beam-former apparatus of claim 1,
comprising further: an in-phase analog-to-digital converter
connected receivably to said in-phase sample-and-hold for assigning
an in-phase digital value to said in-phase amplitude and outputting
said in-phase digital value.
3. The ultrasound imaging beam-former apparatus of claim 1,
comprising further: a quadrature analog-to-digital converter
connected receivably to said quadrature sample-and-hold for
assigning a quadrature digital value to said quadrature amplitude
and outputting said quadrature digital value.
4. The ultrasound imaging beam-former apparatus of claim 1, wherein
signal has an outgoing amplitude; a magnitude calculator connected
receivably to said in-phase analog-to-digital converter and said
quadrature analog-to-digital converter for receiving said incoming
time, said in-phase digital value, and said quadrature digital
value and outputting a magnitude; and an apodizer for applying a
difference between an outgoing amplitude of said outgoing signal at
an outgoing time and said magnitude and applying a second
illumination to a image point in substantial proportion to said
difference.
5. The ultrasound imaging beam-former apparatus of claim 1,
comprising further: a second transducer for converting said
outgoing signal to second outgoing ultrasound and for converting at
least a portion of said outgoing ultrasound and said second
outgoing ultrasound that is reflected to a second incoming signal,
said second incoming signal having a second period; and a second
signal receiver for processing said second incoming signal, said
second signal receiver comprising: a second in-phase
sample-and-hold connected receivably to said second transducer for
sampling said second incoming signal at a second incoming time and
outputting a second in-phase amplitude of said second incoming
signal at substantially said second incoming time; a second
quadrature sample-and-hold connected receivably to said second
transducer for sampling said second incoming signal at
substantially one-quarter of said second period after said second
incoming time, said second quadrature sample-and-hold outputting a
second quadrature amplitude of said second incoming signal at
substantially one-quarter of said second period after said second
incoming time; a second phase calculator connected receivably to
said second in-phase sample-and-hold and said second quadrature
sample-and-hold for receiving said second incoming time, said
second in-phase amplitude, and said second quadrature amplitude and
outputting a second phase; and a second phase rotator for applying
a second illumination to said second image point in substantial
proportion to said second phase; and a summer for combining said
difference, said second difference, said phase, and said second
phase before said illumination and said second illumination are
applied to said image point.
6. The ultrasound imaging beam-former apparatus of claim 1, wherein
said signal generator comprises further a generator amplifier for
amplifying said outgoing signal.
7. The ultrasound imaging beam-former apparatus of claim 1, wherein
said signal receiver comprises further a receiver amplifier for
amplifying said incoming signal.
8. The ultrasound imaging beam-former apparatus of claim 1, wherein
said signal receiver comprises further a receiver pre-amplifier for
amplifying said incoming signal.
9. The ultrasound imaging beam-former apparatus of claim 1, wherein
said signal receiver comprises further a band-pass filter for
filtering said incoming signal.
10. The ultrasonic imaging beam-former apparatus of claim 1,
wherein said signal receiver comprises a digital signal
processor.
11. The ultrasonic imaging beam-former apparatus of claim 1,
wherein said outgoing signal is selected from the group consisting
of: an electro-magnetic signal, an electrical signal, and an
optical signal.
12. The ultrasonic imaging beam-former apparatus of claim 1,
wherein said incoming signal is selected from the group consisting
of: an electro-magnetic signal, an electrical signal, and an
optical signal.
13. The ultrasonic imaging beam-former apparatus of claim 1,
wherein said transducer is selected from the group consisting of: a
piezoelectric element, a voice coil, a MEMS device, a capacitive
micro-machined transducer, a crystal oscillator, and a Hall effect
transducer.
14. The ultrasonic imaging beam-former apparatus of claim 1,
wherein said signal receiver is implemented as an integrated
circuit.
15. The ultrasonic imaging beam-former apparatus of claim 1,
wherein the transducer comprises further a plurality of
transducers.
16. The ultrasonic imaging beam-former apparatus of claim 12,
wherein said plurality of transducers forms an array selected from
the group consisting of: a linear array, a phased array a
curvilinear array, an unequally sampled 2-D array, a 1.5-D array, a
catheter based array, an intra-cavity array, an equally sampled 2D,
a sparse 2D array, and fully sampled 2D array.
17. The ultrasonic imaging beam-former apparatus of claim 1,
comprising further a protection circuit to allow both transmit and
receive operations.
18. A method of beam-forming for ultrasound imaging, comprising:
generating an outgoing signal; transducing said outgoing signal to
outgoing ultrasound; receiving at least a portion of reflected
outgoing ultrasound; transducing said reflected ultrasound to an
incoming signal having a period; sampling said incoming signal at
an incoming time to produce an in-phase amplitude of said incoming
signal; sampling said incoming signal at substantially one-quarter
of said period after said incoming time to produce a quadrature
amplitude of said incoming signal; calculating a phase at said
incoming time based on said in-phase amplitude and said quadrature
amplitude; and applying a illumination to an image point in
substantial proportion to said phase.
19. The method of beam-forming for ultrasound imaging of claim 18,
comprising further: assigning an in-phase digital value to said
in-phase amplitude.
20. The method of beam-forming for ultrasound imaging of claim 18,
comprising further: assigning a quadrature digital value to said
quadrature amplitude.
21. The method of beam-forming for ultrasound imaging of claim 18,
comprising further: calculating a magnitude at said incoming time,
based on said in-phase amplitude and said quadrature amplitude;
measuring a difference between an outgoing amplitude of said
outgoing signal and said magnitude; and applying a second
illumination to said image point in substantial proportion to said
difference.
22. The method of beam-forming for ultrasound imaging of claim 18,
comprising further: transducing said outgoing signal to second
outgoing ultrasound; receiving at least a portion of reflected
outgoing ultrasound and second outgoing ultrasound; transducing
said reflected outgoing ultrasound and second outgoing ultrasound
to a second incoming signal having a second period; sampling said
second incoming signal at said incoming time to produce a second
in-phase amplitude of said second incoming signal; sampling said
second incoming signal at substantially one-quarter of said second
period after said incoming time to produce a second quadrature
amplitude of said second incoming signal; calculating a second
phase at said incoming time based on said second in-phase amplitude
and said second quadrature amplitude; summing said phase and said
second phase; and applying a second illumination to said image
point in substantial proportion to said second phase.
23. The method of beam-forming for ultrasound imaging of claim 18,
comprising further amplifying said outgoing signal.
24. The method of beam-forming for ultrasound imaging of claim 18,
comprising further an operation selected from the group consisting
of: amplifying said incoming signal, pre-amplifying said incoming
signal, and storing said incoming signal.
25. The method of beam-forming for ultrasound imaging of claim 18,
comprising further repeating the method of beam-forming to produce
a plurality of image points forming an image.
26. The method of beam-forming for ultrasound imaging of claim 25,
comprising further an operation selected from the group consisting
of: viewing said image, guiding insertion of a needle based on said
image, guiding insertion of a catheter based on said image, guiding
insertion of an endoscope based on said image, estimating blood
flow based on said image, and estimating tissue motion based on
said image.
27. The method of beam-forming for ultrasound imaging of claim 25,
further comprising focusing said plurality of image points.
28. The method of beam-forming for ultrasound imaging of claim 25,
wherein said focusing is repeated on said reflected outgoing
ultrasound at said plurality of image points.
29. The method of beam-forming for ultrasound imaging of claim 25,
wherein the plurality of image points are along a line at a range
of interest.
30. The method of beam-forming for ultrasound imaging of claim 29,
wherein the line is formed at a plurality of ranges to form a
planar image.
31. The method of beam-forming for ultrasound imaging of claim 30,
wherein the planar image is a B-mode image.
32. The method of beam-forming for ultrasound imaging of claim 25,
wherein the plurality of image points lie within a plane at a range
of interest.
33. The method of beam-forming for ultrasound imaging of claim 32,
wherein the plurality of image points form a C-scan.
34. The method of beam-forming for ultrasound imaging of claim 32,
wherein the plane is formed at multiple ranges.
35. The method of beam-forming for ultrasound imaging of claim 32,
wherein the planes form a complex 3D image.
36. The method of beam-forming for ultrasound imaging of claim 18,
wherein an envelope of the magnitude is displayed.
37. The method of beam-forming for ultrasound imaging of claim 18,
further comprising compensating for a path difference based on the
phase.
38. The method of beam-forming for ultrasound imaging of claim 18,
wherein a main lobe resolution and a side lobe level is balanced
based on the magnitude.
39. The method of beam-forming for ultrasound imaging of claim 18,
wherein a sum squared error between a desired system response and a
true system response is minimized.
40. A system for beam-forming for ultrasound imaging, comprising:
means for generating an outgoing signal having an outgoing
amplitude at an outgoing time; means for transducing said outgoing
signal to outgoing ultrasound; means for transducing at least a
portion of reflected outgoing ultrasound to an incoming signal
having a period; means for sampling said incoming signal at an
incoming time and outputting an in-phase amplitude of said incoming
signal; means for sampling said incoming signal at substantially
one-quarter of said period after said incoming time and outputting
a quadrature amplitude of said incoming signal; means for
calculating a phase at said incoming time, based on said in-phase
amplitude and said quadrature amplitude and outputting said phase;
and means for applying a second illumination to said image point in
substantial proportion to said phase; means for calculating a
magnitude at said incoming time, based on said in-phase amplitude
and said quadrature amplitude and outputting said magnitude; means
for measuring a difference between an outgoing amplitude of said
outgoing signal and said magnitude; and means for applying a first
illumination to a image point in substantial proportion to said
difference.
41. The system for beam-forming for ultrasound imaging of claim 40,
comprising further: second means for transducing said outgoing
signal to second outgoing ultrasound; second means for transducing
said reflected outgoing ultrasound and second outgoing ultrasound
to a second incoming signal having a second period; second means
for sampling said second incoming signal at said incoming time and
outputting a second in-phase amplitude of said second incoming
signal; second means for sampling said second incoming signal at
substantially one-quarter of said second period after said incoming
time and outputting a second quadrature amplitude of said second
incoming signal; second means for calculating a second phase at
said incoming time based on said second in-phase amplitude and said
second quadrature amplitude and outputting said second phase;
second means for summing said difference, said second difference,
said phase, and said second phase; and second means for applying a
fourth illumination to said image point in substantial proportion
to said second phase.
42. The system for beam-forming for ultrasound imaging of claim 40,
comprising further means for amplifying said outgoing signal.
43. The system for beam-forming for ultrasound imaging of claim 40,
comprising further means for amplifying said incoming signal.
44. The system for beam-forming for ultrasound imaging of claim 40,
comprising further means for pre-amplifying said incoming
signal.
45. The system for beam-forming for ultrasound imaging of claim 40,
comprising further means for storing said incoming signal.
46. The system for beam-forming for ultrasound imaging of claim 40,
comprising further means for viewing an image comprising said image
point.
47. The system for beam-forming for ultrasound imaging of claim 40,
comprising further means for guiding insertion of a needle, a
catheter, or an endoscope based on an image comprising said image
point.
48. An ultrasound beamformer apparatus, comprising: a signal
generator for producing an outgoing signal having an outgoing
amplitude at an outgoing time; a transducer for converting said
outgoing signal to outgoing ultrasound; a plurality of transducers
for converting at least a portion of said outgoing ultrasound that
is reflected to incoming signals, said incoming signals having
oscillations in time; a plurality of signal receivers for
converting each of said incoming signals to a pair, or time series
of pairs of in phase and quadrature samples; and a focusing
apparatus for combining said in phase and quadrature samples to
yield a focused in phase/quadrature sample.
49. The ultrasound beamformer apparatus of claim 48, wherein:
complex demodulated echo data obtained from a single range from
each transducer array element are sampled; complex echo signals are
multiplied by complex weightings; and the results are summed to
focus at a specific point at the range of interest.
50. The ultrasound beamformer apparatus of claim 48, wherein: the
complex demodulation is performed using an analog demodulation
circuit on each element.
51. The ultrasound beamformer apparatus of claim 48, wherein: the
complex demodulation is performed by sampling the incoming signal
at two points separated in time by approximately 1/4 of a
period.
52. The ultrasound beamformer apparatus of claim 48, wherein: the
complex demodulation is performed via digital means.
53. The ultrasound beamformer apparatus of claim 48, wherein: the
focusing operation is repeated on the same set of echo data at a
plurality of points to form complex image data at that range.
54. The ultrasound beamformer apparatus of claim 53, wherein: the
plurality of image points are along a line at the range of
interest.
55. The ultrasound beamformer apparatus of claim 53, wherein: the
plurality of image points lie within a plane at the range of
interest and thereby form a complex c-scan.
56. The ultrasound beamformer apparatus of claim 53, wherein: the
process of forming image lines is repeated at numerous ranges to
form a planar ultrasound image, possibly being a b-mode image.
57. The ultrasound beamformer apparatus of claim 53, wherein: the
process of forming image planes is repeated at multiple ranges to
form a complex 3D image.
58. The ultrasound beamformer apparatus of claim 48, wherein: the
envelope of the magnitude of the complex image is taken for display
to the user.
59. The ultrasound beamformer apparatus of claim 48, wherein: the
phases of the complex weightings used for focusing are determined
so as to compensate for path length differences between different
transducer array elements and the focal point.
60. The ultrasound beamformer apparatus of claim 48, wherein: the
magnitude of applied complex weightings are selected to maintain a
reasonable balance between main-lobe resolution and side-lobe
levels in the system response.
61. The ultrasound beamformer apparatus of claim 48, wherein: the
complex weightings used for focusing are determined so as to
minimize the sum squared error between some desired system response
and the true system response following the method described by
Ranganathan and Walker in "A Novel Beamformer Design Method for
Medical Ultrasound: Part I: Theory" a paper in press for IEEE
Trans. Ultrason. Ferroelec. Freq. Contr.
62. The ultrasound beamformer apparatus of claim 48, wherein: the
transducer array employed for imaging consists of a plurality of
array elements transducer elements placing in a linear
configuration selected from the group consisting of: a linear
array, a phased array, and a curvilinear array.
63. The ultrasound beamformer apparatus of claim 48, wherein: the
transducer array employed for imaging consists of a plurality of
elements arranged in an unequally sampled 2D configuration or a
1.5-D array.
64. The ultrasound beamformer apparatus of claim 48, wherein: the
transducer array employed for imaging consists of a plurality of
elements that are placed in an equally sampled 2D
configuration.
65. The ultrasound beamformer apparatus of claim 64, wherein a
fraction of the elements of the array are utilized such that the
resulting array is a sparse 2D array.
66. The ultrasound beamformer apparatus of claim 64, wherein: all
elements of the array are utilized such that the resulting array is
a fully sampled 2D array.
67. The ultrasound beamformer apparatus of claim 48, wherein:
connections are made to individual array elements such that
individual elements may be used for either transmission or
reception, but not both, thereby eliminating the need for receive
protection circuitry.
68. The ultrasound beamformer apparatus of claim 48, wherein: only
a fraction of elements are used to form any given image point.
69. The ultrasound beamformer apparatus of claim 48, wherein: the
focusing operation is repeated for different fractions of the
aperture thereby obtaining multiple redundant views of the same
target location.
70. The ultrasound beamformer apparatus of claim 48, wherein: the
multiple looks are averaged after taking their magnitudes so as to
reduce the appearance of speckle in the resulting image.
71. The ultrasound beamformer apparatus of claim 48, wherein: the
complex image points are used over successive acquisitions to
estimate blood flow or tissue motion.
72. The ultrasound beamformer apparatus of claim 48, wherein: the
sampling operation is performed at multiple ranges for a single
transmit event, thereby increasing the image formation rate.
Description
CROSS-REFERENCE TO RELATED APPLICATIONS
[0001] The present application is National Stage filing under 35
U.S.C. 371 of International Applications No. PCT/US2004/000887
which claims priority to U.S. Provisional Application Ser. Nos.
60/440,020 filed on Jan. 14, 2003, 60/439,990 filed on Jan. 14,
2003, and 60/440,262 filed on Jan. 15, 2003 the entire disclosures
of which are incorporated herein by reference.
BACKGROUND
[0002] 1. Field of the Invention
[0003] The present invention relates to ultrasonic diagnostic
imaging systems and methods. More specifically, the preferred
embodiments relate to a device and method for ultrasound imaging
beam-forming that may be incorporated in a substantially integrated
hand-held ultrasonic diagnostic imaging instrument.
[0004] 2. Introduction
[0005] Medical imaging is a field dominated by high cost systems
that may be so complex as to require specialized technicians for
operation and the services of experienced medical doctors and
nurses for image interpretation. Medical ultrasound, which is
considered a low cost modality, utilizes imaging systems costing as
much as $250K. These systems may be operated by technicians with
two years of training or specialized physicians. This high-tech,
high-cost approach works very well for critical diagnostic
procedures. However it makes ultrasound impractical for many of the
routine tasks for which it would be clinically useful.
[0006] A number of companies have attempted to develop low cost,
easy to use systems for more routine use. The most notable effort
is that by Sonosite. Their system produces very high quality images
at a system cost of approximately $20,000. While far less expensive
than high-end systems, these systems are still very sophisticated
and require a well-trained operator. Furthermore, at this price few
new applications may be opened.
[0007] Many ultrasonic imaging systems utilize an array transducer
that is connected to beamformer circuitry through a cable, and a
display that is usually connected directly to or integrated with
the beam-former. This approach is attractive because it allows the
beamformer electronics to be as large as is needed to produce an
economical system. In addition, the display may be of a very high
quality.
[0008] Some conventional system architectures have been improved
upon through reductions in beam-former size. One of the most
notable efforts has been undertaken by Advanced Technologies
Laboratories and then continued by a spin-off company, Sonosite.
U.S. Pat. No. 6,135,961 to Pflugrath et al., entitled "Ultrasonic
Signal Processor for a Hand Held Ultrasonic Diagnostic Instrument,"
hereby incorporated by reference herein in its entirety, describes
some of the signal processing employed to produce a highly portable
ultrasonic imaging system. The Pflugrath '961 patent makes
reference to an earlier patent, U.S. Pat. No. 5,817,024 to Ogle et
al., entitled, "Hand Held Ultrasonic Diagnostic instrument with
Digital Beamformer," hereby incorporated by reference herein in its
entirety. In U.S. Pat. No. 6,203,498 to Bunce et al., entitled
"Ultrasonic Imaging Device with Integral Display," hereby
incorporated by reference herein in its entirety, however, the
transducer, beamformer, and display may be all integrated to
produce a very small and convenient imaging system.
[0009] Other references of peripheral interest are U.S. Pat. No.
6,669,641 to Poland, et al., entitled "Method of and system for
ultrasound imaging," which describes an ultrasonic apparatus and
method in which a volumetric region of the body is imaged by
biplane images. One biplane image has a fixed planar orientation to
the transducer, and the plane of the other biplane image can be
varied in relation to the fixed reference image.
[0010] U.S. Pat. No. 6,491,634 to Leavitt, et al., entitled
"Sub-beam-forming apparatus and method for a portable ultrasound
imaging," describes a sub-beam-forming method and apparatus that is
applied to a portable, one-dimensional ultrasonic imaging system.
The sub-beam-forming circuitry may be included in the probes
assembly housing the ultrasonic transducer, thus minimizing the
number of signals that are communicated between the probe assembly
and the portable processor included in the imaging system.
[0011] U.S. Pat. No. 6,380,766 to Savord, entitled "Integrated
circuitry for use with transducer elements in an imaging system,"
describes integrated circuitry for use with an ultrasound
transducer of an ultrasound imaging system.
[0012] U.S. Pat. No. 6,013,032 to Savord, entitled "Beam-forming
methods and apparatus for three-dimensional ultrasound imaging
using two-dimensional transducer array," describes an ultrasound
imaging system including a two-dimensional array of ultrasound
transducer elements that define multiple sub-arrays, a transmitter
for transmitting ultrasound energy into a region of interest with
transmit elements of the array, a sub-array processor and a phase
shift network associated with each of the sub-arrays, a primary
beam-former and an image generating circuit.
[0013] U.S. Pat. No. 6,126,602 to Savord, et al., entitled "Phased
array acoustic systems with intra-group processors," describes an
ultrasound imaging apparatus and method that uses a transducer
array with a very large number of transducer elements or a
transducer array with many more transducer elements than
beam-former channels.
[0014] U.S. Pat. No. 5,997,479 to Savord, et al., entitled "Phased
array acoustic systems with intra-group processors," describes an
ultrasound imaging apparatus and method that uses a transducer
array with a very large number of transducer elements or a
transducer array with many more transducer elements than
beam-former channels.
[0015] U.S. Pat. No. 6,582,372 to Poland, entitled "Ultrasound
system for the production of 3-D images," describes an ultrasound
system that utilizes a probe in conjunction with little or no
specialized 3-D software/hardware to produce images having depth
cues.
[0016] U.S. Pat. No. 6,179,780 to Hossack, et al., entitled "Method
and apparatus for medical diagnostic ultrasound real-time 3-D
transmitting and imaging," describes a medical diagnostic
ultrasound real-time 3-D transmitting and imaging system that
generates multiple transmit beam sets using a 2-D transducer
array.
[0017] U.S. Pat. No. 6,641,534 to Smith, et al., entitled "Methods
and devices for ultrasound scanning by moving sub-apertures of
cylindrical ultrasound transducer arrays in two dimensions,"
describes methods of scanning using a two dimensional (2-D)
ultrasound transducer array.
[0018] U.S. Pat. No. 4,949,310 to Smith, et al., entitled "Maltese
cross processor: a high speed compound acoustic imaging system,"
describes an electronic signal processing device which forms a
compound image for any pulse-echo ultrasound imaging system using a
two-dimensional array transducer.
[0019] U.S. Pat. No. 6,276,211 to Smith, entitled "Methods and
systems for selective processing of transmit ultrasound beams to
display views of selected slices of a volume," describes the
selection of a configuration of slices of a volume, such as B
slices, I slices, and/or C slices.
[0020] Commercial ultrasound systems have been limited to
one-dimensional (1-D) or linear transducer arrays until fairly
recently. A typical number of transducers in such an array may be
128. Providing separate multiplex and receive circuitry is
manageable with this many transducers, albeit with significant use
of expensive high-voltage switches. Newer arrays, however, may be
likely to be two-dimensional (2-D) or square arrays. The number of
transducers in a two-dimensional array may range up to
128.times.128 or 16,384, and is often in the thousands. Maintaining
separate receive, transmit, and multiplex partitioning for the
transducers in such an array creates a tremendous burden in terms
of cost, space, and complexity. The power consumption and heat
dissipation of thousands high-voltage multiplexers is enough to
discourage the use of two-dimensional arrays in portable ultrasound
imaging systems.
[0021] Current beam-forming strategies can be broadly classified
into the two approaches depicted in FIG. 5. One approach is to use
digital time delays to focus the data, as illustrated in 5 (a).
Geometric delays are calculated and applied to the digitized data
on each channel. In such beam-formers, the data needs to either be
sampled at a very high sampling rate or interpolated.
Implementation of time delays requires sufficient memory to hold a
few hundred samples per channel to implement an adequate delay
envelope, constraining system complexity.
[0022] In the second approach, systems combine time delays with
complex phase rotation, as depicted in 5 (b). Coarse focusing is
implemented by delaying the digitized data on each channel. Fine
focusing is accomplished by phase rotation of data that has
undergone complex demodulation at the center frequency. Such
systems require circuitry to perform complex demodulation on every
channel. Time delay beam-forming requires significant fast memory
to implement a reasonable delay envelope.
[0023] Conventional approaches to generating I/Q data may also
include analog/digital baseband demodulation, or use a Hilbert
transform. Using a demodulation based approach to generate I/Q data
may necessitate significant extra circuitry on each channel, while
use of the Hilbert transform may require a significant amount of
memory to hold the raw RF data.
[0024] Accordingly, existing ultrasound systems with thousands of
separate transmit and receive switches may be too expensive for
many applications. While a variety of systems and methods may be
known, there remains a need for improved systems and methods.
BRIEF DESCRIPTION OF THE DRAWINGS
[0025] The preferred embodiments of the present invention are shown
by a way of example, and not limitation, in the accompanying
figures, in which:
[0026] FIG. 1 is a schematic diagram of an ultrasound imaging
beam-forming apparatus according to a first embodiment of the
invention;
[0027] FIG. 2 is a schematic diagram of a protection circuit for
use with an embodiment of the invention;
[0028] FIG. 3 is a schematic diagram of a protection circuit for
use with an embodiment of the invention;
[0029] FIG. 4 is a schematic diagram of an ultrasound imaging
beam-forming apparatus according to a second embodiment of the
invention;
[0030] FIG. 5 is a schematic diagram of a conventional ultrasound
imaging beam-forming apparatus;
[0031] FIG. 6 are graphs of signals for use with an embodiment of
the invention; and
[0032] FIG. 7 is a schematic diagram of a signal receiver for use
with an embodiment of the invention.
SUMMARY OF THE INVENTION
[0033] The present invention ultrasound imaging beam-former may be
incorporated in an ultrasonic imaging system convenient enough to
be a common component of nearly every medical examination and
procedure. The present invention ultrasound imaging beam-former
provides the potential to have a broad and significant impact in
healthcare. The instant document identifies various clinical
applications of the present invention ultrasound imaging
beam-forming apparatus, but should not be limited thereto, and
other applications will become attained as clinicians gain access
to the system and method.
[0034] The preferred embodiments of the present invention may
improve significantly upon existing methods and/or apparatuses. In
particular, the present invention comprises an ultrasound imaging
beam-former that may be used in a hand held ultrasonic instrument
such as one provided in a portable unit which performs B-mode or
C-Mode imaging and/or collects three dimensional (3-D) image
data.
[0035] According to some embodiments, an ultrasound imaging
beam-former is provided that includes, in a first aspect of the
invention, an ultrasound imaging beam-former apparatus includes a
signal generator for producing an outgoing signal, a transducer for
converting the outgoing signal to outgoing ultrasound and for
converting at least a portion of the outgoing ultrasound that is
reflected to an incoming signal, the incoming signal having a
period, and a signal receiver for processing the incoming signal,
the signal receiver including, an in-phase sample- and-hold
connected receivably to the transducer for sampling the incoming
signal at an incoming time and outputting an in-phase amplitude of
the incoming signal at substantially the incoming time, a
quadrature sample-and-hold connected receivably to the transducer
for sampling the incoming signal at substantially one-quarter of
the period after the incoming time, the quadrature sample-and-hold
outputting a quadrature amplitude of the incoming signal at
substantially one-quarter of the period after the incoming time, a
phase calculator connected receivably to the in-phase
sample-and-hold and the quadrature sample-and-hold for receiving
the incoming time, the in-phase amplitude, and the quadrature
amplitude and outputting a phase, and a phase rotator for applying
an illumination to the image point in substantial proportion to the
phase.
[0036] In a second aspect, a method of beam-forming for ultrasound
imaging includes generating an outgoing signal, transducing the
outgoing signal to outgoing ultrasound, receiving at least a
portion of reflected outgoing ultrasound, transducing the reflected
ultrasound to an incoming signal having a period, sampling the
incoming signal at an incoming time to produce an in-phase
amplitude of the incoming signal, sampling the incoming signal at
substantially one-quarter of the period after the incoming time to
produce a quadrature amplitude of the incoming signal, calculating
a phase at the incoming time based on the in-phase amplitude and
the quadrature amplitude, and applying an illumination to the image
point in substantial proportion to the phase.
[0037] In a third aspect, a system for beam-forming for ultrasound
imaging includes means for generating an outgoing signal, means for
transducing the outgoing signal to outgoing ultrasound, means for
transducing at least a portion of reflected outgoing ultrasound to
an incoming signal having a period, means for sampling the incoming
signal at an incoming time and outputting an in-phase amplitude of
the incoming signal, means for sampling the incoming signal at
substantially one-quarter of the period after the incoming time and
outputting a quadrature amplitude of the incoming signal, means for
calculating a phase at the incoming time, based on the in-phase
amplitude and the quadrature amplitude and outputting the phase,
means for measuring a difference between the outgoing amplitude and
the magnitude, means for applying a first illumination to a image
point in substantial proportion to the difference, and means for
applying a second illumination to the image point in substantial
proportion to the phase.
[0038] The above and/or other aspects, features and/or advantages
of various embodiments will be further appreciated in view of the
following description in conjunction with the accompanying figures.
Various embodiments can include and/or exclude different aspects,
features and/or advantages where applicable. In addition, various
embodiments can combine one or more aspect or feature of other
embodiments where applicable. The descriptions of aspects, features
and/or advantages of particular embodiments should not be construed
as limiting other embodiments or the claims.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS
[0039] The device and method for ultrasound imaging beam-forming
may be utilized with various products and services as discussed
below, but is not limited thereto. Technicians may attempt to
insert needles into a vein based on the surface visibility of the
vein coupled with their knowledge of anatomy. While this approach
works quite well in thin, healthy individuals, it can prove
extremely difficult in patients who may be ill or obese. It may be
desirable to have a relatively small, inexpensive, and portable
ultrasound imaging system for guiding the insertion of intravenous
(IV) devices like needles and catheters into veins, or for drawing
blood.
[0040] Sleep apnea (obstruction of the air passage in the of the
throat) may affect more than eighteen million Americans.
Obstructive sleep apnea may be among the most common variants of
sleep apnea. Obstructive sleep apnea may represent a significant
risk to the patient. It is difficult and expensive to diagnose
obstructive sleep apnea. Typical diagnostic methods require an
overnight hospital stay in an instrumented laboratory. Many at-risk
patients refuse this inconvenient testing regime and thus go
undiagnosed. It may be desirable to have a relatively small,
inexpensive, and portable ultrasound imaging system to aid in the
diagnosis of obstructive sleep apnea in a minimally obtrusive
manner.
[0041] Manual palpation is an exceedingly common diagnostic
procedure. Clinicians use their sense of touch to feel for
subcutaneous lumps or even to estimate the size of lymph nodes or
other masses. While palpation undoubtedly yields valuable
qualitative information, numerous studies have shown it to have
extremely poor sensitivity and that quantitative size estimates may
be completely unreliable. It may be desirable to have a relatively
small, inexpensive, and portable ultrasound imaging system to aid
in observing subcutaneous tissues.
[0042] It may be desirable to place an image display at a
transducer. It may be desirable to have a relatively small,
inexpensive, and portable ultrasound imaging system to aid in
placing the image display at the transducer.
[0043] Ultrasound may be used to search for internal defects in
metallic or ceramic parts in a broad variety of industrial
applications. Current systems may be cost effective, but may be
unwieldy and acquire limited data, making it difficult to ensure
that a thorough search has been performed. It may be desirable to
have a relatively small, inexpensive, and portable ultrasound
imaging system to aid in non-destructive evaluation.
[0044] Furthermore, new users may expect ultrasound images to
produce representations parallel to the skin's surface, i.e. C-Scan
images. It would be desirable for a low cost, system to be capable
of producing C-Scan images. It may further be desirable to display
data in the intuitive C-scan format to allow clinicians with little
or no training in reviewing ultrasound images to make use of the
device.
[0045] Ultrasound imaging devices may be too expensive for some
applications. It may be desirable for an ultrasound imaging device
to rely primarily or exclusively on receive side beam-forming to
reduce or eliminate transmit-side circuitry, enabling the
beam-former to be implemented using large scale integration or as
software, and enabling system to be produced at a lower cost.
[0046] It may further be desirable for an ultrasound imaging device
to rely primarily or exclusively on phase rotation for focusing,
enabling the beam-former to be implemented using large scale
integration or as software, and enabling system to be produced at a
lower cost.
[0047] Ultrasound imaging devices may be insufficiently portable
for some applications. It may be desirable for an ultrasonic
imaging device to be of a small size to make it easy to carry the
device in a pocket or on a belt attachment. This may make the
device as convenient as a stethoscope and will thus open new
applications. It may be desirable for an ultrasound imaging device
to rely primarily or exclusively on receive side beam-forming to
reduce or eliminate transmit-side circuitry, enabling the
beam-former to be implemented using large scale integration or as
software, and enabling the system to be made portable. It may
further be desirable for an ultrasound imaging device to rely
primarily or exclusively on phase rotation for focusing to reduce
or eliminate transmit-side circuitry, enabling the beam-former to
be implemented using large scale integration or as software, and
enabling the system to be made portable.
[0048] Since it would be desirable for a beam-former to be simple,
small, and low cost, it would be further desirable for the size and
speed requirements of digital memory in such a beam-former to be
minimized. It would be further desirable for focusing to be
performed solely by phase rotation of I/Q data, thus eliminating
the need for some circuitry, and allowing some of the remaining
circuitry to be implemented as an integrated circuit. This may also
allow the use of slower memory and reduce the computational
complexity of the beam-former.
[0049] It would be further desirable for I/Q data to be generated
by sampling an RF signal directly. In one embodiment, an analytic
signal (I/Q data) is generated by sampling the received RF signal
directly, in a manner analogous to the Hilbert transform. In one
embodiment, focusing is implemented via phase rotation of this I/Q
data.
[0050] In FIG. 1 is shown an ultrasound imaging beam-former
apparatus 100 according to a first embodiment of the invention.
Ultrasound imaging beam-former apparatus 100 may include a signal
generator 102 for producing an outgoing signal 104 having an
outgoing amplitude 106 at an outgoing time 108, as shown in FIG.
6A. In several embodiments, outgoing signal 104 may be an
electrical signal, an electro-magnetic signal, or an optical
signal.
[0051] If outgoing signal 104 is an optical signal, cross-talk
between the circuits of ultrasound imaging beam-former apparatus
100 may be reduced or eliminated, since optical signals do not, in
general, interfere with one another. This may allow ultrasound
imaging beam-former apparatus 100 to be made smaller than an
equivalent electronic device by increasing the density of the
circuits. In one case, outgoing signal 104 may be processed as an
optical signal and converted to an electrical signal to drive a
transducer. An integrated circuit comprising ultrasound imaging
beam-forming apparatus 100 may be implemented out of
gallium-arsenide (GaAs) so that the both the optical circuits and
the electrical circuits can be implemented on the same device. In
another case, a transducer utilizing sono-luminescence to convert
light directly into sound may be used, dispensing entirely with any
need for an electrical-optical interface.
[0052] In several embodiments, signal generator 102 may be a
storage device, such as a read-only memory (ROM), an oscillator
such as a crystal oscillator, a resonant circuit such as a
resistor-inductor-capacitor (RLC) or tank circuit, a resonant
cavity such as a ruby laser or a laser diode or a tapped delay
line.
[0053] In the event that signal generator 102 is a storage device,
outgoing signal 104 may have been stored previously, to be read out
when needed. In this embodiment, several versions of outgoing
signal 104 may be stored for use with various objects 170 to be
imaged. Ultrasound imaging beam-forming apparatus 100 may thus be
set to produce a signal appropriate for a particular object 170 to
be imaged by choosing one of the stored versions of outgoing signal
104.
[0054] In the event that signal generator 102 is an oscillator,
outgoing signal 104 may be a sinusoid of varying frequencies. In
this case, outgoing signal 104 may be generated at an arbitrarily
high clock speed and still be forced through filters of arbitrarily
small bandwidth. This may be advantageous, for example, if a wide
band signal is inconvenient. A resonant circuit or a resonant
cavity may work in a similar manner. Furthermore, an oscillator may
be used to produce a range of frequencies, from which a frequency
that generates an optimum response may be selected.
[0055] In the event that signal generator 102 is tapped delay line,
outgoing signal 104 could be generated in a manner similar to a
spreading code in a code division multiple access (CDMA) format
cell phone system. In this case outgoing signal 104 would not need
to be a pure sinusoid, but may be a code with a fixed repetition
length, such as a Walsh or a Gold code. This may, for example,
allow an autocorrelation length of outgoing signal 104 to be
adjusted to enhance or suppress coded excitation of an incoming
signal.
[0056] If signal generator 102 is a tapped delay line it may be
followed by an equalizer to bias or pre-emphasize a range of
frequencies in outgoing signal 104. In one embodiment, the
equalizer may be an adaptive equalizer that operates on an incoming
signal analogous to the sound reflected by the imaged object 170.
In this case, the incoming signal could be measured and the result
applied to the adaptive equalizer to compensate for frequency
attenuation of the sound by amplifying one or more frequencies of
the incoming signal or outgoing signal 104 as necessary. This may
be useful if, for example, object 170 attenuates or absorbs sound
to the point that no return signal is available for imaging. In one
embodiment, the adaptive equalizer could be placed in parallel with
signal generator 102 and in series with the incoming signal.
[0057] In one embodiment, an equalizer could be placed in series
with signal generator 102. In this case the equalizer could
emphasize a particular frequency or frequencies in outgoing signal
104. The equalizer may, for example, place a bias or pre-emphasis
toward lower frequencies on outgoing signal 104. This embodiment
may be appropriate if, for example, object 170 to be imaged is
expected to have features that attenuate lower frequencies
significantly more than higher frequencies to the extent that
imaging may be difficult. The converse may be true as well, in that
the equalizer may have a bias or pre-emphasis toward higher
frequencies.
[0058] In one embodiment, outgoing signal 104 may be amplified. In
one embodiment, signal generator 102 may include a generator
amplifier 158 for amplifying outgoing signal 104. Generator
amplifier 158 may pre-emphasize certain frequencies of outgoing
signal 104 to suit the attenuation characteristics of object 170 to
be imaged as well. Signal generator 102 may also include an
oscillator to produce an appropriate modulation frequency, such as
a radio frequency (RF) signal, with which to modulate outgoing
signal 104.
[0059] A transducer 110 may convert outgoing signal 104 to outgoing
ultrasound 112. In several embodiments, transducer 110 may be a
piezoelectric element, a voice coil, a crystal oscillator or a Hall
effect transducer 110. In one embodiment, reversals of outgoing
signal 104 produce vibration of a surface of transducer 110 at
substantially the frequency of outgoing signal 104. In another
embodiment, reversals of outgoing signal 104 produce vibrations of
a surface of transducer 110 at frequencies that are significantly
higher or lower than the frequency of outgoing signal 104, such as
harmonics of outgoing signal 104. This vibration may, in turn,
produce successive compressions and rarefactions of an atmosphere
surrounding the surface of transducer 110, also at substantially
the frequency of outgoing signal 104. If the frequency of outgoing
signal 104 is substantially higher than a frequency at which sound
may be heard, the successive compressions and rarefactions of the
atmosphere may be termed ultrasound.
[0060] In one embodiment, transducer 110 may include a plurality of
transducers 110. In one embodiment, plurality of transducers 110
may be arranged in an array 166. In several embodiments, array 166
may be a linear array, a phased array, a curvilinear array, an
unequally sampled 2-D array, a 1.5-D array, an equally sampled 2D
array, a sparse 2D array, or a fully sampled 2D array.
[0061] If outgoing ultrasound 112 is reflected by object 170, some
of outgoing ultrasound 112 may return to ultrasound imaging system
100 as reflected ultrasound 182. Reflected ultrasound 182 may be
converted to an incoming signal 114 having a period 116, as shown
in FIG. 6B. In several embodiments, incoming signal 114 may be an
electro-magnetic signal, an electrical signal or an optical signal.
In several embodiments, incoming signal 114 may be amplified,
pre-amplified, or stored.
[0062] In one embodiment, outgoing ultrasound 112 may be delayed or
attenuated partially by object 170. A first portion 174 of outgoing
ultrasound 112, for example, may be reflected immediately upon
encountering a nearer surface 178 of object 170 while a second
portion 176 of outgoing ultrasound 112 is not reflected until it
encounters a further surface 180 of object 170. A round trip of
second portion 176 will thus be longer than a round trip of first
portion 174, resulting in a delay of second portion 176 relative to
first portion 174, as well as delays of both first and second
portions 174,176 relative to outgoing ultrasound 112. Furthermore,
second portion 176 may be damped or attenuated by a material of
object 170. The delays may be measured for disparate points of
object 170, producing an image 168 of object 170.
[0063] Apparatus 100 may include a signal receiver 118 for
processing incoming signal 114. In one embodiment, signal receiver
118 may be implemented as a digital signal processor 164. In one
embodiment, signal receiver 118 may be implemented as an integrated
circuit.
[0064] Ultrasonic transducers associated with ultrasound imaging
systems may be driven from a single terminal with the second
terminal grounded. A transducer may be used to transmit ultrasound
signals as well as receive reflected ultrasound. A signal received
at a transducer may typically be several orders of magnitude
smaller than the signal that was transmitted due to, inter alia,
signal attenuation by the target tissue. Some of the signal may be
lost due to transducer inefficiencies as well. It may be thus
necessary to couple the transducer to a high-voltage transmit
signal while the ultrasound is being transmitted, and then to a
sensitive low-noise pre-amplifier while the reflected ultrasound is
being received.
[0065] A switch that couples the transducer to the transmit and
receive signals must be capable of withstanding high peak transmit
voltages (typically 50-200 volts) while isolating the pre-amplifier
input from those voltage levels, since they would otherwise destroy
the pre-amplifier. If a receiver for the signals from the
transducers is implemented as a high-density, low-voltage
integrated circuit (IC), the switches themselves may need to be
implemented off-chip in a separate package from materials and
devices that can withstand the high voltage transmit pulses.
[0066] In one embodiment, ultrasound imaging system 100 may include
a protection circuit 172 to allow both transmit and receive
operations, as shown in FIG. 2. A piezoelectric transducer array
202, shown on the left, acts as an interface to a signal processor
by converting electrical signals to acoustic pulses and vice versa.
Images may be formed by transmitting a series of acoustic pulses
from the transducer array 202 and displaying signals representative
of the magnitude of the echoes received from these pulses. A
beam-former 214 applies delays to the electrical signals to steer
and focus the acoustic pulses and echoes.
[0067] Image formation begins when a state of a transmit/receive
switch (TX/RX switch) 204 is altered to connect the transducer
elements 202 to individual transmit circuits. Next, transmit
generators 206 output time varying waveforms with delay and
amplitude variations selected to produce a desired acoustic beam.
Voltages of up to 200 Volts may be applied to the transducer
elements 202. Once transmission is complete, the state of the TX/RX
switch 204 is altered again to connect the transducer elements 202
to individual receive circuitry associated with each element.
[0068] Signals representative of incoming echoes may be amplified
by pre-amplifiers 208 and time gain control (TGC) 210 circuits to
compensate for signal losses due to diffraction and attenuation.
Note that the transducer array 202 shown in FIG. 2 has one common
electrode 212, and the non-common electrodes may be multiplexed
between high-voltage transmit and low-voltage receive signals. This
conventional TX/RX switch 204 is the source of considerable expense
and bulk in typical ultrasound systems.
[0069] In FIG. 3 is shown an alternative ultrasound imaging
beam-forming apparatus 300 with a protection circuit for use with
an embodiment of the invention. Ultrasound imaging beam-forming
apparatus 300 may include a signal generator 302 for producing an
outgoing signal 304.
[0070] Ultrasound imaging beam-forming apparatus 300 may also
include a transducer 306 for converting outgoing signal 304 to
outgoing ultrasound 308 at a frequency of outgoing signal 304. In
one embodiment, transducer 306 may have a transmit side 314 forming
an interface with outgoing signal 304.
[0071] In one embodiment, transmit side 314 may be connected
operably to a transmit switch 318. In several embodiments, transmit
switch 318 may be an electronic switch, an optical switch, a
micro-mechanical switch, a transistor, a field-effect transistor
(FET), a bi-polar transistor, a metal-oxide-semiconductor (MOS)
transistor, a complementary metal-oxide-semiconductor (CMOS)
transistor, or a metal-oxide-semiconductor field-effect transistor
(MOSFET). Transmit switch 318 may be connected switchably to signal
generator 302 and a ground 320.
[0072] In one embodiment, transducer 306 may convert at least a
portion of reflected ultrasound 310 to an incoming signal 312. In
several embodiments, incoming signal 312 may be an electro-magnetic
signal, an electrical signal, or an optical signal. In one
embodiment, transducer 306 may have a receive side 316 forming an
interface with incoming signal 312.
[0073] In one embodiment, receive side 316 may be connected
operably to a receive switch 322. In several embodiments, receive
switch 322 may be an electronic switch, an optical switch, a
micro-mechanical switch, a transistor, a field-effect transistor, a
bi-polar transistor, a MOS transistor, a CMOS transistor, or a
MOSFET transistor. Receive switch 322 may be connected switchably
to a signal receiver 324 and ground 320.
[0074] In one embodiment, transmit switch 318 may connect transmit
side 314 to signal generator 302 for a first predetermined period
of time while signal generator 302 generates outgoing signal 304.
In this embodiment, receive switch 322 may connect receive side 316
to signal receiver 324 for a second predetermined period of time
while signal receiver 324 receives incoming signal 312. Transmit
switch 318 may connect transmit side 314 to ground 320 during
substantially second predetermined period of time while signal
receiver 324 receives incoming signal 312, and receive switch 322
may connect receive side 316 to ground 320 during substantially
first predetermined period of time while signal generator 302
generates outgoing signal 304. In one embodiment, transmit side 314
and receive side 316 are on separate transducers 306.
[0075] In one embodiment, signal receiver 118 may include a
receiver amplifier 160 for amplifying incoming signal 114. In one
embodiment, signal receiver 118 may include a receiver
pre-amplifier 162 for amplifying incoming signal 114. In one
embodiment, signal receiver 118 may include a band-pass filter 164
for filtering incoming signal 114.
[0076] In one embodiment, signal receiver 118 may include an
in-phase sample- and-hold 120 connected receivably to transducer
110 for sampling incoming signal 114 at an incoming time 122 and
outputting an in-phase amplitude 124 of incoming signal 114 at
substantially incoming time 122. In one embodiment, signal receiver
118 may include an in-phase analog-to-digital converter 126
connected receivably to in-phase sample-and-hold 120 for assigning
an in-phase digital value 128 to in-phase amplitude 124 and
outputting in-phase digital value 128.
[0077] In one embodiment, signal receiver 118 may include a
quadrature sample-and-hold 130 connected receivably to transducer
110 for sampling incoming signal 114 at substantially one-quarter
of period 116 after incoming time 122, quadrature sample-and-hold
130 outputting a quadrature amplitude 132 of incoming signal 114 at
substantially one-quarter of period 116 after incoming time 122.
One-quarter of period 116 is merely exemplary. Incoming signal 114
may be sampled at any appropriate interval or fraction of period
116. In one embodiment, signal receiver 118 may include a
quadrature analog-to-digital converter 134 connected receivably to
quadrature sample-and-hold 130 for assigning a quadrature digital
value 136 to quadrature amplitude 132 and outputting quadrature
digital value 136.
[0078] In one embodiment, signal receiver 118 may include a
magnitude calculator 138 connected receivably to in-phase
analog-to-digital converter 126 and quadrature analog-to-digital
converter 134 for receiving incoming time 122, in-phase digital
value 128, and quadrature digital value 136 and outputting a
magnitude 140. In one embodiment, signal receiver 118 may include a
phase calculator 142 connected receivably to in-phase
analog-to-digital converter 126 and quadrature analog-to-digital
converter 134 for receiving incoming time 122, in-phase digital
value 128, and quadrature digital value 136 and outputting a phase
144.
[0079] In one embodiment, incoming signal 114 may be band-pass
filtered by band-pass filter 164 and diverted to in-phase
sample-and-hold 120 and quadrature sample-and-hold 130. An in-phase
clock signal 184 driving in-phase sample-and-hold 120 may be of the
same frequency as a quadrature clock signal 186 driving quadrature
sample-and-hold 130. Quadrature clock signal 186 may, however, be
offset by a quarter of period 116 with respect to in-phase clock
signal 184 at an assumed center frequency of incoming signal 114.
An output of in-phase sample-and-hold 120 may be digitized by
in-phase analog-to-digital converter 126 while an output of
quadrature sample-and-hold 130 is digitized in quadrature
analog-to-digital converter 134, forming I and Q channel data.
[0080] Reflected ultrasound 182 may be considered to be real part
of an amplitude and phase modulated complex exponential signal, or
analytic signal. The modulating signal may be expressed
mathematically as: [0081] , A(t)e.sup.j.phi.(t) with instantaneous
amplitude A(t) and phase .phi.(t). This is superimposed on a
carrier signal e.sup.-j.omega..sup.0.sup.t, where
.omega..sub.0=2.pi.f.sub.0 and f.sub.0 is the frequency of the
signal. Therefore the analytic signal S(t) can be written as, S
.function. ( t ) = .times. A .function. ( t ) .times. e - j
.function. ( .omega. 0 .times. t - .PHI. .function. ( t ) ) =
.times. A .function. ( t ) .times. cos .function. ( .omega. 0
.times. t - .PHI. .function. ( t ) ) - jA .function. ( t ) .times.
sin .function. ( .omega. 0 .times. t - .PHI. .function. ( t ) ) ( 1
) ##EQU1##
[0082] Only the real part of S (t), which is equivalent to
reflected ultrasound 182, is able to be acquired experimentally.
I(t)=Re{S(t)}=A(t)cos(.omega..sub.0t-.phi.(t)) (2)
[0083] The output of in-phase analog-to-digital converter 126 is
the signal in equation 2 after sampling, or
I(nT)=InT)=A(nT)cos(.omega..sub.0nT-.phi.(nT)), n=0, 1, 2, 3 . . .
(3)
[0084] where T is the sample interval. However, we also require the
imaginary component of S (t), shown below in equation 4, to perform
beam-forming. Q(t)=Im{S(t)}=-A(t)sin(.omega..sub.0t-.phi.(t))
(4)
[0085] Quadrature clock signal 186 has a time lag of a quarter
period at the assumed center frequency relative to the in-phase
clock signal 184, as shown 1 schematically in FIG. 7. Therefore the
relative time lag is: 1 4 .times. f 0 , or .times. .times. .pi. 2
.times. .omega. 0 . ##EQU2##
[0086] The output of quadrature sample-and-hold 130 is, Q ^
.function. ( nT ) = 1 .times. { nT + .pi. 2 .times. .omega. 0 } = A
.function. ( nT + .pi. 2 .times. .omega. 0 ) .times. cos .function.
( .omega. 0 .function. ( nT + .pi. 2 .times. .omega. 0 ) - .PHI.
.function. ( nT + .pi. 2 .times. .omega. 0 ) ) ( 5 ) ##EQU3##
[0087] We assume that the modulating signal A(t)e.sup.j.phi.(t)
varies slowly with time and approximate, A .function. ( nT + .pi. 2
.times. .omega. 0 ) .apprxeq. A .function. ( nT ) .times. .times.
and ( 6 ) .PHI. .function. ( nT + .pi. 2 .times. .omega. 0 )
.apprxeq. .PHI. .function. ( nT ) ( 7 ) ##EQU4##
[0088] Equation 5 can now be rewritten as follows. Q ^ .function. (
nT ) .apprxeq. .times. A .function. ( nT ) .times. cos .function. (
.omega. 0 .times. ( nT + .pi. 2 .times. .omega. 0 ) - .PHI.
.function. ( nT ) ) , n = 0 , 1 , 2 , 3 .times. .apprxeq. .times. -
A .function. ( nT ) .times. sin .function. ( .omega. 0 .times. nT -
.PHI. .function. ( nT ) ) .apprxeq. .times. Q .function. ( nT ) ( 8
) ##EQU5##
[0089] We therefore approximate the imaginary component of S (t),
or Q(t) in equation 4, by estimating it to be the output of
quadrature sample-and-hold 130.
[0090] Geometric time delays may be calculated and converted to
phase delays at the assumed center frequency. Complex weights that
implement apodization and focus with the calculated phase delays
may be applied to the I/Q data. In one embodiment, signal receiver
118 may include an apodizer 146 for applying a difference 148
between outgoing amplitude 106 and magnitude 140 and applying a
first illumination 150-1 to an image points 154 in substantial
proportion to difference 148. In one embodiment, signal receiver
118 may include a phase rotator 152 for applying a second
illumination 150-2 to image point 154 in substantial proportion to
phase 144.
[0091] In a second embodiment of the invention, shown in FIG. 4,
apparatus 100 may include a second transducer 110-2 for converting
outgoing signal 104 to second outgoing ultrasound 112-2. Some of
second outgoing ultrasound 112-2 may return to second transducer
110-2 if it is reflected by object 170 as well. Second transducer
110-2 may convert at least a portion of outgoing ultrasound 112 and
second outgoing ultrasound 112-2 to a second incoming signal 114-2
having a second period 116-2, as shown in FIG. 6C.
[0092] In one embodiment, signal receiver 118 may include a second
in-phase sample-and-hold 120-2 connected receivably to second
transducer 110-2 for sampling second incoming signal 114-2 at
incoming time 122 and outputting a second in-phase amplitude 124-2
of second incoming signal 114-2 at substantially incoming time 122.
In one embodiment, signal receiver 118 may include a second
in-phase analog-to-digital converter 126-2 connected receivably to
second in-phase sample-and-hold 120-2 for assigning a second
in-phase digital value 128-2 to second in-phase amplitude 124-2 and
outputting second in-phase digital value 128-2.
[0093] In one embodiment, signal receiver 118 may include a second
quadrature sample-and-hold 130-2 connected receivably to second
transducer 110-2 for sampling second incoming signal 114-2 at
substantially one-quarter of second period 116-2 after incoming
time 122, second quadrature sample-and-hold 130-2 outputting a
second quadrature amplitude 132-2 of second incoming signal 114-2
at substantially one-quarter of second period 116-2 after incoming
time 122. In one embodiment, signal receiver 118 may include a
second quadrature analog-to-digital converter 134-2 connected
receivably to second quadrature sample-and-hold 130-2 for assigning
a second quadrature digital value 136-2 to second quadrature
amplitude 132-2 and outputting second quadrature digital value
136-2.--[0085] In one embodiment, signal receiver 118 may include a
second magnitude calculator 138-2 connected receivably to second
in-phase analog-to-digital converter 126-2 and second quadrature
analog-to-digital converter 134-2 for receiving incoming time 122,
second in-phase digital value 128-2, and second quadrature digital
value 136-2 and outputting a second magnitude 140-2. In one
embodiment, signal receiver 118 may include a second phase
calculator 142-2 connected receivably to second in-phase
analog-to-digital converter 126-2 and second quadrature
analog-to-digital converter 134-2 for receiving incoming time 122,
second in-phase digital value 128-2, and second quadrature digital
value 136-2 and outputting a second phase 144-2.
[0094] In one embodiment, signal receiver 118 may include a second
apodizer 146-2 for applying a second difference 148-2 between
outgoing amplitude 106 and second magnitude 140-2 and applying a
third illumination 150-3 to an image point 154 in substantial
proportion to second difference 148-2. In one embodiment, signal
receiver 118 may include a second phase rotator 152-2 for applying
a fourth illumination 150-4 to image point 154 in substantial
proportion to second phase 144-2. In one embodiment, signal
receiver 118 may include a summer 156 for combining difference 148,
second difference 148-2, phase 144, and second phase 144-2 before
first, second, third, and fourth illuminations 150-1-150-4 are
applied to image point 154.
[0095] In a third embodiment, a method of beam-forming for
ultrasound imaging may include the steps of generating an outgoing
signal 104 having an outgoing amplitude 106 at an outgoing time
108, transducing outgoing signal 104 to outgoing ultrasound 112,
receiving at least a portion of reflected outgoing ultrasound 112,
transducing reflected ultrasound to an incoming signal 114 having a
period 116, sampling incoming signal 114 at an incoming time 122 to
produce an in-phase amplitude 124 of incoming signal 114, assigning
an in-phase digital value 128 to in-phase amplitude 124 sampling
incoming signal 114 at substantially one-quarter of period 116
after incoming time 122 to produce a quadrature amplitude 132 of
incoming signal 114, assigning a quadrature digital value 136 to
quadrature amplitude 132, calculating a magnitude 140 at incoming
time 122 based on in-phase digital value 128 and quadrature digital
value 136, calculating a phase 144 at incoming time 122 based on
in-phase digital value 128 and quadrature digital value 136,
measuring a difference 148 between outgoing amplitude 106 and
magnitude 140, applying a first illumination 150-1 to an image
point 154 in substantial proportion to difference 148, and applying
a second illumination 150-2 to image point 154 in substantial
proportion to phase 144.
[0096] In one embodiment, the method of beam-forming for ultrasound
imaging may further include the steps of transducing outgoing
signal 104 to second outgoing ultrasound 112-2, receiving at least
a portion of reflected outgoing ultrasound 112 and second outgoing
ultrasound 112-2, transducing reflected outgoing ultrasound 112 and
second outgoing ultrasound 112-2 to a second incoming signal 114-2
having a second period 116-2, sampling second incoming signal 114-2
at incoming time 122 to produce a second in-phase amplitude 124-2
of second incoming signal 114-2, assigning a second in-phase
digital value 128-2 to second in-phase amplitude 124-2, sampling
second incoming signal 114-2 at substantially one-quarter of second
period 116-2 after incoming time 122 to produce a second quadrature
amplitude 122-2 of second incoming signal 114-2, assigning a second
quadrature digital value 136-2 to second quadrature amplitude
122-2, calculating a second magnitude 140-2 at incoming time 122
based on second in-phase digital value 128-2 and second quadrature
digital value 136-2, calculating a second phase 144-2 at incoming
time 122 based on second in-phase digital value 128-2 and second
quadrature digital value 136-2, measuring a second difference 148-2
between outgoing amplitude 106 and second magnitude 140-2, summing
difference 148, second difference 148-2, phase 144, and second
phase 144-2, applying a third illumination 150-3 to image point 154
in substantial proportion to second difference 148-2, and applying
a fourth illumination 150-4 to image point 154 in substantial
proportion to second phase 144-2.
[0097] In one embodiment, the method of beam-forming may be
repeated to produce a plurality of image points 154 forming an
image 168. In several embodiments, image 168 may be viewed, used to
guide insertion of a needle, used to guide insertion of a catheter,
used to guide insertion of an endoscope, used to estimate blood
flow, or used to estimate tissue motion. In one embodiment,
plurality of image points 154 may be focused. In one embodiment,
focusing may be repeated on reflected outgoing ultrasound 112 at
plurality of image points 154.
[0098] In one embodiment, plurality of image points 154 may be
along a line at a range of interest. In one embodiment, a line may
be formed at a plurality of ranges to form a planar image. In one
embodiment, the planar image may be a B-mode image. In one
embodiment, plurality of image points 154 may lie within a plane at
a range of interest. In one embodiment, plurality of image points
154 may form a C-scan. In one embodiment, the plane may be formed
at multiple ranges. In one embodiment, several planes may form a
complex 1-D image.
[0099] In one embodiment, an envelope of magnitude 140 may be
displayed. In one embodiment, phase 144 may be used to compensate
for a path difference 148 between various transducers and object
170. In one embodiment, a main lobe resolution and a side lobe
level may be balanced based on magnitude 140. In one embodiment, a
sum squared error between a desired system response and a true
system response may be minimized.
[0100] One skilled in the art would appreciate that a variety of
tissue information may be obtained through judicious pulse
transmission and signal processing of received echoes with the
current invention. Such information could be displayed in
conjunction with or instead of the aforementioned echo
information.
[0101] One such type of information is referred to as color flow
Doppler as described in U.S. Pat. No. 4,573,477 to Namekawa et al.,
entitled "Ultrasonic Diagnostic Apparatus," hereby incorporated by
reference herein in its entirety. Another useful type of
information is harmonic image data as described in U.S. Pat. No.
6,251,074 to Averkiou et al., entitled "Ultrasonic Tissue Harmonic
Imaging" and U.S. Pat. No. 5,632,277 to Chapman et al., entitled
"Ultrasound Imaging System Employing Phase Inversion Subtraction to
Enhance the Image," both of which are hereby incorporated by
reference herein in their entirety. Yet another type of information
that may be obtained and displayed is known as Power Doppler as
described in U.S. Pat. No. 5,471,990 to Thirsk, entitled
"Ultrasonic Doppler Power Measurement and Display System," hereby
incorporated by reference herein in its entirety.
[0102] Angular scatter information might also be acquired using a
method described in a co-pending U.S. patent application Ser. No.
10/030,958, entitled "Angular Scatter Imaging System Using
Translating Apertures Algorithm and Method Thereof," filed Jun. 3,
2002, of which is hereby incorporated by reference herein in its
entirety. Speckle is a common feature of ultrasound images. While
it is fundamental to the imaging process, many users find its
appearance confusing and it has been shown to limit target
detectability. A variety of so called compounding techniques have
been described which could be valuable for reducing the appearance
of speckle in ultrasound transducer drive images. These techniques
include spatial compounding and frequency compounding, both of
which are well described in the literature.
[0103] One skilled in the art would appreciate that the common
practice of frequency compounding could be readily applied to the
current invention. By transmitting a plurality of pulses at
different frequencies and forming separate detected images using
the pulses one may obtain multiple unique speckle patterns from the
same target. These patterns may then be averaged to reduce the
overall appearance of speckle.
[0104] The well known techniques of spatial compounding may also be
applied to the current invention. The most conventional form of
spatial compounding, which we call two-way or transmit-receive
spatial compounding, entails the acquisition of multiple images
with the active transmit and receive apertures shifted spatially
between image acquisitions. This shifting operation causes the
speckle patterns obtained to differ from one image to the next,
enabling image averaging to reduce the speckle pattern.
[0105] In another technique, which we term one-way or receive-only
spatial compounding, the transmit aperture is held constant between
image acquisitions while the receive aperture is shifted between
image acquisitions. As with two-way spatial compounding, this
technique reduces the appearance of speckle in the final image.
[0106] In many ultrasound applications the received echoes from
tissue have very small amplitude, resulting in an image with poor
signal to noise ratio. This problem may be addressed through the
use of a technique known as coded excitation. In this method the
transmitted pulse is long in time and designed so that it has a
very short auto-correlation length. In this manner the pulse is
transmitted and received signals are correlated with the
transmitted pulse to yield a resultant signal with good signal to
noise ratio, but high axial resolution (short correlation length).
This method could be readily applied in the present invention
ultrasound transducer drive device and method to improve the
effective signal to noise ratio. The coded excitation technique is
described in U.S. Pat. No. 5,014,712 to O'Donnell, entitled "Coded
Excitation for Transmission Dynamic Focusing of Vibratory Energy
Beam," hereby incorporated by reference herein in its entirety.
[0107] An aspect in fabricating a system like the present invention
ultrasound imaging beam-forming apparatus is in construction of the
transducer array. Both cost and complexity could be reduced by
incorporating a transducer implemented using photolithographic
techniques, i.e. the transducer is formed using micro electro
mechanical systems (MEMS). One particularly attractive approach has
been described in U.S. Pat. No. 6,262,946 to Khuri-Yakub et al.,
entitled "Capacitive Micromachined Ultrasonic Transducer Arrays
with Reduced Cross-Coupling," hereby incorporated by reference
herein in its entirety.
[0108] While the present invention may be embodied in many
different forms, a number of illustrative embodiments are described
herein with the understanding that the present disclosure is to be
considered as providing examples of the principles of the invention
and such examples are not intended to limit the invention to
preferred embodiments described herein and/or illustrated
herein.
Broad Scope of the Invention:
[0109] While illustrative embodiments of the invention have been
described herein, the present invention is not limited to the
various preferred embodiments described herein, but includes any
and all embodiments having equivalent elements, modifications,
omissions, combinations (e.g., of aspects across various
embodiments), adaptations and/or alterations as would be
appreciated by those in the art based on the present disclosure.
The limitations in the claims are to be interpreted broadly based
on the language employed in the claims and not limited to examples
described in the present specification or during the prosecution of
the application, which examples are to be construed as
non-exclusive. For example, in the present disclosure, the term
"preferably" is non-exclusive and means "preferably, but not
limited to." In this disclosure and during the prosecution of this
application, means-plus-function or step-plus-function limitations
will only be employed where for a specific claim limitation all of
the following conditions are present in that limitation: a) "means
for" or "step for" is expressly recited; b) a corresponding
function is expressly recited; and c) structure, material or acts
that support that structure are not recited. In this disclosure and
during the prosecution of this application, the terminology
"present invention" or "invention" may be used as a reference to
one or more aspect within the present disclosure. The language
present invention or invention should not be improperly interpreted
as an identification of criticality, should not be improperly
interpreted as applying across all aspects or embodiments (i.e., it
should be understood that the present invention has a number of
aspects and embodiments), and should not be improperly interpreted
as limiting the scope of the application or claims. In this
disclosure and during the prosecution of this application, the
terminology "embodiment" can be used to describe any aspect,
feature, process or step, any combination thereof, and/or any
portion thereof, etc. In some examples, various embodiments may
include overlapping features. In this disclosure, the following
abbreviated terminology may be employed: "e.g." which means "for
example;" and "NB" which means "note well."
* * * * *