U.S. patent application number 16/845640 was filed with the patent office on 2020-07-30 for three-dimensional (3d) and/or four-dimensional (4d) ultrasound imaging.
This patent application is currently assigned to B-K Medical ApS. The applicant listed for this patent is B-K Medical ApS. Invention is credited to Ole Moller SORENSEN.
Application Number | 20200241134 16/845640 |
Document ID | 20200241134 / US20200241134 |
Family ID | 1000004750566 |
Filed Date | 2020-07-30 |
Patent Application | download [pdf] |
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United States Patent
Application |
20200241134 |
Kind Code |
A1 |
SORENSEN; Ole Moller |
July 30, 2020 |
Three-Dimensional (3D) and/or Four-Dimensional (4D) Ultrasound
Imaging
Abstract
An ultrasound imaging system (100) includes at least first and
second arrays (108) of transducer elements, which are angularly
offset from each other in a same plane. Transmit circuitry (112)
excites the first and second arrays to concurrently transmit over a
plurality of angles. Receive circuitry (114) controls the first and
second arrays to concurrently receive echo signals over the
plurality of angles. An echo processor (116) processes the received
signals, producing a first data stream for the first array and a
second data stream for the second array. The first and second data
streams include digitized representations of the received echo
signals. A sample matcher (118) compares samples of the first and
second data streams and determines a cross-correlation there
between. A correlation factor generator (120) that generates a
correlation factor signal based on the determined
cross-correlation. A scan converter (122) generates a 3D image for
display based on the correlation factor signal and the first and
second data streams.
Inventors: |
SORENSEN; Ole Moller; (Tune,
DK) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
B-K Medical ApS |
Herlev |
|
DK |
|
|
Assignee: |
B-K Medical ApS
Herlev
DK
|
Family ID: |
1000004750566 |
Appl. No.: |
16/845640 |
Filed: |
April 10, 2020 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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15318206 |
Dec 12, 2016 |
10649083 |
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PCT/IB2014/062221 |
Jun 13, 2014 |
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16845640 |
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Current U.S.
Class: |
1/1 |
Current CPC
Class: |
G01S 15/8993 20130101;
G01S 15/8927 20130101; G01S 15/8925 20130101; G01S 7/52044
20130101 |
International
Class: |
G01S 15/89 20060101
G01S015/89; G01S 7/52 20060101 G01S007/52 |
Claims
1. An ultrasound imaging system, comprising: at least two 1D arrays
of transducer elements, including a first array of transducer
elements and a second array of transducer elements angularly offset
from each other in a same plane; transmit circuitry that excites
the first and second arrays of transducer elements to concurrently
transmit beams at each of a plurality of different angles; receive
circuitry that controls the first and second arrays of transducer
elements to concurrently receive echo signals at each of the
plurality of different angles; an echo processor that beamforms the
received signals from the first and second arrays to produce a
first data stream for the first array and a second data stream for
the second array, and processes, using a synthetic aperture
algorithm, the beamformed signals simultaneously to calculate a 3D
beam profile in a defined spatial angle, wherein the first and
second data streams include digitized representations of the
received echo signals and a number of samples in a data stream
depends on a length of a receive period and on a sample frequency;
and a scan converter that generates a 3D image based on the 3D beam
profile.
2. The system of claim 1, wherein the first and second arrays of
transducer elements are orthogonal to each other.
3. The system of claim 1, wherein one of the first array or the
second array includes a contiguous array of transducer elements and
the other of the first or second arrays includes two segments, each
of which butts up to the contiguous array at a central region of
the contiguous array.
4. The system of claim 1, wherein the first and second arrays each
include two segments, each of which butts up to a non-transducing
region.
5. The system of claim 1, wherein the first and second arrays each
include two segments, each of which butts up to a transducing
region.
6. The system of claim 5, wherein the transducing region is shared
by the first and second arrays.
7. The system of claim 1, wherein the at least two arrays include
at least a third array and a fourth array of transducer
elements.
8. The system of claim 7, wherein the first, the second, the third,
and the fourth arrays of transducer elements are angularly offset
from each other by forty-five degrees.
9. The system of claim 1, where the scan converter applies a
predetermined threshold value to suppress background
scatter-echoes.
10. The system of claim 1, further comprising: a controller that
controls an angle of the beams of the at least two 1D arrays.
11. The system of claim 10, wherein the controller changes the
angle of one of the beams and activates the at least two 1D arrays
to transmit and receive.
12. The system of claim 10, wherein the controller sequentially
changes the angle of one of the beams for an entire set of angles
and activates the at least two 1D arrays to transmit and receive at
each angle of the entire set of angles.
13. The system of claim 10, wherein the angle is controlled to
focus the beams over a predetermined number of different angles
based on a predetermined angular increment for transmit and
receive.
14. The system of claim 13, wherein a transmit operation and a
receive operation is performed by each of the at least two 1D
arrays at each of the angles.
15. The system of claim 14, wherein the angle of one of the beams
is incremented over the predetermined number of different angles
while the angle of the other of the beams is held constant.
16. The system of claim 15, wherein the angle of the other of the
beams is incremented one increment after each time the one of the
beams is incremented over the predetermined number of different
angles.
17. The system of claim 15, wherein the angle is forty-five degrees
and the increment is one degree.
18. The system of claim 1, wherein the scan converter determines a
gray-scale for the 3D image by multiplying cross-correlation values
of a correlation factor signal by averages of amplitudes of samples
of the first and second data streams.
19. A method, comprising: concurrently receiving echo signals at
each of a plurality of different angles, wherein the echo signals
are in response to concurrently transmitted beams at each of the
plurality of different angles by at least two 1D arrays of
transducer elements, and the at least two 1D arrays includes a
first array of transducer elements and a second array of transducer
elements angularly offset from each other in a same plane;
beamforming the received signals from the first and second arrays
to produce a first data stream for the first array and a second
data stream for the second array, wherein the first and second data
streams include digitized representations of the received echo
signals and a number of samples in a data stream depends on a
length of a receive period and on a sample frequency; processing,
using a synthetic aperture algorithm, the first and second data
streams simultaneously to calculate a 3D beam profile in a defined
spatial angle; and scan converting the 3D beam profile to generate
a 3D image.
20. A computer readable storage medium encoded with computer
executable instructions which when executed by a processor cause
the processor to: concurrently receive echo signals at each of a
plurality of different angles, wherein the echo signals are in
response to concurrently transmitted beams at each of the plurality
of different angles by at least two 1D arrays of transducer
elements, and the at least two 1D arrays includes a first array of
transducer elements and a second array of transducer elements
angularly offset from each other in a same plane; beamform the
received signals from the first and second arrays to produce a
first data stream for the first array and a second data stream for
the second array, wherein the first and second data streams include
digitized representations of the received echo signals and a number
of samples in a data stream depends on a length of a receive period
and on a sample frequency; process, using a synthetic aperture
algorithm, the first and second data streams simultaneously to
calculate a 3D beam profile in a defined spatial angle; and scan
convert the 3D beam profile to generate a 3D image.
Description
TECHNICAL FIELD
[0001] The following generally relates to ultrasound imaging and
more particularly to an ultrasound imaging apparatus configured for
three-dimensional (3D) and/or four-dimensional (4D) ultrasound
imaging.
BACKGROUND
[0002] An ultrasound imaging system provides useful information
about the interior characteristics of an object under examination.
An example ultrasound imaging system has included an ultrasound
probe with a transducer array and a console. The ultrasound probe
houses the transducer array, which includes one or more transducer
elements. The console includes a display monitor and a user
interface.
[0003] The transducer array transmits an ultrasound signal into a
field of view and receives echoes produced in response to the
signal interacting with structure therein. The received echoes are
processed, generating images of the scanned structure. The images
can be visually presented through the display monitor. Depending on
the configuration of the ultrasound imaging apparatus, the images
can be two-dimensional (2D), three-dimensional (3D) and/or
four-dimensional (4D).
[0004] An ultrasound imaging system equipped for 3D and/or 4D
imaging has been either semi-mechanical or has included a 2D matrix
of elements. A semi-mechanical ultrasound imaging system has
included an electromechanical drive system that converts rotational
motion of a motor into translational, rotational and/or wobbling
movement of the ultrasound transducer array. Unfortunately, this
approach requires additional hardware, which can increase cost and
the footprint.
[0005] An ultrasound imaging system with a 2D matrix of elements
includes a larger number of elements, interconnects to each of the
elements and corresponding channels for the elements in the
console, relative to a configuration with a 1D, 1.5D or 1.75D array
of transducer elements. Unfortunately, a 2D matrix of elements
increases cost, routing complexity, and processing requirements,
relative to a configuration without a 1D, 1.5D or 1.75D array of
transducer elements.
SUMMARY
[0006] Aspects of the application address the above matters, and
others.
[0007] In one aspect, an ultrasound imaging system includes at
least two 1D arrays of transducer elements. The at least two 1D
arrays includes a first array of transducer elements and a second
array of transducer elements. The first and second arrays of
transducer elements are angularly offset from each other in a same
plane. The ultrasound imaging system further includes transmit
circuitry that excites the first and second arrays of transducer
elements to concurrently transmit over a plurality of angles. The
ultrasound imaging system further includes receive circuitry that
controls the first and second arrays of transducer elements to
concurrently receive echo signals over the plurality of angles. The
ultrasound imaging system further includes an echo processor that
processes the received signals, producing a first data stream for
the first array and a second data stream for the second array. The
first and second data streams include digitized representations of
the received echo signals. The ultrasound imaging system further
includes a sample matcher that compares samples of the first and
second data streams and determines a cross-correlation there
between. The ultrasound imaging system further includes a
correlation factor generator that generates a correlation factor
signal based on the determined cross-correlation. The ultrasound
imaging system further includes a scan converter that generates a
3D image for display based on the correlation factor signal and the
first and second data streams.
[0008] In another aspect, a method includes comparing echo signals
concurrently received by at least two 1D arrays of a transducer
probe. The at least two arrays are disposed in a same plane,
transverse to each other. The method further includes determining a
correlation factor signal based on the comparison. The method
further includes generating a 3D image based on the echo signals
and the correlation factor signal.
[0009] In another aspect, a computing apparatus includes a computer
processor that generates cross-correlation values between samples
of at least two ultrasound signals, wherein the at least two
ultrasound signals are acquired with at least two transducer arrays
spatially oriented transverse to each other in a same plane, and
generates a 3D ultrasound imaged based on the cross-correlation
values and the samples.
[0010] Those skilled in the art will recognize still other aspects
of the present application upon reading and understanding the
attached description.
BRIEF DESCRIPTION OF THE DRAWINGS
[0011] The application is illustrated by way of example and not
limitation in the figures of the accompanying drawings, in which
like references indicate similar elements and in which:
[0012] FIG. 1 schematically illustrates an ultrasound imaging
system that includes a probe with multiple 1D arrays of transducer
elements and a console;
[0013] FIG. 2 illustrates the envelope signal for a first array
with an object in the beam profile;
[0014] FIG. 3 illustrates the envelope signal for a second
different array with the object not in the beam profile;
[0015] FIG. 4 shows the correlation factor signal for the envelope
signals of FIGS. 2 and 3;
[0016] FIG. 5 illustrates the envelope signal for a first array
with an object in the beam profile;
[0017] FIG. 6 illustrates the envelope signal for a second
different array with the object in the beam profile;
[0018] FIG. 7 shows the correlation factor signal for the envelope
signals of FIGS. 5 and 6;
[0019] FIG. 8 illustrates the envelope signal for first array with
an object in the beam profile;
[0020] FIG. 9 illustrates the envelope signal for a second
different array with the object in the beam profile;
[0021] FIG. 10 shows the correlation factor signal for the envelope
signals of FIGS. 8 and 9;
[0022] FIG. 11 illustrates an embodiment where one of the
transducer arrays includes a series of contiguous elements, and the
other of the transducer arrays includes two segments, each of which
butts up to the one of the transducer arrays;
[0023] FIG. 12 illustrates an embodiment where the other of the
transducer arrays includes a series of contiguous elements, and the
one of the transducer arrays includes two segments, each of which
butts up to the other of the transducer arrays;
[0024] FIG. 13 illustrates an embodiment where both of the
transducer arrays include two segments, each of which butts up to a
region that does not include any transducer elements;
[0025] FIG. 14 illustrates an embodiment where both of the
transducer arrays include two segments, each of which butts up to a
transducer element that is shared by the transducer arrays;
[0026] FIG. 15 illustrates an embodiment with at least four
transducer arrays; and
[0027] FIG. 16 illustrates an example method for 3D ultrasound
imaging using at least two transducer arrays configured as shown in
one of FIGS. 11, 12, 13, 14 and 15.
DETAILED DESCRIPTION
[0028] FIG. 1 schematically illustrates a system 100 that includes
an ultrasound imaging probe 102 and an ultrasound imaging console
104. In this example, the probe 102 and the console 104 communicate
through a communication path 106.
[0029] The ultrasound imaging probe 102 includes N one-dimensional
(1D) transducer arrays, including a transducer array 108.sub.1, . .
. , a transducer array 108.sub.N, where N is an integer equal to or
greater than two, collectively referred to herein as transducer
arrays 108. The transducer arrays 108.sub.1, . . . , 108.sub.N
respectively include sets 110.sub.1, . . . , 110.sub.N of
transducer elements. The transducer arrays 108 can be linear,
curved, and/or otherwise shaped arrays. A transducer array 108 can
include sixty-four (64), ninety-six (96), two hundred and fifty-six
(256), and/or other number of transducer elements.
[0030] In one instance, the probe 102 includes two transducer
arrays (i.e., N=2), which are transverse to each other, or
orthogonal, in a same plane, and acquire data for 3D and/or 4D
imaging, using a limited number of transducer elements and a
corresponding number of signal channels, without mechanically
moving any of the 1D transducer arrays 108 and without including a
2D matrix transducer and the associated high number of
interconnects and channels. This can reduce complexity and cost,
relative to a configuration that mechanically move a transducer
array and/or includes a 2D matrix.
[0031] The console 104 includes transmit circuitry 112 that
controls excitation of the transducer elements 110 of the
transducer arrays 108 to transmit ultrasound signals. In one
instance, this includes controlling at least two of the transducer
arrays 108 to concurrently transmit beams from the elements 110 of
at least two of the arrays 108. The console 104 further includes
receive circuitry 114 that routes RF analog (echo) signals received
by the transducer elements 110. A switch can be used to switch
between the transmit circuitry 112 and the receive circuitry
114.
[0032] Angling of the beams can be through phased array and/or
other approaches, during which a time-correlating and/or other
approach can be used for focus and/or for direction of focus for
transmission and/or reception. Transmission and reception can be
repeated until a spatial angle of interest is covered. For example,
where each transducer array 108 is focused over forty-five (45)
different angles with one (1) degree resolution, angling is
repeated 45.times.45, or 2025 times. Other angular and/or
resolution is also contemplated herein.
[0033] The console 104 further includes an echo processor 116 that
converts the received RF analog signals for each of the arrays 108
into digital representations in respective data streams. For two
arrays 108, each including 96 elements, this includes processing
(e.g., delay and summing) the 96 signals from each of the 96
elements of each of the arrays 108 and producing two data streams,
one for each of the transducer arrays 108. Envelope detection,
using a Hilbert transform, etc., can be used to detect the
amplitude, which is included in the data streams. The number of
samples in a data stream depends on the length of the receive
period and on the sample frequency.
[0034] The console 104 further includes a sample matcher 118 that
compares the samples in different data streams. The comparison can
be performed sample-wise, using a predetermined number of earlier
and later samples, multiplied with a predetermined weighting
function. For the comparison, the sample matcher 118 can apply a
cross-correlation approach where a cross-correlation of one (1)
indicates an exact match, a cross-correlation of zero (0) indicates
no match, and a cross-correlation there between indicates a
relative degree of match there between.
[0035] The console 104 further includes a correlation factor signal
generator 120. The correlation factor signal generator 120, in one
instance, generates a correlation factor signal for two of the
arrays 108. The correlation factor signal includes a sequence of
correlation factors describing how equal the samples in the signals
are as a function of time during reception. The correlation factor
signal is based on the cross-correlation values determined by the
sample matcher 118.
[0036] Briefly turning to FIGS. 2, 3, 4, 5, 6, 7, 8, 9 and 10,
example envelope signals and corresponding correlation factor
signals are illustrated. In FIGS. 2, 3, 4, 5, 6, 7, 8, 9 and 10,
the envelope signals start at the point in time just following
transmission. A first or y-axis 202 represents amplitude and a
second or x-axis 204 represents time.
[0037] FIGS. 2-4 show an example in which an object it located in
the beam profile of one of the arrays 108. FIG. 2 shows the
envelope signal for the array 108 with the object in the beam
profile. A region 206 corresponds to echo signals from the object.
FIG. 3 shows the envelope signals for the array 108 with no object
in the beam profile. The echo signals include low level, such as
inherent noise of the system and low level background scatter. FIG.
4 shows the correlation factor signal 402, using a
cross-correlation approach with the envelope signals of FIGS. 2 and
3. The envelope signals are not correlated, and the resulting
correlation factor signal 402 is low.
[0038] FIGS. 5-7 show an example in which an object it located in
both beam profile. FIG. 5 shows the envelope signals for one of the
arrays 108 with the object in the beam profile, and FIG. 6 shows
the envelope signals for the other one of the arrays 108 with the
object in the beam profile. Regions 502 and 602 correspond to echo
signals from the object. FIG. 7 shows the correlation factor signal
702, using a cross-correlation approach with the envelope signals
of FIGS. 5 and 6. The envelope signals of FIGS. 5 and 6 are
correlated, and the resulting correlation factor signal 702 is
high.
[0039] With FIGS. 2-7, the object is solid, having a constant
factor of reflection all over its cross-section.
[0040] In FIG. 8-10, the object (e.g., such as a blood vessel or a
gall bladder) contains a fluid. In this situation, the echoes are
strong from the edges of the object and very low from the inside
fluid. This is caused by the fact the low level echo from the
inside of the object (the envelope) might be lower than the
background noise.
[0041] FIG. 8 shows the envelope signals for one of the arrays 108
with the object in the beam profile, and FIG. 9 shows the envelope
signals for the other one of the arrays 108 with the object in the
beam profile. Regions 802 and 902 correspond to echo signals from
the edges of the object. Regions 804 and 904 correspond to echo
signals from the inside of the object.
[0042] FIG. 10 shows the correlation factor signal 1002, using a
cross-correlation approach with the envelope signals of FIGS. 8 and
9. The envelope signals of FIGS. 8 and 9 corresponding to the edges
are correlated, and the resulting correlation factor signal 1002 is
high. The envelope signals of FIGS. 8 and 9 corresponding to the
inside are correlated, and lower than the background noise.
[0043] Returning to FIG. 1, the console 104 further includes a scan
converter 122, which coverts processed signals and generates an
image for display, and a display 124, which can be used to display
the scan converted data. To establish a gray-scale for visual
presentation, in one instance, the correlation factor signal can be
used as multipliers for an average value between two envelope
signals. This, with or without the use of a low level threshold,
can suppress background scatter-echoes, etc.
[0044] The console 104 further includes a user interface (UI) 126
with an input device(s) (e.g., a mouse, keyboard, touch controls,
etc.), which allows for user interaction with the system 100. The
console 104 further includes a controller 128 that controls at
least one of the transmit circuitry 112, the receive circuitry 114,
the echo processor 116, the sample matcher 118 or the scan
converter 122.
[0045] Variations are discussed.
[0046] In one variation, where the object is solid (as discussed in
connection with FIGS. 2-7), a lowest sample value approach is
employed. For this approach, the sample matcher 118 identifies and
selects the lowest sample value of a set of compared samples of the
envelope signals. Doing this, the values used for the resulting
signal, always relate to the most selective array in the angle of
direction from which the signal originates. If the two values are
equal, it does not matter which one is selected.
[0047] In another variation, a synthetic aperture approach is
employed. With one synthetic aperture approach, a phased array is
not employed, and all element signals from both of the arrays 108
are processed simultaneously in one process calculating a 3D beam
profile in a defined spatial angle.
[0048] In another variation, at least one of the transducer arrays
108 includes a 1.5D or 1.75D array of transducer elements.
[0049] In another variation, at least one of the sample matcher
118, the correlation factor generator 120 or the scan converter 122
is implemented by a computing system that is remote from the system
100. An example of such a computing system includes at least one
processor (e.g., a microprocessor, a central processing unit, etc.)
that executes at least one computer readable instruction stored in
computer readable storage medium ("memory"), which excludes
transitory medium and includes physical memory and/or other
non-transitory medium. The microprocessor may also execute one or
more computer readable instructions carried by a carrier wave, a
signal or other transitory medium.
[0050] FIGS. 11, 12, 13, 14 and 15 illustrate non-limiting examples
of the spatial relationship of the transducer arrays 108.
[0051] Initially refereeing to FIG. 11, two transducer arrays 108
(the transducer arrays 108.sub.1 and 108.sub.N) are spatially
oriented with respect to each other such that they are in a same
plane and cross at central region 1102, and are angularly offset
from each other by ninety (90) degrees or approximately 90 degrees.
In this example, the transducer array 108.sub.1 is a single array
of contiguous transducer elements 1104, and the transducer array
108.sub.N includes two segments 1106.sub.1 and 1106.sub.2, each of
which butts up to the transducer array 108.sub.1.
[0052] Next at FIG. 12, a configuration similar to that of FIG. 11
is illustrated. This example is similar to that of FIG. 11 except
that the transducer array 108.sub.N includes the single array of
contiguous transducer elements 1202, and the transducer array
108.sub.1 includes two segments 1204.sub.1 and 1204.sub.2, each of
which butts up to the transducer array 108.sub.N.
[0053] Turning to FIG. 13, an embodiment in which the transducer
array 108.sub.1 includes the two segments 1202.sub.1 and 1202.sub.2
and the transducer array 108.sub.N includes the two segments
1106.sub.1 and 1106.sub.2, and the four segments 1106.sub.1,
1106.sub.2, 1202.sub.1 and 1202.sub.2 butt-up to a region 1302 that
does not include any transducer elements, is illustrated.
[0054] FIG. 14 illustrates an embodiment in which the transducer
array 108.sub.1 includes the two segments 1202.sub.1 and 1202.sub.2
and the transducer array 108.sub.N includes the two segments
1106.sub.1 and 1106.sub.2, and the four segments 1106.sub.1,
1106.sub.2, 1202.sub.1 and 1202.sub.2 butt-up to a transducer
element 1402 that is shared by the transducer arrays 108.sub.1 and
108.sub.N.
[0055] FIG. 15 illustrates an embodiment with at least four
transducer arrays 108 (the transducer arrays 108.sub.1 and
108.sub.N and transducer arrays 108.sub.I and 108.sub.J). In this
embodiment, the transducer arrays 108 are spatially oriented with
respect to each other such that they are in a same plane and cross
at central region 1102, and are angularly offset from each other by
forty-five (45) degrees or approximately 45 degrees. A middle
region can include a transducer element for one of the arrays 108,
a transducer element shared by two or more of the arrays 108, or no
transducer element.
[0056] Other configurations are also contemplated herein.
[0057] FIG. 16 illustrates an example method for 3D ultrasound
imaging using two of the transducer arrays 108 configured as shown
in one of FIGS. 11, 12, 13, 14 and 15.
[0058] It is to be understood that the following acts are provided
for explanatory purposes and are not limiting. As such, one or more
of the acts may be omitted, one or more acts may be added, one or
more acts may occur in a different order (including simultaneously
with another act), etc.
[0059] At 1602, one of the arrays 108 is angled at an angle of
interest. For example, the array 108 maybe angled at -45 degrees
for a set of angles in an angular range from -45 to +45 degrees. In
another instance, a different initial angle and/or a different set
of angles is employed.
[0060] At 1604, the other of the arrays 108 is angled at an angle
of interest. Likewise, the array 108 maybe angled at -45 degrees
for a set of angles in an angular range from -45 to +45 degrees. In
another instance, a different initial angle and/or a different set
of angles is employed.
[0061] At 1606, the two arrays 108 are simultaneously excited to
transmit.
[0062] At 1608, the two arrays 108 synchronously receive.
[0063] At 1610, the received analog RF signals for each of the two
arrays 108 are beamformed, producing two data stream signals with
digital representations of the received analog RF signals.
[0064] At 1612, the envelope of each of the data stream signals is
detected.
[0065] At 1614, correlation factors are determined between the
envelopes of the data stream signals and saved.
[0066] At 1616, it is determined if the other of the arrays is to
be angled at another angle of interest. If so, acts 1604 through
1614 are repeated for another angle of interest. For example, the
array 108 maybe incremented to -44 degrees or other angle in the
angular range.
[0067] If not, at 1618, it is determined if the one of the arrays
is to be angled at another angle of interest. If so, acts 1602
through 1616 are repeated for another angle of interest. For
example, the array 108 maybe incremented to -44 degrees or other
angle in the angular range.
[0068] If not, at 1620, a 3D image is generated based on the
correlation factors and the envelope signals. The 3D image can be
visually presented, conveyed to another device, further processed,
etc.
[0069] The above may be implemented by way of computer readable
instructions, encoded or embedded on computer readable storage
medium, which, when executed by a computer processor(s), cause the
processor(s) to carry out the described acts. Additionally or
alternatively, at least one of the computer readable instructions
is carried by a signal, carrier wave or other transitory
medium.
[0070] In a variation, echo signals from multiple angles can be
processed simultaneously, which can reduce the number of iterations
in the inner loop (act 1616) of FIG. 16. Reducing the number of
iterations can increase the frame rate of the system, and thereby
the number of 3D images produced each second. 4D mode can be
implemented if this number is high enough to generate useful 3D
images as function of time.
[0071] The application has been described with reference to various
embodiments. Modifications and alterations will occur to others
upon reading the application. It is intended that the invention be
construed as including all such modifications and alterations,
including insofar as they come within the scope of the appended
claims and the equivalents thereof.
* * * * *