U.S. patent application number 14/966429 was filed with the patent office on 2016-04-07 for ultrasonic diagnostic apparatus.
This patent application is currently assigned to Kabushiki Kaisha Toshiba. The applicant listed for this patent is Kabushiki Kaisha Toshiba, Toshiba Medical Systems Corporation. Invention is credited to Kazuya AKAKI, Eiji GOTO, Yu IGARASHI, Koichiro KURITA, Go TANAKA.
Application Number | 20160095573 14/966429 |
Document ID | / |
Family ID | 52022384 |
Filed Date | 2016-04-07 |
United States Patent
Application |
20160095573 |
Kind Code |
A1 |
TANAKA; Go ; et al. |
April 7, 2016 |
ULTRASONIC DIAGNOSTIC APPARATUS
Abstract
An ultrasonic diagnostic apparatus according to the present
embodiment includes an ultrasonic probe, image generation
circuitry, acquisition circuitry, calculation circuitry, guide
image generation circuitry, and control circuitry. The ultrasonic
probe transmits ultrasonic waves, and receives reflected waves. The
image generation circuitry generates cross-section image data based
on the reflected waves. The acquisition circuitry acquires, from
volume data corresponding to three-dimensional region containing a
blood vessel inside the subject, cross-section position information
corresponding to the cross-section image data. The calculation
circuitry calculates collection position information in the volume
data based on a running direction of a blood vessel contained in
the volume data, the collection position information corresponding
to a position from which blood flow velocity information is
collected. The guide image generation circuitry generates guide
image data based on the cross-section position information and the
collection position information. The control circuitry causes the
guide image data to be displayed.
Inventors: |
TANAKA; Go; (Otawara,
JP) ; AKAKI; Kazuya; (Utsunomiya, JP) ; GOTO;
Eiji; (Utsunomiya, JP) ; KURITA; Koichiro;
(Nasushiobara, JP) ; IGARASHI; Yu; (Utsunomiya,
JP) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
Kabushiki Kaisha Toshiba
Toshiba Medical Systems Corporation |
Minato-ku
Otawara-shi |
|
JP
JP |
|
|
Assignee: |
Kabushiki Kaisha Toshiba
Minato-ku
JP
Toshiba Medical Systems Corporation
Otawara-shi
JP
|
Family ID: |
52022384 |
Appl. No.: |
14/966429 |
Filed: |
December 11, 2015 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
|
|
PCT/JP2014/065799 |
Jun 13, 2014 |
|
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14966429 |
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Current U.S.
Class: |
600/443 |
Current CPC
Class: |
A61B 8/461 20130101;
A61B 8/463 20130101; A61B 8/4254 20130101; A61B 8/5207 20130101;
A61B 8/54 20130101; A61B 8/14 20130101; A61B 8/085 20130101; A61B
8/523 20130101; A61B 8/06 20130101; A61B 8/42 20130101; A61B 8/488
20130101; A61B 8/4444 20130101; A61B 8/483 20130101 |
International
Class: |
A61B 8/06 20060101
A61B008/06; A61B 8/08 20060101 A61B008/08; A61B 8/00 20060101
A61B008/00; A61B 8/14 20060101 A61B008/14 |
Foreign Application Data
Date |
Code |
Application Number |
Jun 13, 2013 |
JP |
2013-124987 |
Claims
1. An ultrasonic diagnostic apparatus comprising: an ultrasonic
probe configured to transmit ultrasonic waves into a subject, and
receive reflected waves generated by reflection of the ultrasonic
waves inside the subject; an image generator configured to
generate, on the basis of the reflected waves received by the
ultrasonic probe, cross-section image data corresponding to a
two-dimensional region inside the subject; acquisition circuitry
configured to acquire, from volume data corresponding to
three-dimensional region containing a blood vessel inside the
subject, cross-section position information corresponding to a
cross-section position of the cross-section image data; calculation
circuitry configured to calculate collection position information
in the volume data on the basis of a direction in which a blood
vessel contained in the volume data runs, the collection position
information being position information corresponding to a position
from which blood flow velocity information is collected; guide
image generation circuitry configured to generate guide image data
on the basis of the cross-section position information and the
collection position information; and control circuitry configured
to cause the guide image data to be displayed.
2. The ultrasonic diagnostic apparatus according to claim 1,
wherein a position from which the blood flow velocity information
is collected is a collection range arranged on a collection
cross-section scanned by the ultrasonic probe for collecting the
blood flow velocity information, the calculation circuitry is
configured to calculate, as the collection position information,
position information in the volume data that corresponds to the
collection cross-section and the collection range, and the guide
image generation circuitry is configured to generate, as guide
image data, image data that the operator uses to move the
ultrasonic probe to a position at which the collection
cross-section having the collection range arranged therein is
scanned.
3. The ultrasonic diagnostic apparatus according to claim 2,
wherein the guide image generation circuitry is configured to
generate the guide image data by, on two-dimensional image data
generated from the volume data, superimposing, at a position based
on the cross-section position information, a marker indicating a
cross-section currently scanned by the ultrasonic probe and
additionally superimposing, at a position based on the collection
position information, markers indicating the collection range and
the collection cross-section.
4. The ultrasonic diagnostic apparatus according to claim 3,
further comprising: extraction circuitry configured to extract a
blood vessel region contained in the volume data; and input
circuitry configured to receive specification of an observation
area within the volume data from the operator, wherein the
calculation circuitry is configured to calculate, in the volume
data, a position and an angle of a scan line extending along a
running direction of a blood vessel in the observation area, the
running direction having been calculated by use of the blood vessel
region, and calculate the collection position information by using
an optimum line determined by the calculated position and
angle.
5. The ultrasonic diagnostic apparatus according to claim 4,
wherein the calculation circuitry is configured to acquire, in the
volume data, a three-dimensional range corresponding to a
three-dimensional scan range which can be scanned by the ultrasonic
probe; move the optimum line while keeping the position of the
observation area stationary within the three-dimensional range in
order to search for the collection range and the collection
cross-section; and calculate the collection position information by
searching for a position that is a scan cross-section that allows
scanning of the moved optimum line, and that gives the smallest
angle between the moved optimum line and the running direction of
the blood vessel in the observation area.
6. The ultrasonic diagnostic apparatus according to claim 5,
wherein the calculation circuitry is configured to arrange, in the
collection cross-section, a running line passing through the
observation area and extending along the running direction of the
blood vessel in the observation area, and then calculate the
position of the running line in the volume data, and the guide
image generation circuitry is further configured to superimpose a
line indicating the running line, on the two-dimensional image
data, as an angle marker for angle correction.
7. The ultrasonic diagnostic apparatus according to claim 5,
wherein the three-dimensional scan range is acquired by having the
operator move the ultrasonic probe within a possible range with the
ultrasonic probe kept in contact with a body surface of a subject,
and the calculation circuitry is configured to calculate a position
of the three-dimensional range from the three-dimensional scan
range and the cross-section position information.
8. The ultrasonic diagnostic apparatus according to claim 5,
wherein the calculation circuitry is configured to calculate the
position of the three-dimensional ranges by using information
indicating where a body surface of the subject is located in the
volume data.
9. The ultrasonic diagnostic apparatus according to claim 4,
wherein the calculation circuitry is configured to arrange the
optimum line parallel to a running direction of a blood vessel in
the observation area, the running direction having been calculated
by use of the blood vessel region.
10. The ultrasonic diagnostic apparatus according to claim 5,
wherein the calculation circuitry is configured to calculate a
plurality of pieces of candidate position information by searching
for a position corresponding to an angle equal to or smaller than a
predetermined value between the optimum line moved within the
three-dimensional range and the running direction of the blood
vessel in the observation area, and obtaining a plurality of
candidate sets each including a candidate collection range and a
candidate scan cross-section; and when having received from the
operator a request to change guide image data based on the piece of
candidate position information that has a certain rank among the
pieces of candidate position information, the control circuitry is
configured to cause guide image data to be displayed that is based
on the piece of candidate position information of a rank succeeding
the certain rank.
11. The ultrasonic diagnostic apparatus according to claim 10,
wherein the control circuitry is configured to determine ranks of
the pieces of candidate position information in ascending order of
the angles.
12. The ultrasonic diagnostic apparatus according to claim 10,
wherein, in a situation where one candidate set has been extracted
by use of the predetermined value, the calculation circuitry, upon
receiving from the operator a request to change guide image data
based on candidate position information of the candidate set, is
configured to search for a position of another candidate set that
gives a value equal to or smaller than a value that exceeds the
predetermined value.
13. The ultrasonic diagnostic apparatus according to claim 2,
wherein the control circuitry is further configured to cause the
display to display thereon information needed by the operator in
moving the ultrasonic probe to a position that allows scanning of
the collection cross-section.
14. The ultrasonic diagnostic apparatus according to claim 2,
wherein, when the operator has moved the ultrasonic probe to a
position that allows scanning of the collection cross-section, the
control circuitry is further configured to cause information to be
output that notifies the operator that the collection cross-section
is being scanned.
15. The ultrasonic diagnostic apparatus according to claim 2,
wherein, when the operator has moved ultrasonic probe to a position
at which the collection cross-section is scanned, the control
circuitry is configured to cause the collection range while
superimposing the collection range on ultrasonic image data of the
collection cross-section to be displayed and cause collection of
blood flow velocity information in the collection range to be
started.
16. The ultrasonic diagnostic apparatus according to claim 1,
wherein the volume data is volume data photographed by a medical
diagnostic imaging apparatus of a kind other than an ultrasonic
diagnostic apparatus.
17. The ultrasonic diagnostic apparatus according to claim 1,
wherein the volume data is volume data from which a region where a
blood flow exists can be extracted, the volume data having been
photographed by transmission and reception of ultrasonic waves.
Description
CROSS-REFERENCE TO RELATED APPLICATIONS
[0001] This application is a continuation of PCT international
application Ser. No. PCT/JP2014/065799 filed on Jun. 13, 2014 which
designates the United States, incorporated herein by reference, and
which claims the benefit of priority from Japanese Patent
Applications No. 2013-124987, filed on Jun. 13, 2013, incorporated
herein by reference.
FIELD
[0002] Embodiments described herein relate generally to an
ultrasonic diagnostic apparatus.
BACKGROUND
[0003] Conventionally, an ultrasonic diagnostic apparatus uses
Doppler information (Doppler signals) extracted from reflected
waves of ultrasound waves to generate and display a Doppler
spectrum (Doppler waveform) indicating blood flow velocity
information. A Doppler waveform is a waveform obtained by plotting
blood flow velocities in a time series within a range defined as an
observation area by an operator. Such a range is defined by an
operator who has referred to a two-dimensional ultrasonic image
(two-dimensional B mode image, or two-dimensional color Doppler
image).
[0004] For example, in a pulsed wave (PW) mode where Doppler
waveforms are collected by the PW Doppler method, the operator
arranges a sampling gate in a particular part inside a blood vessel
in accordance with how the blood vessel runs as visualized in a
two-dimensional ultrasonic image. In the PW mode, a Doppler
waveform indicating blood flow velocity information in a sampling
gate is displayed. Otherwise, for example, in a continuous wave
(CW) mode where Doppler waveforms are collected by the CW Doppler
method, the operator arranges a sampling marker in the form of a
line so that the sampling marker may pass through a blood vessel
visualized in a two-dimensional ultrasonic image. In the CW mode,
Doppler waveforms indicating all of blood flow velocity information
along a scan line (beam line) set at the same position as the
sampling marker are displayed.
[0005] In order to obtain Doppler information, the operator needs
arranging the sampling gate or the sampling marker at an optimum
position by adjusting the contact position and the contact angle of
an ultrasonic probe with reference to a two-dimensional ultrasonic
image. However, the above operation is not easy operation since it
is difficult for the operator to know even with reference to a
two-dimensional ultrasonic image how a blood vessel runs in a
three-dimensional space.
BRIEF DESCRIPTION OF THE DRAWINGS
[0006] FIG. 1 is a block diagram depicting an exemplary
configuration of an ultrasonic diagnostic apparatus according to
the present embodiment;
[0007] FIG. 2 and FIG. 3 are illustrations for explaining
acquisition circuitry;
[0008] FIG. 4 is an illustration depicting one example of settings
that are conventionally applied in Doppler waveform collection in
the PW mode;
[0009] FIG. 5 is an illustration depicting one example of
processing for acquiring a three-dimensional range;
[0010] FIG. 6 is an illustration depicting another example of
processing for acquiring a three-dimensional range;
[0011] FIG. 7, FIG. 8, FIG. 9, FIG. 10, FIG. 11, FIG. 12 and FIG.
13 are illustrations for explaining navigation processing to be
performed by calculation circuitry and guide image generation
circuitry;
[0012] FIG. 14 is an illustration for explaining a display form at
the completion of the navigation.
[0013] FIG. 15, FIG. 16, FIG. 17 and FIG. 18 are illustrations for
explaining a display form of Doppler waveforms according to the
present embodiment;
[0014] FIG. 19 is a flowchart for explaining one example of
processing to be performed by the ultrasonic diagnostic apparatus
according to the present embodiment;
[0015] FIG. 20A and FIG. 20B are diagrams for explaining a first
modified example;
[0016] FIG. 21 is an illustration for explaining a second modified
example; and
[0017] FIG. 22 is an illustration for explaining a third modified
example.
DETAILED DESCRIPTION
[0018] An ultrasonic diagnostic apparatus according to the present
embodiment includes an ultrasonic probe, image generation
circuitry, acquisition circuitry, calculation circuitry, guide
image generation circuitry, and control circuitry. The ultrasonic
probe transmits ultrasonic waves, and receives reflected waves. The
image generation circuitry generates cross-section image data based
on the reflected waves. The acquisition circuitry acquires, from
volume data corresponding to three-dimensional region containing a
blood vessel inside the subject, cross-section position information
corresponding to the cross-section image data. The calculation
circuitry calculates collection position information in the volume
data based on a running direction of a blood vessel contained in
the volume data, the collection position information corresponding
to a position from which blood flow velocity information is
collected. The guide image generation circuitry generates guide
image data based on the cross-section position information and the
collection position information. The control circuitry causes the
guide image data to be displayed.
[0019] The following describes an embodiment of an ultrasonic
diagnostic apparatus in detail with reference to the accompanying
drawings.
Embodiment
[0020] Firstly, the configuration of the ultrasonic diagnostic
apparatus according to the present embodiment is described. FIG. 1
is a block diagram illustrating an exemplary configuration of an
ultrasonic diagnostic apparatus according to the present
embodiment. As depicted in FIG. 1, the ultrasonic diagnostic
apparatus according to the present embodiment includes an
ultrasonic probe 1, a display 2, input circuitry 3, and an
apparatus body 10. A position sensor 4 is attached to the
ultrasonic probe 1, and a transmitter 5 is provided near the
apparatus body 10. The apparatus body 10 is connected to an
external apparatus 6 via a network.
[0021] The ultrasonic probe 1 transmits ultrasonic waves into a
subject P, and receives reflected waves generated by reflection of
the ultrasonic waves inside the subject P. The ultrasonic probe 1
includes, for example, a plurality of piezoelectric transducer
elements, and these piezoelectric transducer elements generate
ultrasonic waves based on drive signals supplied from
transmitting-and-receiving circuitry 11 to be described later of
the apparatus body 10. The ultrasonic probe 1 receives reflected
waves from the subject P and converts them into electric signals.
The ultrasonic probe 1 further includes, for example, a matching
layer that is provided on the piezoelectric transducer elements, a
backing material that prevents ultrasonic waves from propagating
toward the rear from the piezoelectric transducer elements. The
ultrasonic probe 1 is detachably connected to the apparatus body
10.
[0022] When ultrasonic waves are transmitted to the subject P from
the ultrasonic probe 1, the transmitted ultrasonic waves are
successively reflected by surfaces across which acoustic impedance
is discontinuous in the body tissue of the subject P, and are
received by the piezoelectric transducer elements of the ultrasonic
probe 1 as reflected wave signals. Here, piezoelectric transducer
elements that have received reflected waves convert the
corresponding reflected waves into reflected wave signals, which
are electric signals. The amplitudes of the reflected wave signals
generated by the piezoelectric transducer elements depend on
differences in acoustic impedance at the discontinuous surfaces by
which the ultrasonic waves are reflected. A reflected wave signal
of a transmitted ultrasonic pulse reflected by, for example, the
surface of a blood flow or a cardiac wall or the like in motion
undergoes frequency deviation due to the Doppler effect depending
on the velocity component of the moving body with respect to the
transmitting direction of the ultrasonic wave.
[0023] The ultrasonic probe 1 connected to the apparatus body 10
is, for example, a one-dimensional ultrasonic probe having a
plurality of piezoelectric transducer elements arrayed in a single
row. Examples of a one-dimensional ultrasonic probe include
sectorial, linear, and convex ultrasonic probes. Otherwise, the
ultrasonic probe 1 connected to the apparatus body 10 is, for
example, a mechanical 4D probe that two-dimensionally scans the
subject P by using a plurality of piezoelectric transducer elements
arrayed in a single row and also three-dimensionally scans the
subject P by swinging the piezoelectric transducer elements at a
given angle (swing angle). Otherwise, the ultrasonic probe 1
connected to the apparatus body 10 is, for example, a 2D probe,
which is capable of three-dimensionally scanning the subject P with
a plurality of piezoelectric transducer elements disposed in a
matrix. A 2D probe is also capable of two-dimensionally scanning
the subject P by focusing and transmitting ultrasonic waves.
[0024] The ultrasonic diagnostic apparatus according to the present
embodiment collects Doppler waveforms by the PW Doppler method or
the CW Doppler method as described below. In this embodiment, the
ultrasonic probe 1 connected to the apparatus body 10 is an
ultrasonic probe capable of not only transmitting and receiving
ultrasonic waves for use in photographing B-mode image data and
color Doppler image data but also transmitting and receiving
ultrasonic waves for use in collecting Doppler waveforms in the PW
mode based on the PW Doppler method or in the CW mode based on the
CW Doppler method.
[0025] Here, as described above, the position sensor 4 is attached
to the ultrasonic probe 1. As described above, the transmitter 5 is
arranged at any desired position near the apparatus body 10. The
position sensor 4 and the transmitter 5 constitute a position
detection system for use in detecting position information (the
coordinates and the angle) of the ultrasonic probe 1. For example,
the position sensor 4 is a magnetic sensor attached to the
ultrasonic probe 1. The position sensor 4 is attached to, for
example, an end portion of the ultrasonic probe 1. The transmitter
5 is, for example, a device that forms a magnetic field centering
around and directed outward from the transmitter 5.
[0026] The position sensor 4 detects the intensity and the gradient
of a three-dimensional magnetic field formed by the transmitter 5.
The position sensor 4 then calculates, on the basis of the detected
information on the magnetic field, the position (the coordinates
and the angle) of the position sensor 4 in a space having its
origin at the transmitter 5, and transmits the calculated position
to the apparatus body 10. Here, three-dimensional coordinates and
an angle at which the position sensor 4 is located are transmitted
as three-dimensional position information of the ultrasonic probe 1
by the position sensor 4 to the apparatus body 10.
[0027] The present embodiment is also applicable to a case where
the position information of the ultrasonic probe 1 is acquired by
use of a system other than the above position detection system. For
example, the present embodiment may be applied to a case where the
position information of the ultrasonic probe 1 is acquired by use
of a gyro sensor or an acceleration sensor.
[0028] The input circuitry 3 is connected to the apparatus body 10
via interface circuitry 19 to be described below. The input
circuitry 3 includes, for example, a mouse, a keyboard, buttons,
panel switches, a touch command screen, a foot switch, a trackball,
and a joystick, receives various setting requests from an operator
of the ultrasonic diagnostic apparatus, and transfers the received
various setting requests to the apparatus body 10.
[0029] The display 2 displays a graphical user interface (GUI) for
the operator of the ultrasonic diagnostic apparatus to input
various setting requests by using the input circuitry 3, and
displays ultrasonic image data generated in the apparatus body 10
and other data.
[0030] The external apparatus 6 is an apparatus connected to the
apparatus body 10 via the interface circuitry 19 to be described
below and a network. For example, the external apparatus 6 is a
database in a picture archiving and communication system (PACS),
which is a system that manages various medical image data, or a
database in an electronic health record system that manages
electronic health records having medical images attached thereto.
Alternatively, the external apparatus 6 is, for example, any one of
various medical diagnostic imaging apparatuses, such as an X-ray
computed tomography (CT) apparatus and a magnetic resonance imaging
apparatus (MRI), other than an ultrasonic diagnostic apparatus
according to the present embodiment.
[0031] For example, the apparatus body 10 according to the present
embodiment can acquire various medical image data uniformly
formatted in an image format conforming to DICOM (Digital Imaging
and Communications in Medicine) from the external apparatus 6 via
the interface circuitry 19. For example, the apparatus body 10
acquires via the interface circuitry 19 from the external apparatus
6, via the interface circuitry 19 to be described later, volume
data (such as X-ray CT volume data or MRI volume data) to be
compared with ultrasonic image data generated by the apparatus body
10.
[0032] The apparatus body 10 is an apparatus that generates
ultrasonic image data based on reflected wave signals received by
the ultrasonic probe 1. For example, the apparatus body 10
according to the present embodiment is an apparatus capable of
generating two-dimensional ultrasonic image data based on
two-dimensional reflected wave data. Also for example, the
apparatus body 10 according to the present embodiment is an
apparatus capable of generating three-dimensional ultrasonic image
data based on three-dimensional reflected wave data. In the
following, three-dimensional ultrasonic image data is referred to
as "ultrasonic volume data".
[0033] The apparatus body 10 includes the
transmitting-and-receiving circuitry 11, B-mode process circuitry
12, Doppler process circuitry 13, image generation circuitry 14,
image memory circuitry 15, an image processor 16, internal memory
circuitry 17, control circuitry 18, and the interface circuitry 19,
as depicted in FIG. 1.
[0034] The transmitting-and-receiving circuitry 11 includes, for
example, a pulse generator, transmission delay circuitry, and a
pulser, and supplies drive signals to the ultrasonic probe 1. The
pulse generator repeatedly generates rate pulses to form ultrasonic
waves at a given rate frequency. The transmission delay circuitry
assigns, to the respective rate pulses generated by the pulse
generator, delay times for the respective piezoelectric transducer
elements. The delay times are needed for focusing the ultrasonic
waves generated by the ultrasonic probe 1 into a beam shape and
determining the transmission directivity. The pulser applies the
drive signals (drive pulses) to the ultrasonic probe 1 at the
timing based on the rate pulses. That is, the transmission delay
circuitry varies the delay times assigned to the respective rate
pulses, thereby adjusting to any desired direction the transmission
direction of the ultrasonic waves transmitted from the plane of the
piezoelectric transducer elements.
[0035] The transmitting-and-receiving circuitry 11 has a function
capable of instantly changing, for example, transmission
frequencies or transmission drive voltages in order to execute a
given scan sequence on the basis of instructions of the control
circuitry 18 to be described below. In particular, changing
transmission drive voltages is implemented by oscillator circuitry
of a linear amplifier type capable of instantly switching values
thereof or by a mechanism that electrically switches a plurality of
power supply units.
[0036] The transmitting-and-receiving circuitry 11 further
includes, for example, a pre-amplifier, an analog-to-digital (A/D)
converter, reception delay circuitry, and an adder, and performs a
variety of processing on the reflected wave signals received by the
ultrasonic probe 1, thereby generating reflected wave data. The
pre-amplifier amplifies the reflected wave signal for each channel.
The A/D converter performs A/D conversion on the amplified
reflected wave signals. The reception delay circuitry provides
delay times needed for determining the reception directivity. The
adder performs addition processing on the reflected wave signals
processed by the reception delay circuitry and generates the
reflected wave data. As a result of the addition processing of the
adder, the reflection component of the reflected wave signal from a
direction corresponding to the reception directivity is emphasized.
By the reception directivity and the transmission directivity, an
integrated beam of ultrasonic transmission and reception is
formed.
[0037] When scanning a two-dimensional region inside the subject P,
the transmitting-and-receiving circuitry 11 according to the
present embodiment causes the ultrasonic probe 1 to transmit an
ultrasonic beam configured to scan a two-dimensional region. The
transmitting-and-receiving circuitry 11 according to the present
embodiment then generates two-dimensional reflected wave data from
two-dimensional reflected wave signals received by the ultrasonic
probe 1. When scanning a three-dimensional region inside the
subject P, the transmitting-and-receiving circuitry 11 according to
the present embodiment causes the ultrasonic probe 1 to transmit an
ultrasonic beam for scanning a three-dimensional region. The
transmitting-and-receiving circuitry 11 according to the present
embodiment then generates three-dimensional reflected wave data
from three-dimensional reflected wave signals received by the
ultrasonic probe 1.
[0038] Here, even when the ultrasonic probe 1 is a one-dimensional
ultrasonic probe, the ultrasonic diagnostic apparatus according to
the present embodiment can generate three-dimensional reflected
wave data by using the above-described position detection system.
For example, the operator conducts a three-dimensional scan of the
subject P by conducting two-dimensional scans of a plurality of
cross-sections while varying the position and the angle of the
ultrasonic probe 1 with the ultrasonic probe 1 kept in contact with
the body surface of the subject P. The transmitting-and-receiving
circuitry 11 thus generates two-dimensional reflected wave data of
a plurality of cross-sections. For example, the control circuitry
18 can reconstruct three-dimensional reflected wave data by
three-dimensionally arranging two-dimensional reflected wave data
of a plurality of cross-sections, on the basis of three-dimensional
position information of the ultrasonic probe 1 acquired from the
position detection system.
[0039] The form of the output signal from the
transmitting-and-receiving circuitry 11 is selectable from various
forms such as a case of a signal referred to as a radio frequency
(RF) signal in which phase information is included and a case of
amplitude information after envelope detection processing.
[0040] The B-mode process circuitry 12 receives the reflected wave
data from the transmitting-and-receiving circuitry 11, performs
such processing as logarithmic amplification and envelope detection
processing, and generates data in which the signal intensity is
expressed by the luminance of brightness (B-mode data).
[0041] The Doppler process circuitry 13 performs frequency analysis
on velocity information from the reflected wave data received from
the transmitting-and-receiving circuitry 11, extracts a blood flow,
tissue, or the echo component of a contrast agent on the basis of
the Doppler effect, and generates data (Doppler data) containing
moving body information such as the velocity, the dispersion, and
the power extracted at multi-points. A moving body in the present
embodiment is blood that flows in a blood vessel.
[0042] The B-mode process circuitry 12 and the Doppler process
circuitry 13 according to the present embodiment can process both
two-dimensional reflected wave data and three-dimensional reflected
wave data.
[0043] The image generation circuitry 14 generates ultrasonic image
data generated by the B-mode process circuitry 12 and the Doppler
process circuitry 13. That is, the image generation circuitry 14
generates, from B-mode data generated by the B-mode process
circuitry 12, B-mode image data in which the signal intensity is
expressed by brightness. The image generation circuitry 14 also
generates color Doppler image data from Doppler data generated by
the Doppler process circuitry 13. The color Doppler image data is
average velocity image data, dispersion image data, power image
data, or a combination of any of the forgoing data, which indicates
moving body information (information on moves of a blood flow or
tissue).
[0044] Here, the image generation circuitry 14, in general,
converts (scan-converts) the scan line signal sequences of
ultrasonic scans into scan line signal sequences of a video format
typified by television and the like, thereby generating ultrasonic
image data for display. Specifically, the image generation
circuitry 14 performs coordinate conversion depending on the
scanning form of ultrasonic waves by the ultrasonic probe 1,
thereby generating the ultrasonic image data for display. The image
generation circuitry 14 further performs, as a variety of image
processing other than the scan conversion, processing by using a
plurality of image frames after the scan conversion. Examples of
the processing include: image processing (smoothing processing) to
regenerate an image with the average luminance value; and image
processing (edge enhancement processing) that applies a
differential filter within the images. The image generation
circuitry 14 combines character information on various parameters,
scales, body marks, and other information with the ultrasonic image
data.
[0045] That is, the B-mode data and the Doppler data are ultrasonic
image data before scan conversion processing, and the data that the
image generation circuitry 14 generates is the ultrasonic image
data for display after scan conversion processing. The B-mode data
and the Doppler data are also referred to as raw data.
[0046] The image generation circuitry 14 can also generate M-mode
image data from time-series data of B-mode data on one scan line
generated by the B-mode process circuitry 12. The image generation
circuitry 14 can also generate, from Doppler data generated by the
Doppler process circuitry 13, a Doppler waveform obtained by
plotting blood flow velocity information in a time series.
[0047] Furthermore, the image generation circuitry 14 performs
coordinate conversion on three-dimensional B-mode data generated by
the B-mode process circuitry 12, thereby generating
three-dimensional B-mode image data. The image generation circuitry
14 further performs coordinate conversion on three-dimensional
Doppler data generated by the Doppler process circuitry 13, thereby
generating three-dimensional Doppler image data. Three-dimensional
B-mode data and three-dimensional Doppler data are treated as
volume data before scan conversion. That is, the image generation
circuitry 14 generates "three-dimensional B-mode data and
three-dimensional Doppler data" as "ultrasonic volume data".
[0048] Moreover, the image generation circuitry 14 performs
rendering processing on ultrasonic volume data to generate various
kinds of two-dimensional image data for displaying the ultrasonic
volume data on the display 2. One example of the rendering
processing to be performed by the image generation circuitry 14 is
processing to generate multi-planar reconstruction (MPR) image data
from the volume data by applying MPR. Other examples of the
rendering processing to be performed by the image generation
circuitry 14 are processing to apply "curved MPR" to the volume
data and processing to apply "maximum intensity projection" to the
volume data. Still another example of the rendering processing to
be performed by the image generation circuitry 14 is volume
rendering (VR) processing to generate two-dimensional image data
having three-dimensional information incorporated therein.
[0049] The image generation circuitry 14 can also perform the above
various kinds of rendering processing on volume data collected by
another medical diagnostic imaging apparatus. Such volume data is
three-dimensional X-ray CT image data (X-ray CT volume data)
collected by an X-ray CT apparatus or three-dimensional MRI image
data (MRI volume data) collected by an MRI apparatus. In one
exemplary case, on the basis of information acquired by acquisition
circuitry 161 described below, the image generation circuitry 14
generates two-dimensional X-ray CT image data from X-ray CT volume
data by applying MPR processing using a cross-section corresponding
to a scan cross-section in two-dimensional ultrasonic image data
currently generated.
[0050] The image memory circuitry 15 is a memory that stores
therein the image data for display generated by the image
generation circuitry 14. The image memory circuitry 15 can also
store therein the data generated by the B-mode process circuitry 12
and the Doppler process circuitry 13. The B-mode data and the
Doppler data stored in the image memory circuitry 15 can be called
up by the operator after diagnosis, and are made into the
ultrasonic image data for display via the image generation
circuitry 14, for example.
[0051] In the present embodiment, the image processor 16 is
installed in the apparatus body 10 to assist collection of Doppler
waveforms. The image processor 16 includes the acquisition
circuitry 161, extraction circuitry 162, calculation circuitry 163,
and guide image generation circuitry 164 as depicted in FIG. 1.
[0052] The acquisition circuitry 161 acquires cross-section
position information in volume data corresponding to a
three-dimensional region containing a blood vessel inside the
subject P. The cross-section position information is position
information corresponding to a cross-section position of
cross-section image data. That is, on the basis of the reflected
waves received by the ultrasonic probe 1, the image generation
circuitry 14 generates cross-section image data corresponding to a
two-dimensional region inside the subject P. The acquisition
circuitry 161 acquires, in the volume data, position information
corresponding to a cross-section position of the cross-section
image data generated by the image generation circuitry 14. For
example, the acquisition circuitry 161 according to the present
embodiment acquires the cross-section position information in
volume data, which is three-dimensional medical image data, by
acquiring a correspondence relation that specifies the position of
a cross-section corresponding to a scan cross-section of the
ultrasonic probe 1. The above volume data is volume data
photographed by a medical diagnostic imaging apparatus of a kind
other than an ultrasonic diagnostic apparatus, and is X-ray CT
volume data, for example.
[0053] The correspondence relation acquired by the acquisition
circuitry 161 is conventionally used for a "simultaneous display
function". The "simultaneous display function" is the function of
simultaneously displaying on a screen of the display 2 in real
time: two-dimensional ultrasonic image data of a scan cross-section
subject to change following a move of the ultrasonic probe 1; and
two-dimensional X-ray CT image data of X-ray CT volume data having
its positions matched with respective corresponding positions of
the two-dimensional ultrasonic image data. FIG. 2 and FIG. 3 are
illustrations for explaining the acquisition circuitry.
[0054] As depicted in FIG. 2, the acquisition circuitry 161
acquires, from the position detection system composed of the
position sensor 4 attached to the ultrasonic probe 1 and the
transmitter 5, three-dimensional position information (the
coordinates and the angle) on the ultrasonic probe 1 in an actual
space.
[0055] In executing the "simultaneous display function", the three
axes (X,Y,Z) of the ultrasonic probe 1 are aligned with the three
axes of X-ray CT volume data 100 (refer to FIG. 2). For example, an
operator presses down a set button while keeping the ultrasonic
probe 1 having the position sensor 4 attached thereto in vertical
contact with the subject P. The acquisition circuitry 161 sets
straight three axes defined as those extending in directions
perpendicular to one another, from three-dimensional position
information of the ultrasonic probe 1 acquired when the set button
is pressed down.
[0056] Subsequently, as depicted in FIG. 2, the operator presses
the set button again after moving the ultrasonic probe 1 so as to
have ultrasonic image data 200 displayed in which a feature portion
that is the same as a feature portion visualized in MPR image data
101a of the X-ray CT volume data 100 is visualized. Furthermore,
the operator specifies the feature portion in the MPR image data
101a and the feature portion in the ultrasonic image data 200, for
example, using a mouse. As a feature portion, a blood vessel, a
xiphisternum, or the like is used, for example.
[0057] The acquisition circuitry 161 acquires the correspondence
relation among the position of "any given scan cross-section" in
the actual space, the position of the "any given scan
cross-section" in ultrasonic image data generated by an ultrasonic
scan, and the position of a cross-section in the X-ray CT volume
data 100 that corresponds to the "any given scan cross-section", on
the basis of: three-dimensional position information of the
ultrasonic probe 1 acquired when the set button is pressed down
again; position information of the feature portion in the X-ray CT
volume data 100; and position information of the feature portion in
the ultrasonic image data 200.
[0058] For example, the control circuitry 18 can use the above
correspondence relation to specify a cross-section in the X-ray CT
volume data 100 that corresponds to a scan cross-section, and the
image generation circuitry 14 can then generate MPR image data from
the X-ray CT volume data 100 by using the cross-section specified
by the control circuitry 18. Thus, the display 2 simultaneously
displays ultrasonic image data 200A of a moved scan cross-section
and MPR image data 101A of the same cross-section.
[0059] Here, the above correspondence relation can convert the
coordinates of the "any given scan cross-section" in ultrasonic
image data generated by an ultrasonic scan into coordinates in the
X-ray CT volume data 100. The above correspondence relation can
also convert the coordinates of any given position in the X-ray CT
volume data 100 into coordinates in the ultrasonic image data.
[0060] With reference to FIG. 1 again, the extraction circuitry 162
extracts a blood vessel region contained in volume data. For
example, the extraction circuitry 162 extracts a voxel having a CT
value corresponding to blood, thereby extracting a blood vessel
region contained in the X-ray CT volume data 100. The present
embodiment may be applied to a case where the operator extracts a
blood vessel region in volume data by manually setting the position
of a blood vessel.
[0061] Processing to be performed by the calculation circuitry 163
and the guide image generation circuitry 164 in the present
embodiment by using the correspondence relation acquired by the
acquisition circuitry 161 and the blood vessel region extracted by
the extraction circuitry 162 will be described later in detail.
[0062] The internal memory circuitry 17 stores therein control
programs to perform transmission and reception of ultrasonic waves,
image processing, and display processing, and a variety of data
such as diagnostic information (for example, patient IDs and
doctor's findings), diagnosis protocols, and various body marks.
The internal memory circuitry 17 is used also for such purposes as
archiving image data stored in the image memory circuitry 15 as
necessary.
[0063] Furthermore, the internal memory circuitry 17 is used also
for archiving various medical images transferred from the external
apparatus 6. Specifically, the internal memory circuitry 17 stores
therein volume data conforming to the DICOM standards that has been
transferred from the external apparatus 6 via the interface
circuitry 19 to be described later. In the present embodiment, the
internal memory circuitry 17 stores therein volume data (for
example, X-ray CT volume data or MRI volume data) containing a
blood vessel of the subject P from which Doppler waveforms are
collected.
[0064] The control circuitry 18 controls the entire processing of
the ultrasonic diagnostic apparatus. Specifically, on the basis of
various setting requests input from the operator via the input
circuitry 3 and various control programs and various data loaded
from the internal memory circuitry 17, the control circuitry 18
controls processing in the transmitting-and-receiving circuitry 11,
the B-mode process circuitry 12, the Doppler process circuitry 13,
the image generation circuitry 14, and the image processor 16. The
control circuitry 18 performs control so that ultrasonic image data
for display stored in the image memory circuitry 15 or the internal
memory circuitry 17 can be displayed on the display 2. The control
circuitry 18 also performs control so that processing result of the
image processor 16 can be displayed on the display 2.
[0065] The interface circuitry 19 is an interface with the input
circuitry 3, a network, and the external apparatus 6. Various
setting requests and various instructions from the operator
received by the input circuitry 3 are transferred to the control
circuitry 18 by the interface circuitry 19. The interface circuitry
19 notifies, via a network, the external apparatus 6 of a request
to transfer image data, the request having been received by the
input circuitry 3 from the operator. Image data transferred by the
external apparatus 6 is stored in the internal memory circuitry 17
by the interface circuitry 19.
[0066] The foregoing describes the overall configuration of the
ultrasonic diagnostic apparatus according to the present
embodiment. With the foregoing configuration, the ultrasonic
diagnostic apparatus according to the present embodiment collects
Doppler waveforms indicating blood flow velocity information based
on Doppler information.
[0067] Conventionally, when Doppler waveforms are collected, the
operator searches, in the B mode or in the color Doppler mode, for
a scan cross-section that results in visualization of a blood
vessel as an observation area from which the operator intends to
collect Doppler waveforms. The operator then, with reference to
two-dimensional ultrasonic image data (two-dimensional B mode image
data or two-dimensional color Doppler image data), determines a
scan cross-section for collecting Doppler waveforms (a scan
cross-section for collecting blood flow information). In the
following, a scan cross-section scanned by the ultrasonic probe 1
for collecting blood flow velocity information is referred to as a
"collection cross-section".
[0068] The operator then arranges, in the collection cross-section,
a range from which Doppler waveforms are collected. In the
following, a range arranged in a collection cross-section for blood
flow information collection is referred to as a "collection range".
For example, in the PW mode, the operator arranges a sampling gate
in an observation area inside a blood vessel, in accordance with
how the blood vessel runs as visualized in two-dimensional
ultrasonic image data of a collection cross-section, the sampling
gate being the collection range. In the PW mode, Doppler waveforms
indicating blood flow velocity information in the sampling gate are
displayed.
[0069] For example, in the CW mode, the operator arranges a linear
sampling marker so that the sampling marker may pass through a
blood vessel containing an observation area visualized in
two-dimensional ultrasonic image data of the collection
cross-section. In the CW mode, Doppler waveforms indicating all of
blood flow velocity information along a scan line set at the same
position as the sampling marker are displayed. FIG. 4 is an
illustration depicting one example of settings that are
conventionally applied in Doppler waveform collection in the PW
mode.
[0070] The right illustration in FIG. 4 depicts B mode image data
of a collection cross-section displayed on the display 2.
Specifically, the right illustration in FIG. 4 depicts B mode image
data, of a collection cross-section, in which a long-axis
cross-section of a blood vessel under observation has been
visualized. The operator arranges a sampling gate in the long-axis
cross-section of the blood vessel in the B mode image data (refer
to the parallel double line depicted in the right illustration in
FIG. 4). The operator or the control circuitry 18 then arranges a
line marker at the position of a scan line that passes through the
sampling gate and that allows scanning inside the collection
cross-section (refer to the dotted line depicted in the right
illustration in FIG. 4). Here, blood flow velocity information
obtained from Doppler information is not blood flow velocity
information in the running direction of the blood vessel, but is
blood flow velocity information in a direction of the scan line on
the line marker. Here, the angle between the blood flow direction
(the running direction of the blood vessel) and the direction of
the scan line is denoted as ".theta.". The Doppler process
circuitry 13 makes angle correction, using "1/cos .theta.", to the
blood flow velocity information obtained from the Doppler
information, thereby obtaining the blood flow velocity information
in the running direction of the blood vessel.
[0071] The operator not only arranges the sampling gate and the
line marker, but also arranges an angle marker parallel to the
running direction of the blood vessel in the sampling gate so that
the Doppler process circuitry 13 can be notified of ".theta." for
making the angle correction (refer to two line segments that cross
over the parallel double line in the right illustration in FIG. 4).
The direction of the angle marker can be adjusted by the operator.
The Doppler process circuitry 13 obtains ".theta." from the angle
between the line marker and the angle marker, and makes the angle
correction.
[0072] Position information of the sampling gate and the line
marker serves as position information for defining the collection
range from which Doppler information is sampled. Position
information of the angle marker, which is information for the angle
correction, can also be included as the position information for
defining the collection range.
[0073] After completing the arrangement of the sampling gate and
the line marker and adjustment of the angle marker, the operator
then inputs, via the input circuitry 3, a request to start
collection of Doppler waveforms in the PW mode. Consequently,
collection of Doppler waveforms is started, and the display 2
displays thereon a Doppler waveform as depicted in the left
illustration in FIG. 4.
[0074] In the CW mode, a sampling marker and an angle marker, which
correspond to a line marker in the PW mode, are arranged. In the CW
mode, position information of a sampling marker, which passes
through a blood vessel, serves as position information for defining
a collection range from which Doppler information is sampled. In
the CW mode, position information of an angle marker, which is
information for angle correction, can be additionally included as
the position information for defining the collection range.
[0075] In order to obtain Doppler information, the operator needs
arranging a collection range by adjusting the contact position and
the contact angle of the ultrasonic probe 1 to the optimum position
and angle thereof with reference to two-dimensional ultrasonic
image data. The optimum contact position and the optimum contact
angle of the ultrasonic probe 1 are, for example, a position and an
angle that give the smallest value of ".theta.". As the angle
".theta." between the running direction of the blood vessel and the
direction of the scan lines approaches "0 degrees", "1/cos .theta."
approaches "1", resulting in a smaller error in the blood flow
velocity information due to the angle correction. On the other
hand, as the angle ".theta." between the running direction of the
blood vessel and the direction of the scan lines increases, "1/cos
.theta." becomes smaller, resulting in a larger error in the blood
flow velocity information due to the angle correction.
[0076] However, it is difficult for the operator to know, even with
reference to two-dimensional ultrasonic image data, how a blood
vessel runs in a three-dimensional space. Hence, arranging the
collection range so that the angle between the running direction of
the blood vessel and the direction of the scan line can be as small
as possible is a difficult operation for the operator. In addition,
even when the operator has determined that a long-axis
cross-section of a blood vessel under observation has been
visualized, a cross-section that the operator refers to actually
disagrees with a long-axis cross-section in some cases because the
image data is two-dimensional. In such a case, an error is incurred
in ".theta." because the angle marker is not set parallel to the
running direction of the blood vessel. Consequently, blood flow
velocity information cannot be accurately obtained.
[0077] To address this inconvenience, the present embodiment
includes the calculation circuitry 163 and the guide image
generation circuitry 164 configured to perform the following
processing by using, for example, a blood vessel region extracted
by the extraction circuitry 162 as well as the cross-section
position information acquired by the acquisition circuitry 161 by
use of the correspondence relation, for the purpose of simplifying
operations that the operator performs to display the optimum blood
flow velocity information. The following description focuses on
processing to be performed in the PW mode. Note that the
acquisition circuitry 161 acquires a correspondence relation of
volume data (for example, the X-ray CT volume data 100) before the
following processing is started.
[0078] The calculation circuitry 163 calculates collection position
information, which is position information in volume data (volume
data of another kind) that corresponds to a position from which
blood flow velocity information is collected, on the basis of the
running direction of the blood vessel in the volume data. Here, the
position from which blood flow velocity information is collected is
a collection range arranged in a collection cross-section to be
scanned by the ultrasonic probe for collecting blood flow velocity
information. The calculation circuitry 163 calculates, as the
collection position information, position information in the volume
data that corresponds to both of the collection cross-section and
the collection range. Specifically, on the basis of the running
direction of a blood vessel contained in volume data (volume data
of another kind), the calculation circuitry 163 calculates, in the
volume data, position information of a collection range and a
collection cross-section whereby collected blood flow velocity
information has an error within a tolerable range. That is, the
calculation circuitry 163 calculates, not in the actual space but
in a virtual space in volume data of another kind from which a
blood vessel region can be extracted, collection position
information serving as position information of a collection range
for collecting Doppler waveforms and of a collection cross-section
in which the collection range is arranged.
[0079] The guide image generation circuitry 164 then generates
guide image data on the basis of the cross-section position
information and the collection position information. Specifically,
using the correspondence relation and the collection position
information, the guide image generation circuitry 164 generates
guide image data that the operator uses to move the ultrasonic
probe 1 to a position that allows scanning of the collection
cross-section having the collection range arranged therein. More
specifically, the guide image generation circuitry 164 uses
two-dimensional image data generated from the volume data (volume
data of another kind). This two-dimensional image data is, for
example, VR image data of the X-ray CT volume data 100. The VR
image data may be generated by the image generation circuitry 14 or
may be generated by the guide image generation circuitry 164. Then,
on this two-dimensional image data, the guide image generation
circuitry 164 superimposes, at a position based on the
cross-section position information, a marker indicating a current
scan cross-section of the ultrasonic probe 1, and also
superimposes, at a position based on the collection position
information, a marker indicating the collection range and the
collection cross-section. Thus, the guide image generation
circuitry 164 generates the guide image data. The guide image data
serves as an image for navigation for the operator to perform an
operation to move the ultrasonic probe 1.
[0080] At the start, the calculation circuitry 163 acquires, in the
volume data, a three-dimensional range corresponding to a
three-dimensional scan range which can be scanned by the ultrasonic
probe 1. Here, the three-dimensional scan range is acquired by
having the operator move the ultrasonic probe 1 within a possible
range while keeping the ultrasonic probe 1 in contact with the body
surface of the subject P. The calculation circuitry 163 then
calculates the position of the three-dimensional range from the
three-dimensional scan range and the correspondence relation
already acquired by the acquisition circuitry 161. FIG. 5 is an
illustration depicting one example of processing for acquiring the
three-dimensional range.
[0081] For example, ultrasonic scanning of the heart is performed
with the ultrasonic probe 1 kept in contact with a portion between
ribs. That is, the ultrasonic probe 1 cannot necessarily scan a
cross-section that contains an observation area at any given
contact position and contact angle. To avoid this inconvenience,
for example, the operator defines a three-dimensional scan range by
moving the ultrasonic probe 1 within a range that can be scanned
thereby as depicted in the left illustration in FIG. 5 with the
ultrasonic probe 1 kept in contact with the body surface of the
subject P. The acquisition circuitry 161 acquires position
information of the three-dimensional scan range in the actual space
from the position sensor 4, and notifies the calculation circuitry
163 thereof. The calculation circuitry 163 then calculate, in the
X-ray CT volume data 100, the position of three-dimensional range
300 corresponding to the three-dimensional scan range as depicted
in the left illustration in FIG. 5, on the basis of position
information of the three-dimensional scan range in the actual
space, and the cross-section position information (for example, the
cross-section position information acquired from the correspondence
relation). The three-dimensional range 300 is a range that is
searched for the collection range and the collection cross-section
in the X-ray CT volume data 100. Limiting the range to the
three-dimensional range 300 reduces a load needed for processing of
calculating position information of the collection range and the
collection cross-section from which optimum Doppler waveforms can
be collected.
[0082] However, the position of the three-dimensional range 300 may
be calculated without the use of the correspondence relation. In
such a case, the calculation circuitry 163 calculates the position
of the three-dimensional ranges by using information indicating
where a body surface of the subject P is located in the X-ray CT
volume data 100. FIG. 6 is an illustration depicting another
example of processing for acquiring the three-dimensional range.
For example, the calculation circuitry 163 calculates the position
of a body surface 400 of the subject P in the X-ray CT volume data
100 as depicted in FIG. 6 by using a CT value corresponding to the
air. The body surface 400 is a range with which the ultrasonic
probe 1 can make contact. For example, the calculation circuitry
163 calculates the position of the three-dimensional range 300 on
the basis of the position of the body surface 400 in the X-ray CT
volume data 100, and the shape and the size of a cross-section
two-dimensionally scanned by the ultrasonic probe 1.
[0083] Note that, for example, the calculation circuitry 163 may
calculate a bone region of the subject P in the X-ray CT volume
data 100 by using a CT value corresponding to a bone and then
calculate the position of the three-dimensional range 300 by
further using the position of the bone region. Alternatively, the
calculation circuitry 163 may calculate the position of the
three-dimensional range 300 by further using a range that is a part
of the body surface 400 as specified by the operator.
[0084] After the completion of scanning the three-dimensional scan
range, the operator uses the input circuitry 3 to input a request
to start navigation while keeping the ultrasonic probe 1 scanning a
cross-section in the three-dimensional scan range. This inputting
causes the calculation circuitry 163 and the guide image generation
circuitry 164 to start the following navigation processing. FIG. 7
to FIG. 13 are illustrations for explaining the navigation
processing to be performed by the calculation circuitry and the
guide image generation circuitry.
[0085] The right illustration in FIG. 7 depicts B mode image data
as cross-section image data of a current scan cross-section. The
left illustration in FIG. 7 depicts the above-described VR image
data 101 generated from the X-ray CT volume data 100. The
calculation circuitry 163 acquires the position information of the
current scan cross-section from the acquisition circuitry 161, and,
by using the acquired position information and the correspondence
relation, calculates the position of a cross-section in the X-ray
CT volume data 100 (hereinafter, referred to as a corresponding
scan cross-section) that corresponds to the current scan
cross-section. As depicted in FIG. 7, the guide image generation
circuitry 164 superimposes, in the VR image data 101, a frame 500
applicable to the corresponding scan cross-section at the position
calculated by the calculation circuitry 163. Additionally, as
depicted in FIG. 7, the image generation circuitry 14 superimposes,
on B mode image data of the current scan cross-section, a frame 600
corresponding to the current scan cross-section. For example, the
frame 500 and the frame 600 are depicted as yellow solid lines.
Note that a blood vessel is visualized in the VR image data
101.
[0086] The input circuitry 3 then receives, from the operator,
designation of an observation area within the volume data. For
example, as depicted in the left illustration in FIG. 8, the
operator clicks the mouse after moving the cursor of the mouse
inside the blood vessel in the VR image data 101. The VR image data
101 is an image generated from the X-ray CT volume data 100, which
includes three-dimensional information. Therefore, the calculation
circuitry 163 is capable of calculating the three-dimensional
position of a position designated by the operator as an observation
area.
[0087] With this capability, as depicted in FIG. 9, the calculation
circuitry 163 calculates the three-dimensional position in the
X-ray CT volume data 100 of an observation area designated in the
VR image data 101. Then, as depicted FIG. 9, the extraction
circuitry 162 uses a CT value to extract a blood vessel region 501
located at the three-dimensional position of the observation area.
In the present embodiment, the extraction circuitry 162 may extract
a blood vessel wall from the blood vessel region 501. Furthermore,
in the present embodiment, the extraction circuitry 162 may have
extracted a blood vessel region (or a blood vessel wall) all of the
X-ray CT volume data 100 in advance.
[0088] The calculation circuitry 163 then calculates the running
direction of the blood vessel in the observation area by using a
blood vessel region 501. For example, as depicted in FIG. 9, the
calculation circuitry 163 calculates a blood vessel running vector
502 in the observation area. FIG. 9 illustrates the blood vessel
running vector 502 as a double-headed arrow.
[0089] The calculation circuitry 163 then calculates the position
and the angle of a scan line that follows the running direction of
the blood vessel (the blood vessel running vector 502) in the X-ray
CT volume data 100. The scan line that follows the running
direction of the blood vessel (the blood vessel running vector 502)
is an optimum scan line that gives the smallest error in blood flow
velocity information collected from the observation area. The
position and the angle of the optimum scan line that gives the
smallest error in blood flow velocity information collected from
the observation area is the position and the angle of a scan line
that passes through the observation area and runs in the same
direction as the running direction of the blood vessel. The
calculation circuitry 163 calculates the position and angle of the
optimum scan line in the X-ray CT volume data 100. The calculation
circuitry 163 then defines, as an optimum line corresponding to the
optimum scan line, a line determined from the calculated position
and angle. The calculation circuitry 163 then calculates position
information (collection position information) of the collection
range and the collection cross-section by using the optimum
line.
[0090] The calculation circuitry 163 arranges, as an optimum line
503, a line that passes through the observation area and that
coincides with the blood vessel running vector 502, as depicted in
FIG. 10. In other words, the calculation circuitry 163 arranges the
optimum line 503 parallel to the blood vessel running vector 502
(the running direction of the blood vessel in the observation area,
which has been calculated by use of the blood vessel region). The
angle between the optimum line 503 and the blood vessel running
vector 502 becomes "0 degrees", and an error in the blood flow
velocity information collected from a scan line corresponding to
the optimum line 503 becomes the smallest. In other words, the
optimum line 503 serves, in the X-ray CT volume data 100, as a
marker corresponding to an optimum line marker. As depicted in FIG.
10, the calculation circuitry 163 arranges a double line 504
containing the observation area, perpendicular to the optimum line
503. The double line 504 serves, in the X-ray CT volume data 100,
as a marker corresponding to an optimum sampling gate. The optimum
line 503 and the double line 504 serve as an optimum collection
range for collecting Doppler waveforms of the observation area in
the PW mode.
[0091] As depicted in FIG. 10, the calculation circuitry 163 then
arranges a running line 505 passing through the observation area
and extending in the running direction of the blood vessel in the
observation area. In other words, the calculation circuitry 163
arranges the running line 505 perpendicularly to the double line
504. The running line 505 serves, in the X-ray CT volume data 100,
as a marker corresponding to an optimum angle marker that enables a
highly accurate angle correction.
[0092] The calculation circuitry 163 then moves the optimum line
503 while the position of the observation area is kept stationary
within the above-described three-dimensional range 300, in order to
search for the collection range and the collection cross-section.
Note that, because it is currently in the PW mode, the calculation
circuitry 163 moves the optimum line 503 while keeping the relative
positional relation thereof with the optimum line 503 and the
double line 504. Here, the calculation circuitry 163 does not move
the running line 505.
[0093] The calculation circuitry 163 then searches for a position
that is a scan cross-section that enables scanning of the moved
optimum line 503 and that gives the smallest angle between the
moved optimum line 503 and the blood vessel running vector 502. The
calculation circuitry 163 calculates the collection position
information by searching with the above search condition. Thus, as
depicted in FIG. 11, the calculation circuitry 163 calculates the
positions of "a line 506 and a double line 507" that satisfy the
above search condition as the position of the collection range. As
depicted in FIG. 11, the calculation circuitry 163 further
calculates the position of "a frame 508" that satisfies the above
search condition as the position of the collection cross-section.
Thus, the calculation circuitry 163 calculates the collection
position information. Note that, as depicted in FIG. 11, the
position of the running line 505 is maintained.
[0094] The guide image generation circuitry 164 then generates
guide image data by superimposing the markers indicating the "line
506 and double line 507", the "frame 508", and the "running line
505", respectively, on the "VR image data 101 and frame 500"
depicted in the left illustration in FIG. 8. That is, as depicted
in the left illustration in FIG. 12, the guide image generation
circuitry 164 superimposes a dotted line frame 509 indicating the
frame 508, superimposes a dotted line 510 indicating the line 506,
superimposes a double line 511 indicating the double line 507, and
superimposes a line 512 indicating the running line 505 as an angle
marker for angle correction. The guide image generation circuitry
164 depicts the dotted line frame 509 in green so that it can be
differentiated from the frame 500. Consequently, the guide image
data is displayed on the display 2 under the control of the control
circuitry 18.
[0095] That is, the dotted line frame 509 works as marker
indicating the collection cross-section. The dotted line 510 and
the double line 511 work as markers indicating the collection
range. The operator starts moving the ultrasonic probe 1 with
reference to the guide image data depicted in the left illustration
in FIG. 12. In response to movement of the ultrasonic probe 1, B
mode image data in the right illustration in FIG. 12 is updated,
and the position of the frame 500 moves on the basis of the
cross-section position information obtained from the correspondence
relation. With reference to the frame 500 that is moving, the
operator starts moving the ultrasonic probe 1 so that the frame 500
can coincide with the dotted line frame 509.
[0096] Furthermore, the control circuitry 18 may display on the
display 2, along with the guide image data, information needed by
the operator in moving the ultrasonic probe 1 to a position at
which the collection cross-section is scanned. For example, the
guide image generation circuitry 164 acquires, from the internal
memory circuitry 17, a three-dimensional body mark corresponding to
an area to be photographed. For example, the guide image generation
circuitry 164 then arranges two probe frame formats on the
three-dimensional body mark, as depicted in FIG. 13. The guide
image generation circuitry 164 arranges one of the probe frame
formats at a position corresponding to the position of the
ultrasonic probe 1 at the time of a request to start navigation,
and the other one of the probe frame format at a position
corresponding to the position of the ultrasonic probe 1 at the time
of scanning of the collection cross-section. As depicted in FIG.
13, for example, the guide image generation circuitry 164 then
arranges arrows indicating a parallel-shift movement and a rotation
movement, respectively, as operations to be performed at the
position that allows scanning of the collection cross-section. The
control circuitry 18 then displays image data depicted in FIG. 13
on the display 2.
[0097] The guide image generation circuitry 164 may generate and
display, at the position of the frame 500, guide image data on
which B mode image data is superimposed. Additionally, in the
present embodiment, two-dimensional image data of the X-ray CT
volume data 100 used for the guide image data may be MPR image
data. In this case, the operator may thumbnail a plurality of
pieces of the guide image data using a plurality of pieces of MPR
image data or may display them as moving images. Furthermore, in
the present embodiment, the operator who has referred to the guide
image data may adjust the positions of the collection range and the
collection cross-section.
[0098] When the operator has then moved the ultrasonic probe 1 to
the position at which the collection cross-section is scanned, the
control circuitry 18 causes information to be output that notifies
the operator that the collection cross-section is being scanned.
Additionally, when the operator has moved ultrasonic probe 1 to the
position at which the collection cross-section is scanned, the
control circuitry 18 displays the collection range while
superimposing the collection range on ultrasonic image data of the
collection cross-section. FIG. 14 is an illustration for explaining
a display form at the completion of the navigation.
[0099] When a scan cross-section being scanned by the ultrasonic
probe 1 has reached the position corresponding to the dotted line
frame 509, i.e., when the frame 500 overlaps the dotted line frame
509, the guide image generation circuitry 164 deletes the frame 500
and changes the green dotted line frame 509 into a green solid line
509' as depicted in FIG. 14. In this manner, the operator can
recognize that the collection cross-section is being scanned. Note
that, at the same time, the guide image generation circuitry 164 or
the image generation circuitry 14 may change the yellow frame 600
into a green frame 600', as depicted in FIG. 14. Also in this
manner, the operator can recognize that the collection
cross-section is being scanned.
[0100] Furthermore, when the frame 500 overlaps the dotted line
frame 509, the guide image generation circuitry 164 or the image
generation circuitry 14 superimposes on B mode image data of the
collection cross-section a "line marker and sampling gate"
corresponding to the "dotted line 510 and the double line 511,
which are markers for the collection range in the guide image
data", as depicted in FIG. 14. The guide image generation circuitry
164 or the image generation circuitry 14 further superimposes an
"angle marker" corresponding to the "line 512 serving as a marker
for angle correction in the guide image data", as depicted in FIG.
14. In the present embodiment, the operator may adjust the "line
marker and sampling gate" superimposed on B mode image data of the
collection cross-section. In this case, the positions of the
respective markers in the guide image data may be moved in tandem
with one another.
[0101] The control circuitry 18 then start collection of blood flow
velocity information (Doppler waveforms) in the collection range.
Note that, when Doppler waveforms are collected, the Doppler
process circuitry 13 does not use the angle between an angle marker
and a line marker that are superimposed on B mode image data. The
Doppler process circuitry 13 uses the angle between the running
line 505 and the line 506 as ".theta." for angle correction.
[0102] A display form for a Doppler waveform may be selected by the
operator or may have been set at the initial setting. Display
formats for a Doppler waveform that are implementable in the
present embodiment are described herein below by way of FIG. 15 to
FIG. 18. FIG. 15 to FIG. 18 are diagrams for explaining Doppler
waveform display forms according to the present embodiment.
[0103] The display form depicted in FIG. 15 is used to further
display Doppler waveforms in addition to the display form at the
completion of navigation depicted in FIG. 14. In FIG. 15, the
display 2 displays thereon guide image data and B mode image data
side by side, and displays thereon a Doppler waveform below the
guide image data and the B mode image data.
[0104] Unlike the display form depicted in FIG. 15, the display
form depicted in FIG. 16 is used to display, in place of guide
image data using the VR image data 101, image data obtained by
superimposing, on MPR image data, a marker corresponding to a
collection cross-section, a marker corresponding to an collection
range, and a marker corresponding to an angle marker. The MPR image
data has been obtained by cutting the X-ray CT volume data 100
along a cross-section thereof that contains a collection
cross-section.
[0105] A display form depicted in FIG. 17 enables display of
Doppler waveforms in a display region of the guide image data so as
to enable side by side display of the Doppler waveform and B mode
image data. A display form depicted in FIG. 18 enables color
Doppler image data in the color Doppler mode to be superimposed on
a part of the B mode image data displayed in the display form in
FIG. 17. In the present embodiment, a display form enabling display
of a three-dimensional body mark may be optionally implemented.
[0106] Here, in the display form depicted in FIG. 18, color Doppler
image data is displayed in a color ROI defined by the operator as a
region of interest (ROI) on the B mode image data. A scan
cross-section being ultrasonically scanned by the ultrasonic probe
1 at the completion of the navigation is a long-axis cross-section
passing through the long axis of a blood vessel or a cross-section
near the long-axis cross-section of the blood vessel. The long-axis
cross-section of a blood vessel or a cross-section near the
long-axis cross-section of the blood vessel contains a line through
which the blood vessel runs, and serves as a cross-section from
which blood flow information such as a velocity, a dispersion, and
power can be highly accurately calculated. That is, the display
form depicted in FIG. 18 enables the operator to refer to not only
Doppler waveforms collected at an optimum position but also color
Doppler image data collected from an optimum cross-section.
[0107] Thus, the above-described navigation function can be used as
a function allowing the operator to move the ultrasonic probe 1, by
specifying an observation area, to a cross-section that is an
optimum cross-section for Doppler waveform collection and that
contains a color ROI from which blood flow information is highly
accurately calculated. The navigation function described in the
present embodiment can be used as a function allowing the operator
to move the ultrasonic probe 1, by specifying an observation area,
to a color ROI that enables generation and display of color Doppler
image data in which highly accurate blood flow information is
visualized.
[0108] The foregoing describes navigation performed in the PW mode.
When navigation is performed in the CW mode, the above manner is
applicable except for the difference that, in the three-dimensional
range 300 for example, the optimum line 503 is moved, and the line
506 depicted in FIG. 11 is set as a collection range.
[0109] Next, processing in the ultrasonic diagnostic apparatus
according to the present embodiment performs is described with
reference to FIG. 19. FIG. 19 is a flowchart for explaining one
example of processing that the ultrasonic diagnostic apparatus
according to the present embodiment performs. In connection with
FIG. 19, processing after the acquisition of a correspondence
relation with volume data of another kind is described. The
correspondence relation is intended for calculation of position
information of a collection range and a collection cross-section
for execution of the PW mode.
[0110] As depicted in FIG. 19, the control circuitry 18 according
to the present embodiment determines whether the request to start
navigation has been received from the operator (Step S101). Here,
if the request to start navigation has not been received (No at
Step S101), the control circuitry 18 stands by until the request to
start navigation is received.
[0111] In contrast, if the request to start navigation has been
received (Yes at Step S101), the guide image generation circuitry
164 performs processing under the instruction of the control
circuitry 18, whereby a marker for a current scan cross-section is
superimposed on VR image data of the volume data (Step S102; refer
to FIG. 7). Subsequently, the calculation circuitry 163 then
determines whether specification of an observation area has been
received on the VR image data (Step S103). Here, if specification
of an observation area has not been received (No at Step S103), the
calculation circuitry 163 stands by until specification of an
observation area is received.
[0112] In contrast, if specification of an observation area has
been received (Yes at Step S103), the calculation circuitry 163
calculates the position of the specified observation area in the
volume data, and calculates the running direction of the blood
vessel in the observation area (Step S104; refer to FIG. 9). The
calculation circuitry 163 then calculates the position of an
optimum line in the volume data (step S105; refer to FIG. 10). The
calculation circuitry 163 then arranges a double line
(corresponding to the sampling gate) and a running line
(corresponding to the angle marker) on the optimum line (Step S106;
refer to FIG. 10).
[0113] The calculation circuitry 163 then moves the double line and
the optimum line in the three-dimensional range with the
observation area at the center while the position of the running
line is maintained, and searches for a collection range and a
collection cross-section that corresponds to a scan cross-section
allowing scanning of the move optimum line and that give the
smallest angle between the moved optimum line and running direction
of the blood vessel (Step S107; refer to FIG. 11). The calculation
circuitry 163 then calculates position information of the
collection range and collection cross-section obtained by the
searching (Step S108).
[0114] Subsequently, the guide image generation circuitry 164
generates guide image data by using the correspondence relation and
the position information, and the display 2 displays thereon the
guide image data (Step S109; refer to FIG. 12). The operator starts
moving the ultrasonic probe 1 with reference to the guide image
data.
[0115] Subsequently, the control circuitry 18 determines whether a
scan cross-section coincides with the collection cross-section
(Step S110). Here, if the scan cross-section does not coincide with
collection cross-section (No at Step S110), guide image data for a
new scan cross-section is generated and displayed under the control
of the control circuitry 18 at Step S109.
[0116] In contrast, if the scan cross-section coincides with the
collection cross-section (Yes at Step S110), the control circuitry
18 notifies that the collection cross-section is being scanned
(Step S111; refer to FIG. 14). The control circuitry 18 then
displays the line marker, the sampling gate, and the angle marker
while superimposing them on ultrasonic image data of the collection
cross-section (step S112).
[0117] The control circuitry 18 then starts collection and display
of Doppler waveforms (Step S113), and ends the navigation
processing.
[0118] As described so far, in the present embodiment, position
information of an optimum collection range and collection
cross-section within a three-dimensional range is calculated by use
of the running direction, calculated by use of volume data from
which a blood vessel region can be extracted, of a blood vessel in
an observation area, so that guide image data is generated and
displayed. Consequently, operations that the operator performs to
display optimum blood flow velocity information can be simplified
in the present embodiment.
[0119] The above embodiment is described as a case of searching,
with optimum search conditions, for one set of a collection range
and a collection cross-section within a three-dimensional scan
range of volume data, the three-dimensional scan range
corresponding to a three-dimensional range defined as a
three-dimensional region that can be scanned. However, a collection
cross-section is rigidly a cross-section obtained by searching a
virtual space of volume data. For this reason, the following cases
may occur: a case where the operator cannot scan a collection
cross-section in the actual space when intending to scan the
collection cross-section; and a case where scanning a collection
cross-section in the actual space results in generation of a shadow
due to a bone or the like in B mode image data.
[0120] To avoid such cases, the present embodiment may be
implemented as a first modified example described below. In the
first modified example, the calculation circuitry 163 searches for
a position that gives an angle equal to or smaller than a
predetermined value between an optimum line moved in the
three-dimensional range and the running direction of a blood vessel
in an observation area. For example, the predetermined value is "60
degrees".
[0121] The calculation circuitry 163 then obtains a plurality of
candidate sets each consisting of a candidate collection range and
a candidate scan cross-section, and calculates a plurality of
pieces of candidate position information. Here, the control
circuitry 18 determines ranks of the pieces of candidate position
information, for example, in ascending order of the angles. FIG.
20A and FIG. 20B are diagrams for explaining the first modified
example.
[0122] For example, as depicted in FIG. 20A, when the predetermined
value TH.theta. is "60 degrees", the control circuitry 18 sets a
piece of candidate position information with "angle: 45 degrees" as
a first candidate, sets a piece of candidate position information
with "angle: 48 degrees" as a second candidate, and a piece of
candidate position information with "angle: 50 degrees" as a third
candidate.
[0123] Subsequently, when having received from the operator a
request to change guide image data based on a piece of candidate
position information that has a certain rank among the pieces of
candidate position information, the control circuitry 18 displays
guide image data based on a piece of candidate position information
of a rank succeeding the certain rank. For example, the operator
presses down a "Next" button of the input circuitry 3 when an
appropriate B mode image has not been displayed from a collection
cross-section of the first candidate. In this case, the control
circuitry 18 causes guide image data based on position information
of the first candidate to be displayed. Note that, in order to
notify that a candidate has been changed to another candidate of a
lower rank, the control circuitry 18 may change the color of a
marker superimposed on guide image data for the second candidate
from the color of a marker superimposed on guide image data for the
first candidate.
[0124] Here, the control circuitry 18 may determine the ranking by
a method other than a method using angle values. For example, the
control circuitry 18 assigns the first rank to a piece of candidate
position information that gives the smallest angle, and assigns the
following ranks to the other pieces of candidate position
information in ascending order of amount of moving operation from
the piece of candidate position information of the first rank.
Alternatively, for example, the control circuitry 18 assigns ranks
to the plurality of pieces of candidate position information in
ascending order of amount of moving operation from the current
position of the ultrasonic probe 1.
[0125] It is possible that only one candidate set has been
extracted by use of the predetermined value. In such a situation,
upon receiving from the operator a request to change guide image
data based on candidate position information of this candidate set,
the calculation circuitry 163 searches for the positions of
candidate sets that give values equal to or smaller than a value
that exceeds the predetermined value. For example, as depicted in
FIG. 20B, when only a first candidate with "angle: 45 degrees" has
been obtained by searching on condition that "TH.theta.=60
degrees", the calculation circuitry changes the condition to
"TH.theta.'=65 degrees". Consequently, for example, as depicted in
FIG. 20B, the calculation circuitry 163 sets, as a second
candidate, a candidate set of a candidate collection range and a
candidate scan cross-section from which position information with
"angle: 61 degrees" can be obtained. The control circuitry 18 then
causes guide image data based on position information of "angle: 61
degrees" to be displayed.
[0126] In the present embodiment, when no candidate set has been
obtained by searching using the predetermined value, searching may
be conducted again for the positions of candidate sets that give
values equal to or smaller than a value that exceeds the
predetermined value. Alternatively, in the present embodiment, when
no candidate set has been obtained by searching using the
predetermined value, the operator may be notified of a request to
define a new three-dimensional scan range that allows scanning of
an observation area.
[0127] The above embodiment describes a case where, by use of a
correspondence relation based on the position sensor 4,
cross-section position information corresponding to the position of
a cross-section of cross-section image data (B mode image data)
generated by the image generation circuitry 14 is acquired in
volume data of another kind such as X-ray CT volume data or MRI
volume data. However, the above embodiment may also be applied to a
case where, using a well-known position matching technique such as
the cross-correlation method, the acquisition circuitry 161
acquires, every time cross-section image data is generated,
cross-section position information of the cross-section image data
in volume data. The above embodiment describes a case of using
volume data of another kind such as X-ray CT volume data or MRI
volume data from which a blood vessel region can be extracted.
However, the present embodiment may also be applied to a case of
using volume data, photographed by ultrasound transmission and
reception, from which a region where a blood flow exists can be
extracted. In this second modified example, color Doppler volume
data or power volume data obtained by three-dimensional scanning by
the color flow mapping (CFM) method is used as the volume data.
[0128] For example, the operator conducts scanning in the color
Doppler mode when defining a three-dimensional scan range depicted
in the left illustration in FIG. 5. For example, from
three-dimensional position information of the ultrasonic probe 1
acquired from the position sensor 4 by the acquisition circuitry
161, the control circuitry 18 reconstructs three-dimensional
reflected-wave data using respective pieces of two-dimensional
reflected-wave data of a plurality of cross-sections, and transmits
the reconstructed data to the Doppler process circuitry 13. FIG. 21
is an illustration for explaining the second modified example.
[0129] According to this manner, the image generation circuitry 14
generates power volume data 700 as depicted in FIG. 21, for
example. The extraction circuitry 162 extracts a blood flow region
710 as depicted in FIG. 21 by extracting voxels to which brightness
values according to power values have been assigned. For the blood
flow region 710, the running direction of the blood vessel can be
calculated. In the second modified example, the correspondence
relation between the position of a scan cross-section being scanned
by the ultrasonic probe 1 and the position of power volume data 700
can be acquired only on the basis of three-dimensional position
information of the ultrasonic probe 1 acquired from the position
sensor 4. Ultrasonic volume data, such as the power volume data
700, from which a blood vessel region can be extracted may be
ultrasonic volume data generated by scanning a three-dimensional
region inside the subject P with, for example, a mechanical 4D
probe or a 2D probe.
[0130] Furthermore, the navigation processing that the image
processor 16 performs is applicable to M mode photography. For
example, the M mode is executed for obtaining motion information of
a cardiac valve or a myocardium located on a scan line. FIG. 22 is
an illustration for explaining a third modified example. For
example, the third modified example is applied to a case where a
sampling line for the M mode is arranged at its optimum position
and angle as depicted in FIG. 22. In this third modified example,
conditions with which the sampling line for the M mode comes to its
optimum position and angle can be defined, for example, by having
the operator specify, on VR image data of volume data of a heart, a
direction in which a normal cardiac valve would move, or a
direction in which a normal myocardium would move.
[0131] Of the various kinds of processing described in the above
embodiment, the first modified example, the second modified example
and the third modified example, the whole or a part of each of the
described kinds of processing as those to be automatically
performed may be manually performed, and the whole or a part of
each of the pieces described as those to be manually performed may
be automatically performed. Furthermore, the processing procedure,
the control procedure, the specific names, and information
containing various pieces of data and various parameters may be
desirably changed.
[0132] The respective constituent elements of the devices and
apparatuses depicted in the above description are functionally
conceptual, and do not necessarily need to be configured physically
as depicted. That is, the specific forms of distribution or
integration of the devices and apparatuses are not limited to those
depicted, and the whole or a part thereof can be configured by
being functionally or physically distributed or integrated in any
form of units, depending on various types of loads, usage
conditions, and the like. Furthermore, the whole of or a part of
the various processing functions performed in the respective
devices and apparatuses can be implemented by a CPU, and a program
executed by the CPU, or implemented as hardware by wired logic.
[0133] The image processing method described in the foregoing
embodiment, the first modified example, the second modified example
and the third modified example can be implemented by executing, on
a computer such as a personal computer or a workstation, an image
processing program prepared in advance. This program can be
distributed via a network such as the Internet. This program can
also be recorded on a computer-readable recording medium such as a
hard disk, a flexible disk (FD), a compact disc read only memory
(CD-ROM), a magnetic optical disc (MO), or a digital versatile disc
(DVD), and executed by being read out from the recording medium by
the computer.
[0134] As described above, according to the embodiment, the first
modified example, the second modified example, and the third
modified example, operations that the operator performs for
displaying blood flow velocity information are simplified.
[0135] While certain embodiments have been described, these
embodiments have been presented by way of example only, and are not
intended to limit the scope of the inventions. Indeed, the novel
embodiments described herein may be embodied in a variety of other
forms; furthermore, various omissions, substitutions and changes in
the form of the embodiments described herein may be made without
departing from the spirit of the inventions. The accompanying
claims and their equivalents are intended to cover such forms or
modified examples as would fall within the scope and spirit of the
inventions.
* * * * *