JP2002165798A - Ultrasonic diagnostic equipment - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an ultrasonic diagnostic equipment which can fit a measur ing position with the movement of internal organs dynamically when we measure M-mode or D-mode and the like. SOLUTION: At a preparing registration stage, a measuring position is registered as a user on B-mode image of each frame over one heart beat of a heart. At a practical measuring stage, actual measuring position is set on a basis of the registered measuring position. At M-mode measurement an M-line direction is registered and at D-mode measurement the coordinate of a sample position (sample volume) is registered.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

[0001] 1. Field of the Invention [0002] The present invention relates to an ultrasonic diagnostic apparatus, and more particularly to an automatic setting of a measurement position.

[0002]

2. Description of the Related Art Ultrasonic diagnostic apparatuses are equipped with various measurement modes. The B mode is a mode for displaying a two-dimensional tomographic image of a living body. The M mode is a mode in which an ultrasonic beam is sequentially formed in a fixed direction, and an M mode image in which a series of echo data on each ultrasonic beam is represented on a time axis is displayed. The horizontal axis of the M-mode image corresponds to the time axis, and the vertical axis corresponds to the depth axis. The D-mode image is an image in which the frequency analysis result of Doppler information acquired in a certain sample volume (sample position) is represented on a time axis, the horizontal axis corresponds to the time axis, and the vertical axis is the velocity axis ( Frequency axis). In the D mode image, the power for each frequency is displayed as a luminance value.

Conventionally, when displaying an M-mode image, first, a specific direction is displayed on the B-mode image.
A user is set as a line, and an ultrasonic beam is formed continuously or intermittently in the relevant direction. Similarly, when displaying a D-mode image, first, a sample volume is user-set on the B-mode image, and an ultrasonic beam is formed continuously or intermittently in the direction passing through the sample volume. The echo data corresponding to the sample volume is extracted from the echo data on each ultrasonic beam, and Doppler analysis (for example, FFT operation) is performed on them.

Conventionally, the M line or the sample volume is set, for example, on a B-mode image in a predetermined time phase of the heart, and remains fixed even if the heart moves with the heartbeat.

[0005]

Therefore, even if an organ such as the heart moves periodically, the M line or the sample volume is absolutely fixed on the transmitting and receiving coordinate system regardless of the movement. Even if the specific position in the set organ relatively moves, it does not follow it. For this reason, there has been a problem that an ultrasonic measurement is performed on a place deviating from the specific position and an image is formed. This problem is caused not only by heart beats but also by respiratory movements. In addition, this problem can similarly occur in measurement in which a region of interest (ROI) is set, for example.

The present invention has been made in view of the above-mentioned conventional problems, and has as its object to dynamically set a measurement position in accordance with a periodic movement of an organ, thereby performing highly reliable measurement. Is to make it happen.

[0007]

(1) In order to achieve the above object, the present invention relates to an ultrasonic diagnostic apparatus for performing ultrasonic diagnosis of a periodically moving organ. On the two-dimensional tomographic image, input means for user registration of a specific position of the organ as a registered measurement position, storage means for storing a series of registered measurement positions in association with the movement phase of the organ, A setting means for dynamically setting an actual measurement position in accordance with the series of registered measurement positions according to an exercise time phase, and a measurement means for executing measurement of predetermined data at the actual measurement position. .

According to the above configuration, in the preparatory registration step, the registered measurement position is designated by the user on each two-dimensional tomographic image, and the registered measurement position is registered while being associated with the movement phase of the organ. Next, in the actual measurement step, the actual measurement position is dynamically set based on a series of registered measurement positions according to the movement phase of the organ. Therefore, according to the present invention, the actual measurement position can be dynamically set (that is, the automatic tracking setting) based on the trajectory of the periodic movement of the past organ, so that the measurement accuracy can be improved. The organ is, for example, the heart, but any other organ that moves at a constant cycle can obtain the same effect as described above.

Preferably, a movement time phase of the organ is specified based on a biological signal of the organ. Here, the biological signal includes an electrocardiographic signal, a pulse wave signal, a respiratory signal, and the like.

[0010] Preferably, the apparatus further includes transmission / reception control means for transmitting / receiving ultrasonic waves to / from the actual measurement position. If the actual measurement position indicates an azimuth, an ultrasonic beam is formed in the azimuth. If the actual measurement position is a sample position or a sample volume, an ultrasonic beam passing through the position is set. Measurement data corresponding to the actual measurement position is extracted from the echo data sequence obtained above.

Preferably, the apparatus further includes an interpolation operation means for obtaining an actual measurement position by interpolation from two registered measurement positions. According to this configuration, it is possible to specify the actual measurement position from the registered measurement positions of the two adjacent exercise time phases.

(2) To achieve the above object,
The present invention provides an ultrasonic diagnostic apparatus that performs ultrasonic diagnosis of an organ that periodically moves, on a two-dimensional tomographic image of the organ in each exercise phase, for user registration of an M-line direction passing through the organ. Input means, storage means for storing a series of M-line orientations in association with the movement time phases of the organ, and dynamic ultrasound beam orientations according to the series of M-line orientations in accordance with the movement time phases of the organ. Setting means for setting
Image forming means for forming an M-mode image based on the echo data of each motion phase acquired on the ultrasonic beam.

(3) To achieve the above object,
The present invention provides an ultrasonic diagnostic apparatus that performs an ultrasonic diagnosis of an organ that moves periodically, on a two-dimensional tomographic image of the organ in each exercise phase, for user registration of a specific position of the organ as a registration sample position. Input means, storage means for storing a series of registered sample positions in association with the organ movement phase, and moving the ultrasonic beam direction according to the series of registered sample positions in accordance with the organ movement phase. Azimuth setting means for dynamically setting, according to the series of registered sample positions, position setting means for dynamically setting an actual sample position on each ultrasonic beam, and for each movement time phase acquired at the actual sample position. Image forming means for forming a Doppler image based on Doppler information. Here, the Doppler image may be a so-called D-mode image.

[0014]

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS Preferred embodiments of the present invention will be described below with reference to the drawings.

FIG. 1 shows a preferred embodiment of an ultrasonic diagnostic apparatus according to the present invention, and FIG. 1 is a block diagram showing the overall configuration.

The ultrasonic probe 10 has an array vibrator (not shown), and the array vibrator includes a plurality of vibrating elements. An ultrasonic beam is formed using the array transducer, and a known scanning surface is formed by scanning the ultrasonic beam. The ultrasonic probe 10 is used in contact with a body surface or inserted into a body cavity.

The transmitting circuit 12 is a circuit for supplying a transmitting signal to a plurality of vibrating elements constituting the array vibrator, and functions as a so-called transmitting beamformer.

The receiving circuit 14 is a circuit that receives a plurality of received signals from a plurality of vibrating elements constituting an array transducer, executes a phasing addition process, and outputs a received signal after the phasing addition. is there. This receiving circuit 14 functions as a so-called receiving beamformer.

The transmission / reception control circuit 24 includes the transmission circuit 1
2 and a circuit that controls the receiving circuit 14 and the like. In the M mode, the transmitting circuit 12 and the receiving circuit 14 are controlled so that an ultrasonic beam is formed at a registered measurement position as described later. In the D mode, control is performed to form an ultrasonic beam passing through the sample position so that Doppler measurement is performed on the registered sample position, as described later. To control the Doppler detection circuit 20 to extract Doppler information and detect Doppler information.

The B-mode processing circuit 16 is a circuit that generates B-mode image data based on the reception signal after the phasing addition output from the receiving circuit 14. The data is output to the display processing circuit 18 and stored in the B-mode storage circuit 17 as necessary. The B mode storage circuit 17 stores a plurality of frames of B
It is constituted by a memory for storing a mode image.

The Doppler detection circuit 20 applies, for example, an FFT to the reception signal after the phasing addition output from the reception circuit 14.
It is a circuit that executes an operation and executes an operation to analyze the frequency spectrum of Doppler information. The frequency analysis result is output to the display processing circuit 18, and D-mode image data is formed from the frequency analysis result. The M-mode processing circuit 22 is a circuit that forms an M-mode image based on the reception signal after the phasing addition output from the receiving circuit 14, and the data of the M-mode image is output to the display processing circuit 18. .

The display processing circuit 18 is a circuit constituted by a so-called digital scan converter (DSC), and has a coordinate conversion function, a data interpolation function, and the like. The display device 26 is constituted by a display, and a B-mode image and a D-mode image are displayed on a display screen of the display device 26.
A desired ultrasonic image such as a mode image or an M-mode image is displayed.

On the other hand, an electrocardiographic signal from an electrocardiograph (not shown) is input to the biological signal receiving section 28 as a biological signal. The biological signal received via the biological signal receiving unit 28 is output to the display processing circuit 18 and stored in the biological signal storage circuit 30. The display device 26 displays a waveform of a biological signal together with, for example, a B-mode image or an M-mode image as needed.

The input device 32 is composed of a keyboard, a trackball, and the like. Using the input device 32, it is possible to register a measurement position on each B-mode image in a preparatory registration stage as described later in detail. . Specifically, information on the measurement position for each frame is stored on the memory 36 in association with the time phase of the biological signal. Here, the measurement position is, for example, the azimuth of the M line in the M mode, and the coordinates of the sample position (sample volume) in the D mode.

The time phase detection circuit 34 includes the biological signal storage circuit 3
This is a circuit that performs time phase detection on a biological signal output from 0 or a directly input biological signal, and outputs information representing a time phase in a heartbeat to the memory 36.
As described above, the information of the measurement position is stored on the memory 36 in association with each time phase.
The interpolation circuit 38 is a circuit that performs an interpolation operation based on the two measurement positions stored in the memory 36 and generates a measurement position as an interpolation value between them, as will be described later in the present embodiment. So-called linear interpolation is performed.

The measurement position setting control section 40 is a circuit for controlling the operation of each circuit in a preparation registration stage and an actual measurement stage which will be described in detail later.

By the way, the information of the measurement position output from the interpolation circuit 38 is sent to the display processing circuit 18 and is used for displaying a cursor representing an M line or a sample volume, for example, as described later. Is transmitted to the transmission / reception control circuit 24. The transmission / reception control circuit 24 sets the azimuth of the ultrasonic beam and the depth of a sample volume for extracting Doppler information based on the measurement position.

The configuration example shown in FIG. 1 is merely an example, and various other configuration examples can be adopted.

FIG. 2 conceptually shows a display screen 42 of the display device 26. On this display screen 42, for example, a two-dimensional tomographic image as a B-mode image 44 is displayed. When performing the M mode measurement, the B mode image 4
The user sets the M line 46 in an arbitrary direction on the line 4, and an M mode image (not shown) is formed using the echo data on the M line. Specifically, an ultrasonic beam is repeatedly formed in the direction of the M line 46, and an M-mode image is formed by expressing an echo data string on each ultrasonic beam on a time axis. This is executed by the M mode processing circuit 22 described above.

When the D-mode measurement is performed, a sample position (sample volume) 48 is set by the user on the B-mode image 44, and an ultrasonic beam is repeatedly formed in a direction passing through the sample position 48. Echo data corresponding to the sample position 48 is extracted from a plurality of pieces of echo data thus obtained, and Doppler information analysis is performed on the echo data. Then, based on the analysis result, a D-mode image is formed as described above.

In FIG. 2, reference numeral 50 represents a waveform of an electrocardiographic signal as a biological signal, and here, a marker 52 represents a time phase of the B-mode image 44. Of course, the display example shown in FIG. 2 is one example, and various other display examples can be adopted.

FIG. 3 conceptually shows the contents stored in the memory 36. In the memory 36, a measurement position is set by a user on a B-mode image of each frame for one heartbeat in a preparatory registration step described later, and coordinate data of the measurement position is stored in each storage cell of the memory 36. Is done. In the example shown in FIG.
The storage cells for each of the addresses are shown, and in any case, the information of the measurement position is managed for each time phase.

FIG. 4 conceptually shows the processing contents of the interpolation circuit 38.

In the preparatory registration stage shown at the top of the figure,
For example, a plurality of (for example, N = 4) B-mode images are acquired over one heartbeat from the R wave to the next R wave in the electrocardiographic signal, and the B-mode images are temporarily stored in the B-mode storage circuit 17. . Then, as will be described in detail later, each B-mode image is sequentially read, and the coordinates (including the azimuth) of the measurement position on each B-mode image are registered by the user. The information of the registered coordinates is stored in the memory 36 as described above.

In the actual measurement stage shown in the lower part of FIG.
First, a B-mode image over a plurality of frames for one heartbeat of the heart is acquired first, and the number of frames for one heartbeat is confirmed in advance. Then, the measurement position is determined by interpolation based on the time phase of each frame in the next heartbeat,
For the measurement position, formation of an ultrasonic beam, setting of a sample position, and the like are performed.

In FIG. 4, four frames are drawn as the preparatory registration stage, and eight frames are drawn as the actual measurement stage. However, this is merely an example. The registration of the measurement position and the interpolation calculation of the actual measurement position are executed.

In this embodiment, the preparation registration stage and the actual measurement stage are performed on the basis of one heartbeat. However, if the preparation registration stage and the actual measurement stage have the same number of heartbeats, the preparation is performed on a plurality of heartbeats. The same effect as the present invention can be obtained.

The operation of the apparatus in the preparation registration stage according to the present embodiment will be described with reference to FIG. First, in S100, the B-mode image and the biological signal are stored over, for example, one heartbeat or several heartbeats. S101
In, the method of setting the measurement position by the user is selected,
If the sequential setting is set here, 0 is substituted as an initial value for a variable i in S102, and then the i-th B-mode image is displayed on the screen in S103. Therefore,
In S104, the user specifies a measurement position on the B-mode image, and the measurement position is registered in the memory 36.

In S105, it is determined whether or not such registration work has been completed. If not completed, the variable i is incremented by one in S106.
Steps 103 and thereafter are repeatedly executed.

On the other hand, if the slow reproduction setting is selected as the setting method in S101, the reproduction speed is arbitrarily selected by the user in S107, and S1 is selected.
At 08, the user performs the operation of registering the measurement position at the same time as performing the slow reproduction of the B-mode image. That is, a manual trace of the measurement position is executed.

On the other hand, if the thinning setting is selected as the setting method in S101, the thinning rate k is set by the user in S109, 0 is substituted as an initial value in a variable j in S110, and the j-th in S111. Is displayed on the screen. Therefore,
In S112, a measurement position is designated by the user on the B-mode image, and the measurement position is registered in the memory 36. In S114, it is determined whether or not such registration work has been completed. If not completed, k is added to the variable j in S113, and the added value becomes j, and the steps after S111 are repeatedly executed. You.

After the preparatory registration step as shown in FIG. 5, M measurement positions are registered in one heartbeat from the R wave to the next R wave in the electrocardiographic signal.

FIG. 6 shows the operation of the apparatus in the actual measurement stage according to the present embodiment.

First, in S201, a B-mode image is formed over one heartbeat from the R wave to the next R wave with reference to an electrocardiographic signal as a biological signal. In S202, 1
The number M of B-mode images in the heart rate is calculated, and then, in S203, 0 is substituted for a variable m as an initial value, and 0 is substituted for a variable s as an initial value.

In S204, it is determined whether or not this processing is to be terminated. If not, it is determined in S205 whether or not m is smaller than M. If the condition is satisfied, the interpolation operation of the sample position described later with reference to FIG. 7 is executed in S206.
Move to 7. That is, S205 is a step of judging whether or not the variable m as a counter exceeds the number M of B-mode images in one heartbeat confirmed in advance, which is larger than the number M of B-mode images confirmed in advance. When the actual number of B-mode images is exceeded, interpolation processing cannot be performed, and processing for directly adopting past sample positions is executed. In S207, control for setting the actual measurement position to the sample position calculated in S206 is executed. Then, in S208, transmission / reception of ultrasonic waves, that is, formation of an ultrasonic beam, is performed for the sample position. In S209, it is determined whether an R wave has been detected. If no R wave has been detected, the process proceeds to S210.
In step S204, the variable m is incremented by one.
Are performed. On the other hand, in S209, R
If a wave is detected, in step S211 the number m of images at the RR interval in the actual measurement stage is sequentially substituted for M, and the number M of images in one heartbeat is updated. Then, in order to perform the same processing as described above for the next heartbeat, the steps after S203 are repeatedly executed.

That is, according to the processing shown in FIG. 6, the interpolation calculation of the sample position in the next heartbeat can be performed by using the number of B-mode images in the previous heartbeat.

FIG. 7 is a flowchart showing the specific processing contents of the interpolation operation step S206 shown in FIG.

In S301, the value of s set in S203 is substituted for n. Then, in S302, it is determined whether or not n is smaller than N. That is, when n is equal to N, it is determined that the next heartbeat has occurred, and FIG.
Will be bypassed.

In step S303, as shown in FIG. 4, the current frame position in the total number of frames in the actual measurement stage corresponds to any one of the plurality of frame sections sequentially updated and registered in the preparation registration stage to the actual measurement stage. In step S304, it is determined whether or not the condition shown in step S303 is satisfied while incrementing n by one. When the condition is satisfied, step S305 is executed.

That is, in the stage where n is incremented, if it corresponds to the section to which the current frame belongs in the actual measurement stage, S305 is executed.
In S305, the weight values α and β are used to perform a so-called linear interpolation operation, and the measurement position is obtained by the interpolation operation by performing the known linear operation shown in S305 of FIG. In S306, the value of n is substituted for s. That is, by storing the value of n already calculated in this way, it is possible to execute the interpolation calculation in the next interpolation section at high speed. In S301, n = 0
By doing so, the step of S306 can be omitted. In this case, the variable s becomes unnecessary, so
There is no need to set “s = 0” in.

According to the above-described interpolation calculation, the interpolation calculation of the sample position is performed based on the contrast between the number of frames for one heartbeat which is sequentially updated in the preparation registration stage and the actual measurement stage and the number of frames for one heartbeat in the actual measurement stage. Can do
There is an advantage that the sample position can be set with high accuracy in the actual measurement stage without registering the sample position in detail in the preparation registration stage. Further, during execution of the actual measurement stage, the value of the number of frames M corresponding to one heartbeat is updated at any time. Therefore, even if the number of frames differs between the preparatory registration stage and the actual measurement stage, the setting accuracy of the sample position does not decrease. There is an advantage. In the present embodiment, the time phase of the heartbeat from the R wave to the next R wave is represented by a numerical value from 0 to 1.0, and the numerical value controls the time phase of the frame.

In the above embodiment, the sample position is stored on the XY coordinate system, that is, the orthogonal coordinate system. However, the storage of the sample position may be performed on the polar coordinate system.

In particular, in the case of performing the M mode measurement, there is an advantage that the transmission / reception control can be performed more easily by registering the sample position as the azimuth in the polar coordinate format.

The operation examples shown in FIGS. 5 to 7 are of course only examples, and various other operations can be adopted. In the preparation registration stage and the actual measurement stage, 1
It is considered that the change in the value of the number M of images corresponding to the heartbeat is usually small, and in that case, the operation may be performed with the value of M fixed at the number of images in the preparation registration stage. In any case, by registering the measurement position in advance in association with the periodic movement of the heart in advance, the measurement position can be dynamically linked to the periodic movement of the heart when actually performing the measurement. It is possible to set, and as a result, the reliability of the data acquired at the measurement position can be significantly increased.

[0055]

As described above, according to the present invention,
The measurement position can be automatically set by following the periodic movement of the organ.

[Brief description of the drawings]

FIG. 1 is a block diagram of an ultrasonic diagnostic apparatus according to the present embodiment.

FIG. 2 is a diagram showing a screen display example.

FIG. 3 is a conceptual diagram showing information stored in a memory.

FIG. 4 is a conceptual diagram showing a preparation registration stage and an actual measurement stage.

FIG. 5 is a flowchart showing an operation of the apparatus in a preparation registration stage.

FIG. 6 is a flowchart showing an operation of the apparatus in an actual measurement stage.

FIG. 7 is a flowchart showing an interpolation operation.

[Explanation of symbols]

Reference Signs List 10 ultrasonic probe, 12 transmission circuit, 14 reception circuit, 16 B mode processing circuit, 17 B mode storage circuit, 18 display processing circuit, 20 Doppler detection circuit, 22
M mode processing circuit, 24 transmission / reception control circuit, 28 biological signal receiving unit, 30 biological signal storage circuit, 32 input device, 34 time phase detection circuit, 36 memory, 38 interpolation circuit, 40 measurement position setting control unit.

Claims (6)

[Claims] 1. An ultrasonic diagnostic apparatus for performing ultrasonic diagnosis of an organ that moves periodically, wherein a user registers a specific position of the organ as a registered measurement position on a two-dimensional tomographic image of the organ in each exercise time phase. An input unit for storing a series of registered measurement positions in association with the movement phase of the organ; and moving an actual measurement position according to the series of registration measurement positions in accordance with the movement phase of the organ. An ultrasonic diagnostic apparatus, comprising: a setting unit that sets the target data; and a measuring unit that performs measurement of predetermined data at the actual measurement position. 2. The ultrasonic diagnostic apparatus according to claim 1, wherein a movement phase of the organ is specified based on a biological signal of the organ. 3. The ultrasonic diagnostic apparatus according to claim 1, further comprising transmission / reception control means for transmitting / receiving ultrasonic waves to / from the actual measurement position. 4. The ultrasonic diagnostic apparatus according to claim 1, further comprising interpolation calculation means for obtaining an actual measurement position by interpolation from two registered measurement positions. 5. An ultrasonic diagnostic apparatus for performing ultrasonic diagnosis of a periodically moving organ, wherein a user registers an M-line direction passing through the organ on a two-dimensional tomographic image of the organ in each moving phase. Input means, and storage means for storing a series of M-line directions in association with the movement phase of the organ, and moving the ultrasonic beam direction in accordance with the series of M-line directions according to the movement phase of the organ. An ultrasonic diagnostic apparatus, comprising: a setting unit for setting the distance, and an image forming unit for forming an M-mode image based on the echo data of each motion phase acquired on the ultrasonic beam. 6. An ultrasonic diagnostic apparatus for performing ultrasonic diagnosis of a periodically moving organ, wherein a user registers a specific position of the organ as a registered sample position on a two-dimensional tomographic image of the organ in each movement phase. Input means for storing, a series of registered sample positions stored in association with the movement phase of the organ, and, according to the movement phase of the organ, the ultrasonic beam direction according to the series of registered sample positions. Azimuth setting means for dynamically setting, position setting means for dynamically setting an actual sample position on each ultrasonic beam according to the series of registered sample positions, and each movement time phase acquired at the actual sample position And an image forming means for forming a Doppler image based on the Doppler information.