JP4598260B2 - Ultrasonic diagnostic equipment - Google Patents

Description

[0001]
BACKGROUND OF THE INVENTION
The present invention relates to an ultrasonic diagnostic apparatus, and more particularly to automatic setting of a measurement position.
[0002]
[Prior art]
The ultrasonic diagnostic apparatus is 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 ultrasonic beams are 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 the time axis is displayed. The horizontal axis of the M-mode image corresponds to the time axis, and the vertical axis thereof corresponds to the depth axis. The D-mode image is an image representing the frequency analysis result of Doppler information acquired at a certain sample volume (sample position) on the time axis, the horizontal axis corresponds to the time axis, and the vertical axis represents the velocity axis ( Corresponds to the frequency axis). In the D-mode image, the power for each frequency is displayed as a luminance value.
[0003]
Conventionally, when displaying an M-mode image, first, a specific azimuth is set as an M line on the B-mode image, and an ultrasonic beam is formed continuously or intermittently with respect to the azimuth. Similarly, when displaying a D-mode image, first, the sample volume is set by the user on the B-mode image, and an ultrasonic beam is formed continuously or intermittently with respect to 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.
[0004]
Conventionally, the M line or sample volume is set on a B-mode image at a predetermined time phase of the heart, for example, and remains fixed even when the heart moves with a heartbeat.
[0005]
[Problems to be solved by the invention]
Therefore, even if an organ such as the heart moves periodically, the M line or sample volume is absolutely fixed on the transmission / reception coordinate system regardless of the movement, and the specific position in the initially set organ is Even if it moves relatively, it does not follow it. For this reason, there has been a problem in that an ultrasonic measurement is performed at a place deviated from the specific position and an image is formed. This problem is caused not only by the heart beat but also by breathing exercises. In addition, this problem can occur similarly in measurement for setting a region of interest (ROI), for example.
[0006]
The present invention has been made in view of the above-described conventional problems, and its purpose is to dynamically set the measurement position by following the periodic movement of the organ, thereby realizing highly reliable measurement. It is in.
[0007]
[Means for Solving the Problems]
(1) In order to achieve the above object, the present invention provides an ultrasonic diagnostic apparatus for performing ultrasonic diagnosis of an organ that moves periodically, on a two-dimensional tomographic image of the organ in each movement time phase. Input means for registering a specific position as a registered measurement position, storage means for storing a series of registered measurement positions in association with the movement time phase of the organ, and the series according to the movement time phase of the organ And a setting unit that dynamically sets the actual measurement position according to the registered measurement position, and a measurement unit that performs measurement of predetermined data at the actual measurement position.
[0008]
According to the above configuration, in the preparation registration step, the registered measurement position is designated by the user on each two-dimensional tomographic image, and is registered while being associated with the motion 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 motion phase of the organ. Therefore, according to the present invention, since the actual measurement position can be dynamically set (that is, automatic follow-up setting) based on the trajectory of the periodic motion of the past organ, the measurement accuracy can be improved. The organ is, for example, the heart, but other than the above, the same effects as those described above can be obtained if the organ moves at a constant cycle.
[0009]
Desirably, the movement time phase of the organ is specified based on the biological signal of the organ. Here, examples of the biological signal include an electrocardiogram signal, a pulse wave signal, and a respiratory signal.
[0010]
Desirably, a transmission / reception control means for executing transmission / reception of an ultrasonic wave with respect to the actual measurement position is included. If the actual measurement position represents 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 string obtained above.
[0011]
Desirably, an interpolation calculation means for obtaining an actual measurement position by interpolation calculation from two registered measurement positions is included. According to this configuration, it is possible to specify the actual measurement position from the registered measurement positions of two adjacent movement time phases.
[0012]
(2) In order to achieve the above object, the present invention provides an ultrasonic diagnostic apparatus for performing an ultrasonic diagnosis of an organ that moves periodically, on a two-dimensional tomographic image of the organ in each movement phase. Input means for user registration of the M line orientation passing through the organ, storage means for storing a series of M line orientations in association with the movement time phase of the organ, and depending on the movement time phase of the organ, Setting means for dynamically setting the ultrasonic beam azimuth according to a series of M line azimuths, and image forming means for forming an M-mode image based on echo data of each motion time phase acquired on the ultrasonic beam. It is characterized by including.
[0013]
(3) Further, in order to achieve the above object, the present invention provides an ultrasonic diagnostic apparatus for performing ultrasonic diagnosis of an organ that moves periodically, on a two-dimensional tomographic image of the organ in each movement time phase. In accordance with the movement time phase of the organ, the input means for registering the specific position of the organ as a registered sample position, the storage means for storing a series of registered sample positions in association with the movement time phase of the organ, An azimuth setting means for dynamically setting an ultrasonic beam azimuth according to the series of registered sample positions; a position setting means for dynamically setting an actual sample position on each ultrasonic beam according to the series of registered sample positions; Image forming means for forming a Doppler image based on Doppler information of each movement time phase acquired at the actual sample position. Here, the Doppler image may be a so-called D-mode image.
[0014]
DETAILED DESCRIPTION OF THE INVENTION
DESCRIPTION OF EXEMPLARY EMBODIMENTS Hereinafter, preferred embodiments of the invention will be described with reference to the drawings.
[0015]
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 thereof.
[0016]
The ultrasonic probe 10 has an array transducer (not shown), and the array transducer is composed of a plurality of transducer 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 the body surface or inserted into a body cavity.
[0017]
The transmission circuit 12 is a circuit that supplies a transmission signal to a plurality of vibration elements constituting the array transducer, and functions as a so-called transmission beam former.
[0018]
The reception circuit 14 is a circuit that outputs a reception signal after phasing addition by inputting a plurality of reception signals from a plurality of vibration elements constituting the array transducer and executing a phasing addition process. The reception circuit 14 functions as a so-called reception beam former.
[0019]
The transmission / reception control circuit 24 is a circuit that controls the transmission circuit 12, the reception circuit 14, and the like. In the M mode, the transmission circuit is configured so that an ultrasonic beam is formed at a registered measurement position as described later. 12 and the receiving circuit 14 are controlled. In the D mode, control is performed to form an ultrasonic beam that passes through the sample position so that Doppler measurement is performed on the registered sample position as will be described later. The Doppler detection circuit 20 is controlled to extract Doppler information and detect Doppler information.
[0020]
The B-mode processing circuit 16 is a circuit that generates B-mode image data based on the received signal after phasing addition output from the receiving circuit 14, and the B-mode image data formed thereby is displayed on the display processing circuit. On the other hand, it is stored in the B-mode storage circuit 17 as required. The B-mode storage circuit 17 is composed of a memory that stores a plurality of frames of B-mode images.
[0021]
The Doppler detection circuit 20 is a circuit that performs, for example, an FFT operation on the received signal after phasing addition output from the receiving circuit 14 and an operation for analyzing a 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 received signal after phasing addition output from the receiving circuit 14, and the data of the M mode image is output to the display processing circuit 18. .
[0022]
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 configured by a display, and a desired ultrasonic image such as a B-mode image, a D-mode image, or an M-mode image is displayed on the display screen of the display device 26.
[0023]
On the other hand, an electrocardiogram signal from an electrocardiograph (not shown) is input to the biosignal receiving unit 28 as a biosignal. The biological signal received via the biological signal receiving unit 28 is output to the display processing circuit 18 and is stored in the biological signal storage circuit 30. For example, the waveform of the biological signal is displayed on the display device 26 together with, for example, a B-mode image and an M-mode image.
[0024]
The input device 32 is constituted by a keyboard, a trackball, and the like, and the measurement position can be registered on each B-mode image at the preparation registration stage as will be described in detail later by using the input device 32. Specifically, information on the measurement position for each frame is stored in the memory 36 in association with the time phase of the biological signal. Here, for example, the measurement position is the orientation of the M line for the M mode, and the coordinates of the sample position (sample volume) for the D mode.
[0025]
The time phase detection circuit 34 performs time phase detection on the biological signal output from the biological signal storage circuit 30 or the directly input biological signal, and stores information representing the time phase in the heartbeat in the memory 36. It is a circuit to output. As described above, the measurement position information is stored on the memory 36 while being associated with each time phase. The interpolation circuit 38 is a circuit that performs an interpolation operation based on two measurement positions stored on the memory 36 and generates a measurement position as an interpolation value between them. In this embodiment, as will be described later. So-called linear interpolation is performed.
[0026]
The measurement position setting control unit 40 is a circuit that controls the operation of each circuit in a preparation registration stage and an actual measurement stage, which will be described in detail later.
[0027]
Incidentally, the information on 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 as will be described later. The data is output to the transmission / reception control circuit 24, and the transmission / reception control circuit 24 sets the azimuth of the ultrasonic beam and the depth of the sample volume for extracting Doppler information based on the measurement position.
[0028]
The above configuration example shown in FIG. 1 is, of course, an example, and various other configuration examples can be adopted.
[0029]
FIG. 2 conceptually shows the display screen 42 of the display device 26. On the display screen 42, for example, a two-dimensional tomographic image as a B-mode image 44 is displayed. When executing the M mode measurement, the M line 46 is set in an arbitrary direction on the B mode image 44 by the user, and an M mode image (not shown) is formed using echo data on the M line. . Specifically, an ultrasonic beam is repeatedly formed in the direction of the M line 46, and an echo data string on each ultrasonic beam is represented on the time axis to form an M mode image. This is executed by the M-mode processing circuit 22 described above.
[0030]
When performing D-mode measurement, 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 the plurality of echo data thus obtained, and Doppler information is analyzed for the extracted echo data. Based on the analysis result, a D-mode image is formed as described above.
[0031]
In FIG. 2, reference numeral 50 represents the waveform of an electrocardiogram signal as a biological signal, and here the marker 52 represents the time phase of the B-mode image 44. Of course, the display example shown in FIG. 2 is an example, and various other display examples can be adopted.
[0032]
FIG. 3 conceptually shows the contents stored in the memory 36. On the memory 36, the measurement position is set by the user on the B-mode image of each frame for one heartbeat of the heart at the preparatory registration stage to be described later, and the coordinate data of the measurement position is stored in each storage cell of the memory 36. Is done. In the example shown in FIG. 3, storage cells for each of the X address and the Y address are shown, and in any case, information on the measurement position is managed for each time phase.
[0033]
FIG. 4 conceptually shows the processing contents of the interpolation circuit 38.
[0034]
In the preparatory registration stage shown in the upper part of the figure, for example, a plurality of (for example, N = 4) B-mode images are acquired over one heart beat from the R wave to the next R wave in the electrocardiogram signal, and these B-mode images are acquired. Is once stored in the B-mode storage circuit 17. Then, as will be described in detail later, each B-mode image is read in order, and the coordinates (including the orientation) of the measurement position are registered by the user on each B-mode image. The registered coordinate information is stored on the memory 36 as described above.
[0035]
In the actual measurement stage shown in the lower part of FIG. 4, first, a B-mode image over a plurality of frames for one heart beat is acquired in advance, and the number of frames for one heart beat is confirmed in advance. A measurement position is determined by interpolation calculation based on the time phase of each frame in the next heartbeat, and an ultrasonic beam is formed and a sample position is set for the measurement position.
[0036]
In FIG. 4, four frames are drawn as the preparation and registration stage, and eight frames are drawn as the actual measurement stage. Of course, this is an example. Registration and actual measurement position interpolation are performed.
[0037]
In this embodiment, both the preparation registration stage and the actual measurement stage are based on one heart rate. However, if the preparation registration stage and the actual measurement stage are the same number of heartbeats, even if the preparation registration stage and the actual measurement stage are performed for a plurality of heartbeats, The same effect as the invention can be obtained.
[0038]
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, for example, a B-mode image and a biological signal are stored for one heartbeat or several heartbeats. In S101, the measurement position setting method by the user is selected. When the setting is sequentially set here, 0 is substituted for the variable i as an initial value in S102, and then the i-th B-mode image is displayed in S103. Displayed on the screen. Therefore, the measurement position is designated on the B-mode image by the user in S104 and is registered in the memory 36.
[0039]
In S105, it is determined whether or not such registration work has been completed. If the registration has not been completed, the variable i is incremented by one in S106, and the above-described steps after S103 are repeatedly executed.
[0040]
On the other hand, when the slow playback setting is selected as the setting method in S101, the playback speed is arbitrarily selected by the user in S107. In S108, the user performs the slow playback of the B-mode image and simultaneously the measurement position by the user. The work of registering is executed. That is, the manual trace of the measurement position is executed.
[0041]
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 for the variable j in S110, and the j-th B mode in S111. The image will be displayed on the screen. Therefore, in S112, the measurement position is designated by the user on the B-mode image and registered in the memory 36. In S114, it is determined whether or not such registration work has been completed. If it has not been completed, k is added to the variable j in S113, and the added value becomes j, and each step from S111 is repeatedly executed. The
[0042]
After the preparation registration stage as shown in FIG. 5 described above, M measurement positions are registered in one heartbeat from the R wave to the next R wave in the electrocardiogram signal.
[0043]
FIG. 6 shows the operation of the apparatus in the actual measurement stage according to this embodiment.
[0044]
First, in S201, a B-mode image is formed over one heartbeat from an R wave to the next R wave with reference to an electrocardiogram signal as a biological signal. In S202, the number M of B-mode images for one heartbeat is calculated. Next, in S203, 0 is substituted for the variable m and 0 is substituted for the variable s.
[0045]
In S204, it is determined whether or not to end this process. If not, it is determined whether or not m is smaller than M in S205. If the condition is satisfied, the interpolation operation of the sample position described later with reference to FIG. 7 is executed in S206. On the other hand, if the condition in S205 is not satisfied, the process proceeds from S205 to S207. That is, S205 is a step of determining whether or not the variable m as a counter exceeds the number M of B-mode images confirmed in advance for one heartbeat, and is greater than the number M of B-mode images confirmed in advance. When the actual number of B-mode images exceeds, interpolation processing cannot be performed, and thus processing for adopting past sample positions is performed. In S207, control for setting the actual measurement position to the sample position calculated in S206 is executed. In S208, transmission / reception of ultrasonic waves, that is, formation of an ultrasonic beam, is executed for the sample position. In S209, it is determined whether or not an R wave has been detected. If no R wave has been detected, the variable m is incremented by 1 in S210, and the processes from S204 are executed. On the other hand, if an R wave is detected in S209, the number of images m at the RR interval in the actual measurement stage is sequentially substituted for M in S211, and the number of images M for one heartbeat is updated. Then, in order to perform the same processing as described above for the next heartbeat, each step after S203 is repeatedly executed.
[0046]
That is, according to the processing shown in FIG. 6, it is possible to perform the interpolation calculation of the sample position at the next heartbeat using the number of B-mode images at the previous heartbeat.
[0047]
FIG. 7 shows a specific processing content of the interpolation calculation step S206 shown in FIG. 6 as a flowchart.
[0048]
In S301, the value of s set in S203 is substituted for n. In S302, it is determined whether n is smaller than N. That is, when n matches N, it is determined that the next heartbeat occurs, and the process shown in FIG. 7 is bypassed.
[0049]
In S303, as shown in FIG. 4, whether the current frame position in the total number of frames in the actual measurement stage corresponds to any of a plurality of frame sections that are sequentially updated and registered in the actual measurement stage from the preparation registration stage. In step S304, it is determined whether or not the condition shown in step S303 is satisfied while incrementing n by 1. If the condition is satisfied, step S305 is executed.
[0050]
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 so-called linear interpolation calculation, and the measurement position is obtained by interpolation calculation by performing the known linear calculation 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, the interpolation calculation in the next interpolation section can be executed at high speed. By setting n = 0 in S301, the process of S306 can be excluded. In this case, since the variable s is not required, it is not necessary to set “s = 0” in S203.
[0051]
According to the above-described interpolation calculation, the interpolation calculation of the sample position is performed based on the comparison between the number of frames for one heartbeat that is sequentially updated from the preparation registration stage to the actual measurement stage and the number of frames for one heartbeat in the actual measurement stage. Therefore, 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. In addition, during execution of the actual measurement stage, the value of the number of frames M corresponding to one heartbeat is updated at any time, so even if the number of frames differs between the preparation registration stage and the actual measurement stage, the setting accuracy of the sample position does not decrease. There is an advantage. In this 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 time phase of the frame is managed by the numerical value.
[0052]
In the above embodiment, the sample position is stored on the XY coordinate system, that is, the orthogonal coordinate system. Of course, the storage may be performed on the polar coordinate system.
[0053]
In particular, when performing M-mode measurement, there is an advantage that transmission / reception control can be performed more simply by registering the sample position as an orientation in the polar coordinate format.
[0054]
Of course, the operation examples shown in FIGS. 5 to 7 are merely examples, and various other operations can be employed. In addition, it is considered that the change in the value of the number M of images corresponding to one heartbeat is usually small between the preparation registration stage and the actual measurement stage. In this case, the M value is fixed to the number in the preparation registration stage. May be. In any case, by registering the measurement position in advance in association with the periodic movement of the heart, the measurement position is dynamically linked to the periodic movement of the heart when actually measuring. As a result, the reliability of data acquired at the measurement position can be remarkably increased.
[0055]
【The invention's effect】
As described above, according to the present invention, it is possible to automatically set the measurement position 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 an embodiment.
FIG. 2 is a diagram illustrating 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 the operation of the apparatus in a preparation registration stage.
FIG. 6 is a flowchart showing the operation of the apparatus in an actual measurement stage.
FIG. 7 is a flowchart showing an interpolation calculation.
[Explanation of symbols]
DESCRIPTION OF SYMBOLS 10 Ultrasonic probe, 12 Transmission circuit, 14 Reception circuit, 16 B mode processing circuit, 17 B mode memory circuit, 18 Display processing circuit, 20 Doppler detection circuit, 22 M mode processing circuit, 24 Transmission / reception control circuit, 28 Living body 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)

In an ultrasonic diagnostic apparatus for performing ultrasonic diagnosis of periodically moving organs,
On the two-dimensional tomographic image of the organ in each motion time phase, an input means for registering the 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;
Setting means for dynamically setting an actual measurement position according to the series of registered measurement positions according to the movement time phase of the organ;
Measuring means for executing measurement of predetermined data at the actual measurement position;
An ultrasonic diagnostic apparatus comprising: The apparatus of claim 1.
An ultrasonic diagnostic apparatus characterized in that a movement time phase of an organ is specified based on a biological signal of the organ. The apparatus of claim 1.
An ultrasonic diagnostic apparatus comprising: a transmission / reception control means for executing transmission / reception of an ultrasonic wave with respect to the actual measurement position. The apparatus of claim 1.
An ultrasonic diagnostic apparatus comprising an interpolation calculation means for obtaining an actual measurement position from two registered measurement positions by interpolation calculation. In an ultrasonic diagnostic apparatus for performing ultrasonic diagnosis of periodically moving organs,
An input means for registering the M line direction passing through the organ on the two-dimensional tomographic image of the organ in each motion phase,
Storage means for storing a series of M-line orientations in association with the movement phase of the organ;
Setting means for dynamically setting an ultrasonic beam azimuth according to the series of M-line azimuth according to the movement phase of the organ;
Image forming means for forming an M-mode image based on echo data of each motion time phase acquired on the ultrasonic beam;
An ultrasonic diagnostic apparatus comprising: In an ultrasonic diagnostic apparatus for performing ultrasonic diagnosis of periodically moving organs,
On the two-dimensional tomographic image of the organ in each movement time phase, an input means for registering the specific position of the organ as a registered sample position,
Storage means for storing a series of registered sample positions in association with the motion phase of the organ;
Orientation setting means for dynamically setting the ultrasonic beam orientation according to the series of registered sample positions according to the movement time phase of the organ;
Position setting means for dynamically setting an actual sample position on each ultrasonic beam according to the series of registered sample positions;
Image forming means for forming a Doppler image based on Doppler information of each motion time phase acquired at the actual sample position;
An ultrasonic diagnostic apparatus comprising:

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