JP4764125B2 - Ultrasonic diagnostic apparatus and control program for ultrasonic diagnostic apparatus - Google Patents

Description

  The present invention relates to an ultrasonic diagnostic apparatus that includes a two-dimensional array ultrasonic probe, transmits ultrasonic waves into a subject, and obtains diagnostic information in the subject based on reflected waves from the subject. In particular, the present invention relates to an ultrasonic diagnostic apparatus that performs a contrast echo method using an ultrasonic contrast agent.

  Conventionally, a contrast echo method using an ultrasonic contrast agent has been performed using an ultrasonic diagnostic apparatus including a so-called one-dimensional ultrasonic probe. The contrast echo method is a method of imaging using the fact that ultrasonic contrast agents containing gas have characteristics such as ultrasonic reflection, scattering and resonance that are significantly different from those of living tissue. This is a technique for imaging using the fact that the harmonic component generated from the image is different from the biological tissue.

  The contrast echo method injects an ultrasound contrast agent into the blood in the living body and clearly visualizes the ultrasound contrast agent that penetrates into the living body along the blood flow. The purpose is to visualize the state (blood flow, blood volume, etc.) and the tissue permeated with blood more clearly.

  There are various concrete imaging methods of the contrast echo method. For example, by changing the sound pressure of an ultrasonic wave to be transmitted and received, the frequency band of a filter, and the like between a scan mode for imaging an ultrasound contrast agent and a scan mode for imaging a tissue image Visualize the agent and tissue image clearly.

  Depending on the type of the ultrasound contrast agent, the ultrasound contrast agent may be destroyed at the moment when the ultrasound contrast agent is irradiated in the scan mode for imaging the ultrasound contrast agent. For example, an ultrasonic contrast agent (levovist) or the like generates a high-band ultrasonic wave when irradiated with an ultrasonic wave having a relatively high sound pressure, but is destroyed at that moment.

  When the ultrasound contrast agent is destroyed in this way, it is impossible to observe how the ultrasound contrast agent penetrates the living body along the blood flow. Therefore, it is necessary to irradiate ultrasonic waves at regular time intervals without continuously irradiating ultrasonic waves in the scan mode for imaging the ultrasonic contrast agent. By setting this fixed time interval, the ultrasound contrast agent penetrates the living body while the ultrasound is not irradiated, and then irradiates the ultrasound in a scan mode for imaging the ultrasound contrast agent. This makes it possible to clearly visualize the ultrasound contrast agent that has penetrated the living body. And in the scan mode for imaging the ultrasound contrast agent, scan by changing the sound pressure of the ultrasound and the frequency band of the filter, etc. The tissue image can be visualized.

  In this way, the ultrasound contrast agent penetrates the living body by alternately performing the scan mode for imaging the ultrasound contrast agent and the scan mode for imaging the tissue image. Can be clearly visualized, and the tissue image can be collected and displayed in a so-called real time.

  In addition, when scanning in the scan mode for imaging ultrasound contrast agents, the sound pressure of the ultrasound and the frequency band of the filter may be different, so the tissue image may not be visualized clearly. By alternately performing the scan mode for imaging and the scan mode for imaging the tissue image, the tissue image can also be clearly visualized.

  On the other hand, by using a so-called two-dimensional array ultrasonic probe in which ultrasonic transducers are two-dimensionally arranged, spatial scanning (hereinafter sometimes referred to as volume scanning) is performed to obtain three-dimensional biological information. Can be collected. Attempts have been made to implement a contrast echo method using an ultrasound contrast agent using an ultrasound diagnostic apparatus equipped with this two-dimensional array ultrasound probe (for example, Patent Document 1), but the contrast echo method has not yet been established. Not.

  When volume scanning is performed using a two-dimensional array ultrasonic probe, volume data is collected and a three-dimensional image can be displayed. In this volume scan, unlike the case of scanning a scan plane composed of a two-dimensional plane, the number of ultrasonic scanning lines to be transmitted and received is remarkably increased, so that the amount of data obtained is also increased. Therefore, by performing volume scanning, much information useful for image diagnosis can be obtained as compared with the case of scanning a two-dimensional scan plane.

JP 2000-333958 A

  However, when volume scanning is performed, the number of scanning lines is larger than that of scanning on a plane, and the number of frames of an image that can be visualized within a certain time is reduced. Therefore, when a volume scan is performed to generate a three-dimensional image, the volume rate is lower than when a two-dimensional scan surface is scanned to generate a two-dimensional image. As a result, the real-time property is deteriorated as compared with the case where a two-dimensional image is generated, and the three-dimensional image cannot be recognized as a moving image. As described above, since the real-time property is poor and it cannot be recognized as a moving image, it is difficult to search for a diagnostic part in the region of interest while viewing the generated three-dimensional image or to time the image collection.

  If the scanning line density of ultrasonic waves is reduced, the volume rate is increased and the real-time property is improved, but there is a problem that a detailed image cannot be obtained due to the reduction of the scanning line density.

  An object of the present invention is to solve the above-mentioned problems, and to provide an ultrasonic diagnostic apparatus that can visualize a tissue image with a real-time property and obtain a clear three-dimensional image for an ultrasonic contrast agent. And

The invention described in claim 1 includes a two-dimensional array ultrasonic probe in which ultrasonic transducers are two-dimensionally arranged, and a first scan mode for imaging a tissue image within a predetermined time interval. The two-dimensional array ultrasonic probe is repeatedly executed alternately with a second scan mode for imaging an ultrasound contrast agent, and in the first scan mode, a scan plane composed of a two-dimensional plane is A transmission / reception unit that causes a two-dimensional array ultrasound probe to scan, and in the second scan mode, causes the two-dimensional array ultrasound probe to scan in a three-dimensional space including a scan plane composed of the two-dimensional plane; Image data is generated based on the volume data obtained as a result of scanning the space, and 2 based on the data obtained by scanning the scan surface. An ultrasonic diagnostic apparatus comprising: an image generation unit that generates original tomographic image data; and a display control unit that displays an image based on the image data and a tomographic image based on the tomographic image data on a display unit It is.
According to a second aspect of the present invention, there is provided a two-dimensional array ultrasonic probe in which ultrasonic transducers are two-dimensionally arranged, and a first scan mode for imaging a tissue image within a predetermined time interval. The second scan mode for imaging the ultrasound contrast agent is switched, and a switching signal for repeating this switching is output, and the first scan mode and the second scan mode are output in accordance with the sequential control unit that outputs the switching signal. The two-dimensional array ultrasonic probe is repeatedly executed in the predetermined time interval, and the two-dimensional array ultrasonic probe generates a scan plane composed of a two-dimensional plane in the first scan mode. The probe is scanned, and in the second scan mode, the two-dimensional array is scanned in a three-dimensional space including a scan plane composed of the two-dimensional plane. A transmitter / receiver that causes the wave probe to scan, and volume data obtained as a result of scanning in the three-dimensional space, and two-dimensional data based on data obtained by scanning the scan plane. An ultrasonic diagnostic apparatus comprising: an image generation unit that generates tomographic image data; and a display control unit that displays an image based on the image data and a tomographic image based on the tomographic image data on a display unit. .
According to a third aspect of the present invention, in the second aspect of the present invention, the transmission / reception unit transmits an ultrasonic transmission sound pressure in the first scan mode to an ultrasonic transmission sound in the second scan mode. The two-dimensional array ultrasonic probe is scanned with a sound pressure lower than the pressure.
According to a fourth aspect of the present invention, in the invention according to the second or third aspect, the display control unit causes the display unit to simultaneously display an image based on the image data and the tomographic image. It is characterized by that.
According to a fifth aspect of the present invention, in the invention according to any one of the second to fourth aspects, in the first scan mode, the transmission / reception unit alternately forms two scan planes orthogonal to each other. A two-dimensional array ultrasonic probe is scanned.
According to a sixth aspect of the present invention, in the invention according to any one of the second to fifth aspects, the image generation unit is along a plane that is substantially orthogonal to a transmission / reception direction of the ultrasonic wave based on the volume data. The display control unit causes the display unit to display an image based on the image data along the plane and a tomographic image based on the tomographic image data.
According to a seventh aspect of the invention, in the sixth aspect of the invention, the image generation unit averages the image data along the plane in a predetermined thickness range along the transmission / reception direction, and The display control unit displays an image based on the averaged image data and a tomographic image based on the tomographic image data on the display unit.
According to an eighth aspect of the present invention, in the invention according to any one of the second to fifth aspects, the image generation unit includes the volume data in a predetermined line-of-sight direction as image data based on the volume data. The voxel data having the maximum voxel value is projected from the inside to generate maximum value projection image data.
According to a ninth aspect of the present invention, in the invention according to any one of the second to fifth aspects, the image generation unit includes the volume data in a predetermined line-of-sight direction as image data based on the volume data. The minimum value projection image data is generated by projecting voxel data having the minimum voxel value from the inside.
According to a tenth aspect of the present invention, in the invention according to any one of the second to fifth aspects, the image generation unit cuts the volume data at a predetermined cutting plane as image data based on the volume data. Thus, a cut surface is generated, and image data along the cut surface is generated.
According to an eleventh aspect of the present invention, in the invention according to any one of the second to tenth aspects, the display control unit is generated based on the volume data in a tomographic image based on the tomographic image data. A marker indicating the position of the image is superimposed and displayed on the display unit.
According to a twelfth aspect of the present invention, in the invention according to any one of the second to eleventh aspects, the display control unit adds a tomogram based on the tomographic image data to an image generated based on the volume data. A marker indicating the position of the image is superimposed and displayed on the display unit.
The invention according to claim 13 is the invention according to claim 1, wherein the transmitting / receiving unit executes the first scan mode within the predetermined time interval with respect to the two-dimensional array ultrasonic probe. The time for performing is longer than the time for executing the second scan mode.
According to a fourteenth aspect of the present invention, in the invention according to any one of the second to twelfth aspects, the sequential control unit executes the first scan mode within the predetermined time interval. A switching signal that is longer than the time during which the second scan mode is executed is output.
According to a fifteenth aspect of the present invention, in the first or thirteenth aspect of the invention, the transmission / reception unit causes the second scan mode to be executed in synchronization with the movement of the heart of the subject. It is characterized by.
The invention according to claim 16 is the invention according to any one of claims 2 to 12, or the invention according to claim 14, wherein the sequential control unit is synchronized with the movement of the heart of the subject. A switching signal from the scan mode to the second scan mode is output.
According to a seventeenth aspect of the present invention, in the first or thirteenth aspect of the present invention, the transmission / reception unit receives a trigger signal based on an ECG signal and performs the second scan mode according to the trigger signal. It is characterized by performing.
The invention according to claim 18 is the invention according to claim 17, wherein the transmission / reception unit performs the second scan mode and receives a new trigger signal after a predetermined time has elapsed since receiving the trigger signal. Each time, the second scan mode is performed by increasing the length of the predetermined time.
According to a nineteenth aspect of the present invention, in the invention according to any one of the second to twelfth aspects or the fourteenth aspect, the sequential control unit receives the trigger signal based on an ECG trigger signal. A switching signal from the scan mode to the second scan mode is output.
According to a twentieth aspect of the invention, in the invention according to the nineteenth aspect, the sequential control unit starts from the first scan mode after the elapse of a predetermined time after receiving the trigger signal as the switching signal. 2 to output a signal for switching to the second scan mode, and every time a new trigger signal is received, the predetermined time is lengthened to output a signal for switching from the first scan mode to the second scan mode. It is characterized by doing.
According to a twenty-first aspect of the present invention, in order to visualize a tissue image within a predetermined time interval in an ultrasonic diagnostic apparatus including a two-dimensional array ultrasonic probe in which ultrasonic transducers are two-dimensionally arranged. The first scan mode and the second scan mode for imaging the ultrasound contrast agent are alternately and repeatedly executed by the two-dimensional array ultrasound probe. In the first scan mode, two-dimensional The two-dimensional array ultrasonic probe is caused to scan a scan surface composed of a plane, and in the second scan mode, the two-dimensional array ultrasound probe is scanned within a three-dimensional space including the scan plane composed of the two-dimensional plane. By generating image data based on a transmission / reception function and volume data obtained as a result of scanning in the three-dimensional space, and scanning the scan surface An image generation function for generating two-dimensional tomographic image data based on the obtained data, and a display control function for displaying an image based on the image data and a tomographic image based on the tomographic image data on a display unit Is a control program for an ultrasonic diagnostic apparatus.

  According to the present invention, a clear three-dimensional image of the ultrasonic contrast agent can be obtained by scanning the three-dimensional space in the scan mode for imaging the ultrasonic contrast agent. On the other hand, in a scan mode for visualizing a tissue image, a two-dimensional scan surface is scanned to ensure real-time properties and obtain a tissue image as a moving image. As a result, by observing a tissue image in which real-time property is ensured, positioning within the region of interest becomes easy, and a clear three-dimensional image of the tissue infiltrated with the ultrasound contrast agent can be obtained. It becomes.

  An ultrasonic diagnostic apparatus according to an embodiment of the present invention will be described with reference to FIGS.

  The ultrasonic diagnostic apparatus 1 according to this embodiment is used in a state where an ultrasonic contrast agent is injected into a subject, and performs a contrast echo method. In particular, the ultrasound diagnostic apparatus 1 according to this embodiment performs a volume scan (3D scan) when imaging an ultrasound contrast agent, and includes a two-dimensional plane when imaging a tissue image in a subject. A two-dimensional scan plane is scanned (referred to as 2D scan). Then, the ultrasonic diagnostic apparatus 1 alternately displays volume contrast (3D scan) and 2D scan to display the ultrasound contrast agent as a three-dimensional image on the display unit, and the tissue image as a two-dimensional image. Display as a tomographic image on the display. As a result, blood vessels, tissues, and the like that have penetrated the ultrasound contrast agent are clearly imaged in three dimensions, and other tissue images are pursued in real time and are recognized as moving images by the operator. .

  When imaging an ultrasound contrast agent, it is necessary to perform transmission / reception of ultrasonic waves, signal processing, and the like in accordance with the characteristics of the ultrasound contrast agent. For example, a case where “levovist” is used as a general ultrasonic contrast agent will be described. Levovist is destroyed when it receives ultrasonic waves with a relatively high sound pressure (high intensity). And when a levobist destroys, a high frequency ultrasonic wave is generated. Therefore, when using Levovist, ultrasound is transmitted at a relatively high sound pressure (high intensity), and an image is generated based on the harmonic component of the received signal, thereby clearly imaging the ultrasound contrast agent. Can do. As a result, blood vessels and tissues that have penetrated the ultrasonic contrast agent can be visualized more clearly.

  However, when high sound pressure ultrasonic waves are received, Levovist will be destroyed, so if you continue to transmit high sound pressure ultrasonic waves, the ultrasound contrast agent (Levovist) that subsequently flows into blood vessels or tissues will continue to be destroyed. . As a result, since the ultrasonic contrast agent (levovist) cannot be sufficiently distributed to the region of interest, it is impossible to clearly visualize blood vessels, tissues, and the like into which the ultrasonic contrast agent (levovist) should permeate. Therefore, it is necessary to temporarily stop the transmission of ultrasonic waves with high sound pressure in order to sufficiently spread the region of interest without destroying the ultrasound contrast agent (levovist) that subsequently flows into blood vessels or tissues. is there. Thus, by stopping transmission / reception of ultrasonic waves with high sound pressure, it is possible to sufficiently spread the ultrasonic contrast agent (levovist) to the region of interest.

  However, while transmission / reception of high-sound-pressure ultrasonic waves is stopped, not only imaging of an ultrasound contrast agent (levovist) but also imaging of other tissues becomes impossible.

  Therefore, the ultrasonic diagnostic apparatus 1 according to this embodiment transmits and receives relatively low sound pressure (low intensity) ultrasonic waves while stopping transmission and reception of high sound pressure ultrasonic waves, thereby obtaining a tissue image. Visualize. At this time, by performing 2D scanning, a two-dimensional tomographic image pursuing real-time characteristics can be obtained.

  In this embodiment, an ultrasonic contrast agent and a tissue image are visualized using the above-described ultrasonic contrast agent (levovist). In order to visualize the ultrasound contrast agent, relatively high sound pressure ultrasound is transmitted and received. At that time, 3D scanning is performed, and three-dimensional image data of the ultrasound contrast agent is obtained based on the harmonic component of the received signal. On the other hand, ultrasonic waves with a relatively low sound pressure are transmitted and received while the 3D scan is temporarily stopped to spread the ultrasonic contrast agent to the region of interest. At that time, B-mode tomographic image data as two-dimensional image data of a tissue image is obtained by performing 2D scanning.

  By switching between 3D scanning and 2D scanning as described above, a clear three-dimensional image of a tissue or the like infiltrated with an ultrasound contrast agent can be obtained, and a B-mode tomographic image of the tissue image can be obtained as a moving image. Will be. In other words, a 3D scan provides a three-dimensional image of a tissue or the like infiltrated with an ultrasound contrast agent, and a 2D scan improves real-time characteristics and obtains a B-mode tomographic image of the tissue image as a moving image. It is done.

  Incidentally, the volume scan (3D scan) has a larger number of scanning lines than the 2D scan, and it takes much time to scan one three-dimensional scan region. For example, even if 2D scanning is performed with about 120 scanning lines and scanning is performed at a frame rate of about 50 frames / s, with 3D scanning, the scanning line density is reduced to 60 × 20 = 1200. Even if the scanning line is used, the rate is 5 volumes / second. Therefore, in the case of 3D scanning, the real-time property and time resolution of the moving image are significantly reduced.

  As in this embodiment, by performing 2D scanning with low sound pressure ultrasound during a scan mode in which 3D scanning is performed with high sound pressure ultrasound to visualize the ultrasound contrast agent, real-time characteristics are good, A B-mode tomogram with high temporal resolution is obtained.

  The ultrasonic diagnostic apparatus 1 according to this embodiment displays a B mode for displaying a B-mode tomogram, an M mode for displaying a temporal position change of a reflection source in the ultrasonic beam direction as a motion curve, and blood flow information. The apparatus is operable in accordance with a known mode such as a Doppler mode (pulse Doppler (PW) or continuous wave Doppler (CW)) and a CFM (Color Flow Mapping) mode for displaying blood flow information two-dimensionally.

(Constitution)
Hereinafter, the configuration of an ultrasonic diagnostic apparatus according to an embodiment of the present invention will be described with reference to FIG. FIG. 1 is a block diagram showing a schematic configuration of an ultrasonic diagnostic apparatus according to an embodiment of the present invention.

  The two-dimensional array ultrasonic probe 2 is a known two-dimensional array ultrasonic probe. The two-dimensional array ultrasonic probe 2 is a three-dimensional shape in which ultrasonic transducers are arranged in a matrix (lattice) shape, and ultrasonic waves are transmitted three-dimensionally by scanning, and spread radially from the probe surface. Data can be received as an echo signal. The two-dimensional array ultrasonic probe 2 can scan the two-dimensional scan plane and receive the two-dimensional data as an echo signal, and can scan the scan plane with an inclination.

  Here, the scannable region of the two-dimensional array ultrasonic probe 2 will be described with reference to FIG. FIG. 2 is a schematic diagram for explaining a region to be scanned and a scan plane by the ultrasonic diagnostic apparatus according to the embodiment of the present invention.

  As shown in FIG. 2, the three-dimensional scan region 10 that can be scanned by the two-dimensional array ultrasonic probe 2 is a three-dimensional space. The two-dimensional array ultrasonic probe 2 can also scan a two-dimensional plane within the three-dimensional scan region 10. That is, the two-dimensional array ultrasonic probe 2 can scan the two-dimensional scan surface 11 shown in FIG. 2 to obtain a two-dimensional image. The scan surface 11 is a scan surface directly below the two-dimensional array ultrasonic probe 2.

  The two-dimensional array ultrasonic probe 2 can also tilt the scan surface electronically with the scan surface 11 as the center. As described above, when the two-dimensional array ultrasonic probe 2 is used, it is possible to electronically tilt the two-dimensional scan plane without tilting the ultrasonic probe by hand.

  The transmission / reception unit 3 causes the two-dimensional array ultrasonic probe 2 to perform volume scan (3D scan) or 2D scan. Specifically, the transmission / reception unit 3 includes a transmission unit 31, a reception unit 32, and an in-probe scan control unit 33. The transmission unit 31 includes a known transmission unit, and supplies an electric signal to the two-dimensional array ultrasonic probe 2 to generate an ultrasonic wave. The receiving unit 32 includes a known receiving unit and receives a signal from the two-dimensional array ultrasonic probe 2.

  The intra-probe scan control unit 33 performs switching between volume scan (3D scan) and 2D scan in accordance with a 3D scan / 2D scan switching command sent from the control unit 9. The transmission unit 31 and the reception unit 32 cause the two-dimensional array ultrasonic probe 2 to execute a 3D scan or a 2D scan according to the switching of the scan. That is, the transmission / reception unit 3 causes the two-dimensional array ultrasonic probe 2 to scan either the three-dimensional scan region 10 or the two-dimensional scan surface 11 formed of a two-dimensional plane. The scan switching is performed in accordance with a scan switching command from the control unit 9.

  The transmission unit 31 includes a clock generation circuit, a transmission delay circuit, and a pulsar circuit (not shown). The clock generation circuit is a circuit that generates a clock signal that determines the transmission timing and transmission frequency of the ultrasonic signal. The transmission delay circuit is a circuit that performs transmission focus with a delay when transmitting ultrasonic waves. The pulsar circuit incorporates pulsars corresponding to the number of individual paths (channels) corresponding to each ultrasonic transducer, generates a drive pulse at a transmission timing multiplied by a delay, and generates each pulse of the two-dimensional array ultrasonic probe 2. It is designed to be supplied to the sonic transducer.

  The receiving unit 32 includes a preamplifier circuit, an A / D conversion circuit, and a reception delay / adder circuit (not shown). The preamplifier circuit amplifies the echo signal output from each ultrasonic transducer of the two-dimensional array ultrasonic probe 2 for each reception channel. The A / D converter circuit A / D converts the amplified echo signal. The reception delay / adder circuit gives a delay time necessary for determining the reception directivity to the echo signal after A / D conversion, and adds the delay time. By the addition, the reflection component from the direction according to the reception directivity is emphasized. The signal added by the receiving unit 32 is referred to as “RF data (or raw data)”. The RF data output from the receiving unit 32 is output to the signal processing unit 4.

  The signal processing unit 4 includes a so-called B-mode processing unit, visualizes echo amplitude information, and generates B-mode ultrasonic raster data from the echo signal. Specifically, the signal processing unit 4 includes a filter switching unit 41, a harmonic filter 42, a fundamental frequency filter 43, and a raster data generation unit 44. In this embodiment, only the B mode processing unit is described as the signal processing unit 4, but the signal processing unit 4 is not limited to the B mode processing unit. The signal processing unit 4 may include a color processing unit that performs imaging of echo Doppler information.

  The filter switching unit 41 sends the RF data output from the transmission / reception unit 3 to either the harmonic filter 42 or the fundamental frequency filter 43 in accordance with a 3D scan / 2D scan switching command sent from the control unit 9. Output. In this embodiment, since the 3D scan is performed when imaging the ultrasound contrast agent, the filter switching unit 41 outputs the RF data obtained when the 3D scan is performed to the harmonic filter 42. Further, since the 2D scan is performed when the tissue image is visualized, the filter switching unit 41 outputs the RF data obtained when the 2D scan is performed to the fundamental frequency filter 43.

  The harmonic filter 42 and the fundamental frequency filter 43 perform band-pass filter processing on the RF data transmitted from the transmission / reception unit 3. For example, the harmonic filter 42 extracts a harmonic component having a frequency twice as high as the transmission frequency (fundamental frequency) and outputs the harmonic component to the raster data generation unit 44. On the other hand, the fundamental frequency filter 43 extracts the component of the transmission frequency (fundamental frequency) and outputs it to the raster data generation unit 44.

  The echo signal from the ultrasound contrast agent includes harmonic components having frequencies of 2 times, 3 times,... The transmission frequency (fundamental frequency). Further, the frequency of the echo signal from the living tissue is equal to the transmission frequency. That is, the echo signal from the living tissue contains a lot of fundamental frequency components. Therefore, if the signal is passed through a band-pass filter that passes only twice the fundamental frequency, the echo signal from the living tissue is greatly attenuated. On the other hand, since the echo signal from the ultrasound contrast agent contains a harmonic component twice the fundamental frequency, the second harmonic component is extracted and imaged by passing through the bandpass filter. Can do.

  When performing a 3D scan to visualize the ultrasound contrast agent, the filter switching unit 41 outputs the RF data obtained by the 3D scan to the harmonic filter 42. Thereby, a filter process is performed using the band pass filter which takes out a harmonic component, and a harmonic component can be taken out. On the other hand, when 2D scanning is performed to visualize the tissue image, the filter switching unit 41 outputs the RF data obtained by the 2D scanning to the fundamental frequency filter 42. As a result, the filter processing is performed using the bandpass filter for extracting the fundamental frequency component, and the fundamental frequency component can be extracted.

  The raster data generation unit 44 generates B-mode ultrasonic raster data (data after signal processing) based on the signal output from the harmonic filter 42 or the fundamental frequency filter 43. Specifically, the raster data generation unit 44 detects an envelope from the filtered signal output from the harmonic filter 42 or the fundamental frequency filter 43, and performs logarithmic conversion on the detected data. Apply compression processing.

  Further, the signal processing unit 4 may include a known Doppler mode processing unit or CFM processing unit. The Doppler mode processing unit generates blood flow information by a pulse Doppler method (PW Doppler method) or a continuous wave Doppler method (CW Doppler method). The Doppler mode processing unit extracts the Doppler shift frequency component from the signal sent from the transmission / reception unit 4 by phase detection of the received signal in the blood flow observation point having a predetermined size, and further performs the FFT processing. Thus, a Doppler frequency distribution representing the blood flow velocity in the blood flow observation point having a predetermined size is generated. The CFM processing unit visualizes moving blood flow information and generates color ultrasonic raster data. Blood flow information includes information such as speed, dispersion, and power, and blood flow information is obtained as binarized information. Specifically, the CFM processing unit includes a phase detection circuit, an MTI filter, an autocorrelator, and a flow velocity / dispersion calculator. This CFM processing unit performs high-pass filter processing (MTI filter processing) for separating tissue signals and blood flow signals, and uses blood flow information such as blood flow velocity, dispersion, and power by autocorrelation processing. Ask for points. In addition, non-linear processing for reducing and reducing tissue signals may be performed.

  The DSC 5 (digital scan converter) reads the data after signal processing represented by the scanning line signal sequence output from the signal processing unit 4 and converts it into coordinate system data based on the spatial information (scan conversion processing). . That is, the scanning method is converted by reading out in synchronization with the standard television scanning so that the signal sequence synchronized with the ultrasonic scanning can be displayed on the display unit 8 of the television scanning method.

  When the 3D scan is executed, the DSC 5 generates voxel data (volume data) based on the signal-processed data output from the signal processing unit 4, and sends the voxel data (volume data) to the image processing unit 6. Output. Further, the DSC 5 does not perform any processing, and the image processing unit 6 may convert the raster data after the signal processing into voxel data. When the 2D scan is executed, the DSC 5 generates B-mode tomogram data based on the signal-processed data output from the signal processor 4, and sends the B-mode tomogram data to the display controller 7. Output.

  The image processing unit 6 performs image processing on voxel data (volume data) output from the DSC 5 when a volume scan (3D scan) is performed. For example, the image processing unit 6 performs volume rendering (hereinafter sometimes referred to as VR processing) on voxel data (volume data) to generate three-dimensional image data. This volume rendering is a three-dimensional image display method widely used in medical image diagnostic apparatuses such as X-ray CT apparatuses and MRI apparatuses other than ultrasonic diagnostic apparatuses.

  In this volume rendering, a predetermined gaze direction (projection direction of projected light) is determined for voxel data (volume data), ray tracing processing is performed from any gaze, and voxel values (luminance values, etc.) on the gaze The three-dimensional image data is generated by three-dimensionally extracting the organ and the like by outputting the integral value and the weighted cumulative addition value to the image pixels on the projection plane.

  In addition to the volume rendering, the image processing unit 6 can also perform maximum / minimum value projected image processing, MPR image processing, and the like.

  An image generated by calculating the maximum value among the voxel values penetrated by the projection ray and storing the obtained maximum value in the pixel is referred to as a maximum value projection image (MIP image). An image generated by calculating a minimum value from among the voxel values and storing the obtained minimum value in a pixel is referred to as a minimum value projection image (MINIP image).

  An image of an arbitrary cross section generated by a cut surface obtained by cutting voxel data (volume data) at a specific plane (cut plane) is referred to as an MPR (Multi Plane Construction) image.

  The content of the image processing in the image processing unit 6 can be arbitrarily determined by the operator.

  The display control unit 7 receives the B-mode tomogram data output from the DSC 6 and causes the display unit 8 to display a B-mode tomogram based on the B-mode tomogram data. The display control unit 7 receives 3D image data, MPR image data, and the like output from the image processing unit 6 and causes the display unit 8 to display a 3D image, an MPR image, and the like based on the data. Further, the display control unit 7 causes the display unit 8 to simultaneously display a B-mode tomographic image obtained by 2D scanning, a three-dimensional image obtained by 3D scanning, and the like. As a result, a B-mode tomographic image representing a tissue image and a three-dimensional image representing an ultrasonic contrast agent, in which real-time characteristics are pursued, are displayed on the display unit 8.

  The display unit 8 includes a monitor such as a CRT or a liquid crystal display, and a B-mode tomographic image, a three-dimensional image, or an MPR image is displayed on the monitor screen.

  The control unit 9 is connected to each part of the ultrasonic diagnostic apparatus 1 and controls each part of the ultrasonic diagnostic apparatus 1. In this embodiment, the control unit 9 outputs a scan switching command to the intra-probe scan control unit 33 and the filter switching unit 41 in accordance with a predetermined sequence. The controller 9 corresponds to the “sequential controller” of the present invention.

  A timer 91 is connected to the controller 9. This timer 91 is used, for example, when measuring the timing of outputting a scan switching command. The timer 91 measures a predetermined time, and the control unit 9 outputs a scan switching command to the intra-probe scan control unit 33 and the filter switching unit 41 every predetermined time.

  An electrocardiographic waveform can also be used as the timing for outputting a scan switching command. In this case, an electrocardiograph (not shown) is installed outside the ultrasonic diagnostic apparatus 1. This electrocardiograph acquires an electrocardiographic waveform (ECG signal) of the subject. The electrocardiograph is provided with a signal generator that generates a trigger signal (referred to as an ECG trigger signal) when an R wave is detected. The ECG trigger signal generated by the signal generator is an ultrasonic wave. It is output to the control unit 9 in the diagnostic apparatus 1. An electrocardiograph may be installed inside the ultrasonic diagnostic apparatus 1.

  When receiving an ECG trigger signal from an electrocardiograph (not shown), the control unit 9 outputs a scan switching command to the intra-probe scan control unit 33 and the filter switching unit 41. In this embodiment, upon receiving the ECG trigger signal, the control unit 9 outputs a 3D scan execution command to the intra-probe scan control unit 33 and the filter switching unit 41. The intra-probe scan control unit 33 switches the 2D scan to the 3D scan in accordance with the scan switching command. Further, the filter switching unit 41 outputs the RF data output from the transmission / reception unit 3 to the harmonic filter 42 in accordance with the scan switching command. In this way, the scan may be switched according to the ECG trigger signal based on the electrocardiogram waveform.

  A storage device (not shown) composed of a memory such as a ROM or a RAM is connected to the control unit 9. The storage device stores a control program for controlling each part of the ultrasound diagnostic apparatus 1. The control unit 9 is configured by, for example, a CPU, and controls each unit of the ultrasonic diagnostic apparatus 1 by executing a control program stored in the storage device, so that the function of the transmission / reception unit 3, the function of the signal processing unit 4, The function of the DSC 5, the function of the image processing unit 6, and the function of the display control unit 7 are executed.

  The ultrasonic diagnostic apparatus 1 is provided with an operation unit (not shown). The operation unit is an input device for performing various settings relating to ultrasonic transmission / reception conditions. Information or a command input by the operation unit is output to the control unit 9, and the control unit 9 performs processing according to the command. For example, the operator designates the projection direction (line-of-sight direction) of the projection light with respect to the voxel data (volume data) using the operation unit. Specifically, the operation unit includes a pointing device such as a joystick or a trackball, a switch, various buttons, a mouse, a keyboard, or a TCS (Touch Command Screen).

(Function)
Next, the operation of the ultrasonic diagnostic apparatus 1 according to the embodiment of the present invention will be described. The ultrasonic diagnostic apparatus 1 according to this embodiment performs the following first operation, second operation, third operation, and fourth operation.

(First operation)
First, the first operation of the ultrasonic diagnostic apparatus 1 according to the embodiment of the present invention will be described with reference to FIG. FIG. 3 is a flowchart showing in sequence the first operation of the ultrasonic diagnostic apparatus according to the embodiment of the present invention.

  In the first operation, the control unit 9 outputs a scan switching command to the intra-probe scan control unit 33 and the filter switching unit 41 at a preset time interval. This time interval is determined in advance by the operator and is stored in advance in a storage device (not shown) connected to the control unit 9. When receiving a time measurement start command from the control unit 9, the timer 91 measures the time, and when a preset time has elapsed, the control unit 9 sends the scan switching command to the intra-probe scan control unit 33 and the filter. Output to the switching unit 41. The time interval can be changed to an arbitrary time interval by the operator.

  First, an ultrasound contrast agent (levovist) is injected into the subject. The control unit 9 outputs a 2D scan execution command to the intra-probe scan control unit 33 and the filter switching unit 41. Further, the control unit 9 resets the timer 91 and outputs a time measurement start command to the timer 91. Thereby, the timer 91 starts measuring the time after the 2D scan is started.

  When the intra-probe scan control unit 33 receives a 2D scan execution command from the control unit 9, the transmission unit 31 and the reception unit 32 are arranged on the two-dimensional array ultrasonic probe 2 in a two-dimensional plane according to the 2D scan execution command. The dimension scan plane is scanned (step S01). For example, the two-dimensional scanning surface 11 immediately below the two-dimensional array ultrasonic probe 2 shown in FIG. 2 is scanned. At this time, the transmission unit 31 causes the two-dimensional array ultrasonic probe 2 to transmit a relatively low sound pressure ultrasonic wave. By transmitting ultrasonic waves with a relatively low sound pressure, the ultrasonic contrast agent (levovist) can penetrate into blood vessels and tissues without being destroyed.

  The reception unit 32 performs amplification, A / D conversion, and delay / addition processing on the echo signal output from the two-dimensional array ultrasonic probe 2 to generate RF data, and the filter switching unit 41 of the signal processing unit 4. Output to.

  When the filter switching unit 41 receives the RF data from the receiving unit 32, the filter switching unit 41 outputs the RF data to the fundamental frequency filter 43 in accordance with the 2D scan execution command from the control unit 9. The fundamental frequency filter 43 performs band pass filter processing on the RF data, extracts a fundamental frequency component, and outputs the fundamental frequency component to the raster data generation unit 44. The raster data generation unit 44 generates B-mode ultrasonic raster data based on the data output from the fundamental frequency filter 43 and outputs the B-mode ultrasonic raster data to the DSC 5. The DSC 5 performs scan conversion processing on the B-mode ultrasonic raster data to generate B-mode tomographic image data that can be displayed on the television scanning display unit 8. When receiving the B-mode tomographic image data from the DSC 5, the display control unit 7 displays the B-mode tomographic image on the monitor screen of the display unit 8.

  The transmission / reception unit 3 continues 2D scanning until the scan switching command is output from the control unit 9, the signal processing unit 4 generates B-mode ultrasound raster data, and the DSC 5 generates B-mode tomographic image data. To do. Then, the display control unit 7 causes the display unit 8 to display a B-mode tomographic image as a two-dimensional image. Since the 2D scan has a high frame rate, the B-mode tomogram displayed on the display unit 8 is displayed as a moving image. As a result, a B-mode tomographic image pursuing real-time characteristics is displayed.

  Then, the timer 91 measures the time from the start of the 2D scan, and when a preset time has elapsed (step S02, Yes), the control unit 9 sends a scan switching command to the in-probe scan control unit 33 and the filter switching unit. 41 is output. In this case, since the 2D scan has been performed first, the control unit 9 outputs a 3D scan execution command to the intra-probe scan control unit 33 and the filter switching unit 41.

  When the intra-probe scan control unit 33 receives a 3D scan execution command from the control unit 9, the transmission unit 31 and the reception unit 32 cause the 2D array ultrasonic probe 2 to scan the 3D space according to the 3D scan execution command. (Step S03). For example, the three-dimensional scan area 10 shown in FIG. 2 is scanned. At this time, the transmission unit 31 transmits a relatively high sound pressure ultrasonic wave to the two-dimensional array ultrasonic probe 2. By transmitting ultrasonic waves having a relatively high sound pressure, the ultrasonic contrast agent (levovist) is destroyed, and high-band ultrasonic waves are generated.

  The receiving unit 32 performs delay / addition processing on the echo signal output from the two-dimensional array ultrasonic probe 2 to generate RF data, and outputs the RF data to the filter switching unit 41 of the signal processing unit 4.

  When the filter switching unit 41 receives the RF data from the receiving unit 32, the filter switching unit 41 outputs the RF data to the harmonic filter 42 in accordance with the 3D scan execution command from the control unit 9. The harmonic filter 42 performs band-pass filter processing on the RF data, extracts the harmonic component, and outputs it to the raster data generation unit 44. The raster data generation unit 44 generates B-mode ultrasonic raster data based on the data output from the harmonic filter 42 and outputs it to the DSC 5. The DSC 5 generates voxel data (volume data) based on the B-mode ultrasound raster data, and outputs the voxel data (volume data) to the image processing unit 6.

  The image processing unit 6 generates three-dimensional image data, MPR image data, and the like by performing volume rendering processing, MPR processing, and the like on the voxel data. Upon receiving the three-dimensional image data output from the image processing unit 6, the display control unit 7 causes the display unit 8 to display a three-dimensional image. Since this three-dimensional image is created based on the harmonic component generated by the ultrasonic contrast agent (levovist), the ultrasonic contrast agent (levobist) is imaged three-dimensionally. As a result, blood vessels, tissues and the like permeated with the ultrasound contrast agent (levovist) can be clearly imaged three-dimensionally.

  When the timer 91 measures a preset time, the control unit 9 outputs a scan switching command to the intra-probe scan control unit 33 and the filter switching unit 41 in order to stop the 3D scan and execute the 2D scan. . This time, a 2D scan execution command is output. Thereby, 3D scanning is stopped (step S04), and 2D scanning is performed again (step S01).

  Thus, by switching between 3D scanning and 2D scanning at regular intervals, a three-dimensional image of the ultrasound contrast agent can be obtained, and a tissue image can be obtained as a two-dimensional moving image. .

  Even if the set time does not elapse, when one volume scan is completed, the control unit 9 outputs a 2D scan execution command to the intra-probe scan control unit 33 and the filter switching unit 41. Also good. In this case, the control unit 9 is provided with a counter (not shown) that counts the number of 3D scans. When the counter counts one volume scan, the control unit 9 outputs a scan switching command (2D scan execution command) to the intra-probe scan control unit 33 and the filter switching unit 41.

  As described above, a clear three-dimensional image of an ultrasonic contrast agent can be obtained by performing volume scanning (3D scanning) with relatively high sound pressure ultrasonic waves. Furthermore, during the volume scan (3D scan), the 2D scan is performed with an ultrasonic wave having a relatively low sound pressure, thereby improving the real-time property and obtaining a tissue image as a moving image. The ultrasound contrast agent (levovist) is destroyed by performing a volume scan (3D scan), but by temporarily stopping the 3D scan, the ultrasound contrast agent (levovist) can penetrate into the region of interest. It is possible to display and observe a state in which the ultrasonic contrast agent (levovist) penetrates as a three-dimensional image. Then, while the 3D scan is temporarily stopped, the tissue image is obtained as a moving image by performing the 2D scan with a relatively low sound pressure ultrasonic wave. That is, it is possible to infiltrate the ultrasonic contrast agent (levovist) to the region of interest while performing the 2D scan with the ultrasonic wave having a relatively low sound pressure.

  In addition, when performing 2D scanning at a relatively low sound pressure, so-called biplane scanning may be performed. This biplane scan is a scan for obtaining B-mode tomographic images orthogonal to each other by alternately scanning two-dimensional scan planes orthogonal to each other. This biplane scan will be described with reference to FIGS. 4 and 5. FIG. FIG. 4 is a schematic diagram for explaining a scan plane in biplane scanning. FIG. 5 is a diagram showing an image obtained by scanning.

  Here, a scan plane in the case of performing a biplane scan will be described with reference to FIG. As shown in FIG. 4, the transmission / reception unit 3 causes the two-dimensional array ultrasonic probe 2 to alternately scan the scan surface 11a and the scan surface 11b. The scan surface 11a and the scan surface 11b are surfaces orthogonal to each other. Thereby, B-mode tomographic image data on the scan surface 11a and B-mode tomographic image data on the scan surface 11b are obtained.

  When the transmission / reception unit 3 receives a 2D scan execution command from the control unit 9, the transmission / reception unit 3 causes the two-dimensional array ultrasonic probe 2 to perform biplane scanning with ultrasonic waves having a relatively low sound pressure, and B modes of scan planes orthogonal to each other. Tomographic image data is collected and a B-mode tomographic image is displayed on the monitor screen 8 a of the display unit 8. For example, as shown in FIG. 4, the transmitting / receiving unit 3 causes the two-dimensional array ultrasonic probe 2 to scan a two-dimensional scan surface 11a and a scan surface 11b. As a result of this scan, the DSC 5 generates B-mode tomographic image data of the scan surface 11a and B-mode tomographic image data of the scan surface 11b.

  For example, the display control unit 7 displays the collected B-mode tomographic image 12a and the B-mode tomographic image 12b orthogonal to the B-mode tomographic image 12a on the monitor screen 8a of the display unit 8 shown in FIG. The B-mode tomogram 12a is a two-dimensional image obtained by scanning the scan plane 11a shown in FIG. 4, and the B-mode tomogram 12b is obtained by scanning the scan plane 11b shown in FIG. It is a two-dimensional image.

  When the preset time elapses as described above, the control unit 9 outputs a 3D scan execution command to the intra-probe scan control unit 33 and the filter switching unit 41. As a result, a 3D scan is performed with relatively high sound pressure ultrasonic waves, and a three-dimensional image of the ultrasonic contrast agent is obtained.

  In this way, when 2D scanning is performed, biplane scanning is performed and B-mode tomographic images that are orthogonal to each other are displayed, so that a tissue image can be grasped in three dimensions and interest in penetrating the ultrasound contrast agent is obtained. It becomes possible to accurately grasp the position of the region.

  In addition, when imaging an ultrasound contrast agent (levovist), instead of performing volume rendering in the image processing unit 6 to generate three-dimensional image data, MPR processing is performed to obtain image data of an arbitrary cross section (MPR image). Data) may be generated. Specifically, the image processing unit 6 performs MPR processing on voxel data (volume data) obtained by 3D scanning to generate MPR image data of an arbitrary cross section.

  As described above, when the 3D scan is performed, voxel data (volume data) is generated in the DSC 5, and the voxel data is output from the DSC 5 to the image processing unit 6. The image processing unit 6 cuts a specific plane designated by the operator with respect to the voxel data, and generates image data (MPR image data) of the cut surface. The cut surface is designated by the operator using an operation unit (not shown). This cutting plane can be arbitrarily designated. The MPR image data generated in this way is output from the image processing unit 6 to the display control unit 7. The display control unit 7 causes the display unit 8 to simultaneously display the MPR image representing the ultrasound contrast agent and the B-mode tomographic image obtained by performing the 2D scan.

  Further, the image processing unit 6 may generate a new image (hereinafter referred to as a “MPR image with thickness”) by adding a plurality of MPR images in the thickness direction of the MPR image and averaging them. That is, the MPR image with thickness is generated by adding and averaging pixel values within the range of the specified width in the thickness direction of the specified cut surface. In addition to the cut surface, the width in the thickness direction is designated by the operator, and the width can be arbitrarily designated.

  When imaging an ultrasound contrast agent, the two-dimensional scan plane 11 directly under the two-dimensional array ultrasound probe 2 is used instead of generating volume data by performing volume rendering in the image processing unit 6. The image data of a two-dimensional plane orthogonal to (may be referred to as “C-plane image data” hereinafter) may be generated and displayed. Here, a two-dimensional plane orthogonal to the two-dimensional scan plane 11 will be described with reference to FIG. FIG. 6 is a schematic diagram for explaining the position of the C plane in the three-dimensional scan region.

  As shown in FIG. 6, a two-dimensional plane orthogonal to the two-dimensional scan plane 11 immediately below the two-dimensional array ultrasonic probe 2 is defined as a C plane. The C plane is substantially orthogonal to the transmission / reception direction of the ultrasonic waves. Here, as an example, three C planes are set, and the C plane 13a, the C plane 13b, and the C plane 13c are set in order from the two-dimensional array ultrasonic probe 2. The designation of the C plane is designated by an operator using an operation unit (not shown). For example, by designating the distance from the two-dimensional array ultrasonic probe 2, the position of the C plane is designated.

  As described above, when 3D scanning is performed, voxel data (volume data) is generated from the DSC 5, and the voxel data is output from the DSC 5 to the image processing unit 6. The image processing unit 6 cuts the C plane designated by the operator for the voxel data, and generates image data (C plane image data) of the C plane. For example, when the C plane 13a, the C plane 13b, and the C plane 13c are designated by the operator, the image processing unit 6 generates image data (C plane image data) along the C plane based on the voxel data. To do.

  The C plane image data generated in this way is output from the image processing unit 6 to the display control unit 7. The display control unit 7 causes the display unit 8 to simultaneously display the C-plane image representing the ultrasound contrast agent and the B-mode tomographic image obtained by performing the 2D scan.

  Also, the image processing unit 6 adds a plurality of C-plane images in the thickness direction of the C-plane and further averages them to generate a new image (hereinafter referred to as a “thick C-plane image”). good. This addition averaging process will be described with reference to FIG. FIG. 7 is a schematic diagram for explaining addition averaging processing of the position of the C plane in the three-dimensional scan region and the C plane image in the thickness direction.

  For example, a case where a C-plane image with thickness centered on the C-plane 13b is generated will be described. As shown in FIG. 7, when the C surface 13b is designated by the operator and a predetermined width is designated by the operator in the thickness direction around the C surface 13b, the image processing unit 6 is designated. In addition, by adding and averaging pixel values within the specified width range in the thickness direction of the C surface 13b, a thick C surface image centered on the C surface 13b is generated.

  A display example of the C-plane image representing the ultrasound contrast agent generated as described above and the B-mode image obtained by the 2D scan is shown in FIG. FIG. 8 is a diagram illustrating a display example of a B-mode slice and the C plane image.

  As shown in FIG. 8, the display control unit 7 monitors the C plane image 14a on the C plane 13a, the C plane image 14b on the C plane 13b, and the C plane image 14c on the C plane 13c as the C plane images. It is displayed on the screen 8a. This C-plane image is an image obtained by imaging an ultrasonic contrast agent.

  Further, the display control unit 7 displays the B-mode image on the monitor screen 8a of the display unit 8 simultaneously with the C-plane image. As described above, when the biplane scan is performed as the 2D scan, the display control unit 7 causes the display unit 8 to display the B-mode tomographic image 12a and the B-mode tomographic image 12b that are orthogonal to each other. Since the B-mode tomographic image is an image obtained by performing 2D scanning, the operator can recognize it as a moving image.

  The display control unit 7 can also display markers on the B-mode tomographic images 12a and 12b that indicate the positions of the C-plane images 14a, 14b, and 14c, that is, the positions of the C-planes 13a, 13b, and 13c. When the position of the C plane (distance from the two-dimensional array ultrasonic probe 2) is specified using an operation unit (not shown), information indicating the position of the C plane is output to the display control unit 7. When receiving the information indicating the position of the C plane, the display control unit 7 causes the display unit 8 to display a marker indicating the position of the C plane on the B-mode tomographic image. As shown in FIG. 8, for example, in order to indicate the position of the C plane 13c, the display control unit 7 displays a marker 15 indicating the position of the C plane 13c on the B mode tomographic image 12a, and on the B mode tomographic image 12b. A marker 16 indicating the position of the C plane 13c is displayed. For the C surface 13a and the C surface 13b as well as the C surface 13c, markers indicating their positions are displayed on the B mode tomographic image 12a and the B mode tomographic image 12b.

  Similarly, the display controller 7 can also display markers indicating the positions of the B-mode tomographic images 12a and 12b, that is, the positions of the two-dimensional scan planes 11a and 11b, on the C-plane images 14a, 14b, and 14c. As shown in FIG. 8, for example, in order to indicate the position of the B-mode tomographic image 12a, that is, the position of the two-dimensional scan plane 11a, the display control unit 7 displays the two-dimensional scan plane on the C plane images 14a, 14b, and 14c. A marker 17 indicating the position of 11a is displayed. Further, in order to indicate the position of the B-mode tomographic image 12b, that is, the position of the two-dimensional scan plane 11b, the display control unit 7 displays the marker 18 indicating the position of the two-dimensional scan plane 11b on the C plane images 14a, 14b, and 14c. Is displayed. Since the two-dimensional scan planes 11a and 11b are orthogonal to each other, the markers 17 and 18 are also displayed orthogonal to each other.

  When the C-plane image data with thickness is generated, the display control unit 7 determines that the C-plane image with thickness around the C-plane 13a, the C-plane image with thickness around the C-plane 13b, and the C-plane A thick C-plane image centered on 13c is displayed on the display unit 8.

  Further, the display control unit 7 may display the markers 15 and 16 indicating the positions of the C planes 13a, 13b and 13c on the B-mode tomographic images 12a and 12b, and simultaneously display the marker indicating the thickness width. good. As shown in FIG. 8, the display control unit 7 displays the marker 16 indicating the C surface 13c on the B-mode tomographic image 12b, and includes markers 16a and 16b indicating the width in the thickness direction around the C surface 13c. Display. Similarly to the C surface 13c, the C surface 13a and the C surface 13b are also displayed with markers indicating the width in the thickness direction on the B mode tomographic image 12a and the B mode tomographic image 12b.

  As described above, by displaying the marker indicating the position of the C-plane image or the marker indicating the position of the B-mode tomographic image, the position of the C-plane image in the depth direction can be easily grasped. By displaying both the C-plane image and the B-mode tomographic image, it is possible to easily grasp the position of the site where the ultrasound contrast agent is injected.

  Further, when imaging an ultrasound contrast agent, instead of performing volume rendering in the image processing unit 6 to generate a three-dimensional image, a MIP image or a MINIP image may be generated. Specifically, the image processing unit 6 performs maximum value / minimum value projection processing on voxel data (volume data) obtained by 3D scanning to generate MIP image data or MINIP image data.

  As described above, when the 3D scan is performed, voxel data (volume data) is generated in the DSC 5, and the voxel data is output from the DSC 5 to the image processing unit 6. For the voxel data, the image processing unit 6 calculates the maximum value or the minimum value from the voxel values (on the line-of-sight direction) that are penetrated by the projection rays, and stores the obtained maximum value or minimum value in the pixel. Thus, the maximum value (minimum value) projection image data is generated. The MIP image data or MINIP image data generated in this way is output from the image processing unit 6 to the display control unit 7. The display control unit 7 causes the display unit 8 to simultaneously display the MIP image or the MINIP image and the B-mode tomographic image obtained by performing the 2D scan.

  When performing the maximum value or minimum value projection processing, the projection direction (line-of-sight direction) or the like is set by the operator specifying the projection direction (line-of-sight direction) and the voxel range with an operation unit (not shown). .

(Second operation)
Next, the second operation of the ultrasonic diagnostic apparatus 1 according to the embodiment of the present invention will be described with reference to FIGS. FIG. 9 is a flowchart sequentially illustrating the second operation of the ultrasonic diagnostic apparatus according to the embodiment of the present invention. FIG. 10 is a diagram for explaining the switching timing of the volume scan (3D scan) and the 2D scan according to the ECG trigger signal.

  In this second operation, the ultrasound diagnostic apparatus 1 performs scanning by switching between 3D scanning and 2D scanning in accordance with an ECG trigger signal output from an electrocardiograph (not shown). That is, by performing scanning while switching the scan in synchronization with the ECG signal, an image of the ultrasound contrast agent in the same time phase can be obtained in each scan.

  In the second operation, as in the first operation, an ultrasonic contrast agent (levovist) that is destroyed when receiving an ultrasonic wave having a relatively high sound pressure is used.

  First, an ultrasound contrast agent (levovist) is injected into the subject. The control unit 9 outputs a 2D scan execution command to the intra-probe scan control unit 33 and the filter switching unit 41. When the intra-probe scan control unit 33 receives a 2D scan execution command from the control unit 9, the transmission unit 31 and the reception unit 32 apply a relatively low sound pressure to the two-dimensional array ultrasonic probe 2 according to the 2D scan execution command. The two-dimensional scan plane is scanned with sound waves (step S10).

  The receiving unit 32 generates RF data by performing a delay / addition process on the echo signal output from the two-dimensional array ultrasonic probe 2 and outputs the RF data to the filter switching unit 41 of the signal processing unit 4.

  When the filter switching unit 41 receives the RF data from the receiving unit 32, the filter switching unit 41 outputs the RF data to the fundamental frequency filter 43 in accordance with the 2D scan execution command output from the control unit 9. The fundamental frequency filter 43 extracts the fundamental frequency component and outputs it to the raster data generation unit 44. The raster data generation unit 44 generates B-mode ultrasonic raster data based on the data output from the fundamental frequency filter 43 and outputs it to the DSC 5. The DSC 5 performs a scan conversion process on the B-mode ultrasonic raster data to generate B-mode tomographic image data. The display control unit 7 causes the display unit 8 to display a B-mode tomogram based on the B-mode tomogram data.

  The transmission / reception unit 3 continues the 2D scan until a scan switching command is output from the control unit 9. Since the 2D scan has a high frame rate, the display unit 8 displays a B-mode tomographic image as a moving image.

  Then, when an electrocardiograph (not shown) collects an electrocardiographic signal (ECG signal) of the subject and an R wave is detected as shown in FIG. 10, a signal generator ( (Not shown) generates an ECG trigger signal and outputs the ECG trigger signal to the control unit 9.

  When receiving the ECG trigger signal from the electrocardiograph (step S11), the control unit 9 outputs a scan change command to the intra-probe scan control unit 33 and the filter switching unit 41. In this case, since the 2D scan has been performed first, the control unit 9 outputs a 3D scan execution command to the intra-probe scan control unit 33 and the filter switching unit 41.

  When the intra-probe scan control unit 33 receives a 3D scan execution command from the control unit 9, the transmission unit 31 and the reception unit 32 scan the 3D space in the 2D array ultrasonic probe 2 according to the 3D scan execution command. (Step S12). At this time, the transmission unit 31 transmits a relatively high sound pressure ultrasonic wave to the two-dimensional array ultrasonic probe 2. By transmitting an ultrasonic wave having a relatively high sound pressure, the ultrasonic contrast agent (levovist) is destroyed and a high-band ultrasonic wave is generated. The receiving unit 32 performs delay / addition processing on the echo signal output from the two-dimensional array ultrasonic probe 2 to generate RF data, and outputs the RF data to the filter switching unit 41 of the signal processing unit 4.

  When the filter switching unit 41 receives the RF data from the receiving unit 32, the filter switching unit 41 outputs the RF data to the harmonic filter 42 in accordance with the 3D scan execution command from the control unit 9. The harmonic filter 42 performs band-pass filter processing on the RF data, extracts the harmonic component, and outputs it to the raster data generation unit 44. The raster data generation unit 44 generates B-mode ultrasonic raster data based on the data output from the harmonic filter 42 and outputs it to the DSC 5. The DSC 5 generates voxel data (volume data) based on the B-mode ultrasound raster data, and outputs the voxel data (volume data) to the image processing unit 6.

  The image processing unit 6 generates three-dimensional image data, MPR image data, and the like by performing volume rendering processing, MPR processing, and the like on the voxel data. Upon receiving the three-dimensional image data output from the image processing unit 6, the display control unit 7 causes the display unit 8 to display a three-dimensional image. Since this three-dimensional image is created based on the harmonic component generated by the ultrasonic contrast agent (levovist), the ultrasonic contrast agent (levobist) is imaged three-dimensionally. As a result, blood vessels, tissues and the like permeated with the ultrasound contrast agent (levovist) can be clearly imaged three-dimensionally.

  When the timer 91 measures a preset time, the control unit 9 outputs a scan switching command to the intra-probe scan control unit 33 and the filter switching unit 41 in order to stop 3D scanning and execute 2D scanning. . This time, a 2D scan execution command is output. Thereby, 3D scanning is stopped (step S13), and 2D scanning is performed again (step S10).

  Similarly to the first operation, when one volume scan is completed even if the set time has not elapsed, the control unit 9 sends a scan switching command to the in-probe scan control unit 33 and the filter switching unit 41. May be output. In this case, a counter is provided to count the number of 3D scans, and when the counter counts one volume scan, the control unit 9 outputs a scan switching command.

  When the control unit 9 receives the ECG trigger signal again (step S11), a 3D scan is executed to visualize the ultrasound contrast agent (step S12). As shown in FIG. 10, every time an R wave is detected and an ECG trigger signal is output to the control unit 9, a 3D scan is performed, and the 2D scan is executed during the 3D scan.

  As described above, by executing the 3D scan according to the ECG trigger signal, a three-dimensional image of the ultrasound contrast agent in the same time phase is obtained. That is, a three-dimensional image of the same time phase such as a blood vessel or tissue infiltrated with an ultrasound contrast agent (levovist) is obtained. By performing 2D scanning between 3D scans, a tissue image can be obtained as a two-dimensional moving image. Further, while performing the 2D scanning, an ultrasonic contrast agent (levobist) penetrates to the region of interest. It becomes possible to make it. Thereby, it is possible to display and observe the state in which the ultrasonic contrast agent penetrates as a three-dimensional image.

  In the second operation, similarly to the first operation, biplane scanning may be performed as 2D scanning, and B-mode tomographic images orthogonal to each other may be displayed on the display unit 8. When voxel data (volume data) is obtained by performing 3D scanning, instead of performing volume rendering on the voxel data to generate a three-dimensional image, a C-plane image, MIP image, or MINIP image Or the like may be generated and displayed on the display unit 8.

(Third operation)
Next, a third operation of the ultrasonic diagnostic apparatus 1 according to the embodiment of the present invention will be described with reference to FIGS. FIG. 11 is a flowchart showing, in order, the third operation of the ultrasonic diagnostic apparatus according to the embodiment of the present invention. FIG. 12 is a diagram for explaining the switching timing of the volume scan (3D scan) and the 2D scan according to the ECG trigger signal.

  In the third operation, the ultrasound diagnostic apparatus 1 performs scanning by switching between 3D scanning and 2D scanning in accordance with an ECG trigger signal output from an electrocardiograph (not shown). Also, the 3D scan is performed by shifting the timing of the 3D scan performed last time and the timing of the 3D scan performed this time by a predetermined time. Thereby, the three-dimensional image of the ultrasonic contrast agent in a different time phase can be obtained each time.

  In the third operation, as in the first operation, an ultrasonic contrast agent (levovist) that is destroyed when an ultrasonic wave having a relatively high sound pressure is received is used.

  First, an ultrasound contrast agent (levovist) is injected into the subject. The control unit 9 outputs a 2D scan execution command to the intra-probe scan control unit 33 and the filter switching unit 41. As a result, the transmission / reception unit 3 causes the two-dimensional array ultrasonic probe 2 to scan the two-dimensional scan surface with a relatively low sound pressure ultrasonic wave (step S20).

  Similar to the first operation and the second operation described above, when 2D scanning is performed, the RF data is filtered by the fundamental frequency filter 43, and then the raster data generation unit 44 exceeds the B mode. Sound wave raster data is generated, DS mode 5 generates B mode tomographic image data, and the B mode tomographic image is displayed on the display unit 8. The transmission / reception unit 3 continues the 2D scan until a scan switching command is output from the control unit 9. Thereby, the B-mode tomogram is displayed on the display unit 8 as a moving image.

An electrocardiograph (not shown) collects the electrocardiographic waveform (ECG signal) of the subject, and when an R wave is detected as shown in FIG. 12, an ECG trigger signal is output to the control unit 9. Here, the ECG trigger signal output first is referred to as ECG trigger signal I _{1 for} convenience.

Control unit 9 receives the ECG trigger signal I ₁ from the electrocardiograph (step S21), and outputs the scan changing instruction within the scan control unit 33 and the filter switching unit 41 probe. In this case, the control unit 9 outputs a 3D scan execution command. As a result, the transmission / reception unit 3 causes the two-dimensional array ultrasonic probe 2 to scan the three-dimensional scan region 10 with relatively high sound pressure ultrasonic waves (step S22).

  Similar to the first operation and the second operation described above, when 3D scanning is performed, the RF data is filtered by the harmonic filter 42, and then the raster data generation unit 44 exceeds the B mode. Sonic raster data is generated, voxel data (volume data) is generated by the DSC 5, and the voxel data (volume data) is output to the image processing unit 6. The image processing unit 6 generates three-dimensional image data, MPR image data, and the like by performing volume rendering processing or the like on the voxel data. As a result, a three-dimensional image representing the ultrasonic contrast agent is displayed on the display unit 8.

  When the timer 91 measures a preset time, the control unit 9 outputs a scan switching command to the intra-probe scan control unit 33 and the filter switching unit 41 in order to stop the 3D scan and execute the 2D scan. . This time, a 2D scan execution command is output. As a result, the 3D scan is stopped (step S23), the 2D scan is executed (step S23), and the B-mode tomographic image is displayed on the display unit 8 as a moving image.

  As in the first operation, the controller 9 sends a 2D scan execution command to the in-probe scan controller 33 and the filter after performing one volume scan even before the set time has elapsed. You may output to the switch part 41. FIG. In this case, when the counter counts the number of 3D scans and the counter counts one volume scan, the control unit 9 sends a scan switching command (2D scanning execution command) to the intra-probe scan control unit 33 and the filter switching unit. 41 is output.

When the next R wave is detected by the electrocardiograph, an ECG trigger signal is output to the control unit 9 again. Here, the ECG trigger signal output second is referred to as an ECG trigger signal I _{2 for} convenience.

When the controller 9 receives the ECG trigger signal I ₂ (step 24), the control unit 9 without immediately outputs scan switching instruction to continue the 2D scan receiver portion 3. Control unit 9 receives the ECG trigger signal _{I 2,} and resets the timer 91, thereby measuring the time the timer 91. When the timer 91, the control unit 9 measures the time from receiving the ECG trigger signal I _2, passes a preset time .DELTA.t, the control unit 9 scans change command (implementation instructions 3D scanning) Is output to the intra-probe scan control unit 33 and the filter switching unit 41. The time δt is determined in advance by the operator and is stored in advance in a storage device (not shown) connected to the control unit 9. Last, since the output immediately scan changing instruction receiving ECG trigger signal I ₁ (Working instructions 3D scan), this time, the time δt only by shifting the time phase (delay by) performing 3D scanning.

  When a 3D scan execution command is output from the control unit 9, the transmission / reception unit 3 causes the two-dimensional array ultrasonic probe 2 to scan the three-dimensional scan region 10 with a relatively high sound pressure ultrasonic wave (step S25).

  Similar to the first operation and the second operation described above, when a 3D scan is performed, 3D image data or the like is generated by the image processing unit 6, and a 3D image representing an ultrasonic contrast agent is displayed on the display unit 8. Etc. are displayed.

The three-dimensional image displayed at this time is an image obtained by scanning when the time δt has elapsed since the R wave was detected. Therefore, the three-dimensional image obtained by scanning according to the ECG trigger signal I ₁ and the three-dimensional image obtained by scanning when the time δt has elapsed have different collected time phases and are shifted by the time δt. Yes (being late) Thus, by performing 3D scanning at a time phase different from the previous time phase, it is possible to display and observe a three-dimensional image of a different time phase.

  When the timer 91 measures a preset time, the control unit 9 outputs a scan switching command (2D scan execution command) to the transmission / reception unit 3 or the like. In addition, when one volume scan is counted by the counter, the control unit 9 may output a 2D scan execution command to the transmission / reception unit 3 or the like. Thereby, the 2D scan is executed (step S23), and the B-mode tomogram is displayed on the display unit 8 as a moving image.

When the next R wave is detected by the electrocardiograph, an ECG trigger signal is output to the control unit 9 again. Here, the ECG trigger signal output third is referred to as ECG trigger signal I _{3 for} convenience.

When the controller 9 receives the ECG trigger signal I ₃ (step S24), and without immediately outputs a scan switching instruction to continue the 2D scan receiver portion 3. The timer 91 measures the time after the control unit 9 receives the ECG trigger signal I ₃ , and when the time (2δt) elapses, the control unit 9 scans the scan change command (3D scan execution command) within the probe. The data is output to the control unit 33 and the filter switching unit 41.

Last, because it outputs scan change instruction when the elapsed time .DELTA.t after receiving ECG trigger signal I _2, this time, performs 3D scan delays the time phase only more time .DELTA.t (step S25). That is, when the time (2δt) has elapsed after receiving the ECG trigger signal I ₃ , the control unit 9 outputs a scan change command (3D scan execution command) to the intra-probe scan control unit 33 and the filter switching unit 41.

  As described above, every time the ECG trigger signal is received from the electrocardiograph, the control unit 9 delays the time by δt and outputs a scan change command (3D scan execution command) to the transmission / reception unit 3 or the like. That is, the control unit 9 delays the timing for outputting the scan change command (3D scan execution command) every time a new ECG trigger signal is received. As a result, the time phase for performing the 3D scan is delayed by time δt, so that a three-dimensional image having a different time phase can be obtained each time. Then, Step S23 to Step S25 are repeated.

  In the third operation, similarly to the first operation, biplane scanning may be performed as 2D scanning, and B-mode tomographic images orthogonal to each other may be displayed on the display unit 8. When voxel data (volume data) is obtained by performing 3D scanning, instead of performing volume rendering on the voxel data to generate a three-dimensional image, a C-plane image, MIP image, or MINIP image Or the like may be generated and displayed on the display unit 8.

  In the second operation and the third operation, one 3D scan is performed during one heartbeat, but one 3D scan may be performed during two or more heartbeats. For example, the number of executions of the 3D scan may be adjusted according to the penetration state of the ultrasonic contrast agent (levovist). When ultrasound contrast agent (levovist) is difficult to penetrate, 3D scan is performed at a rate of once during a plurality of heartbeats, so that the ultrasound contrast agent (levovist) can penetrate to the region of interest without being destroyed. it can.

(Fourth operation)
Next, a fourth operation of the ultrasonic diagnostic apparatus 1 according to the embodiment of the present invention will be described with reference to FIG. FIG. 13 is a diagram for explaining the switching timing of the volume scan (3D scan) and the 2D scan according to the ECG trigger signal.

  In the fourth operation, unlike the ultrasonic contrast agent (levobis) used in the first to third operations, a low MI (Mechanical Index) ultrasonic contrast agent is used. This low-MI ultrasonic contrast agent can provide a high contrast effect and a high-luminance image even when high-sonic pressure ultrasonic waves are not irradiated. Therefore, in the fourth operation, unlike the above-described first to third operations, scanning is performed with a relatively low sound pressure ultrasonic wave. As a result, since the ultrasonic contrast agent is not destroyed even when receiving an ultrasonic wave, a 3D scan can be performed a plurality of times during one heartbeat.

  In the fourth operation, the ultrasound diagnostic apparatus 1 performs 3D scanning and 2D scanning according to an ECG trigger signal output from an electrocardiograph (not shown), similarly to the second operation and the third operation. Switch to scan.

  First, a low MI ultrasound contrast agent is injected into a subject. The control unit 9 outputs a 2D scan execution command to the intra-probe scan control unit 33 and the filter switching unit 41. When the intra-probe scan control unit 33 receives a 2D scan execution command from the control unit 9, the transmission unit 31 and the reception unit 32 apply a relatively low sound pressure to the two-dimensional array ultrasonic probe 2 according to the 2D scan execution command. The two-dimensional scan plane is scanned with the ultrasonic wave. Then, the B-mode tomographic image of the tissue image is displayed on the display unit 8 as in the first to third operations. The transmission / reception unit 3 continues the 2D scan until a scan switching command is output from the control unit 9. Thereby, the B-mode tomogram is displayed on the display unit 8 as a moving image.

  When an R wave is detected by an electrocardiograph (not shown) and an ECG trigger signal is output to the control unit 9, the control unit 9 sends a scan change command to the intra-probe scan control unit 33 and the filter switching unit 41. Output. In this case, since the 2D scan has been performed first, the control unit 9 outputs a 3D scan execution command to the intra-probe scan control unit 33 and the filter switching unit 41. As a result, the transmission / reception unit 3 causes the two-dimensional array ultrasonic probe 2 to scan the three-dimensional scan region 10 with ultrasonic waves having a relatively low sound pressure.

  Similar to the first to third operations described above, 3D scanning is performed to generate three-dimensional image data and the like in the image processing unit 6, and the display unit 8 represents a low MI ultrasound contrast agent 3. Dimensional images etc. are displayed.

  When the timer 91 measures a preset time, the control unit 9 outputs a scan switching command (2D scan execution command) to the transmission / reception unit 3 or the like. Thereby, 2D scanning is performed and a B-mode tomogram is displayed on the display unit 8 as a moving image. When the counter counts one volume scan, the control unit 9 may output a 2D scan execution command to the transmission / reception unit 3 or the like.

  Then, when performing the 2D scan, the timer 91 measures the time, and when a preset time elapses, the control unit 9 sends a scan switching command (3D scan execution command) to the in-probe scan control unit 33. And output to the filter switching unit 41.

  Since the low-MI ultrasound contrast agent is not destroyed even when it is irradiated with ultrasound, the ultrasound contrast agent can penetrate into the region of interest even if the time interval of the 3D scan is shortened. Therefore, unlike the scan performed in the first to third operations, the 3D scan can be performed a plurality of times during one heartbeat. As described above, even if 3D scanning is performed a plurality of times during one heartbeat, the ultrasonic contrast agent is not destroyed, so that the region of interest can be penetrated. By performing 3D scanning a plurality of times during one heartbeat, it is possible to observe a state in which the ultrasound contrast agent penetrates the blood vessel as a three-dimensional image. Further, by performing the 2D scan during the 3D scan, the tissue image can be displayed on the display unit 8 as a moving image.

  When the control unit 9 receives the next ECG trigger signal, the control unit 9 outputs a 3D scan execution command to the intra-probe scan control unit 33 and the filter switching unit 41 to perform the 3D scan. Thereafter, the above scan is repeated.

  In the fourth operation, similarly to the first operation, biplane scanning may be performed as 2D scanning, and B-mode tomographic images orthogonal to each other may be displayed on the display unit 8. When voxel data (volume data) is obtained by performing 3D scanning, instead of performing volume rendering on the voxel data to generate a three-dimensional image, a C-plane image, MIP image, or MINIP image Or the like may be generated and displayed on the display unit 8.

  In the second to fourth operations, the timing of performing the 3D scan is measured according to the ECG trigger signal. However, the timing of performing the 3D scan according to the shape change of the B-mode tomographic image obtained by performing the 2D scan. Can also be measured.

  For example, when a heart is imaged, a B-mode tomogram of the heart can be displayed as a moving image on the display unit 8 by performing a 2D scan. The image processing unit 6 receives B-mode tomogram data sequentially collected, and obtains one cycle of heart motion from the change in the shape of the B-mode tomogram. Then, the control unit 9 outputs a 3D scan execution command to the transmission / reception unit 3 and the like every cycle. In this way, the operation cycle of the heart can be obtained from a shape change such as a B-mode slice without using an ECG signal, and a three-dimensional image of an ultrasound contrast agent is collected in synchronization with the motion of the heart. It becomes possible.

1 is a block diagram showing a configuration of an ultrasonic diagnostic apparatus according to an embodiment of the present invention. It is a schematic diagram for demonstrating the area | region and scanning surface which the ultrasound diagnosing device which concerns on embodiment of this invention scans. It is a flowchart which shows 1st operation | movement of the ultrasound diagnosing device which concerns on embodiment of this invention in order. It is a schematic diagram for demonstrating the scanning surface in a biplane scan. It is a figure which shows the image obtained by performing a scan. It is a schematic diagram for demonstrating the position of the C surface in a three-dimensional scan area | region. It is a schematic diagram for explaining the addition averaging process of the position of the C plane in the three-dimensional scan region and the C plane image in the thickness direction. It is a figure which shows the example of a display of a B mode tomogram and C surface image. It is a flowchart which shows 2nd operation | movement of the ultrasound diagnosing device which concerns on embodiment of this invention in order. It is a figure for demonstrating the switching timing of a volume scan (3D scan) and 2D scan according to an ECG trigger signal. It is a flowchart which shows the 3rd operation | movement of the ultrasound diagnosing device which concerns on embodiment of this invention in order. It is a figure for demonstrating the switching timing of a volume scan (3D scan) and 2D scan according to an ECG trigger signal. It is a figure for demonstrating the switching timing of a volume scan (3D scan) and 2D scan according to an ECG trigger signal.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 Ultrasonic diagnostic apparatus 2 Two-dimensional array ultrasonic probe 3 Transmission / reception part 4 Signal processing part 5 DSC
6 Image processing unit 7 Display control unit 8 Display unit 9 Control unit 31 Transmission unit 32 Reception unit 33 In-probe scan control unit 41 Filter switching unit 42 Harmonic filter 43 Fundamental frequency filter 44 Raster data generation unit 91 Timer

Claims (21)

A two-dimensional array ultrasonic probe in which ultrasonic transducers are two-dimensionally arranged;
Within the predetermined time interval, a first scan mode for imaging a tissue image and a second scan mode for imaging an ultrasound contrast agent are alternately applied to the two-dimensional array ultrasound probe . In the first scan mode, the scan plane consisting of a two-dimensional plane is scanned by the two-dimensional array ultrasonic probe, and in the second scan mode, the scan plane consisting of the two-dimensional plane is included. A transmitting / receiving unit that causes the two-dimensional array ultrasonic probe to scan in a three-dimensional space;
An image generation unit that generates image data based on volume data obtained as a result of scanning in the three-dimensional space, and generates two-dimensional tomographic image data based on data obtained by scanning the scan surface When,
A display control unit for displaying an image based on the image data and a tomographic image based on the tomographic image data on a display unit;
An ultrasonic diagnostic apparatus comprising: A two-dimensional array ultrasonic probe in which ultrasonic transducers are two-dimensionally arranged;
A switching signal for switching between a first scan mode for imaging a tissue image and a second scan mode for imaging an ultrasound contrast agent within a predetermined time interval and repeating this switching, A sequential control unit to output ,
According to the cutting place signal, the first scan mode and the said two-dimensional array ultrasonic probe and a second scan mode are alternately within the predetermined time interval, is repeatedly executed, in the first scan mode The 2D array ultrasonic probe scans a scan plane composed of a two-dimensional plane, and in the second scan mode, the two-dimensional array ultrasonic probe is scanned in a three-dimensional space including the scan plane composed of the two-dimensional plane. A transmission / reception unit to be scanned,
An image generation unit that generates image data based on volume data obtained as a result of scanning in the three-dimensional space, and generates two-dimensional tomographic image data based on data obtained by scanning the scan surface When,
A display control unit for displaying an image based on the image data and a tomographic image based on the tomographic image data on a display unit;
An ultrasonic diagnostic apparatus comprising: The transmitting / receiving unit causes the two-dimensional array ultrasonic probe to scan by setting the ultrasonic transmission sound pressure in the first scan mode to a lower sound pressure than the ultrasonic transmission sound pressure in the second scan mode. The ultrasonic diagnostic apparatus according to claim 2 . The ultrasonic diagnostic apparatus according to claim 2 , wherein the display control unit causes the display unit to simultaneously display an image based on the image data and the tomographic image. The transceiver unit, wherein in the first scan mode, according to any one of the preceding claims 2, characterized in that to scan the two-dimensional array ultrasonic probe alternately two scanning surfaces which are orthogonal to each other Ultrasound diagnostic equipment. The image generation unit generates image data along a plane substantially orthogonal to a transmission / reception direction of the ultrasonic wave based on the volume data;
6. The display control unit according to claim 2 , wherein the display control unit causes the display unit to display an image based on the image data along the plane and a tomographic image based on the tomographic image data. Ultrasonic diagnostic equipment. The image generation unit adds and averages image data along the plane in a predetermined thickness range along the transmission / reception direction,
The ultrasonic diagnostic apparatus according to claim 6, wherein the display control unit displays an image based on the averaged image data and a tomographic image based on the tomographic image data on the display unit. The image generation unit projects voxel data having a maximum voxel value from the volume data on a predetermined line-of-sight direction as image data based on the volume data, and generates maximum value projection image data. The ultrasonic diagnostic apparatus according to any one of claims 2 to 5. The image generation unit generates minimum value projection image data by projecting voxel data having a minimum voxel value from the volume data in a predetermined line-of-sight direction as image data based on the volume data. The ultrasonic diagnostic apparatus according to any one of claims 2 to 5. The image generation unit generates a cut surface by cutting the volume data at a predetermined cutting plane as image data based on the volume data, and generates image data along the cutting plane. The ultrasonic diagnostic apparatus according to claim 2 . The display controller, a tomographic image based on the tomographic image data, from claim 2, characterized in that displayed on the display unit by superimposing a marker indicating the position of the image generated on the basis of the volume data The ultrasonic diagnostic apparatus according to claim 10. The display controller, the image generated on the basis of the volume data, claim 2, characterized in that to be displayed on the display unit by superimposing a marker indicating the position of the tomographic image based on the tomographic image data The ultrasonic diagnostic apparatus according to claim 11. The transmission / reception unit executes, for the two-dimensional array ultrasonic probe, the time for executing the first scan mode is longer than the time for executing the second scan mode within the predetermined time interval. The ultrasonic diagnostic apparatus according to claim 1 . The sequential control unit outputs a switching signal in which the time for executing the first scan mode is longer than the time for executing the second scan mode within the predetermined time interval. The ultrasonic diagnostic apparatus according to any one of claims 2 to 12 . The transceiver unit, the ultrasonic diagnostic apparatus according to claim 1 or 13, characterized in that to execute the second scanning mode in synchronism with the movement of the heart of the subject. 13. The sequential control unit outputs a switching signal from the first scan mode to the second scan mode in synchronization with the motion of the subject's heart. Or the ultrasonic diagnostic apparatus according to claim 14 . The transmitting and receiving unit receives a trigger signal based on the ECG signal, the ultrasonic diagnostic apparatus according to claim 1 or 13, characterized in that the second scan mode according to the trigger signal.   The transmission / reception unit performs the second scan mode after a predetermined time has elapsed after receiving the trigger signal, and increases the length of the predetermined time each time a new trigger signal is received. The ultrasonic diagnostic apparatus according to claim 17, wherein a mode is performed. The sequential control unit of claims 12 to claim 2, characterized in that for outputting a switched with signals to the second scan mode and receives a trigger signal based on the ECG trigger signal from the first scan mode The ultrasonic diagnostic apparatus of any one or Claim 14 . The sequential control unit outputs a switching signal from the first scan mode to the second scan mode and receives a new trigger signal after a predetermined time has elapsed since the trigger signal was received as the switching signal. whenever the ultrasonic diagnostic apparatus according to claim 19, characterized in that for outputting a switched with signals to the second scan mode from the predetermined time said by increasing the length the first scan mode. In an ultrasonic diagnostic apparatus equipped with a two-dimensional array ultrasonic probe in which ultrasonic transducers are arranged two-dimensionally,
Within a predetermined time interval, a first scan mode for imaging a tissue image and a second scan mode for imaging an ultrasound contrast agent are alternately repeated on the two-dimensional array ultrasound probe. In the first scan mode, the scan plane consisting of a two-dimensional plane is scanned by the two-dimensional array ultrasonic probe, and in the second scan mode, the scan plane consisting of the two-dimensional plane is included 3 A transmission / reception function for causing the two-dimensional array ultrasonic probe to scan in a dimensional space;
Image generation function for generating image data based on volume data obtained as a result of scanning in the three-dimensional space, and generating two-dimensional tomographic image data based on data obtained by scanning the scan plane When,
A display control function for displaying an image based on the image data and a tomographic image based on the tomographic image data on a display unit;
A control program for an ultrasonic diagnostic apparatus, characterized in that

Images