JP2010220875A - Ultrasonic diagnostic device, and control program therefor - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide an ultrasonic diagnostic device capable of executing contrast echo imaging of real time performance higher compared with that in the prior art, and a control program therefor. <P>SOLUTION: This ultrasonic diagnostic device selects a flash scan priority mode or a monitoring scan priority mode, in response to a situation, by a CHI function using three-dimensional trigger scan. The three-dimensional trigger scan is executed in flash scan, when selecting the flash scan priority mode, and a flash image is obtained at a high volume rate. Meanwhile, the three-dimensional trigger scan is executed in monitoring scan, when selecting the monitoring scan priority mode, and a monitoring image is obtained at a high volume rate. <P>COPYRIGHT: (C)2011,JPO&INPIT

Description

  The present invention relates to an ultrasonic diagnostic apparatus for performing contrast harmonic imaging (CHI) for administering a contrast agent to a subject and imaging a state in which the contrast agent flows into a diagnostic site in the subject, and the like. It relates to the control method.

  Ultrasound diagnosis can be performed repeatedly by simply touching the ultrasound probe from the body surface, and the heart beats and fetal movements can be obtained in real time, and it is highly safe. . In addition, it can be said that this is a simple diagnostic method in which the scale of the system is smaller than other diagnostic devices such as X-rays, CT, and MRI, and inspection can be easily performed while moving to the bedside. Ultrasound diagnostic devices used in this ultrasound diagnosis vary depending on the types of functions that they have, but small ones that can be carried with one hand have been developed. Thus, there is no influence of exposure, and it can be used in obstetrics and home medical care.

  In recent years, intravenous administration-type ultrasound contrast agents have been commercialized and contrast echography has been performed. This technique is intended to evaluate blood flow dynamics by, for example, injecting an ultrasonic contrast agent from a vein in an examination of the heart and liver to enhance the blood flow signal. In many contrast agents, microbubbles function as a reflection source. Due to the sensitive nature of the bubbles, the bubbles are broken by the mechanical action of ultrasonic irradiation at a normal diagnostic level, and as a result, the signal intensity from the scan plane decreases. Therefore, in order to observe the dynamic state of the recirculation in real time, it is necessary to relatively reduce the destruction of bubbles due to scanning, such as imaging by ultrasonic transmission with low sound pressure. Such imaging with low sound pressure ultrasonic transmission also reduces the signal / noise ratio (S / N ratio), and various signal processing methods have been devised to compensate for this.

  Further, taking advantage of the feature that the contrast medium bubbles are destroyed as described above, the following method has been devised. That is, (a) observe the dynamics of the contrast agent filling the scan section under ultrasonic transmission of low sound pressure, (b) switch the irradiation sound pressure to a high sound pressure, and within the section (strictly within the irradiation volume) The contrast agent in (1) is destroyed, and (c) the state of bubbles flowing into the cross-section again is observed. This method is called a replenishment method (see, for example, Patent Document 1). The scanning mode using ultrasonic waves with low acoustic pressure (a) and (c) is called a recirculation mode (or monitoring mode), and the scanning mode using ultrasonic waves with high acoustic pressure (b) is called a flash mode. In particular, in recent years, volume data is obtained by performing ultrasonic scanning (monitoring scan) in the monitoring mode and ultrasonic scanning (flash scan) in the flash mode for a three-dimensional region including the diagnostic region, and obtaining a three-dimensional image. Display technology has been developed.

Japanese Patent Laid-Open No. 11-155858

  However, contrast echo imaging using a conventional ultrasonic diagnostic apparatus has the following problems, for example.

  First, when shooting a three-dimensional area by flash scanning and displaying the area in real time, a three-dimensional area called a normal live volume is scanned with high sound pressure ultrasound while moving the scanning section. . For this reason, the time difference between different ultrasonic scanning cross sections becomes large, and the contrast agent cannot be instantaneously present in the three-dimensional region, so that there is a possibility of lacking real-time properties. Further, even when a three-dimensional area is photographed by monitoring scanning and the area is to be displayed in real time, the normal live volume is scanned with low sound pressure ultrasonic waves while moving the scanning section. Accordingly, the time difference between different ultrasonic scanning sections becomes large, and the volume rate is limited. As a result, even in the monitoring mode, the real-time property is lacking.

  The present invention has been made in view of the above circumstances, and an object thereof is to provide an ultrasonic diagnostic apparatus and an ultrasonic diagnostic apparatus control program capable of executing contrast echo imaging having higher real-time characteristics than conventional ones.

  In order to achieve the above object, the present invention takes the following measures.

  According to the first aspect of the present invention, a first ultrasonic scan using an ultrasonic wave having a sound pressure that does not substantially destroy a contrast agent is applied to a diagnostic site that performs a periodic motion of a subject, and contrast An ultrasonic diagnostic apparatus that performs a second ultrasonic scanning using a sound pressure that substantially destroys the agent, and includes m (m For each of the sub-regions, the first ultrasonic scan or the second ultrasonic scan is performed n times (n is an integer of 2 or more), so that each sub-region over time Data acquisition means for acquiring n pieces of subvolume data in association with time phase information indicating the time phase of the periodic motion, and each of the n pieces of subvolume data over time and the time phase information, The diagnosis at each time phase of the periodic motion based on Data generating means for generating full volume data concerning position, an ultrasonic diagnostic apparatus characterized by comprising a.

  According to a fourth aspect of the present invention, there is provided a first ultrasonic scan using an ultrasonic wave having a sound pressure that does not substantially destroy a contrast agent with respect to a diagnostic site that performs a periodic motion of a subject, and a contrast M, which is spatially continuous and includes at least a part of the diagnostic region in a computer built in the ultrasonic diagnostic apparatus that performs the second ultrasonic scanning using a sound pressure that substantially destroys the agent. By performing the first ultrasonic scan or the second ultrasonic scan n times (n is an integer of 2 or more) for each of the sub-regions (m is an integer of 2 or more), each of the sub-regions A data acquisition function for acquiring n subvolume data over time in association with time phase information indicating a time phase of the periodic motion, and each of the n subvolume data over time and the time Each of the periodic motions based on the phase information An ultrasonic diagnostic apparatus control program, characterized in that to realize a data generation function of generating a full volume data relating to the diagnosis region in the phase.

  As described above, according to the present invention, it is possible to realize an ultrasonic diagnostic apparatus and an ultrasonic diagnostic apparatus control program capable of executing contrast echo imaging having higher real-time characteristics than conventional.

FIG. 1 shows a block diagram of an ultrasonic diagnostic apparatus 1 according to this embodiment. FIG. 2 is a diagram showing the relationship between the sub-volumes v1, v2, v3, and v4, which are scanning ranges by the main scanning process, and the full volume V (= v1 + v2 + v3 + v4) configured by the sub-volumes v1 to v4. FIG. 3 is a conceptual diagram of a CHI scan sequence in the flash scan priority mode. FIG. 4 is a diagram illustrating sub-volumes v1 to v4 acquired in the three-dimensional trigger scan method in which the triggered scan cycle T = 6 heartbeats. FIG. 5 is a conceptual diagram of a CHI scan sequence in the monitoring scan priority mode. FIG. 6 is a conceptual diagram of a CHI scan sequence in the monitoring scan priority mode according to the modification. FIG. 7 is a flowchart showing a flow of processing according to the CHI function using the three-dimensional triggered scan. FIG. 8 is a diagram illustrating an example of a display form of an ultrasonic image acquired by CHI processing using a three-dimensional triggered scan.

  Hereinafter, first and second embodiments of the present invention will be described with reference to the drawings. In the following description, components having substantially the same function and configuration are denoted by the same reference numerals, and redundant description will be given only when necessary.

  FIG. 1 shows a block diagram of an ultrasonic diagnostic apparatus 1 according to this embodiment. As shown in the figure, the ultrasonic diagnostic apparatus 1 includes an ultrasonic probe A, an apparatus main body B, and an interface unit C.

  The ultrasonic probe A generates ultrasonic waves based on a drive signal from the apparatus main body B, converts a reflected wave from the subject into an electric signal, a matching layer provided in the piezoelectric vibrator, It has a backing material that prevents the propagation of ultrasonic waves from the piezoelectric vibrator to the rear. When ultrasonic waves are transmitted from the ultrasonic probe A to the subject P, the transmitted ultrasonic waves are successively reflected by the discontinuous surface of the acoustic impedance of the body tissue and received by the ultrasonic probe A as an echo signal. . The amplitude of this echo signal depends on the difference in acoustic impedance at the discontinuous surface that is supposed to be reflected. In addition, the echo when the transmitted ultrasonic pulse is reflected by the moving blood flow or the surface of the heart wall depends on the velocity component in the ultrasonic transmission direction of the moving body due to the Doppler effect, and the frequency Receive a shift.

  The ultrasonic probe A is capable of performing ultrasonic scanning on a three-dimensional region of a subject. Therefore, the ultrasonic probe A has a configuration in which a transducer is mechanically swung along a direction orthogonal to the arrangement direction to ultrasonically scan a three-dimensional region, or a two-dimensionally arranged two-dimensional vibration element. It has a configuration in which a three-dimensional region is ultrasonically scanned by electrical control. When the former configuration is adopted, since the three-dimensional scanning of the subject is performed by an oscillation circuit, the examiner automatically acquires a plurality of two-dimensional tomographic images only by bringing the probe body into contact with the subject. be able to. The exact distance between the sections can also be detected from the controlled rocking speed. When the latter configuration is adopted, in principle, a three-dimensional region can be ultrasonically scanned in the same time as acquiring a conventional two-dimensional tomographic image.

  The interface unit C includes a monitor 11 and an input device 13.

  Based on the video signal from the apparatus main body B, the monitor 11 uses in vivo morphological information (B mode image), blood flow information (average velocity image, dispersion image, power image, etc.), and a combination thereof as an image. indicate.

  The input device 13 is connected to the apparatus main body B, and includes various switches, buttons, tracks for incorporating various instructions, conditions, regions of interest (ROI) setting instructions, various image quality condition setting instructions, etc. from the operator into the apparatus main body B. It has a ball, mouse, keyboard, etc. For example, when the operator operates the end button or the FREEZE button of the input device 13, the transmission / reception of the ultrasonic wave is ended, and the ultrasonic diagnostic apparatus is temporarily stopped.

  In addition, the input device 13 uses the CHI using the three-dimensional triggered scan, the number of sub-volumes, the repeated period of the triggered scan, the scanning line density, the frame rate, the gain, the frequency, the dynamic range, the filter setting, the depth of field, the focus It has a switch for setting / changing the position.

  The apparatus main body B includes an ultrasonic transmission unit 21, an ultrasonic reception unit 23, a B-mode processing unit 25, a Doppler processing unit 27, an image generation unit 28, a first memory 29, a voxel conversion unit 31, a data analysis unit 33, an image A synthesis unit 35, a storage unit 37, a control processor (CPU) 39, and an interface unit 41 are provided.

  The ultrasonic transmission unit 21 includes a trigger generation circuit, a delay circuit, a pulsar circuit, and the like (not shown). In the pulsar circuit, a rate pulse for forming a transmission ultrasonic wave is repeatedly generated at a predetermined rate frequency fr Hz (period: 1 / fr second). Further, in the delay circuit, a delay time necessary for focusing the ultrasonic wave into a beam shape for each channel and determining the transmission directivity is given to each rate pulse. The trigger generation circuit applies a drive pulse to the probe A at a timing based on this rate pulse.

  The ultrasonic receiving unit 23 has an amplifier circuit, an A / D converter, an adder and the like not shown. The amplifier circuit amplifies the echo signal captured via the ultrasonic probe A for each channel. In the A / D converter, a delay time necessary for determining the reception directivity is given to the amplified echo signal, and thereafter, an addition process is performed in the adder. By this addition, the reflection component from the direction corresponding to the reception directivity of the echo signal is emphasized, and a comprehensive beam for ultrasonic transmission / reception is formed by the reception directivity and the transmission directivity.

  The B-mode processing unit 25 receives the echo signal from the receiving unit 23, performs logarithmic amplification, envelope detection processing, and the like, and generates data in which the signal intensity is expressed by brightness. This data is transmitted to the image generation unit 28 and is displayed on the monitor 11 as a B-mode image in which the intensity of the reflected wave is represented by luminance.

  The Doppler processing unit 27 performs frequency analysis on velocity information from the echo signal received from the receiving unit 23, extracts blood flow, tissue, and contrast agent echo components due to the Doppler effect, and obtains blood flow information such as average velocity, dispersion, and power. Ask for multiple points.

  The image generation unit 28 generates an ultrasound diagnostic image as a display image based on various data received from the B-mode processing unit 25, the Doppler processing unit 27, and the voxel conversion unit 31. Further, the image generation unit 28 performs predetermined image processing such as volume rendering using the volume data received from the data analysis unit 33, and generates a three-dimensional image or the like. The data before entering the image generation unit 28 may be referred to as “raw data”.

  The first memory 29 stores the raw data from the B-mode processing unit 25 or the Doppler processing unit 27 for each frame.

  The voxel conversion unit 31 uses the raw data for each frame recorded in the first memory 29 to generate a plurality of subvolume data.

  The data analysis unit 33 stores a plurality of sub-volume data generated in the voxel conversion unit 31 for each time phase. Further, the data analysis unit 33 performs temporal association (a temporal phase association regarding a periodic motion) between a plurality of sub-volumes based on the temporal phase information in the CHI using a three-dimensional triggered scan described later. Further, the data analysis unit 33 generates full volume data related to the imaging target area by spatially connecting a plurality of sub-volumes associated with time phases.

  The image synthesizing unit 35 synthesizes the image received from the image generating unit 28 together with character information of various parameters, scales, etc., and outputs it as a video signal to the monitor 11.

  The storage unit 37 is a magnetic disk (floppy (registered trademark) disk, hard disk, etc.), an optical disk (CD-ROM, DVD, etc.), a recording medium such as a semiconductor memory, and a device that reads information recorded on these media. . The storage unit 37 includes transmission / reception conditions, a predetermined scan sequence, a program for realizing a CHI function using three-dimensional triggered scan, a control program for executing image generation and display processing, and diagnostic information (patient ID Doctor's findings, etc.), diagnostic protocol, body mark generation program, various signal data and image data, and other data groups. Data in the storage unit 37 can also be transferred to an external peripheral device via the interface unit 41.

  The control processor 39 has a function as an information processing apparatus (computer) and controls the operation of the main body of the ultrasonic diagnostic apparatus. The control processor 39 reads out a program for realizing CHI using a three-dimensional triggered scan, a control program for executing a predetermined scan sequence, image generation / display, and the like from the storage unit 37 and stores it in its own memory. And execute operations and controls related to various processes.

  The interface unit 41 is an interface related to the input device 13, a network, and a new external storage device (not shown). Data such as ultrasonic images and analysis results obtained by the apparatus can be transferred to another apparatus via the network by the interface unit 41.

(CHI function using 3D triggered scan)
Next, the CHI function using the three-dimensional triggered scan of the ultrasonic diagnostic apparatus 1 will be described. This function improves volume rate and real-time performance by selectively executing a three-dimensional triggered scan in either the flash scan or the monitoring scan when performing CHI. This function can be broadly divided into a flash scan priority mode and a monitoring scan priority mode. Hereinafter, each priority mode will be described.

  Note that the three-dimensional trigger scan method is a volume related to a spatially continuous small region including at least a part of a diagnostic region while being associated with information (temporal phase information) for identifying a temporal phase of a periodic motion. Sub-volume) data is spatially and temporally rearranged on the basis of the associated temporal phase information to generate volume data (full volume data) related to the desired range, and the sub-volume according to the temporal phase information Is sequentially updated to execute a three-dimensional scan having a high volume rate and a high real-time property.

  FIG. 2 is a diagram showing the relationship between the sub-volumes v1, v2, v3, and v4, which are scanning ranges by the main scanning process, and the full volume V (= v1 + v2 + v3 + v4) configured by the sub-volumes v1 to v4. In the main scanning process, a volume scan over a repeated period (triggered scan period) T of the triggered scan is executed for each of the sub-volumes v1 to v4 shown in FIG. Therefore, for example, if the motion period of the diagnosis part is 6 (6 periods) within the triggered scan period T and data for subvolumes v1 to v4 is acquired in one motion period, a total of 24 subvolumes are acquired. (See FIG. 4).

  Further, in the present embodiment, as an application example of the CHI function using the three-dimensional triggered scan, a case where the part that performs periodic motion is the heart is taken as an example. However, regardless of this, this function can be applied to any part of the circulatory system. In the present embodiment, for the sake of simplicity, it is assumed that the number n of sub-volumes in the three-dimensional triggered scan is 4 and the triggered scan period T is 6 heartbeats. However, the number of subvolumes n and the triggered scan cycle T can be set to arbitrary values by setting / changing from the input device 13. Furthermore, in this embodiment, an ECG waveform is adopted as time phase information. However, any information may be adopted as long as the information can identify the time phase of the periodic movement without being limited to the example.

[Flash scan priority mode]
In the flash scan priority mode, in the CHI, a three-dimensional triggered scan is executed for the flash scan, and a normal volume scan (normal live volume scan) is executed for the monitoring scan.

  FIG. 3 is a conceptual diagram of a CHI scan sequence in the flash scan priority mode. The arrows in the figure symbolize one sub-volume scan or normal live volume scan. The length of the arrow corresponds to the strength of the sound pressure of the transmission ultrasonic wave in each cross section. In the figure, the subvolume data is represented as vij for convenience. The subscript i corresponds to the subvolume number (ie, spatial information). The subscript j indicates the order (that is, time information) collected in the triggered scan period T. Even if the subscript j is the same between the two sub-volumes, the collected cardiac time phases are not necessarily guaranteed due to the characteristics of the triggered scan.

  As shown in FIG. 3, in the flash scan priority mode, the normal live volume scan for the full volume V is repeated for the monitoring scan using low sound pressure ultrasonic waves. The operator can visually confirm the scan area, the inflow state of the contrast agent, and the like while observing the live image of the full volume V sequentially acquired by the monitoring scan. Further, the operator inputs a flash scan start instruction via the input device 13 or the like at a desired timing (for example, when the contrast agent sufficiently flows into the diagnostic region). In response to the disclosure instruction, the control processor 39 repeatedly executes the trigger scan in the triggered scan cycle T (in this case, 6 heartbeats) from the start instruction, and corresponds to the time phase information (here, ECG waveform). Each subvolume data (24 subvolume data from v11 to v46 in the example of FIG. 3) is acquired.

  Next, the data analysis unit 33 performs full-time data generation by performing temporal correlation between the sub-volumes based on the temporal information and spatially connecting the temporally correlated sub-volumes. To do.

  For example, as shown in FIG. 4, subvolume data v11 to v16 that are data for the triggered scan cycle T related to the subvolume v1, and subvolume data v21 to v1 that are data for the triggered scan cycle T related to the subvolume 2. The time phase association process with v26 is as follows. That is, the time phase information attached to each of the sub volume data v11 to v16 is compared with the time phase information attached to each of the sub volume data v21 to v26, and for example, the time phase deviation is within a predetermined threshold. In some cases, it is determined that the sub-volume is a simultaneous phase. Based on this determination result, the time phase association between the sub volume data v111 to v16 and the sub volume data v21 to v26 can be performed. Further, with respect to the remaining v31 to v46, it is possible to generate the full volume data V as shown in FIG. 2 for each time phase by determining temporal correspondence using time phase information and spatially connecting them. it can.

[Monitoring can priority mode]
In the monitoring scan priority mode, in CHI, a three-dimensional triggered scan is executed for the monitoring scan, and a normal live volume scan is executed for the flash scan.

  FIG. 5 is a conceptual diagram of a CHI scan sequence in the monitoring scan priority mode. In addition, about notation methods, such as an arrow, it is the same as that of FIG.

  As shown in FIG. 5, for the monitoring scan using low sound pressure ultrasonic waves, the control processor 39 performs a triggered scan period T (in this case, 6 in a timing based on R wave generation). The trigger scan is repeatedly executed for the heart rate), and each sub-volume data (24 sub-volume data from v11 to v46) is acquired in association with the time phase information (ECG waveform). Further, the operator inputs a flash scan start instruction via the input device 13 or the like at a desired timing (for example, when the contrast agent sufficiently flows into the diagnostic region). In response to the disclosure instruction, the control processor 39 repeats the normal live volume scan for the full volume V from the start instruction for a predetermined period. Thereby, for example, it is possible to concentrate on the destruction of the contrast medium in the full volume V.

  Next, the data revision unit 33 generates full volume data by performing temporal correlation between the sub-volumes based on the temporal phase information and spatially connecting the temporally correlated sub-volumes. To do. The volume data generation method is substantially the same as in the flash scan priority mode.

[Modification]
Next, a modified example of the monitoring scan priority mode will be described. In this modification, in the monitoring scan, a three-dimensional triggered scan is executed for one subvolume, and a plurality of subvolume data corresponding to various time phases is acquired by sequentially executing this for each subvolume, Full volume data for each time phase is generated by performing temporal and spatial correspondence after the time based on the time phase information.

  FIG. 6 is a conceptual diagram of a CHI scan sequence in the monitoring scan priority mode according to the modification. In addition, about notation methods, such as an arrow, it is the same as that of FIG. 4, FIG.

  As shown in FIG. 6, first, the control processor 39 repeatedly executes a trigger scan at a desired timing for the sub-volume v1 in the triggered scan cycle T / 4 in the monitoring mode, and corresponds to the time phase information (ECG waveform). Each sub-volume data (six sub-volume data from v11 to v16) is acquired. Further, the operator inputs a flash scan start instruction via the input device 13 or the like at a desired timing (for example, when the contrast agent sufficiently flows into the diagnostic region). In response to the disclosure instruction, the control processor 39 repeats the normal live volume scan for the full volume V from the start instruction for a predetermined period.

  Next, in the monitoring mode, the control processor 39 repeatedly executes a trigger scan in the triggered scan cycle T / 4 at a desired timing for the subvolume v2, and associates each subvolume data with the time phase information (ECG waveform). (6 sub-volume data from v21 to v26) is acquired. Further, the operator inputs a flash scan start instruction via the input device 13 or the like at a desired timing. In response to the disclosure instruction, the control processor 39 repeats the normal live volume scan for the full volume V from the start instruction for a predetermined period.

  Hereinafter, as shown in FIG. 6, the same monitoring scan and flash scan are executed for the sub-volumes v3 and v4, so that the sub-volume data v31 to v36 and v41 to 46 are acquired in association with the time phase information.

  Next, the data revision unit 33 generates full volume data by performing temporal correlation between the sub-volumes based on the temporal phase information and spatially connecting the temporally correlated sub-volumes. To do. The volume data generation method is substantially the same as in the flash scan priority mode.

(Operation)
Next, the operation of the ultrasonic diagnostic apparatus 1 including processing according to the CHI function using three-dimensional triggered scan (CHI processing using three-dimensional triggered scan) will be described.

  FIG. 7 is a flowchart showing a flow of operations including CHI processing using three-dimensional triggered scan. As shown in the figure, first, the control processor 39 sets the number of sub-volumes (number of segments) and the scanning range (that is, a full volume area) based on the input from the input device 13 (step S1). . The control processor 39 also scans each sub-volume based on the input from the input device 13 (for example, scanning line density, frame rate, gain, frequency, dynamic range, filter setting, depth of field, focus position, etc.) Is set (step S2).

  When the various parameter settings in steps S1 and S2 are completed and the contrast medium is administered to the subject at a predetermined timing (step S3), the control processor 39 selects one of the monitoring scan priority mode and the monitoring scan priority mode. The CHI process using the three-dimensional triggered scan according to the above is executed, and the sub-volume data obtained as a result is correlated temporally and spatially to generate full volume data for each time phase (steps S4 and S5). .

  The image generation unit 28 performs image processing such as volume rendering using the generated full volume data of each time phase, and generates a three-dimensional image for each time phase. The generated three-dimensional image is displayed on the monitor 11 in the form shown in FIG. 8, for example, as a real-time moving image or as a still image as required (step S6).

(effect)
According to the configuration described above, the following effects can be obtained.

  According to this ultrasonic diagnostic apparatus, the flash scan priority mode or the monitoring scan priority mode can be selected according to the situation by the CHI function using the three-dimensional triggered scan. Therefore, for example, when the flash scan priority mode is selected, a three-dimensional triggered scan is executed in the flash scan, and a flash image can be acquired at a high volume rate. In the three-dimensional triggered scan, since the time difference between the ultrasonic cross sections is small, the bubbles can be destroyed instantaneously. Further, since the monitoring scan is executed by the normal live volume, the guide real-time property can be improved as compared with the conventional case. On the other hand, when the monitoring scan priority mode is selected, a three-dimensional triggered scan is executed in the monitoring scan, and a monitoring image can be acquired at a high volume rate. Therefore, it is possible to check the scan region and the contrast agent inflow state with high accuracy. In addition, since the flash can is executed with the normal live volume, the bubble can be instantaneously destroyed.

  Note that the present invention is not limited to the above-described embodiment as it is, and can be embodied by modifying the constituent elements without departing from the scope of the invention in the implementation stage. For example, each function according to the present embodiment can also be realized by installing a program for executing the processing in a computer such as a workstation and developing these on a memory. At this time, a program capable of causing the computer to execute the technique is stored in a recording medium such as a magnetic disk (floppy (registered trademark) disk, hard disk, etc.), an optical disk (CD-ROM, DVD, etc.), or a semiconductor memory. It can also be distributed.

  In addition, various inventions can be formed by appropriately combining a plurality of components disclosed in the embodiment. For example, some components may be deleted from all the components shown in the embodiment. Furthermore, constituent elements over different embodiments may be appropriately combined.

  As described above, according to the present invention, it is possible to realize an ultrasonic diagnostic apparatus and an ultrasonic diagnostic apparatus control program capable of executing contrast echo imaging having higher real-time characteristics than conventional.

DESCRIPTION OF SYMBOLS 1 ... Ultrasonic diagnostic apparatus, 11 ... Monitor, 13 ... Input device, 21 ... Ultrasonic transmission unit, 23 ... Ultrasonic reception unit, 25 ... B mode processing unit, 27 ... Doppler processing unit, 28 ... Image generation unit, 29 DESCRIPTION OF SYMBOLS 1st memory, 31 ... Voxel conversion unit, 33 ... Data analysis unit, 35 ... Image composition unit, 37 ... Storage unit, 39 ... Control processor (CPU), 41 ... Interface unit, A ... Ultrasonic probe, B ... Main unit, C ... Interface part

Claims (4)

A first ultrasonic scan using an ultrasonic wave having a sound pressure that does not substantially destroy the contrast agent, and a diagnostic site that performs periodic motion of the subject; An ultrasonic diagnostic apparatus for performing a second ultrasonic scan using sound pressure,
The first ultrasonic scan or the second ultrasonic scan is performed n times (m) for each of m (m is an integer of 2 or more) sub-regions that include at least a part of the diagnostic region and are spatially continuous. n is an integer greater than or equal to 2), and data acquisition means for acquiring n subvolume data over time for each of the subregions in association with time phase information indicating the time phase of the periodic motion;
Data generating means for generating full volume data relating to the diagnostic site in each time phase of the periodic movement based on the n subvolume data and the time phase information over time;
An ultrasonic diagnostic apparatus comprising: The data acquisition means performs the first ultrasonic scanning n times (n is an integer of 2 or more) for the m sub-regions,
The data generating means generates the full volume data for acquiring an ultrasound image showing a change over time of a state in which a contrast agent flows into the diagnostic site;
The ultrasonic diagnostic apparatus according to claim 1. The data acquisition means performs the second ultrasonic scanning n times (n is an integer of 2 or more) for the m sub-regions,
The data generating means generates the full volume data for acquiring an ultrasound image using the destruction of the contrast agent flowing into the diagnostic region;
The ultrasonic diagnostic apparatus according to claim 1. A first ultrasonic scan using an ultrasonic wave having a sound pressure that does not substantially destroy the contrast agent, and a diagnostic site that performs periodic motion of the subject; A second ultrasonic scan using sound pressure, and a computer built in the ultrasonic diagnostic apparatus for executing the second ultrasonic scan,
The first ultrasonic scan or the second ultrasonic scan is performed n times (m) for each of m (m is an integer of 2 or more) sub-regions that include at least a part of the diagnostic region and are spatially continuous. n is an integer greater than or equal to 2), and a data acquisition function for acquiring n sub-volume data over time for each of the sub-regions in association with time-phase information indicating a time phase of the periodic motion;
A data generation function for generating full volume data relating to the diagnostic region in each time phase of the periodic movement based on the n subvolume data and the time phase information over time;
An ultrasonic diagnostic apparatus control program characterized by realizing the above.

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