JP2011087759A - Ultrasonic diagnostic apparatus and control program for image quality condition updating - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To set a suitable image quality condition for cardiac synchronization three-dimensional image data in a short period of time. <P>SOLUTION: The ultrasonic diagnostic apparatus has a function of performing cardiac synchronization three-dimensional scanning to a wide-range three-dimensional area comprising a plurality of three-dimensional sub areas and real time three-dimensional scanning to one of the three-dimensional sub areas. When updating the image quality condition of a gain or the like in the process of collecting three-dimensional image data by a cardiac synchronization three-dimensional scanning mode, an updating timing detection part 10 detects the updating start timing of the image quality condition by comparing the image quality condition newly input from an input part 9 and the latest image quality condition already preserved in its own image quality condition storage part, a scanning control part 11 causes the cardiac synchronization three-dimensional scanning mode to transition to a real time three-dimensional scanning mode by controlling a transmission/reception part 2 on the basis of the detection result, and the input part 9 inputs a suitable image quality condition under the observation of the real time three-dimensional image data obtained upon the transition. <P>COPYRIGHT: (C)2011,JPO&INPIT

Description

  The present invention relates to an ultrasonic diagnostic apparatus and an image quality condition update control program, and in particular, an ultrasonic wave that generates a wide range of three-dimensional image data based on subvolume data collected in synchronization with a biological signal such as an electrocardiogram waveform. The present invention relates to a diagnostic apparatus and an image quality condition update control program.

  The ultrasonic diagnostic apparatus performs ultrasonic transmission / reception in a plurality of directions of a subject using an ultrasonic probe in which a plurality of vibration elements are arranged, and generates image data or time series generated based on the reflected wave obtained at this time Data is displayed on a monitor. This device can observe 2D image data and 3D image data in the body in real time with a simple operation by simply bringing the tip of the ultrasound probe into contact with the body surface. Widely used in

  In conventional three-dimensional scanning for the purpose of collecting three-dimensional image data, an ultrasonic probe in which a plurality of vibration elements are arranged one-dimensionally is moved or rotated in a direction perpendicular to the arrangement direction of the subject. Three-dimensional image data has been generated by transmitting and receiving ultrasonic waves to and from the three-dimensional region, and rendering the volume data collected at this time. In recent years, an ultrasonic probe (two-dimensional array ultrasonic probe) in which a plurality of vibration elements are two-dimensionally arranged has been put into practical use. By using this two-dimensional array ultrasonic probe, ultrasonic transmission / reception for a three-dimensional region can be performed by electronic control, so the time required for three-dimensional scanning is greatly shortened and the operability in inspection is remarkably improved. .

  However, when three-dimensional data (volume data) is collected by ultrasonic scanning on a desired three-dimensional region, it is necessary to repeat a large number of transmissions and receptions, and the time required for these transmissions propagates through the body of the subject. A large amount of time is required to collect a wide range of volume data with excellent spatial resolution because it is determined by the speed of ultrasonic waves, the size of the scanning region, the scanning density, and the like.

  On the other hand, a method for improving the real-time property of image data by a so-called parallel simultaneous reception method that simultaneously receives reflected waves from a plurality of directions in a subject has been developed. By applying this method to the above-described three-dimensional scanning, The time required for collecting volume data can be shortened. However, three-dimensional scanning of an organ with pulsatile movement such as the heart requires a large number of parallel receptions, and there is a problem that the circuit configuration of the apparatus becomes extremely complicated in order to realize this. .

  In order to solve such a problem, a three-dimensional region including a diagnosis target part of a subject is divided into a plurality of three-dimensional subregions, and time-series volume data collected from these three-dimensional subregions ( In the following, a heartbeat-synchronized three-dimensional scanning method (Triggered Volume Scan) that synthesizes sub-volume data) based on the heartbeat time phase has been proposed (for example, see Patent Document 1).

  In the above-described method, three-dimensional scanning of a predetermined period (for example, one heartbeat period) is sequentially performed on a plurality of three-dimensional subareas constituting the three-dimensional area, and heartbeat time phase information is added to the subvolume data obtained at this time. Add and save once. When the collection of sub-volume data for a plurality of three-dimensional sub-regions is completed, the volume data of the three-dimensional regions in each heartbeat time phase is generated by synthesizing the sub-volume data collected in the same heartbeat time phase. Then, by processing these volume data and generating three-dimensional image data such as volume rendering image data and surface rendering image data, the three-dimensional information in the desired heartbeat time phase of the region to be diagnosed is used as a moving image. It becomes possible to observe.

Japanese Patent Laid-Open No. 2001-170047

  As described above, it is possible to observe a wide range of three-dimensional image data as a moving image by applying the above-described heartbeat-synchronized three-dimensional scanning method. In the conventional case, since the update is performed under the observation of the 3D image data generated in the heartbeat synchronization 3D scanning mode, the update content is reflected in the entire region or a desired region of the 3D image data. It took a lot of time. A method of newly generating two-dimensional image data such as Bi-Plane image data and MPR image data based on the volume data, and updating the image quality condition of the three-dimensional image data under observation of these two-dimensional image data However, not only does it take a lot of time to start up the dedicated software, but also it is difficult to obtain suitable image quality conditions for 3D image data using 2D image data.

  The present invention has been made in view of such conventional problems, and its purpose is to update image quality conditions such as gain in the process of collecting a wide range of three-dimensional image data by heartbeat-synchronized three-dimensional scanning. By automatically switching from the heartbeat-synchronized 3D scanning mode to the real-time 3D scanning mode based on the detection signal of the update start timing, the update to a suitable image quality condition is observed in a narrow range of 3D image data by the real-time 3D scanning. It is an object of the present invention to provide an ultrasonic diagnostic apparatus and an image quality condition update control program that can be accurately and easily performed below.

  In order to solve the above-described problem, the ultrasonic diagnostic apparatus according to the first aspect of the present invention is a time-sequential heartbeat-synchronized three-dimensional data based on volume data collected from a three-dimensional region of a subject by heartbeat-synchronized three-dimensional scanning. In the ultrasonic diagnostic apparatus for generating image data, based on the image quality condition input means for inputting a new image quality condition in the process of collecting the heartbeat synchronized 3D image data, and the image quality condition input by the image quality condition input means Update timing detection means for detecting an update start timing of image quality conditions, scan control means for transitioning a scanning mode from the heartbeat-synchronized three-dimensional scan to real-time three-dimensional scan based on the update start timing, and the heartbeat-synchronized three-dimensional image Display means for displaying data and real-time three-dimensional image data obtained by the real-time three-dimensional scanning; Wherein the quality condition input means is characterized in that inputting a suitable quality conditions in the heartbeat-synchronous three-dimensional image data based on the real-time 3-dimensional image data that are displayed by the display means.

  According to a tenth aspect of the present invention, the image quality condition update control program of the present invention generates time-sequential heartbeat-synchronized three-dimensional image data based on volume data collected from a three-dimensional region of a subject by heartbeat-synchronized three-dimensional scanning. An image quality condition input function for inputting a new image quality condition in the process of collecting the heartbeat-synchronized three-dimensional image data and an image quality condition based on the image quality condition input by the image quality condition input means. An update timing detection function for detecting an update start timing, a scan control function for changing a scan mode from the heartbeat-synchronized three-dimensional scan to the real-time three-dimensional scan based on the update start timing, the heartbeat-synchronized three-dimensional image data, and the A display function for displaying real-time three-dimensional image data obtained by real-time three-dimensional scanning is executed. It is characterized in that.

  According to the present invention, when image quality conditions such as gain are updated in the process of collecting a wide range of three-dimensional image data by heartbeat-synchronized three-dimensional scanning, real-time 3 By automatically switching to the three-dimensional scanning mode, updating to a suitable image quality condition can be performed accurately and easily under observation of narrow-range three-dimensional image data by real-time three-dimensional scanning.

1 is a block diagram showing the overall configuration of an ultrasonic diagnostic apparatus according to an embodiment of the present invention. The block diagram which shows the specific structure of the transmission / reception part and reception signal processing part with which the ultrasonic diagnosing device of the Example is provided. The figure for demonstrating the ultrasonic transmission / reception direction in the three-dimensional scanning of the Example. The figure which shows the three-dimensional sub area | region in the heart rate synchronous three-dimensional scanning mode of the Example. The figure which shows the specific example of the heart-beat synchronous three-dimensional scanning with respect to the three-dimensional sub area | region of the Example. The block diagram which shows the specific structure of the image data generation part with which the ultrasound diagnosing device of the Example is provided. 6 is a flowchart showing image quality condition setting / updating procedures in the embodiment.

  Embodiments of the present invention will be described below with reference to the drawings.

  The ultrasonic diagnostic apparatus according to the present embodiment has a function of performing heart rate synchronization three-dimensional scanning on a wide range of three-dimensional regions constituted by a plurality of three-dimensional subregions and real-time three-dimensional scanning on any of the three-dimensional subregions. When the image quality condition such as gain is updated in the process of collecting the three-dimensional image data in the heartbeat-synchronized three-dimensional scan mode, the heartbeat-synchronized three-dimensional scan mode is changed to the real-time three-dimensional scan mode based on the detection signal of the update start timing Switching is performed, and updating to suitable image quality conditions is performed under observation of real-time three-dimensional image data obtained at this time.

  In the following embodiments, a reception signal obtained from a subject is processed to generate B-mode data as ultrasonic data, and a heartbeat-synchronized three-dimensional scanning mode and a real-time three-dimensional scanning mode are generated based on the B-mode data. However, the present invention is not limited to this, and the above volume data may be generated based on other ultrasonic data such as color Doppler data.

  In the real-time three-dimensional scanning mode, one or a plurality of three-dimensional sub-regions selected from a plurality of three-dimensional sub-regions composing a wide range of three-dimensional regions in the heartbeat synchronous three-dimensional scanning mode are real-time three-dimensional. Although the case where scanning is performed will be described, real-time three-dimensional scanning may be performed on an arbitrarily set narrow three-dimensional region.

(Device configuration and functions)
The configuration and function of the ultrasonic diagnostic apparatus according to the embodiment of the present invention will be described with reference to FIGS. FIG. 1 is a block diagram showing an overall configuration of the ultrasonic diagnostic apparatus, and FIG. 2 is a block diagram showing a specific configuration of a transmission / reception unit and a received signal processing unit included in the ultrasonic diagnostic apparatus. FIG. 6 is a block diagram showing a specific configuration of an image data generation unit provided in the ultrasonic diagnostic apparatus.

  The ultrasonic diagnostic apparatus 100 shown in FIG. 1 transmits an ultrasonic pulse (transmission ultrasonic wave) to a wide range of three-dimensional regions including a diagnosis target site of a subject, and an ultrasonic reflected wave (transmission ultrasonic wave) (transmission ultrasonic wave) obtained by this transmission ( An ultrasonic probe 3 in which a plurality of vibration elements that convert received ultrasonic waves into electrical signals (received signals) are two-dimensionally arranged, and a drive signal for transmitting ultrasonic pulses in a predetermined direction of the subject. Transmitter / receiver 2 that supplies the oscillating element and phasing and adding the reception signals of a plurality of channels obtained from these oscillating elements, and receiving signal processing that processes the received signal after phasing and adding to generate B-mode data A wide range of three-dimensional image data (hereinafter referred to as a heartbeat-synchronized three-dimensional image) based on volume data obtained by performing heartbeat-synchronized three-dimensional scanning on the unit 4 and a plurality of three-dimensional subregions constituting the three-dimensional region. De And a narrow range of three-dimensional image data (hereinafter referred to as real-time three-dimensional image data) based on volume data obtained by performing real-time three-dimensional scanning on a predetermined three-dimensional sub-region. The image data generation unit 5 for generating the image data) and the display unit 6 for displaying the above-described heartbeat-synchronized three-dimensional image data and real-time three-dimensional image data.

  Furthermore, the ultrasonic diagnostic apparatus 100 includes a biological signal measurement unit 7 that measures an electrocardiogram waveform of the subject, a heartbeat synchronization signal generator 8 that generates a heartbeat synchronization signal based on the detected electrocardiogram waveform, Input of specimen information, input of image quality conditions, setting of volume data generation conditions, setting of image data generation conditions and image data display conditions, and input of various command signals, etc. An update timing detection unit 10 for detecting an update start timing and an update end timing of the image quality condition based on information on the image quality condition input to the heartbeat, and a heartbeat synchronization three-dimensional scan based on the detection result supplied from the update timing detection unit 10 And a scanning control unit 11 that generates a scanning control signal for performing real-time three-dimensional scanning, and the above-mentioned units are controlled in a centralized manner to perform three-dimensional heartbeat synchronization. And a system controller 12 for executing the generation and display of image data and real-time 3-dimensional image data.

  Next, a more detailed description will be given for each unit described above.

  The ultrasonic probe 3 has M vibrating elements (not shown) arranged two-dimensionally at its tip, and transmits and receives ultrasonic waves by bringing the tip into contact with the body surface of the subject. The vibration element is an electroacoustic transducer that converts electrical pulses (driving signals) into ultrasonic pulses (transmitting ultrasonic waves) during transmission, and converts ultrasonic reflected waves (receiving ultrasonic waves) into electrical reception signals during reception. It has a function to do. Each of these vibration elements is connected to the transmission / reception unit 2 via an M channel multi-core cable (not shown). In this embodiment, the ultrasonic diagnostic apparatus 100 having the sector scanning ultrasonic probe 3 in which M vibration elements are two-dimensionally arranged will be described. However, an ultrasonic probe corresponding to linear scanning, convex scanning, or the like is used. You may use.

  Next, the transmission / reception unit 2 illustrated in FIG. 2 includes a transmission unit 21 that supplies a drive signal to the vibration element of the ultrasonic probe 3 and a phasing addition (obtained from a predetermined direction) with respect to a reception signal obtained from the vibration element. The receiving section 22 is provided for performing the addition synthesis by matching the phases of the received signals.

  The transmission unit 21 includes a rate pulse generator 211, a transmission delay circuit 212, and a drive circuit 213, and the rate pulse generator 211 is based on the scanning control signal supplied from the scanning control unit 11, A rate pulse that determines the repetition period of the transmission ultrasonic wave in the real-time three-dimensional scanning mode is generated.

  On the other hand, the transmission delay circuit 212 is based on the scanning control signal supplied from the scanning control unit 11 described above, and in a predetermined delay (θp, φq) and a delay time for focusing to focus the transmission ultrasonic wave to a predetermined depth. A deflection delay time for transmission is given to the rate pulse supplied from the rate pulse generator 211 and supplied to the drive circuit 213.

  The drive circuit 213 has the same number of independent drive circuits as the transmission delay circuit 212, and generates a drive signal based on the rate pulse to which the delay time is given. Then, Mt transmitting vibration elements selected from the M vibrating elements arranged two-dimensionally in the ultrasonic probe 3 are driven by the drive signal, and transmission ultrasonic waves are emitted into the subject.

  On the other hand, the reception unit 22 includes an A / D converter 221 and a reception delay circuit for the Mr channel corresponding to the Mr vibration elements selected for reception among the M vibration elements incorporated in the ultrasonic probe 3. 222 and an adder 223, and the Mr channel received signal supplied from the receiving vibration element is converted into a digital signal by the A / D converter 221 and sent to the reception delay circuit 222.

  The reception delay circuit 222 is based on a control signal supplied from the scanning control unit 11 and is directed to receive a delay time for focusing and a predetermined direction (θp, φq) for focusing a received ultrasonic wave from a predetermined depth. A deflection delay time for setting the characteristics is given to each of the Mr channel reception signals output from the A / D converter 221, and the adder 223 adds and synthesizes the reception signals from the reception delay circuit 222. That is, the reception delay circuit 222 and the adder 223 perform phasing addition on the reception signal obtained from a predetermined direction.

  In addition, the reception delay circuit 222 and the adder 223 of the reception unit 22 enable so-called parallel simultaneous reception in which reception directivities in a plurality of directions are simultaneously formed by controlling the delay time, and three-dimensional scanning can be performed by applying parallel simultaneous reception. The time required is greatly reduced. A part of the transmission unit 21 and the reception unit 22 included in the transmission / reception unit 2 may be provided inside the ultrasonic probe 3.

  FIG. 3 shows a specific example of the ultrasonic transmission / reception direction (θp, φq) in orthogonal coordinates (xyz) with the central axis of the ultrasonic probe 3 as the z axis, and the vibration element is the x axis. Two-dimensionally arranged in the direction and the y-axis direction, and θp and φq indicate angles with respect to the z-axis in the ultrasonic transmission / reception direction projected on the xz plane and the yz plane. The delay times in the transmission delay circuit 212 of the transmission unit 21 and the reception delay circuit 222 of the reception unit 22 are controlled in accordance with the scanning control signal supplied from the scanning control unit 11, and a plurality of three-dimensional subregions or these three-dimensional subregions are controlled. Ultrasonic transmission / reception is performed on a predetermined three-dimensional sub-region selected from the region.

  Next, a plurality of three-dimensional sub-regions set for the three-dimensional region of the subject and heartbeat-synchronized three-dimensional scanning for these three-dimensional sub-regions will be described with reference to FIGS.

  FIG. 4 shows a plurality of three-dimensional sub-regions in the heartbeat-synchronized three-dimensional scanning mode set in the three-dimensional region S0 including the diagnosis target part of the subject. The number of segments Sn (for example, set in the input unit 9) , Sn = 4), four three-dimensional sub-regions S1 to S4 are set by dividing the three-dimensional region S0 in the y direction. Each of the three-dimensional subregions S1 to S4 is controlled by controlling the delay time in the transmission delay circuit 212 of the transmission unit 21 and the reception delay circuit 222 of the reception unit 22 based on the scanning control signal supplied from the scanning control unit 11. A heartbeat-synchronized three-dimensional scan is performed.

  On the other hand, FIG. 5 shows a specific example of heartbeat-synchronized three-dimensional scanning for the above-described three-dimensional subregions S1 to S4. FIG. 5 (a) shows the heartbeat period To measured by the biological signal measuring unit 7. FIG. 5B shows a heartbeat synchronization signal generated by the heartbeat synchronization signal generation unit 8 based on the R wave of the ECG waveform, and FIG. 5C shows the heartbeat synchronization signal. The order of heartbeat-synchronized three-dimensional scanning performed for each of the three-dimensional subregions S1 to S4 (see FIG. 4) is shown.

  In this case, the scanning control unit 11 determines the signal interval (heart rate) To of the heartbeat synchronization signal supplied from the heartbeat synchronization signal generation unit 8 and the heartbeat time phase number Hn preset in the input unit 9 (for example, Hn = 4). ) To set the data collection time δτ of the subvolume data in each of the heartbeat time phases τ1 to τ4, and further, based on the data collection time δτ, the number of segments Sn (Sn) of the three-dimensional subregion with respect to the three-dimensional region S0 = 4) is set. However, the heartbeat time phase τ1 is a heartbeat time phase in which heartbeat-synchronized three-dimensional scanning is started with respect to the three-dimensional subregion S1, and the heartbeat time phases τ2 to τ4 are for each of the three-dimensional subregions S2 to S4. The heartbeat time phase at which heartbeat-synchronized three-dimensional scanning is started is shown.

  Then, the scanning control unit 11 controls the transmission delay circuit 212 and the reception delay circuit 222 of the transmission / reception unit 2 based on the setting information described above. First, the three-dimensional heartbeat time phases τ1 to τ4 in the period [t1-t2]. The heart rate synchronization three-dimensional scanning is sequentially performed on the sub-region S1, and the three-dimensional sub-region S2 of the heartbeat time phases τ1 to τ4 in each of the period [t2-t3], the period [t3-t4], and the period [t4-t5]. A heartbeat synchronization three-dimensional scan with respect to S4 is performed.

  On the other hand, a volume data generation unit 52, which will be described later, included in the image data generation unit 5 is a three-dimensional subregion generated based on ultrasonic transmission / reception in the heartbeat time phase τ1 in the period [t1-t2] to the period [t4-t5]. The volume data in the heartbeat time phase τ1 is generated by synthesizing the sub-volume data of S1 to S4. Similarly, ultrasonic transmission / reception in the heartbeat time phases τ2 to τ4 in the period [t1-t2] to the period [t4-t5] is performed. The volume data in each of the heartbeat time phases τ2 to τ4 is generated by synthesizing the subvolume data of the three-dimensional subregions S1 to S4 generated based on the above.

  Returning to FIG. 2, the received signal processing unit 4 has a function of generating B-mode data, and includes an amplifier circuit 41, an envelope detector 42, and a logarithmic converter 43. The amplification circuit 41 adjusts the gains of the heartbeat-synchronized three-dimensional image data and the real-time three-dimensional image data by amplifying or attenuating the reception signal after the phasing addition supplied from the adder 223 of the reception unit 22, and envelopes The detector 42 performs envelope detection on the reception signal output from the amplifier circuit 41. On the other hand, the logarithmic converter 43 logarithmically converts the amplitude of the received signal detected by the envelope detection, and further adjusts the amplitude range (dynamic range) of the received signal displayed as the above-described image data to generate B-mode data. To do. It should be noted that the envelope detector 42 and the logarithmic converter 43 may be configured in a reversed order, and adjustment of image quality conditions such as gain and dynamic range may be performed by other units or other methods.

  Next, a specific configuration of the image data generation unit 5 shown in FIG. 1 will be described with reference to FIG. The image data generation unit 5 includes a sub volume data generation unit 51, a volume data generation unit 52, and a volume data processing unit 53 as shown in FIG.

  The sub-volume data generation unit 51 includes an ultrasonic data storage unit 511, an interpolation processing unit 512, and a sub-volume data storage unit 513. The ultrasonic data storage unit 511 has a heartbeat synchronization for each of the three-dimensional sub-regions S1 to S4. The B-mode data generated by the reception signal processing unit 4 based on the reception signal obtained by the three-dimensional scanning or the real-time three-dimensional scanning for any one of the three-dimensional sub-regions S1 to S4 indicates the ultrasonic transmission / reception direction (θp, φq). It is stored sequentially as incidental information.

  On the other hand, the interpolation processing unit 512 arranges a plurality of B-mode data read from the ultrasonic data storage unit 511 in units of three-dimensional sub-regions in correspondence with the ultrasonic transmission / reception directions (θp, φq), thereby performing the three-dimensional B mode. Generate sub-volume data consisting of voxels that are isotropic in the x, y, and z directions by forming the data and interpolating the non-uniformly spaced voxels that make up this 3D B-mode data To do. The sub-volume data sequentially generated for each of the three-dimensional sub-regions S1 to S4 is stored in the sub-volume data storage unit 513 using the sub-region information and the heartbeat synchronization signal supplied from the system control unit 12 as supplementary information. Is done.

  In addition, when real-time three-dimensional scanning is performed on any one of the three-dimensional subregions S1 to S4 (for example, the three-dimensional subregion S2), the interpolation processing unit 512 reads the three-dimensional data read from the ultrasonic data storage unit 511. A three-dimensional sub-region generated by interpolating the voxels of the three-dimensional B-mode data by forming the three-dimensional B-mode data by arranging the B-mode data of the sub-region S2 in correspondence with the ultrasonic transmission / reception direction. Is temporarily stored in a volume data storage unit 522 described later provided in the volume data generation unit 52.

  The volume data generation unit 52 includes a calculation unit 521 and a volume data storage unit 522. When heartbeat synchronization three-dimensional scanning is performed on the three-dimensional subregions S1 to S4, the calculation unit 521 includes the subvolume data stored in the subvolume data storage unit 513 of the subvolume data generation unit 51 and its subvolume data. By reading out the heartbeat time phase information and the sub-region information, which are supplementary information, the sub-volume data collected in each of the three-dimensional sub-regions S1 to S4 is synthesized based on the above-mentioned supplementary information, so that a wide-range three-dimensional region S0 is obtained. Generate time-series volume data at. Next, the obtained volume data is temporarily stored in the volume data storage unit 522. That is, the volume data storage unit 522 stores a wide range of volume data in the three-dimensional region S0 collected by the heartbeat-synchronized three-dimensional scan and a narrow range of volume data in the three-dimensional subregion S2 collected by the real-time three-dimensional scan. Is done.

  Next, the volume data processing unit 53 renders the volume data in the heartbeat-synchronized three-dimensional scanning mode or the volume data in the real-time three-dimensional scanning mode sequentially supplied from the volume data generating unit 52 to perform volume rendering image data and surface rendering. It has a function of generating heartbeat-synchronized three-dimensional image data such as image data and real-time three-dimensional image data, and includes, for example, an opacity / color tone setting unit 531, a rendering processing unit 532, and a program storage unit 533. The opacity / color tone setting unit 531 sets the opacity and color tone (luminance) of each voxel based on the voxel value of the volume data, and the rendering processing unit 532 sets the opacity set by the opacity / color tone setting unit 531. In addition, volume data having color tone (luminance) information is rendered based on a predetermined processing program read from the program storage unit 533 to generate time-series three-dimensional image data.

  Returning to FIG. 1, the display unit 6 includes a display data generation unit, a data conversion unit, and a monitor (not shown). The display data generation unit generates the heartbeat-synchronized three-dimensional image data generated by the image data generation unit 5 and the real-time 3. After the three-dimensional image data is converted into a predetermined display format, display data is generated by adding incidental information such as an electrocardiogram waveform supplied from the biological signal measurement unit 7 or subject information input at the input unit 9. . The data converter performs a conversion process such as D / A conversion or TV format conversion on the display data generated by the display data generator and displays the display data on the monitor.

  On the other hand, the biological signal measurement unit 7 that measures the electrocardiographic waveform of the subject is configured to store an ECG electrode that is attached to the body surface of the subject and detects the electrocardiographic waveform, and an electrocardiographic waveform detected by the ECG electrode. And an A / D converter (both not shown) for converting the amplified electrocardiogram waveform into a digital signal. The heartbeat synchronization signal generation unit 8 detects the R wave of the electrocardiogram waveform by comparing the amplitude of the electrocardiogram waveform with a predetermined threshold, and generates a heartbeat synchronization signal based on the R wave. The heartbeat synchronization signal is normally generated at the same timing as the generation of the R wave, but may be generated at a timing delayed by a predetermined time from the R wave.

  Next, the input unit 9 includes an input device such as a keyboard, a trackball, a mouse, a selection button, and an input button on the operation panel and a display panel, and sets image quality conditions for the heart rate synchronized 3D image data and the real-time 3D image data. It has an input image quality condition input function 91 and a volume data generation condition setting function 92 for setting a scanning area and the like in the heart rate synchronization three-dimensional scanning mode and the real-time three-dimensional scanning mode. Also, setting of 3D image data generation conditions and 3D image data display conditions in the heart rate synchronized 3D scanning mode and the real time 3D scanning mode, setting of the number of segments Sn and the number of heartbeat phases Hn in the 3D sub-region, and subject Information is input, and various command signals are input using the above-described display panel and input device.

  The update timing detection unit 10 includes, for example, an image quality condition storage unit and an image quality condition comparison unit (not shown), and the image quality conditions already input in the input unit 9 are sequentially stored in the image quality condition storage unit. On the other hand, the image quality condition comparison unit compares the new image quality condition input in the input unit 9 and supplied via the system control unit 12 with the latest image quality condition stored in the image quality condition storage unit. The update start timing and update end timing of the image quality condition are detected, and the detection results are supplied to the system control unit 12.

  The scanning control unit 11 controls the delay times of the transmission delay circuit 212 and the reception delay circuit 232 based on the volume data generation conditions in the heartbeat synchronization three-dimensional scanning mode and the real-time three-dimensional scanning mode supplied from the input unit 9. The ultrasonic transmission / reception direction in each scanning mode is controlled.

  In particular, when update start timing information of image quality conditions is supplied from the update timing detection unit 10 during the heartbeat-synchronized three-dimensional scan mode, a scan control signal for making a transition from the heartbeat-synchronized three-dimensional scan mode to the real-time three-dimensional scan mode Is generated based on the update start timing information and supplied to the transmission delay circuit 212 and the reception delay circuit 222 of the transmission / reception unit 2. Further, when the update timing detection information of the image quality condition is supplied from the update timing detection unit 10 in the middle of the real-time 3D scanning mode for the purpose of adjusting the image quality condition, the real-time 3D scanning mode is switched to the heartbeat synchronization 3D scanning mode. A scanning control signal for transition is generated at a timing when a predetermined time has elapsed from the update end timing, and is supplied to the transmission delay circuit 212 and the reception delay circuit 222 described above.

  The system control unit 12 includes a CPU and a storage circuit (not shown), and the above-described various information input / set by the input unit 9 is stored in the storage circuit. The CPU performs overall control of each unit of the ultrasonic diagnostic apparatus 100 based on the input information and setting information described above, so that the volume of the subject in the heartbeat-synchronized three-dimensional scanning mode and the real-time three-dimensional scanning mode. Collecting data, and further generating heart rate synchronized 3D image data for the purpose of diagnosis of the subject and real time 3D image data for adjusting image quality conditions based on the obtained volume data Display.

(Image quality condition setting / update procedure)
Next, an image quality condition setting / updating procedure in this embodiment will be described with reference to the flowchart of FIG. Also in this case, in the heart rate synchronization three-dimensional scanning mode, volume data is generated by synthesizing the sub-volume data of the heartbeat time phases τ1 to τ4 collected in the three-dimensional subregions S1 to S4, and the obtained volume data is rendered. Thus, a wide range of heart rate synchronized 3D image data is generated. In the real-time three-dimensional scanning mode, volume data collected in the three-dimensional sub-region S2 selected from the three-dimensional sub-regions S1 to S4 is processed to generate a narrow-range real-time three-dimensional image data.

  Prior to generation of the heartbeat-synchronized three-dimensional image data, the operator of the ultrasonic diagnostic apparatus 100 attaches the ECG electrode provided in the biological signal detection unit 7 to the body surface of the subject, and then inputs the subject information at the input unit 9. Input, volume data generation conditions in heart rate synchronized 3D scanning mode and real time 3D scan mode, settings of 3D image data generation conditions and 3D image data display conditions, number of segments Sn and heart rate in heart rate synchronized 3D scan mode Sets the number of phases Hn. And these input information and setting information are preserve | saved at the memory | storage circuit of the system control part 12 (step S1 of FIG. 7).

  When the above initial setting is completed, the operator sets the biological signal detection unit 7 in an operating state and starts measuring the electrocardiographic waveform of the subject. Further, the input unit 9 generates a 3D image data generation start command. Enter. Then, when this command signal is supplied to the system control unit 12, collection of real-time 3D image data for the 3D sub-region S2 for the purpose of adjusting the image quality condition is started (step S2 in FIG. 7).

  When collecting real-time three-dimensional image data, the scanning control unit 11 supplies a control signal for ultrasonically scanning the three-dimensional sub-region S2 to the transmission delay circuit 212 and the reception delay circuit 222 of the transmission / reception unit 2.

  That is, the rate pulse generator 211 of the transmission unit 21 that has received the 3D image data generation start command via the system control unit 12 generates a rate pulse of a predetermined cycle based on the instruction signal supplied from the system control unit 12. It is generated and supplied to the transmission delay circuit 212. The transmission delay circuit 212 includes a focusing delay time for focusing the ultrasonic wave to a predetermined depth based on the scanning control signal supplied from the scanning control unit 11, and the first ultrasonic transmission / reception direction in the three-dimensional subregion S2. A deflection delay time for transmitting an ultrasonic wave at (θ1, φ1) is given to the rate pulse, and this rate pulse is supplied to the drive circuit 213 of the Mt channel. The drive circuit 213 generates a drive signal based on the rate pulse supplied from the transmission delay circuit 212, and supplies this drive signal to the Mt transmitting vibration elements provided in the ultrasonic probe 3 so as to be within the subject. Transmitting ultrasonic waves to A part of the transmitted ultrasonic wave is reflected by the organ boundary surface or tissue of the subject having different acoustic impedance, and is received by the Mr receiving vibration elements provided in the ultrasonic probe 3 to be used in the Mr channel. It is converted into an electrical reception signal.

  Next, the received signal is converted into a digital signal by the A / D converter 221 of the receiving unit 22, and further focused by the Mr channel reception delay circuit 222 to converge received ultrasonic waves from a predetermined depth. The delay time for deflection and the deflection delay time for setting a strong reception directivity with respect to the reception ultrasonic wave from the ultrasonic transmission / reception direction (θ1, φ1) in the three-dimensional sub-region S2 are supplied from the scan control unit 11 described above. After being given based on the control signal, the adder 223 performs phasing addition. Then, the amplification circuit 41, the envelope detector 42 and the logarithmic converter 43 of the reception signal processing unit 4 to which the reception signal after the phasing addition is supplied perform amplification, envelope detection and logarithmic conversion on the reception signal. The B mode data is generated, and the obtained B mode data is stored in the ultrasonic data storage unit 511 of the sub-volume data generation unit 51 with the ultrasonic transmission / reception direction (θ1, φ1) as supplementary information.

  Next, the scanning control unit 11 controls the delay times in the transmission delay circuit 212 and the reception delay circuit 222 of the transmission / reception unit 2 to sequentially update the ultrasonic waves in the three-dimensional sub-region S2 by Δθ in the θ direction and Δφ in the φ direction. Transmission / reception direction (θp, φq) (θp = θ1 + (p−1) Δθ (p = 1 to P), φq = φ1 + (q−1) Δφ (q = 1 to Q), provided that the ultrasonic transmission / reception direction (θ1 ), Except for φ1), three-dimensional scanning is performed by transmitting and receiving ultrasonic waves in the same procedure. The B-mode data obtained in each transmission / reception direction is also stored in the ultrasonic data storage unit 511 with the above-described ultrasonic transmission / reception direction as supplementary information.

  When the generation and storage of the B-mode data in the three-dimensional sub-region S2 is completed by the above-described procedure, the interpolation processing unit 512 of the sub-volume data generation unit 51 reads the plurality of B-mode data read from the ultrasonic data storage unit 511. Are transmitted and received in the three-dimensional sub-region S2 (θp, φq) (θp = θ1 + (p−1) Δθ (p = 1 to P), φq = φ1 + (q−1) Δφ (q = 1 to Q) ) To form three-dimensional B-mode data, and further, volume data composed of isotropic voxels by interpolating non-uniformly spaced voxels constituting the three-dimensional B-mode data. Is generated. Then, the obtained volume data is temporarily stored in the volume data storage unit 522 of the volume data generation unit 52 (step S3 in FIG. 7).

  On the other hand, the volume data processing unit 53 renders the volume data of the 3D sub-region S2 read from the volume data storage unit 522 of the volume data generation unit 52 to generate real-time 3D image data in a narrow range, and displays the display unit. 6 is displayed on the monitor 6 (step S4 in FIG. 7). Then, by repeating Step S3 and Step S4 described above, the display unit 6 displays the real-time 3D image data generated in the 3D sub-region S2 in real time as a moving image.

  Next, the operator uses the image quality condition input function 91 of the input unit 9 to input image quality conditions such as gain and dynamic range under the observation of real-time 3D image data displayed on the display unit 6. The input image quality condition is stored in the image quality condition storage section provided in the update timing detection section 10 via the system control section 12, and further supplied to the reception signal processing section 4 to set the image quality condition. (Step S5 in FIG. 7). By repeatedly generating and displaying the real-time 3D image data in steps S3 and S4 and setting the image quality conditions in step S5, the image quality conditions for the heartbeat synchronized 3D image data are initialized.

  When the initial setting of the image quality condition is completed, the operator inputs an initial setting end command for the image quality condition at the input unit 9 and this command signal is supplied to the system control unit 12 to thereby beat the heart rate for the three-dimensional region S0. Generation and display of synchronous three-dimensional image data is started.

  When generating the heartbeat-synchronized 3D image data, the scanning control unit 11 ultrasonically scans the 3D sub-regions S1 to S4 with respect to the rate pulse generator 211, the transmission delay circuit 212, and the reception delay circuit 222 of the transmission / reception unit 2. The control signal is supplied.

  That is, the rate pulse generator 211 of the transmission unit 21 that receives the heart rate synchronization signal generated by the heart rate synchronization signal generation unit 8 based on the electrocardiographic waveform obtained from the subject via the system control unit 12 A rate pulse having a predetermined repetition period in synchronization with the synchronization signal is generated and supplied to the transmission delay circuit 212. Then, subvolume data in the heartbeat time phases τ1 to τ4 of the three-dimensional region S0 (that is, the three-dimensional subregions So1 to So4) is generated by the same procedure as in step S3 described above. The area is stored as supplementary information in the sub volume data storage unit 513 of the sub volume data generation unit 51 (step S6 in FIG. 7).

  Next, the volume data generation unit 52 reads the sub volume data stored in the sub volume data storage unit 513 and the above-mentioned supplementary information, and synthesizes these sub-volume data based on the supplementary information to form a wide three-dimensional area S0. Volume data is generated (step S7 in FIG. 7). On the other hand, the volume data processing unit 53 renders the volume data sequentially supplied from the volume data generation unit 52 by the same procedure as in step S4 described above to generate heartbeat synchronized 3D image data and displays it on the display unit 6. (Step S8 in FIG. 7). Then, by repeating the above steps S6 to S8, the heartbeat synchronized 3D image data generated in the 3D region S0 is displayed on the display unit 6 as a moving image. However, in this case, the subvolume data in the three-dimensional subregions S1 to S4 is repeatedly collected in time series as shown in FIG. 5, and the old volume data collected in the same three-dimensional subregion is newly collected. New volume data is generated at a rate period To by sequentially updating the volume data.

  On the other hand, the image quality condition comparison unit of the update timing detection unit 10 compares the image quality condition newly supplied from the input unit 9 with the image quality condition already set in step S5 and stored in its own image quality condition storage unit. Then, the update start timing of the image quality condition is detected by detecting the difference (step S9 in FIG. 7).

  That is, when a new image quality condition is input by the image quality condition input function 91 of the input unit 9, the image quality condition comparison unit of the update timing detection unit 10 determines the new image quality condition supplied from the input unit 9 and its own image quality condition. The update start timing of the image quality condition is detected by detecting a difference from the image quality condition stored in the storage unit. Next, the scanning control unit 11 that has received the detection result via the system control unit 12 transmits a scanning control signal for making a transition from the heartbeat-synchronized three-dimensional scanning mode to the real-time three-dimensional scanning mode. And supplied to the reception delay circuit 222.

  Next, volume data generation and real-time three-dimensional image data generation and display for the three-dimensional sub-region S2 are performed in the same procedure as in steps S3 and S4 described above, and the real-time three-dimensional image data displayed on the display unit 6 is displayed. Under observation, the image quality condition is updated using the image quality condition input function 91 of the input unit 9 (steps S3 to S5 in FIG. 7). Steps S3 to S5 are repeated until real-time three-dimensional image data having a desired image quality is obtained.

  If the desired real-time three-dimensional image data is obtained by updating the image quality condition according to the above procedure, the new input of the image quality condition in the input unit 9 is stopped, and the image quality condition comparison unit of the update timing detection unit 10 By confirming that there is no difference between the image quality condition supplied from the unit 9 and the image quality condition stored in its own image quality condition storage unit in a predetermined period, the update end timing of the image quality condition is detected.

  Next, the scan control unit 11 that has received the detection result via the system control unit 12 transmits a scan control signal for making a transition from the real-time three-dimensional scan mode to the heartbeat-synchronized three-dimensional scan mode. And supplied to the reception delay circuit 222. Then, volume data in the three-dimensional region S0 and heartbeat-synchronized three-dimensional image data are generated and displayed in the same procedure as in steps S6 to S8 described above (steps S6 to S8 in FIG. 7).

  On the other hand, when no difference between the image quality condition supplied from the input unit 9 and the image quality condition stored in the image quality condition storage unit of the update timing detection unit 10 is found in step S9 described above, steps S6 to S8 are performed. By repeating, the generation of volume data in the three-dimensional region S0 and the generation and display of heartbeat-synchronized three-dimensional image data are continuously performed (steps S6 to S9 in FIG. 7).

  According to the embodiment of the present invention described above, when image quality conditions such as gain are updated in the process of collecting a wide range of three-dimensional image data by heartbeat-synchronized three-dimensional scanning, the heartbeat synchronization 3 is based on the detection signal of the update start timing. By automatically switching from the three-dimensional scanning mode to the real-time three-dimensional scanning mode, updating to a suitable image quality condition can be performed accurately and easily under observation of a narrow range of three-dimensional image data by real-time three-dimensional scanning.

  Also, by automatically switching from the real-time 3D scanning mode to the heartbeat synchronized 3D scan mode based on the detection signal of the update end timing, it is easy to change to the heartbeat synchronized 3D scan mode in which the image quality condition is adjusted to a suitable state. Can return. Accordingly, it is possible to efficiently collect high-quality heart-synchronized three-dimensional image data.

  In particular, since setting and updating of image quality conditions are performed based on real-time 3D image data having the same performance as heartbeat synchronized 3D image data collected in the heartbeat synchronized 3D scanning mode, the heart rate synchronized 3D image data It is possible to easily set image quality conditions suitable for a short time.

  Therefore, according to the above-described embodiment, not only the inspection efficiency or the diagnostic efficiency is improved, but also the burden on the operator in the ultrasonic inspection can be greatly reduced.

  As mentioned above, although the Example of this invention has been described, this invention is not limited to the above-mentioned Example, It can change and implement. For example, in the above-described embodiment, the reception signal obtained from the subject is processed to generate B-mode data as ultrasound data, and based on the B-mode data, the heart rate synchronization three-dimensional scanning mode and the real-time three-dimensional scanning are performed. Although the case of generating mode volume data has been described, the present invention is not limited to this, and the volume data described above may be generated based on other ultrasonic data such as color Doppler data.

  In the real-time three-dimensional scanning mode, one or a plurality of three-dimensional sub-regions selected from a plurality of three-dimensional sub-regions composing a wide range of three-dimensional regions in the heartbeat synchronous three-dimensional scanning mode are real-time three-dimensional. Although the case where scanning is performed has been described, real-time three-dimensional scanning may be performed on a narrow three-dimensional region arbitrarily set so that real-time display is possible. Further, in the real-time three-dimensional scanning mode, volume data in a desired three-dimensional region can be displayed in real time by performing three-dimensional scanning with a shallower depth of field or three-dimensional scanning with a coarser scanning density than the heartbeat synchronous three-dimensional scanning mode. It may be collected within the possible time.

  In addition, when real-time three-dimensional scanning is performed on a three-dimensional sub-region selected from a plurality of three-dimensional sub-regions constituting the three-dimensional region in the heartbeat-synchronized three-dimensional scanning mode, the image quality condition update start timing is detected. A method of performing real-time three-dimensional scanning on a three-dimensional sub-region in the heartbeat-synchronized three-dimensional scanning mode, which has been scanned at the time, is not particularly limited.

  On the other hand, in the above-described embodiment, the case has been described in which the volume data in the heartbeat-synchronized three-dimensional scanning mode and the real-time three-dimensional scanning mode is collected using the ultrasonic probe 3 in which the vibrating elements are two-dimensionally arranged. The volume data described above may be collected by mechanically moving one-dimensionally arranged ultrasonic probes at high speed.

  Further, although the case where the image quality condition is set and updated by adjusting the gain and dynamic range for the received signal has been described, the present invention is not limited to this. Further, the case where the above-described image quality condition is adjusted by controlling the amplifier circuit 41, the envelope detector 42, and the logarithmic converter 43 of the received signal processing unit 4 has been described. Other methods may be used.

2. Transmission / reception unit 21 ... Transmission unit 211 ... Rate pulse generator 212 ... Transmission delay circuit 213 ... Drive circuit 22 ... Reception unit 221 ... A / D converter 222 ... Reception delay circuit 223 ... Adder 3 ... Ultrasonic probe 4 ... Received signal processing unit 41 ... amplifier circuit 42 ... envelope detector 43 ... logarithmic converter 5 ... image data generation unit 51 ... sub-volume data generation unit 52 ... volume data generation unit 53 ... volume data processing unit 6 ... display unit 7 ... Biological signal measurement unit 8 ... heart rate synchronization signal generation unit 9 ... input unit 91 ... image quality condition input function 10 ... update timing detection unit 11 ... scanning control unit 12 ... system control unit 100 ... ultrasonic diagnostic apparatus

Claims (10)

In an ultrasonic diagnostic apparatus that generates time-series heartbeat-synchronized three-dimensional image data based on volume data collected from a three-dimensional region of a subject by heartbeat-synchronized three-dimensional scanning,
An image quality condition input means for inputting a new image quality condition in the process of collecting the heartbeat synchronized 3D image data;
Update timing detection means for detecting an update start timing of the image quality condition based on the image quality condition input by the image quality condition input means;
Scanning control means for changing a scanning mode from the heartbeat-synchronized three-dimensional scanning to the real-time three-dimensional scanning based on the update start timing;
Display means for displaying the heartbeat synchronized 3D image data and the real time 3D image data obtained by the real time 3D scanning;
The ultrasonic diagnostic apparatus, wherein the image quality condition input means inputs an image quality condition suitable for the heartbeat-synchronized 3D image data based on the real-time 3D image data displayed by the display means.   The update timing detection unit detects an update end timing of the image quality condition based on the image quality condition input by the image quality condition input unit, and the scan control unit changes the scan mode from the real-time three-dimensional scan to the heart rate. The ultrasonic diagnostic apparatus according to claim 1, wherein control for returning to synchronous three-dimensional scanning is performed based on the update end timing.   The update timing detection unit detects the update start timing and the update end timing by comparing an image quality condition newly input by the image quality condition input unit with a previously input image quality condition. The ultrasonic diagnostic apparatus according to claim 2.   3. The ultrasonic diagnostic apparatus according to claim 2, wherein the update timing detection unit detects a predetermined time after the input of a new image quality condition is stopped by the image quality condition input unit as the update end timing.   The scanning control means performs control for effecting the real-time three-dimensional scanning on a three-dimensional area narrower than a wide three-dimensional area where the heartbeat synchronization three-dimensional scanning is performed based on the update start timing. The ultrasonic diagnostic apparatus according to claim 1.   The scanning control unit is configured to perform the real-time three-dimensional operation on one or a plurality of three-dimensional subregions selected from a plurality of three-dimensional subregions constituting a wide range of three-dimensional regions in which the heartbeat synchronization three-dimensional scanning is performed. The ultrasonic diagnostic apparatus according to claim 5, wherein control for effecting scanning is performed.   The scanning control means performs control for effecting real-time three-dimensional scanning on the three-dimensional sub-region in which the heartbeat-synchronized three-dimensional scanning is performed when the update start timing is detected. The ultrasonic diagnostic apparatus according to claim 6.   The scanning control means performs control for executing, as the real-time three-dimensional scanning, a three-dimensional scanning with a shallower visual field depth or a three-dimensional scanning with a coarser scanning density than the heartbeat-synchronized three-dimensional scanning based on the update start timing. The ultrasonic diagnostic apparatus according to claim 1, wherein the ultrasonic diagnostic apparatus is performed.   The ultrasonic diagnostic apparatus according to claim 1, wherein the image quality condition input unit inputs at least one of a gain and a dynamic range for the reception signal collected by the heartbeat synchronization three-dimensional scanning as the image quality condition. For an ultrasonic diagnostic apparatus that generates time-sequential heartbeat-synchronized three-dimensional image data based on volume data collected from a three-dimensional region of a subject by heartbeat-synchronized three-dimensional scanning,
An image quality condition input function for inputting a new image quality condition in the process of collecting the heartbeat synchronized 3D image data;
An update timing detection function for detecting an update start timing of the image quality condition based on the image quality condition input by the image quality condition input means;
A scanning control function for changing a scanning mode from the heartbeat-synchronized three-dimensional scanning to the real-time three-dimensional scanning based on the update start timing;
An image quality condition update control program for executing a display function for displaying the heartbeat synchronized 3D image data and the real time 3D image data obtained by the real time 3D scanning.

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