JP2009240701A - Ultrasonic diagnostic apparatus - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To highly efficiently collect subvolume data of a heartbeat synchronized three-dimensional scanning method. <P>SOLUTION: When sequentially collecting subvolume data in a plurality of three-dimensional sub regions by applying the heartbeat synchronized three-dimensional scanning method and generating sequential image data with respect to a wide-range three-dimensional region by synthesizing the acquired subvolume data based on the heartbeat time phase information, a trigger interval detection section 12 detects a trigger interval of sequential trigger signals generated by a trigger signal generation section 11 based on a waveform measured from a subject, a scanning condition updating section 13, when the heartbeat period based on the trigger interval is extremely different from a reference heartbeat period preset for a predetermined period, updates the scanning conditions such as the number of segments and the number of heartbeat time phases of the three-dimensional sub region based on the heartbeat synchronization. A scanning control section 15 collects the subvolume data based on the updated scanning conditions. <P>COPYRIGHT: (C)2010,JPO&INPIT

Description

The present invention relates to an ultrasonic diagnostic apparatus, and more particularly to an ultrasonic diagnostic apparatus that enables collection of image data for a three-dimensional region by applying a heartbeat-synchronized three-dimensional scanning method.

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 in which a plurality of vibration elements are two-dimensionally arranged (two-dimensional array ultrasonic probe)
Has been put to 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 collecting three-dimensional data (volume data) by ultrasonic transmission / reception for a desired three-dimensional region, it is necessary to repeat a large number of transmissions / receptions, and the time required for each transmission / reception 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 substantially determined by the sound velocity of the ultrasonic wave, 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, It is possible to reduce the time required for collecting volume data. 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. Further, these volume data are processed to obtain three-dimensional image data such as time-series volume rendering image data or MPR (Multi Planar Reconst
ruction) By generating image data, it is possible to observe three-dimensional information of the diagnosis target part in a desired heartbeat time phase as a moving image or a still image.
Japanese Patent Laid-Open No. 2001-170047

In the above-described heartbeat synchronization three-dimensional scanning method, when the heartbeat period of the electrocardiogram waveform obtained from the subject changes remarkably in time, or when it differs significantly from a preset reference heartbeat period, a plurality of It becomes difficult to synchronize and synthesize sub-volume data sequentially obtained from the three-dimensional sub-region, and it becomes impossible to generate high-quality volume data and three-dimensional image data.

In order to solve the above-mentioned problem, the heartbeat period of the electrocardiographic waveform measured in parallel with the collection of the subvolume data for the three-dimensional subregion of the subject is compared with a preset reference heartbeat period. In the case where the electrocardiogram waveform is significantly different, a method of interrupting the collection of the sub-volume data until an electrocardiogram waveform having a heartbeat period substantially equal to the reference heartbeat period is measured has been conventionally performed. If it cannot be obtained, it takes a lot of time to generate volume data and three-dimensional image data, and the inspection efficiency and diagnostic efficiency are remarkably lowered.

The present invention has been made in view of such conventional problems, and an object of the present invention is to sequentially collect a plurality of sub-volume data by applying a heartbeat-synchronized three-dimensional scanning method and obtain these sub-volumes. When generating time-series image data for a three-dimensional region by synthesizing volume data based on heartbeat time phase information, measurement is performed in time series from the subject in parallel with the collection of the sub-volume data. It is an object of the present invention to provide an ultrasonic diagnostic apparatus capable of synthesizing sub-volume data in a short time and accurately even when the cardiac cycle of an electrocardiographic waveform is significantly different from a preset reference cardiac cycle.

In order to solve the above-mentioned problem, the ultrasonic diagnostic apparatus according to the first aspect of the present invention applies a heartbeat synchronization three-dimensional scanning method to a plurality of three-dimensional sub-regions set for a three-dimensional region of a subject. In the ultrasonic diagnostic apparatus that collects image data in the three-dimensional region, trigger interval detection means for detecting a trigger interval of a trigger signal generated based on the electrocardiographic waveform of the subject;
Imaging condition updating means for updating imaging conditions for the preset three-dimensional area based on the trigger interval; scanning control means for controlling three-dimensional scanning for the three-dimensional sub-area based on the updated imaging conditions; It is characterized by having.

According to an eighth aspect of the present invention, there is provided an ultrasonic diagnostic apparatus according to the present invention, wherein the three-dimensional region is obtained by applying a heartbeat synchronization three-dimensional scanning method to a plurality of three-dimensional subregions set for a three-dimensional region of a subject. In the ultrasonic diagnostic apparatus for collecting image data in, a trigger interval detection means for detecting a trigger interval of a trigger signal generated based on the electrocardiographic waveform of the subject, and the electrocardiographic waveform based on the trigger interval An E / L state determination unit that determines an Early Trigger state or a Late Trigger state, and a three-dimensional scan that is three-dimensionally scanned in the Early Trigger state or the Late Trigger state of the electrocardiogram waveform based on the determination result of the E / L state determination unit It is characterized by comprising display means for displaying information on sub-regions.

According to the present invention, a plurality of subvolume data is sequentially collected by applying a heartbeat-synchronized three-dimensional scanning method, and the obtained subvolume data is synthesized based on the heartbeat time phase information. When generating time-series image data, the heartbeat period of the electrocardiogram waveform measured in time series from the subject in parallel with the collection of the sub-volume data is significantly greater than a preset reference heartbeat period. Even in different cases, the sub-volume data can be synthesized accurately in a short time. For this reason, the diagnostic efficiency and the diagnostic ability are greatly improved, and the burden on the subject and the operator is reduced.

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

The first feature of the ultrasonic diagnostic apparatus according to the present embodiment is that the heart rate synchronous three-dimensional scanning method is applied to sequentially collect sub-volume data in a plurality of three-dimensional sub-regions, and the obtained sub-volume data is used as the heart rate. When generating time-series three-dimensional image data for a wide range of three-dimensional regions by combining based on time-phase information, measurement is performed in time series from the subject in parallel with the collection of the sub-volume data. When the heartbeat period of the electrocardiogram waveform is significantly different from a preset reference heartbeat period, the three-dimensionally scanned three-dimensional subregion is displayed on the display unit separately from the other three-dimensional subregions. .

The second feature of the ultrasonic diagnostic apparatus of the present embodiment is that a heart measured in time series from the subject in parallel with the collection of the sub-volume data when generating the above-described three-dimensional image data. When the radio wave type heartbeat period is significantly different from a preset reference heartbeat period over a predetermined period, the imaging conditions such as the number of segments in the three-dimensional sub-region and the number of heartbeat phases are updated based on the heartbeat period. There is.

In the following embodiments, in order to simplify the description, four three-dimensional sub-regions So1 to So4 before the imaging condition update and six three-dimensional sub-regions Sa1 to Sa4 after the imaging condition update are performed.
Although the case where subvolume data of four heartbeat time phases τ1 to τ4 is collected for each of the six heartbeats 6 is described, the number of subregions (number of segments) and the number of heartbeat time phases are not limited to these.

In addition, a case where a reception signal obtained by ultrasonic transmission / reception with respect to a three-dimensional region is processed to generate B-mode data and three-dimensional image data of the three-dimensional region is generated based on the B-mode data will be described. Three-dimensional image data may be generated based on other ultrasonic data such as color Doppler data.

(Device configuration)
The configuration and basic operation 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 the overall configuration of the ultrasonic diagnostic apparatus, and FIGS. 2 and 6 are specific examples of a transmission / reception unit / reception signal processing unit and a sub-volume data generation unit included in the ultrasonic diagnostic apparatus. It is a block diagram which shows a structure.

An ultrasonic diagnostic apparatus 100 shown in FIG. 1 transmits an ultrasonic pulse (transmitted ultrasonic wave) to a three-dimensional region including a diagnosis target part of a subject, and an ultrasonic reflected wave (received ultrasonic wave) obtained by this transmission. ) Is converted into an electrical signal (received signal), and an ultrasonic probe 3 in which a plurality of vibration elements are two-dimensionally arranged, and a drive signal for transmitting an ultrasonic pulse in a predetermined direction of the subject are the vibration elements. Transmitting and receiving unit 2 for phasing and adding the reception signals of a plurality of channels obtained from these vibration elements, and reception signal processing unit 4 for processing the received signal after phasing addition and generating B-mode data, The sub-volume data is generated by arranging the B-mode data obtained by the three-dimensional scanning for each of the plurality of three-dimensional sub-regions set in the three-dimensional region in correspondence with the ultrasonic transmission / reception direction. A sub-volume data generation unit 5 for adding the identification information of the three-dimensional sub-region (hereinafter referred to as sub-region information) and the heartbeat time phase information to the obtained sub-volume data and storing it in its own storage circuit; A volume data generation unit 6 is provided that synthesizes a plurality of sub volume data supplied from the sub volume data generation unit 5 based on the sub region information and the heartbeat time phase information to generate time-series volume data.

The ultrasonic diagnostic apparatus 100 also includes an image data generation unit 7 that generates 3D image data based on the volume data supplied from the volume data generation unit 6, and a 3D image generated by the image data generation unit 7. Based on the data display and the Early Trigger information and Late Trigger information supplied from the trigger interval detector 12 described later, the Early Trigger state or Late
A display unit 8 for highlighting the three-dimensional sub-region in the Trigger state, input of subject information,
Setting of the number of Early Trigger and Late Trigger, setting of allowable fluctuation range with respect to the reference heartbeat cycle, selection of imaging condition update method, input of instruction signal (update instruction signal) for updating the imaging condition,
An input unit 9 for inputting various command signals and the like is further provided. Furthermore, a biological signal measuring unit 10 for measuring an electrocardiographic waveform of the subject, and a trigger signal generating unit 11 for generating a trigger signal based on the electrocardiographic waveform. A trigger interval detector 12 that detects a trigger interval (that is, a heartbeat cycle) of the trigger signal generated by the trigger signal generator 11, and an Early Trigger state and a Late Trigger state of the electrocardiogram waveform based on the detected trigger interval (E / L state) is determined, and if these states continue for a predetermined number of Early Triggers or Late Triggers, a shooting condition update unit 13 that updates a preset shooting condition based on the trigger interval; Trigger signal generator 11
The heartbeat time phase setting unit 1 sets the heartbeat time phase of the subject based on the trigger signal supplied from
4, the scanning control unit 15 that controls the ultrasonic scanning (that is, the ultrasonic transmission / reception direction) by the transmission / reception unit 2 based on the imaging conditions supplied from the imaging condition update unit 13, and the ultrasonic diagnostic apparatus 100 described above. The system control part 16 which controls each unit of these centrally is provided.

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, which converts an electric pulse (drive signal) into an ultrasonic pulse (transmitted ultrasonic wave) at the time of transmission, and converts an ultrasonic reflected wave (received ultrasonic wave) into an electric reception signal at the time of reception. It has the function to convert to. 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, an ultrasonic diagnostic apparatus 100 using the ultrasonic scanning probe 3 for sector scanning 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 described. May be used.

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 (phase matching) to the reception signal obtained from the vibration element. And a receiver 22 for performing addition.

The transmission unit 21 includes a rate pulse generator 211, a transmission delay circuit 212, and a drive circuit 213.
The rate pulse generator 211 generates a rate pulse for determining the repetition period of the transmission ultrasonic wave and supplies it to the transmission delay circuit 212. The transmission delay circuit 212 is composed of the same number of independent delay circuits as the Mt number of vibration elements used for transmission, and a focusing delay time for focusing the transmission ultrasonic wave to a predetermined depth and a predetermined direction (θp, A deflection delay time for transmission to φq) is given to the rate pulse 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 is M arrayed two-dimensionally by the ultrasonic probe 3.
Driving Mt (Mt ≦ M) vibrating elements selected for transmission from the vibrating elements;
Transmits ultrasonic waves into the body of the subject.

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

The reception delay circuit 222 has a focusing delay time for focusing the received ultrasonic wave from a predetermined depth and a deflection delay time for setting the reception directivity for a predetermined direction (θp, φq). /
An adder 223 adds the reception signals from the reception delay circuit 222 to each of the Mr channel reception signals output from the D converter 221. That is, the reception delay circuit 222 and the adder 2
23, the received signal obtained from the predetermined direction is phased and added. 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. Then, the transmission delay circuit 212 of the transmission unit 21 and the reception delay circuit 22 of the reception unit 22 according to the scanning control signal supplied from the scanning control unit 15.
2 is controlled, and ultrasonic transmission / reception with respect to a plurality of three-dimensional sub-regions is performed.

Next, a plurality of three-dimensional sub-regions set for the three-dimensional region of the subject and ultrasonic transmission / reception 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 scan set in the three-dimensional region S0 including the diagnosis target part of the subject. The three-dimensional region S0 is represented by the number of segments Sn (for example, Sn = By dividing in the y direction in 4), four three-dimensional sub-regions S1 to S4 are set. Then, by controlling the delay time of 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 15, the three-dimensional subregions S1 to S4 are controlled. A three-dimensional scan for each is performed.

On the other hand, FIG. 5 shows a specific example of ultrasonic transmission / reception (three-dimensional scanning) with respect to the above-described three-dimensional sub-regions S1 to S4, and FIG. 5 (a) is measured by the biological signal measurement unit 10. An electrocardiographic waveform having a uniform reference heartbeat period To, FIG. 5B is a trigger signal generated by the trigger signal generation unit 11 based on the R wave of the electrocardiographic waveform, and FIG. 5C is the trigger signal. 3 shows the order of three-dimensional scanning performed on each of the three-dimensional subregions S1 to S4 (see FIG. 4).

In this case, the imaging condition update unit 13 described later is based on the trigger interval To of the trigger signal supplied from the trigger interval detection unit 12 and the heartbeat time phase number Hn (for example, Hn = 4) supplied from the input unit 9. Data collection time δ of subvolume data in each of the heartbeat time phases τ1 to τ4
τ is set, and the number of segments Sn (Sn = 4) of the three-dimensional sub-region with respect to the three-dimensional region S0 is set as an imaging condition based on the data collection time δτ. However, heartbeat time phase τ1
Is a heartbeat time phase at which the three-dimensional scanning for the three-dimensional subregion S1 is started, and the heartbeat time phase τ2
Thru | or (tau) 4 has shown the heartbeat time phase from which the three-dimensional scanning with respect to each of three-dimensional sub-region S2 to S4 is started.

Then, the scanning control unit 15 to which the above setting information is supplied via the system control unit 16 controls the transmission / reception unit 2, and for the three-dimensional subregion S1 of the heartbeat time phases τ1 to τ4 in the period [t1-t2]. Three-dimensional scanning is sequentially performed, and further, a period [t2-t3], a period [t3-t4],
Three-dimensional subregions S2 to S4 of heartbeat time phases τ1 to τ4 in each of the periods [t4-t5]
Is subjected to a three-dimensional scan.

On the other hand, the volume data generation unit 6 described later performs the period [t1-t2] to the period [t4-t5.
] Three-dimensional sub-regions S1 to S generated based on ultrasonic transmission / reception in the heartbeat time phase τ1
The volume data in the heartbeat time phase τ1 is generated by synthesizing the four subvolume data,
Similarly, the sub-volume data of the three-dimensional sub-regions S1 to S4 generated based on the ultrasound transmission / reception in the heartbeat time phases τ2 to τ4 of the period [t1-t2] to the period [t4-t5] is synthesized to Volume data in each of the time phases τ2 to τ4 is generated.

Here, an electrocardiographic waveform having a uniform reference heartbeat period To is represented by three-dimensional sub-regions S1 to S1.
Although the heart-synchronized three-dimensional scanning method when obtained together with the sub-volume data of 4 has been described, the heart-synchronized three-dimensional scanning method when an electrocardiographic waveform in the Early Trigger state or the Late Trigger state is measured will be described later.

Returning to FIG. 2, the reception signal processing unit 4 has a function of generating B-mode data as ultrasonic data, and includes an envelope detector 41 and a logarithmic converter 42. The envelope detector 41 envelope-detects the reception signal after the phasing addition supplied from the adder 223 of the receiving unit 22, and the logarithmic converter 42 logarithmically converts the amplitude of the reception signal subjected to the envelope detection. To generate B-mode data. Note that the envelope detector 41 and the logarithmic converter 42 may be configured by changing the order.

Next, a specific configuration of the sub-volume data generation unit 5 shown in FIG. 1 will be described with reference to the block diagram of FIG.

The subvolume data generation unit 5 includes an ultrasonic data storage unit 51, an interpolation processing unit 52, and a subvolume data storage unit 53. The ultrasonic data storage unit 51 includes a three-dimensional subregion S1.
The B-mode data generated by the reception signal processing unit 4 based on the reception signal obtained by the three-dimensional scanning for each of S to S4 is sequentially stored with the ultrasonic transmission / reception direction (θp, φq) as supplementary information.

On the other hand, the interpolation processing unit 52 arranges a plurality of B-mode data read from the ultrasound data storage unit 51 in units of 3D sub-regions and heartbeat time phases in correspondence with ultrasound transmission / reception directions (θp, φq). The three-dimensional B-mode data is formed by, and further, the voxels at unequal intervals forming the three-dimensional B-mode data are interpolated to form isotropic voxels with respect to the x, y, and z directions. Generate subvolume data. The time-series subvolume data generated for each of the three-dimensional subregions includes the subregion information supplied from the system control unit 16 and the heartbeat time phase information supplied from the heartbeat time phase setting unit 14. It is stored in the sub volume data storage unit 53 as supplementary information.

Returning to FIG. 1 again, the volume data generation unit 6 includes an arithmetic circuit and a storage circuit (not shown). The arithmetic circuit reads out the subvolume data stored in the subvolume data storage unit 53 of the subvolume data generation unit 5 and the accompanying heartbeat time phase information and subregion information, and stores them in each of the three-dimensional subregions. A plurality of sub-volume data collected in this way is synthesized based on the above-mentioned supplementary information, and time-series volume data for a wide range of three-dimensional regions is generated. The obtained volume data is temporarily stored in the storage circuit.

Next, the image data generation unit 7 renders the volume data sequentially supplied from the volume data generation unit 6 in the heartbeat-synchronized three-dimensional scanning mode to generate three-dimensional image data such as volume rendering image data and surface rendering image data. For example, an opacity / color tone setting unit and a rendering processing unit (not shown) are provided. The opacity / color tone setting unit sets the opacity and color tone of each voxel based on the voxel value of volume data, and the rendering processing unit sets the opacity set by the opacity / color tone setting unit. Then, the volume data having the color tone is rendered using a predetermined processing program to generate time-series three-dimensional image data.

The display unit 8 includes a display data generation unit, a data conversion unit, and a monitor (not shown). The display data generation unit is an Early Trigger state or Lat determined by the imaging condition update unit 13.
e. Display data for monitoring in which the three-dimensional subregion corresponding to the electrocardiogram waveform in the trigger state is emphasized, and additional information such as subject information is added to the three-dimensional image data generated by the image data generation unit 7. In addition, display data for diagnosis is generated. The data converter performs D / A conversion and display 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 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 an update method selection unit 91 that selects an update method of the shooting conditions, Number of Early Trigger En and Late Trigger to determine the update of
An E / L number setting unit 92 that sets the number of times Ln, an allowable variation range setting unit 93 that sets an allowable variation range ΔT of the reference heartbeat period, and an update instruction unit 94 that instructs to update imaging conditions are provided.
Furthermore, input of object information, setting of the three-dimensional region S0, input of various command signals, and the like are performed using the above-described input device and display panel.

The imaging conditions include the number of segments Sn (or segment width) and the heartbeat time phase number Hn of the three-dimensional sub-region, and the imaging conditions updated by the imaging condition update unit 13 are automatically set as a method for updating these imaging conditions. And an update instruction signal input from the above-described update instruction unit 94 by an operator who has observed information on the three-dimensional subregion corresponding to the electrocardiogram waveform in the Early Trigger state or the Late Trigger state on the display unit 8. And manually setting the updated shooting conditions.

FIG. 7 shows a specific example of the update method selection unit 91. The update method selection unit 91 includes an automatic update selection unit 911 and a manual update selection unit 912. When the automatic update selection unit 911 is selected in the initial setting or the like, the imaging condition update unit 13 updates the imaging condition (for example, the number of segments) based on the detection result of the trigger interval supplied from the trigger interval detection unit 12. By supplying Sn) to the system control unit 16, a three-dimensional scan for each of the three-dimensional sub-regions based on the updated imaging conditions is started.

In this case, the imaging condition update unit 13 determines whether or not the electrocardiogram waveform is in the Early Trigger state or the Late Trigger state based on the trigger interval of the trigger signal supplied from the trigger interval detection unit 12, and these triggers The state is the number of Early Triggers En or Late Trigge
If it continues for r times Ln, the imaging condition is updated based on the trigger interval.

On the other hand, when the manual update selection unit 912 is selected, the imaging condition update unit 13 updates the imaging conditions according to the same procedure as described above, and the system control unit 1 from the update instruction unit 94 of the input unit 9.
In accordance with the above update instruction signal supplied via 6, the system controller 1
6 to start 3D scanning for each of the 3D sub-regions based on the updated imaging conditions. Specifically, information on a three-dimensional sub-region that has been three-dimensionally scanned in the heartbeat cycle of the electrocardiogram waveform in the Early Trigger state or the Late Trigger state is highlighted on the monitor of the display unit 8, and When highlighting of the dimension sub-region is continuously performed for a predetermined period, an instruction signal for updating the imaging condition is input from the update instruction unit 94.

The biological signal measurement unit 10 has a function of measuring an electrocardiogram waveform of the subject, and an ECG electrode that is mounted on the surface of the subject body to detect the electrocardiogram waveform and an electrocardiogram waveform detected by the ECG electrode. An amplifying circuit for amplifying to a predetermined amplitude and an A / D converter (none of which is shown) for converting the amplified electrocardiographic waveform into a digital signal are provided.

On the other hand, the trigger signal generation unit 11 detects an R wave of the electrocardiogram waveform by comparing the amplitude of the electrocardiogram waveform with a predetermined threshold, for example, and generates a trigger signal based on the R wave. The generation of the trigger signal is usually performed at the same timing as the R wave, but may be a timing delayed by a predetermined time from the R wave. The trigger interval detection unit 12 detects the trigger interval in the time-series trigger signal supplied from the trigger signal generation unit 11.

Next, the imaging condition update unit 13 includes an E / L state determination unit 131, an E / L state counting unit 132, and an imaging condition setting unit 133. The E / L state determination unit 131 is configured by the trigger interval detection unit 12. The electrocardiogram waveform used to generate the trigger signal is in the Early Trigger state or the Late Trigger state by comparing the trigger interval of the detected trigger signal with the lower limit value and upper limit value of the preset heartbeat cycle. It is determined whether or not. On the other hand, the E / L state counting unit 132
/ Early Trigger state or Late Trigger state determined by the L state determination unit 131 is counted. Then, when the determination for the Early Trigger state is repeated a predetermined number of times (En times) in a plurality of continuous heartbeat cycles, the shooting condition setting unit 133 sets the shooting conditions set in advance to a heartbeat cycle suitable for the Early Trigger state. Update to conditions. Similarly, Late Tr
When the determination for the igger state is repeated a predetermined number of times (Ln times) in a plurality of consecutive heartbeat cycles, the shooting condition setting unit 133 updates the preset shooting conditions to the shooting conditions suitable for the heartbeat cycle in the Late Trigger state. To do.

FIG. 8 is a diagram for explaining the heartbeat cycle of the electrocardiogram waveform in the Early Trigger state or the Late Trigger state. FIG. 8A is supplied from the reference heartbeat period To of the electrocardiogram waveform and the input unit 9. The lower limit value Tmin and the upper limit value Tmax set around the reference heartbeat period To based on the allowable fluctuation range ΔT of the reference heartbeat period. On the other hand, FIG. 8B shows an electrocardiogram waveform in the Early Trigger state having a heartbeat period Txa smaller than the lower limit value Tmin.
(C) shows an electrocardiographic waveform in the Late Trigger state having a heartbeat period Txb larger than the upper limit value Tmax.

That is, the imaging condition update unit 13 compares the trigger interval of the trigger signal generated based on the electrocardiographic waveform of the subject with the lower limit value Tmin and the upper limit value Tmax of the heartbeat period. When the trigger interval is smaller than the lower limit value Tmin, it is determined that the electrocardiographic waveform used to generate the trigger signal is in the Early Trigger state, and when the trigger interval is larger than the upper limit value Tmax, It is determined that the electrocardiographic waveform used for generation is in the Late Trigger state.

Next, the heartbeat time phase setting unit 14 in FIG. 1 sets the trigger signal supplied from the trigger signal generation unit 11 and the imaging condition initially set in the input unit 9 or the imaging condition updated in the imaging condition update unit 13. Based on each of the three-dimensional sub-regions S1 to S4 having the number of segments Sn (Sn = 4), the heartbeat time phases τ1 to τ4 having the heartbeat time phase number Hn (Hn = 4) are set. Then, the information on the heartbeat time phases τ1 to τ4 is supplied to the subvolume data generation unit 5, and the three-dimensional subregion S1.
To the time-series subvolume data obtained from each of S4 to S4.

On the other hand, the scanning control unit 15 is based on the imaging conditions supplied from the imaging condition update unit 13 or the input unit 9 via the system control unit 16, and a plurality of three-dimensional subs set in the three-dimensional region S0 of the subject. Scan control for performing ultrasonic scanning on the region is performed on the transmission delay circuit 212 of the transmission unit 21 and the reception delay circuit 222 of the reception unit 22.

The system control unit 16 includes a CPU and a storage circuit (not shown), and various information input / set / selected by the input unit 9 is stored in the storage circuit. The CPU controls each unit of the ultrasonic diagnostic apparatus 100 based on the input / setting / selection information described above, and controls the heartbeat-synchronized 3D scanning mode for the purpose of generating a wide range of 3D image data. This is performed based on a trigger signal obtained from an electrocardiogram waveform.

Next, the cardiac cycle of the electrocardiographic waveform obtained from the subject in time series is determined from the reference cardiac cycle To.
A method for updating the imaging condition when the heartbeat period Txa is changed to the Early Trigger state (see FIG. 8) will be described with reference to FIG.

9A shows an electrocardiogram waveform measured by the biological signal measurement unit 10, FIG. 9B shows a trigger signal generated by the trigger signal generation unit 11 based on the R wave of the electrocardiogram waveform, and FIG. (C)
Is sub-volume data collected in the three-dimensional sub-region of the imaging condition set or updated based on the trigger interval of the trigger signal, and FIG. 9D is a three-dimensional image of the imaging condition before and after the update. Each sub-region is shown.

For example, an electrocardiographic waveform having a reference heartbeat period To continuously measured until time t2 has an earl having a heartbeat period Txa smaller than the lower limit value Tmin of the heartbeat period due to body movement or the like of the subject.
y When the ECG waveform changes to the Trigger state, this Early Trigger state changes to the specified Early Trigger
Number of segments Sno at time t4 repeated r times En (for example, En = 2)
The shooting condition of (Sno = 4) is updated to the shooting condition of the number of segments Sna (Sna = 6).

In this case, the subvolume data So11 to So14 of the heartbeat time phases τ1 to τ4 in the three-dimensional subregion So1 are sequentially generated in the period [t1-t2] before the imaging condition update. Next, the heartbeat period Txa is set to a new reference heartbeat period with the update of the imaging condition at time t4, and the three-dimensional subregions Sa2 to Sa6 and S6 formed with the number of segments Sna = 6.
Sub-volume data Sa21 to Sa24, Sa of heartbeat time phases τ1 to τ4 at a1
31 to Sa34,... Sa61 to Sa64 and Sa11 to Sa14 are sequentially generated.

In FIG. 9, subvolume data So11 to So14 of the three-dimensional subregion So1 are collected in the period [t1-t2], and 3 adjacent to the three-dimensional subregion So1 in the period [t4-t5] after the imaging condition update. Although the case of collecting the sub-volume data of the dimension sub-region Sa2 has been shown, the present invention is not limited to this. For example, the period [t4-t5], the period [t
5-t6], period [t6-t7]... 3D sub-region Sa1 after imaging condition update
, Sa2, Sa3... May be collected sequentially.

Next, a specific example of the three-dimensional sub-region in the Early Trigger state displayed on the monitor of the display unit 8 is shown in FIG.

In this case, the display unit 8 shows scanning states for the three-dimensional sub-regions So1 to So4 before the imaging condition update and the three-dimensional sub-regions Sa1 to Sa6 after the imaging condition update observed from the x direction in FIG.

For example, as illustrated in FIG. 9, when the trigger interval of the trigger signal supplied from the trigger signal generation unit 11 in the period [t1-t2] is within the allowable variation range of the reference heartbeat period To, 3
Three-dimensional scanning is performed on the three-dimensional sub-region So1 according to the imaging conditions before the update, and the three-dimensional sub-region So1 subjected to the three-dimensional scanning is displayed on the monitor of the display unit 8 by the color A. Next, when a trigger signal having a heartbeat period Txa smaller than the lower limit value Tmin is supplied from the trigger signal generation unit 11 after the time t2 when the three-dimensional scanning for the three-dimensional subregion So2 adjacent to the three-dimensional subregion So1 is started. In the period [t2-t4] in which the count of the Early Trigger state that affects the number of Early Trigger En (En = 2) and the update of the imaging conditions based on the count result are performed, the three-dimensional sub-region So2 of the display unit 8 is Early Trigger. State (ie
Displayed by color B indicating subvolume data collection interruption).

Further, in the period [t4-t5], the three-dimensional scanning is performed on the three-dimensional sub-region Sa2 of the imaging condition updated with the heartbeat period Txa as the reference heartbeat period.
The three-dimensional scanning is sequentially performed on the three-dimensional sub-regions Sa3, Sa4, Sa5... Under the updated imaging conditions at each of 5-t6], [t6-t7], [t7-t8].
The three-dimensional sub-regions Sa2, Sa3, Sa4.
It is displayed on the monitor of the display unit 8 with the same color A as that of the three-dimensional sub-region So1 at t1-t2].

In this case, the three-dimensional region S0 having the segment number Sno (Sno = 4) is displayed on the display unit 8 before the imaging condition update, and the segment number Sna (Sna) is displayed on the display unit 8 after the imaging condition update.
= 3) is displayed. And Early Trig in 3D area S0
The three-dimensional sub-region So2 in the ger state is highlighted with the color B.

9 and 10 show the case where the electrocardiogram waveform is in the Early Trigger state, but in the case of the Late Trigger state, the imaging conditions are updated and the three-dimensional sub-region is displayed by the same procedure. .

(3D image data generation / display procedure)
Next, a procedure for generating / displaying three-dimensional image data for the subject to which the heartbeat synchronization three-dimensional scanning mode is applied will be described with reference to the flowchart of FIG. For the sake of simplicity, subvolume data of heartbeat time phases τ1 to τ4 is collected in the three-dimensional subregions So1 to So4 before the imaging condition update and the three-dimensional subregions Sa1 to Sa6 after the imaging condition update. However, the present invention is not limited to this.

Prior to the generation of three-dimensional image data in the heartbeat-synchronized three-dimensional scanning mode, the ultrasonic diagnostic apparatus 1
00 input the subject information in the input unit 9, and then set the three-dimensional region S0, Ea
Setting of rly Trigger number En and Late Trigger number Ln, setting of permissible fluctuation range ΔT with respect to the reference heart cycle, and selection of an imaging condition update method are performed as necessary. The input information, setting information, and selection information are stored in the storage circuit of the system control unit 16 (
Step S1) in FIG.

When the above initial setting is completed, the operator wears the ECG electrode provided in the biological signal measurement unit 10 on the surface of the subject body and measures the electrocardiogram waveform, and the trigger signal generator 11 A trigger signal is generated based on the R wave detected by comparing the radio wave shape with a predetermined threshold value. Then, the trigger interval detection unit 12 detects the trigger interval of the time-series trigger signal supplied from the trigger signal generation unit 11, and the imaging condition update unit 13 or the system control unit 16 uses this trigger interval as a reference heartbeat cycle. The first imaging condition (ie, three-dimensional sub-regions So1 to S as To)
o4 and heartbeat time phases τ1 to τ4) are set.

Next, the operator inputs a 3D image data generation start command at the input unit 9, and the command signal is supplied to the system control unit 16 to start generation of 3D image data (FIG. 11). Step S2).

Upon generating the three-dimensional image data, the scanning control unit 15 that has received the above-described imaging conditions via the system control unit 16 transmits the transmission delay circuit 212 of the transmission unit 21 and the reception delay circuit 2 of the reception unit 22.
22 is supplied with scanning control signals corresponding to the three-dimensional sub-regions So1 to So4.

That is, the rate pulse generator 211 of the transmission unit 21 that has received the trigger signal generated by the trigger signal generation unit 11 via the system control unit 16 synchronizes the reference signal separately supplied from the system control unit 16 with the trigger signal. Then, by dividing the frequency, a rate pulse synchronized with the electrocardiogram waveform is generated and supplied to the transmission delay circuit 212. The transmission delay circuit 212 is connected to the scanning control unit 15.
A focusing delay time for focusing the ultrasonic wave to a predetermined depth based on the scanning control signal supplied from the first ultrasonic transmission / reception direction (θ1,.
A deflection delay time for transmitting an ultrasonic wave to φ1) is given to the rate pulse, and this rate pulse is supplied to the drive circuit 213 of the Mt channel. Next, 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 to be covered. Transmit ultrasonic waves into the specimen.

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, this received signal is received by the receiving unit 2.
2 is converted into a digital signal by the A / D converter 221, and further, a focusing delay time for converging the received ultrasonic wave from a predetermined depth in the reception delay circuit 222 of the Mr channel and the ultrasonic transmission / reception direction (θ 1 , Φ1), a deflection delay time for setting a strong reception directivity with respect to the received ultrasonic wave is given based on the scanning control signal supplied from the scanning control unit 15 and then adjusted by the adder 223. Phase addition. Then, the envelope detector 41 and the logarithmic converter 42 of the received signal processing unit 4 to which the received signal after the phasing addition is supplied perform envelope detection and logarithmic conversion on the received signal to obtain B-mode data. The generated B-mode data is stored in the ultrasonic data storage unit 51 of the sub-volume data generation unit 5 with the ultrasonic transmission / reception direction (θ1, φ1) as supplementary information.

Next, the scanning control unit 15 controls 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 to sequentially update the three-dimensional subregion by Δθ in the θ direction and Δφ in the φ direction. S1 ultrasonic transmission / reception direction (θp, φq) (θp = θ1 + (p−1) Δθ
(P = 1 to P), φq = φ1 + (q−1) Δφ (q = 1 to Q), except for ultrasonic transmission / reception directions (θ1, φ1)). Transmit and receive and perform 3D scanning. The B-mode data obtained in each transmission / reception direction is also stored in the ultrasonic data storage unit 51 of the sub-volume data generation unit 5 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 subregion So1 of the heartbeat time phases τ2 to τ4 is completed by the same procedure, the interpolation processing unit 52 of the subvolume data generation unit 5 reads from the ultrasonic data storage unit 51. The plurality of read B-mode data are converted into the ultrasonic transmission / reception direction (θ
p, φq) (θp = θ1 + (p−1) Δθ (p = 1 to P), φq = φ1 + (q−1) Δφ
(Q = 1 to Q)) is arranged to form three-dimensional B-mode data, and further, isotropic processing is performed by interpolating unequally spaced voxels constituting the three-dimensional B-mode data. Sub-volume data So11 to So14 composed of voxels is generated (step S3 in FIG. 11).

On the other hand, the trigger interval detection unit 12 detects the trigger interval in the time-series trigger signal supplied from the trigger signal generation unit 11 (step S4 in FIG. 11), and E of the imaging condition update unit 13
The / L state determination unit 131 compares the trigger interval of the trigger signal detected by the trigger interval detection unit 12 with the lower limit value Tmin and the upper limit value Tmax of the heartbeat period set in advance based on the allowable variation range ΔT. Therefore, the electrocardiogram waveform used to generate the trigger signal is
It is determined whether it is in the igger state or the Late Trigger state (step S5 in FIG. 11).
.

If the electrocardiogram waveform measured at this time does not correspond to either the Early Trigger state or the Late Trigger state, the sub-volume data So11 to So14 generated in the heartbeat time phases τ1 to τ4 of the three-dimensional subregion So1 are The heartbeat time phase information supplied from the heartbeat time phase setting unit 14 and the three-dimensional sub-region S supplied from the system control unit 16
The sub-region information o1 is stored as supplementary information (step S8 in FIG. 11) in the sub-volume data storage unit 53 of the sub-volume data generation unit 5 (step S9 in FIG. 11). Furthermore, collection and storage of subvolume data in the heartbeat time phases τ1 to τ4 of the three-dimensional subregions So2 to So4 adjacent to the three-dimensional subregion So1 are performed by the same procedure.

When the collection and storage of the 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) are finished, the volume data generation unit 6
Reads out the subvolume data, heartbeat time phase information, and subregion information stored in the subvolume data storage unit 53 of the subvolume data generation unit 5. Then, these sub-volume data are synthesized based on the above-mentioned supplementary information to generate time-series volume data for a wide range of three-dimensional area S0 (step S10 in FIG. 11).

Next, the image data generation unit 7 renders the volume data sequentially supplied from the volume data generation unit 6 in the heartbeat-synchronized 3D scanning mode to generate 3D image data, and displays the obtained 3D image data The data is displayed on the monitor of the unit 8 (step S11 in FIG. 11).

On the other hand, the above-described three-dimensional sub-regions So1 to So4 are sequentially updated, and generation of three-dimensional image data based on the volume data updated using the sub-volume data newly obtained in the updated three-dimensional sub-region. The display is performed (step S12 in FIG. 11).

On the other hand, in the above-described step S5, for example, when it is determined that the electrocardiographic waveform obtained in the period [t2-t3] is in the Early Trigger state, the E / L state counting unit 132 of the imaging condition updating unit 13 is The Early Trigger state determined by the E / L state determination unit 131 is counted. When the determination for the Early Trigger state is repeated a predetermined number of times (En times) in a plurality of continuous heartbeat cycles, the already set shooting conditions are updated to the shooting conditions suitable for the heartbeat cycle in the Early Trigger state. When it is determined that the electrocardiographic waveform is in the Late Trigger state, the E / L state counting unit 132 of the imaging condition update unit 13 counts the Late Trigger state determined by the E / L state determination unit 131. If the determination for the Late Trigger state is repeated a predetermined number of times (Ln times) in a plurality of consecutive heartbeat cycles, the already set shooting conditions are updated to those suitable for the heartbeat cycle in the Late Trigger state (FIG. 11 step S6).

On the other hand, the monitor of the display unit 8 displays the three-dimensional sub-region in which the sub-volume data is generated in step S3 described above, for example, in a display format as shown in FIG. 10, and in particular, from the subject in step S5. When it is determined that the obtained electrocardiogram waveform is in the Early Trigger state or the Late Trigger state, or when these states occur continuously for a predetermined period, the three-dimensionally scanned three-dimensional subregion So2 is displayed on the display unit 8 at this time. Is highlighted (step S7 in FIG. 11).

Next, the heartbeat time phase τ1 of the three-dimensional sub-regions Sa1 to Sa6 based on the updated imaging conditions
The generation of sub-volume data, the detection of the trigger interval, and the determination of the E / L state at τ4 to τ4 are repeated (steps S3 to S5 in FIG. 11). If the E / L state of the electrocardiogram waveform has occurred a predetermined number of times, steps S3 to S7 are repeated. If the E / L state has not occurred a predetermined number of times, steps S3 to S5 and steps S8 to S8 are performed. Step S12
Is repeated to generate and display three-dimensional image data.

(Modification)
Next, a modification of the present embodiment will be described with reference to FIG. In the above-described embodiment, when the electrocardiogram waveform measured from the subject is determined to be the Early Trigger state or the Late Trigger state, the number of segments Sn in the three-dimensional sub-region is updated based on the cardiac cycle of the electrocardiogram waveform. In this modification, the case where the heartbeat time phase number Hn is updated based on the heartbeat period will be described.

As in FIG. 9, FIG. 12A shows an electrocardiogram waveform measured by the biological signal measurement unit 10, and FIG. 12B shows a trigger signal generator 11 based on the R wave of this electrocardiogram waveform. FIG. 12C shows the sub-volume data collected at the heartbeat time phase set or updated based on the trigger interval of the trigger signal, and FIG. 12D shows the sub-volume data. Each of the three-dimensional sub-regions in which collection is performed is shown.

Then, as shown in FIGS. 12A and 12B, for example, an electrocardiographic waveform having a reference heartbeat period To continuously measured until time t2 is caused by body movement of the subject. Lower limit Tm
When it changes to an electrocardiographic waveform in the Early Trigger state with a heartbeat period Txa smaller than in,
At the time t4 when this Early Trigger state is repeated a predetermined number of times of Early Trigger En (En = 2), the heartbeat time phase number Hna (Hn) from the imaging condition of the heartbeat time phase number Hno (Hno = 4).
The shooting conditions are updated to a = 6).

In this case, the heartbeat time phase τ in the three-dimensional subregion S1 in the reference heartbeat period To before update.
Sub-volume data S11 to S14 of 1 to τ4 are sequentially generated. Then time t
4, the heart rate period Txa is set as a new reference heart rate period with the update of the imaging conditions in
Three-dimensional subregions S2 to S4 of the heartbeat time phases τ1 to τ3 set with the heartbeat time phase number Hna = 3
And sub volume data S21 to Sa23, S31 to S33, S41 to S43, and S11 to S13 in S1 are generated in sequence.

Also in this case, the sub-volume data S11 to So14 of the three-dimensional sub-region S1 are collected in the period [t1-t2], and the three-dimensional sub-adjacent to the three-dimensional sub-region S1 in the period [t4-t5] after the imaging condition update. Although the case of collecting the sub volume data S21 to S23 of the area S2 has been shown, the present invention is not limited to this. For example, the sub volume data S11 to S13 of the three-dimensional sub area S1 is collected in the period [t4-t5]. It doesn't matter.

According to the embodiment of the present invention described above, a plurality of sub-volume data is sequentially collected by applying the heart-beat synchronized three-dimensional scanning method, and the obtained sub-volume data is synthesized based on the heart-beat time phase information. Thus, when generating time-series three-dimensional image data for a wide range of three-dimensional regions, the heartbeat period of the electrocardiographic waveform measured in time series from the subject in parallel with the collection of the subvolume data is determined in advance. Even when the set reference heart rate period is significantly different, the sub-volume data can be synthesized in a short time and accurately. For this reason, the diagnostic efficiency and the diagnostic ability are greatly improved, and the burden on the subject and the operator is reduced.

In particular, in the above-described embodiment, when the electrocardiogram waveform is in the Early Trigger state or the Late Trigger state, the three-dimensional sub-region that has been subjected to the three-dimensional scan is highlighted on the display unit. It is possible to easily grasp whether or not the generation of the sub-volume data for is normally performed.

Further, when the electrocardiogram waveform is in the Early Trigger state or the Late Trigger state, the diagnosis is performed by updating the number of segments or the number of heartbeat phases in the three-dimensional sub-region as the imaging condition based on the heartbeat period of the electrocardiogram waveform. Effective subvolume data can be collected in a short time.

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 input unit 9
As described above, the lower limit value Tmin and the upper limit value Tmax of the heartbeat time phase are determined based on the allowable fluctuation range ΔT with respect to the reference heartbeat time phase set in the allowable fluctuation range setting unit 93 of the above. Tmax may be set directly by the allowable fluctuation range setting unit 93.

Further, the case where the three-dimensional sub-region that is three-dimensionally scanned in the period in which the electrocardiogram waveform is in the Early Trigger state or the Late Trigger state is highlighted on the display unit 8 according to the display format as shown in FIG. The present invention is not limited to this, and other methods for displaying the information of the three-dimensional sub-region may be used. The highlighted display of the three-dimensional sub-region is shown in FIG.
As described above, it may be performed when the Early Trigger state or the Late Trigger state occurs continuously a predetermined number of times, but may be performed together with the occurrence of the Early Trigger state or the Late Trigger state.

Furthermore, although the number of segments in the three-dimensional sub-region and the number of heartbeat time phases have been described as the imaging conditions to be updated based on the heartbeat period, other imaging conditions may be used.

On the other hand, in the above-described embodiment, a B-mode data is generated by processing a reception signal obtained by ultrasonic transmission / reception with respect to a three-dimensional area, and volume data of the three-dimensional area is generated based on the B-mode data. However, three-dimensional image data may be generated based on other ultrasonic data such as color Doppler data.

Further, the case where the above volume data is rendered to generate three-dimensional image data such as volume rendering image data and surface rendering image data has been described. However, based on the volume data, MPR (Multi Planar Reco
nstruction) image data, MIP (Maximum Intensity Projection) image data, and the like may be generated.

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 ultrasonic scanning with respect to the three-dimensional sub area | region of the Example. The block diagram which shows the specific structure of the subvolume data generation part with which the ultrasound diagnosing device of the Example is provided. The figure which shows the specific example of the update method selection part with which the ultrasonic diagnosing device of the Example is provided. The figure for demonstrating the heartbeat period of the electrocardiogram waveform in Early Trigger state or Late Trigger state in the Example. The figure for demonstrating the update method of the imaging condition in the Example. The figure which shows the three-dimensional sub area | region at the time of Early Trigger state generation highlighted on the display part 8 of the Example. 3 is a flowchart showing a procedure for generating / displaying three-dimensional image data in the embodiment. The figure for demonstrating the update method of the imaging condition in the modification of the Example.

Explanation of symbols

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 ... envelope detector 42 ... logarithmic converter 5 ... sub-volume data generation unit 51 ... ultrasonic data storage unit 52 ... interpolation processing unit 53 ... sub-volume data storage unit 6 ... volume data generation unit 7 ... image Data generation unit 8 ... display unit 9 ... input unit 91 ... update method selection unit 92 ... E / L count setting unit 93 ... allowable variation range setting unit 94 ... update instruction unit 10 ... biological signal measurement unit 11 ... trigger signal generation unit 12 ... trigger interval detection unit 13 ... imaging condition update unit 131 ... E / L state determination unit 132 ... E / L state counting unit 133 ... imaging condition setting unit 14 ... heart rate time phase setting unit 15 ... scanning control 16 ... system control unit 100 ... ultrasonic diagnostic apparatus

Claims (9)

In the ultrasonic diagnostic apparatus that collects image data in the three-dimensional region by applying a heartbeat-synchronized three-dimensional scanning method to a plurality of three-dimensional subregions set for the three-dimensional region of the subject,
Trigger interval detection means for detecting a trigger interval of a trigger signal generated based on the electrocardiographic waveform of the subject;
Imaging condition update means for updating imaging conditions for the preset three-dimensional area based on the trigger interval;
An ultrasound diagnostic apparatus, comprising: a scanning control unit that controls three-dimensional scanning with respect to the three-dimensional sub-region based on the updated imaging condition. The ultrasonic diagnostic apparatus according to claim 1, wherein the imaging condition update unit updates at least one of the number of segments and the number of heartbeat phases in the three-dimensional sub-region based on the trigger interval. The imaging condition update means includes an E / L state determination means for determining an Early Trigger state or a Late Trigger state of the electrocardiographic waveform based on the trigger interval, and an E / L for counting the Early Trigger state or the Late Trigger state. 2. The ultrasonic diagnostic apparatus according to claim 1, further comprising: an L state counting unit; and an imaging condition setting unit that resets the imaging condition based on the counting result. An allowable fluctuation range setting means for setting an allowable fluctuation range of a heartbeat cycle, wherein the E / L state determination means compares the trigger interval detected by the trigger interval detection means with the allowable fluctuation range; The ultrasonic diagnostic apparatus according to claim 3, wherein an Early Trigger state or the Late Trigger state is determined. E / L count setting means to set the Early Trigger count or Late Trigger count,
The photographing condition setting means is configured to determine that the counting result obtained by the E / L state counting means is the Early Trigge.
4. The ultrasonic diagnostic apparatus according to claim 3, wherein when the r number of times or the Late Trigger number is reached, the imaging condition is reset based on a trigger interval in the Early Trigger state or the Late Trigger state. Display means for displaying information of a three-dimensional sub-region that is three-dimensionally scanned in the Early Trigger state or Late Trigger state of the electrocardiographic waveform determined by the E / L state determination means. The ultrasonic diagnostic apparatus according to claim 3. Update instruction means for instructing to update imaging conditions, and the scanning control means controls the three-dimensional scanning based on the updated imaging conditions in accordance with an instruction signal supplied from the update instruction means. The ultrasonic diagnostic apparatus according to claim 1. In the ultrasonic diagnostic apparatus that collects image data in the three-dimensional region by applying a heartbeat-synchronized three-dimensional scanning method to a plurality of three-dimensional subregions set for the three-dimensional region of the subject,
Trigger interval detection means for detecting a trigger interval of a trigger signal generated based on the electrocardiographic waveform of the subject;
E / L state determination means for determining an Early Trigger state or a Late Trigger state of the electrocardiographic waveform based on the trigger interval;
The Early Trigger state or L of the electrocardiographic waveform based on the determination result of the E / L state determination means
An ultrasonic diagnostic apparatus comprising: display means for displaying information of a three-dimensional sub-region that is three-dimensionally scanned in an ate Trigger state. The E / L state determination means compares the trigger interval detected by the trigger interval detection means with an allowable fluctuation range of a preset heartbeat cycle, thereby comparing the Early Trigger.
The ultrasonic diagnostic apparatus according to claim 8, wherein the state or the Late Trigger state is determined.

Images