JP2007275457A - Ultrasonic diagnostic system and blood vessel marker display method - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To always perform the stable formation and display of a blood vessel marker without being affected by the fluctuations in the image quality of image data. <P>SOLUTION: An ultrasonic wave is transmitted and received with respect to the concerned blood vessel region of a subject to which an ultrasonic contrast agent is administered and image data is collected on the basis of the obtained receiving signal. Further, the position data (blood vessel data) of the center axis or wall of a blood vessel detected from the image data is stored in a memory circuit and the blood vessel marker is formed based on the blood vessel data to be superposed on the image data to be displayed. Then, in a case that the detection of the blood vessel data in the image data during real time collection becomes difficult by the outflow or the like of the administered ultrasonic contrast agent from the concerned blood vessel, the blood vessel marker is formed using the stored blood vessel data and superposed on the image data during collection to be displayed. <P>COPYRIGHT: (C)2008,JPO&INPIT

Description

  The present invention relates to an ultrasonic diagnostic apparatus and a blood vessel marker display method, and more particularly to an ultrasonic diagnostic apparatus and a blood vessel marker display method capable of displaying a blood vessel marker in association with image data of a blood vessel of interest.

  In recent years, a minimally invasive treatment called MIT (Minimally Invasive Treatment) has attracted attention. A typical example of MIT for patients with ischemic brain disease or heart disease is so-called interventional treatment using an intravascular device such as a catheter under image observation. For example, an X-ray diagnostic apparatus or ultrasonic diagnosis By performing the above-described intravascular device insertion operation under real-time observation of image data obtained by an image diagnostic apparatus such as an apparatus, it is possible to efficiently perform safe and accurate intravascular examination or endovascular treatment. It has become.

  The ultrasonic diagnostic apparatus used for MIT enables real-time observation of two-dimensional image data with a simple operation of simply bringing an ultrasonic probe into contact with the body surface. The B-mode 3D image data and the Doppler mode 3D image data are shortened by a method of mechanically moving the ultrasonic probe, or a method using a so-called two-dimensional array ultrasonic probe in which ultrasonic transducers are two-dimensionally arranged. A method of generating in time has also been developed.

Then, a method for generating blood vessel contour data based on the three-dimensional image data obtained using the above-described ultrasonic probe is proposed (see, for example, Patent Document 1), and the blood vessel on which the contour data is superimposed is proposed. By performing the insertion operation of the intravascular device while observing the three-dimensional image data in real time, the distal end portion of the intravascular device can be easily and accurately advanced to a desired direction or a desired position inside the blood vessel having a complicated branch structure. It becomes possible to arrange.
JP 2004-283373 A

  In order to obtain image data for a target blood vessel for diagnosis or treatment (hereinafter referred to as a blood vessel of interest) with high sensitivity, a method of administering an ultrasound contrast agent inside the blood vessel of interest prior to the generation of the image data is used. ing. Then, by applying the method described in Patent Document 1 described above to a blood vessel of interest to which an ultrasound contrast agent has been administered, blood vessel contour data can be stably collected, and this contour data is superimposed. By observing the image data of the displayed blood vessel, the position and shape of the blood vessel can be accurately grasped.

  However, when most of the injected ultrasound contrast agent is washed out from the above-mentioned blood vessel of interest or when a tissue or the like that is difficult to transmit ultrasonic waves is interposed between the ultrasonic probe and the blood vessel of interest, When the incident angle of the ultrasonic wave with respect to the running of the blood vessel is not appropriate, it is difficult to obtain image data for the blood vessel and blood flow with high sensitivity, and it is impossible to generate blood vessel contour data based on this image data. Had a point.

  The present invention has been made in view of the above-described problems. Even when real-time detection of blood vessel information for a blood vessel of interest of the subject is difficult, the blood vessel information of the blood vessel of interest collected in advance is used. An object of the present invention is to provide an ultrasonic diagnostic apparatus and a blood vessel marker display method capable of stably displaying a blood vessel marker indicating the position and shape of a blood vessel.

  In order to solve the above-described problem, an ultrasonic diagnostic apparatus according to a first aspect of the present invention includes an ultrasonic probe having an ultrasonic vibration element that transmits and receives ultrasonic waves to and from a subject, and the ultrasonic vibration element. A transmitting means for driving and transmitting ultrasonic waves to the subject; a receiving means for receiving reflected signals from the subject obtained by transmitting the ultrasonic waves; Scan control means for scanning a predetermined region of the subject, image data generation means for generating time-series image data based on the reception signal obtained by the ultrasonic transmission / reception, and blood vessel information in the blood vessel of interest in the image data Blood vessel information detecting means for detecting the blood vessel information, blood vessel information storage means for storing the detected blood vessel information, and blood vessel marker generating means for generating a blood vessel marker for the blood vessel of interest based on the blood vessel information Display means for displaying the blood vessel marker in correspondence with the image data, and when the blood vessel information detection means cannot detect the blood vessel information, the blood vessel marker generation means is stored in the blood vessel information storage means in advance. The blood vessel marker is generated using the existing blood vessel information.

  On the other hand, in the blood vessel marker display method of the present invention according to claim 12, the image data generating means generates image data based on a received signal obtained by transmitting / receiving ultrasonic waves to / from the subject, and blood vessel information detecting means Detecting the blood vessel information in the blood vessel of interest in the image data and storing it in the blood vessel information storage means, the step of determining whether the detection is possible or not, and determining whether the blood vessel information is detected by the blood vessel information detection means; A generation unit selects either the blood vessel information detected by the blood vessel information detection unit based on the determination result of the detection possibility or the blood vessel information stored in advance in the blood vessel information storage unit, and selects a blood vessel marker for the blood vessel of interest. And generating and displaying the blood vessel marker in correspondence with the image data. It is.

  According to the present invention, even when real-time collection of blood vessel information on a blood vessel of interest of the subject is difficult, a blood vessel marker indicating the position and shape of the blood vessel can be stabilized by using the blood vessel information of the blood vessel of interest collected in advance. Can be displayed. For this reason, a highly accurate diagnosis or treatment can be efficiently performed on the blood vessel of interest or its nearby tissue, and the safety with respect to the treatment is further improved.

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

  In the embodiments of the present invention described below, ultrasonic waves are transmitted to and received from a blood vessel of interest of the subject to which an ultrasound contrast agent is administered and its surrounding organs (hereinafter collectively referred to as a blood vessel region of interest). Then, image data is collected based on the obtained received signal. Further, position information (hereinafter referred to as blood vessel information) such as a blood vessel central axis and a blood vessel wall detected from the image data is stored in a storage circuit, and a blood vessel marker is generated based on the blood vessel information to generate the image data. Superimposed on the display.

  If it is difficult to detect blood vessel information in the image data being collected in real time due to outflow of the administered ultrasound contrast agent from the blood vessel of interest, a blood vessel marker is generated using the stored blood vessel information. The image data is superimposed and displayed.

  In particular, when a blood vessel marker is generated for a beating blood vessel such as a coronary artery or aorta of the heart, the detection of the blood vessel information and the measurement of the heartbeat time phase for the subject are repeated for a predetermined period of time, and obtained in time series. Information on the heartbeat time phase is added to each of the obtained blood vessel information and stored in the storage circuit. If the detection of blood vessel information in the image data being collected in real time becomes difficult due to the above-mentioned reason, the heartbeat time that is the same as or closest to the heartbeat time phase of the subject among the plurality of stored blood vessel information The blood vessel information to which the phase information is added is read from the storage circuit, and the blood vessel marker generated based on the blood vessel information is displayed superimposed on the image data collected in the heartbeat time phase.

  In the embodiment described below, a case where a three-dimensional blood vessel marker is superimposed and displayed on three-dimensional image data collected in time series in a blood vessel region of interest to which an ultrasound contrast agent has been administered will be described. For example, a two-dimensional blood vessel marker may be displayed superimposed on the three-dimensional image data, or a two-dimensional or three-dimensional blood vessel marker may be displayed superimposed on the two-dimensional image data. Further, the above-mentioned blood vessel marker may be superimposed and displayed on two-dimensional image data or three-dimensional image data collected in time series in a blood vessel region of interest to which no ultrasound contrast agent is administered.

  In the following, 3D B-mode image data (B-mode 3D image data) and 3D Doppler mode image data (Doppler mode 3D image data) are combined, and a 3D blood vessel marker is superimposed. However, a 3D or 2D blood vessel marker may be superimposed and displayed on 3D image data or 2D image data in either the B mode or the Doppler mode. A three-dimensional or two-dimensional blood vessel marker may be superimposed and displayed on three-dimensional image data or two-dimensional image data in another mode such as an (imaging) mode.

  On the other hand, in the following examples, the case where the heartbeat time phase of the subject is measured based on the electrocardiogram waveform will be described, but the heartbeat time phase is measured based on other biological signals such as a heart waveform and a brain waveform. Also good.

(Device configuration)
The configuration of the ultrasonic diagnostic apparatus in this embodiment 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 3 are block diagrams showing specific configurations of a signal detection unit and a data generation unit included in the ultrasonic diagnostic apparatus. It is.

  The ultrasonic diagnostic apparatus 100 of the present embodiment shown in FIG. 1 includes a signal detection unit 1 that detects image data and image signals necessary for generating blood vessel markers from the subject to which an ultrasonic contrast agent is administered, and this image. A data generation unit 2 that processes signals to generate B-mode 3D image data and Doppler mode 3D image data, a marker generation unit 3 that generates 3D blood vessel markers using these 3D image data, and B A data synthesizing unit 4 for generating display data by superimposing a three-dimensional blood vessel marker on the mode three-dimensional image data and the Doppler mode three-dimensional image data; and a display unit 5 for displaying the display data; A heartbeat time phase measuring unit 6 for measuring a heartbeat time phase, an input unit 7 for inputting subject information, setting a region of interest, and the like, and a system control unit 8 for comprehensively controlling the above-described units. .

  The signal detection unit 1 is a two-dimensional array of minute Nx ultrasonic transducer elements that transmit ultrasonic pulses (transmission ultrasonic waves) to the subject, and an ultrasonic reflected wave (from the subject ( An ultrasonic probe 11 that converts (received ultrasound) into an image signal (received signal) and an Nt channel drive signal for transmitting an ultrasound pulse in a predetermined direction of the subject are supplied to the ultrasound transducer. A transmitter 12 and a receiver 13 for phasing and adding Nr channel received signals obtained from the ultrasonic transducer are provided.

  The ultrasonic probe 11 is configured to correspond to sector scanning, linear scanning, convex scanning, and the like, and an operator can arbitrarily select according to a diagnostic part and a diagnostic purpose. In this embodiment, Nx A case will be described in which a sector scanning ultrasonic probe 11 in which two ultrasonic transducer elements are two-dimensionally arranged is used. In order to simplify the description, the case where the number of drive signal channels Nt in the transmission unit 12 and the number of reception signal channels Nr in the reception unit 13 are both equal to the number of ultrasonic vibration elements Nx will be described, but the present invention is not limited to this.

  That is, the ultrasonic probe 11 of the signal detection unit 1 shown in FIG. 2 has Nx ultrasonic vibration elements (not shown) arranged two-dimensionally at its tip, and this tip is used as the body surface of the subject. Send and receive ultrasonic waves in contact. Each of the ultrasonic vibration elements is connected to the transmitter 12 and the receiver 13 via an Nx channel multi-core cable (not shown).

  The transmission unit 12 includes a rate pulse generator 121, a transmission delay circuit 122, and a drive circuit 123. The rate pulse generator 121 includes a reference signal generator and a frequency divider (not shown), and generates a rate pulse that divides the reference signal output from the reference signal generator and determines a repetition period of transmission ultrasonic waves. The reference signal is divided to generate a rectangular wave having a frequency substantially equal to the center frequency of the ultrasonic reflected wave.

  The transmission delay circuit 122 is composed of an Nx channel independent delay circuit, and rates a focusing delay time for focusing the transmission ultrasonic wave to a predetermined depth and a deflection delay time for transmitting in a predetermined direction. This is applied to the rate pulse supplied from the pulse generator 121, and this rate pulse is supplied to the drive circuit 123. The Nx channel drive circuit 123 generates a drive signal in synchronization with the rate pulse supplied from the transmission delay circuit 122 and drives the Nx ultrasonic vibration elements incorporated in the distal end portion of the ultrasonic probe 11. Then, transmission ultrasonic waves are radiated into the subject.

  On the other hand, the receiving unit 13 includes an A / D converter 131, a reception delay circuit 132, and an adder 133 each including an Nx channel, and an Nx channel reception signal supplied from the ultrasonic vibration element is converted into an A / D converter. The signal is converted into a digital signal by the device 131 and sent to the reception delay circuit 132.

  The reception delay circuit 132 determines a focusing delay time for focusing a received ultrasonic wave from a predetermined depth and a deflection delay time for setting a reception directivity with respect to a predetermined direction. The adder 133 adds and synthesizes the reception signals output from the reception delay circuit 132. That is, the received signal obtained from a predetermined direction in the subject is phased and added by the reception delay circuit 132 and the adder 133.

  Next, the data generation unit 2 shown in FIG. 3 performs a B-mode data generation unit 21 that performs signal processing on the reception signal supplied from the reception unit 13 to generate B-mode data, and performs quadrature detection on the reception signal. The Doppler signal detection unit 22 that detects the Doppler signal, the Doppler mode data generation unit 23 that generates the Doppler mode data based on the detected Doppler signal, and the above-described three-dimensional ultrasonic scanning performed on the subject. The B mode data and the Doppler mode data are sequentially stored to generate the B mode volume data and the Doppler mode volume data, and further, the volume data is rendered to obtain the B mode 3D image data and the Doppler mode 3D image data. An image data generation unit 24 for generation is provided.

  The B-mode data generation unit 21 includes an envelope detector 211 and a logarithmic converter 212. The envelope detector 211 envelope-detects the received signal after the phasing addition supplied from the adder 133 of the reception unit 13. The amplitude of the envelope detection signal is logarithmically converted by the logarithmic converter 212. Note that the envelope detector 211 and the logarithmic converter 212 may be configured in a reversed order.

  On the other hand, the Doppler signal detection unit 22 includes a π / 2 phase shifter 221, mixers 222-1 and 222-2, and LPFs (low-pass filters) 223-1 and 223-2, and an adder 133 of the reception unit 13. The received signal supplied from is detected by quadrature detection to detect a Doppler signal.

  That is, the reception signal supplied from the reception unit 13 is input to the first input terminals of the mixers 222-1 and 222-2. On the other hand, the rectangular wave supplied from the rate pulse generator 121 of the transmission unit 12 shown in FIG. 2 is supplied directly to the second input terminal of the mixer 222-1 and is phase-shifted by the π / 2 phase shifter 221. Are shifted by 90 degrees and supplied to the second input terminal of the mixer 222-2. The outputs of the mixers 222-1 and 222-2 are supplied to the LPFs 223-1 and 223-2, and a difference component between the output signal frequency of the receiving unit 13 and the fundamental frequency of the rectangular wave is detected.

  Next, the Doppler mode data generation unit 23 includes a Doppler signal storage unit 231, an MTI filter 232, and an autocorrelation calculator 233, and the Doppler signal detected by the Doppler signal detection unit 22 is temporarily stored in the Doppler signal storage circuit 231. The Next, the MTI filter 232 performs a filtering process on the Doppler signal stored in the Doppler signal storage circuit 231 and extracts a component (blood flow Doppler component) caused by blood flow in the blood vessel.

  The autocorrelation calculator 233 calculates an autocorrelation value for the blood flow Doppler component extracted by the MTI filter 232, and further generates Doppler mode data based on the autocorrelation value. In this case, the autocorrelation calculator 233 can detect blood flow information with high sensitivity by generating Doppler mode data based on the power value of the blood flow Doppler component calculated by the autocorrelation processing. The Doppler mode data may be generated using the average velocity or the dispersion value of the Doppler component.

  On the other hand, the image data generation unit 24 includes a volume data generation unit (not shown), an opacity / tone setting unit, and a rendering processing unit. The volume data generation unit has a B-mode data storage area and a Doppler mode data storage area. The B-mode data generated by the B-mode data generation unit 21 and the Doppler mode generated by the Doppler mode data generation unit 23 B-mode volume data and Doppler mode volume data are generated by sequentially storing the data in the above-described storage areas in correspondence with the scanning direction of the three-dimensional ultrasonic scanning.

  The opacity / color tone setting unit reads the B-mode volume data and the Doppler mode volume data generated by the volume data generation unit, and based on the pixel values (voxel values) of these volume data, Is set in units of pixels.

  The rendering processing unit renders the B-mode volume data and the Doppler mode volume data based on the opacity and color tone information set by the opacity / color tone setting unit to perform B-mode three-dimensional image data and Doppler mode three-dimensional image data is generated.

  Returning to FIG. 1, the marker generation unit 3 includes a region-of-interest setting unit 31, a blood vessel information detection unit 32, a landmark position detection unit 33, a blood vessel information storage unit 34, a detection availability determination unit 35, and a blood vessel marker. A generation unit 36 is provided.

  The region-of-interest setting unit 31 sets a region of interest and a region of interest based on a region-of-interest selection signal supplied from the input unit 7 via the system control unit 8. In this case, the operator performs the B mode 3D image data and the Doppler mode 3D image data generated in the image data generation unit 24 of the data generation unit 2 and displayed on the display unit 5 via the data synthesis unit 4. A blood vessel region of interest to be diagnosed / treated and a suitable tissue region of interest are selected using an input device provided in the input unit 7 described later. Then, the region-of-interest setting unit 31 sets a region of interest and a region of interest for the above-described three-dimensional image data according to the selection signal.

  Note that the above-mentioned tissue region of interest means a region of a tissue or an organ in which the location is always clearly shown in B-mode 3D image data or Doppler mode 3D image data regardless of the presence or absence of an ultrasound contrast agent. For example, a heart wall or a diaphragm is preferable.

  Next, the blood vessel information detection unit 32 includes an arithmetic circuit (not shown), and at least one of B-mode three-dimensional image data and Doppler mode three-dimensional image data in the blood vessel region of interest set by the region-of-interest setting unit 31 (hereinafter, the (Referred to as three-dimensional image data). Then, for example, an image processing method described in Patent Document 1 is applied to the obtained three-dimensional image data to detect position information of the blood vessel wall or the blood vessel central axis. Specifically, the coordinates on the blood vessel wall surface or the blood vessel central axis are detected.

  On the other hand, the landmark position detection unit 33 includes an arithmetic circuit (not shown), and performs spatial filtering processing by extracting three-dimensional image data in the tissue region of interest set by the region of interest setting unit 31. Next, in the three-dimensional image data after the filtering process, for example, the coordinates of the pixel having the maximum pixel value are detected as position information of the landmark (mark), stored in the blood vessel information storage unit 34, and supplied to the blood vessel marker generation unit 36. To do.

  In the blood vessel information storage unit 34, blood vessel information detected by the blood vessel information detection unit 32 with respect to the three-dimensional image data supplied in time series from the image data generation unit 24 (that is, position information of the blood vessel central axis and the blood vessel wall). ) Are stored sequentially. Each of the blood vessel information stored at this time is accompanied by information on the position of the landmark detected by the landmark position detection unit 33 and information on the heartbeat time phase of the subject measured by the heartbeat time phase measurement unit 6 described later. It is added as information.

  Next, the detection possibility determination unit 35 continuously monitors the detection result output by the blood vessel information detection unit 32, and for example, determines whether or not the blood vessel information is normally detected based on the continuity and reproducibility. judge. Then, the determination result is supplied to the blood vessel marker generation unit 36.

  Next, the blood vessel marker generation unit 36 generates a blood vessel marker for the blood vessel of interest based on the determination result supplied from the detection availability determination unit 35. In other words, the blood vessel information detection unit 32 normally detects the blood vessel information for the time-series three-dimensional image data supplied from the image data generation unit 24 of the data generation unit 2 in substantially real time by the detection possibility determination unit 35. If it is determined that the blood vessel marker is generated, the blood vessel marker generation unit 36 generates a blood vessel marker for the blood vessel of interest based on the blood vessel information directly supplied from the blood vessel information detection unit 32.

  On the other hand, when it is determined that the 3D image data supplied from the image data generation unit 24 is applied, the blood vessel marker generation unit 36 is first supplied from the heartbeat time phase measurement unit 6 and the landmark position detection unit 33 in substantially real time. Receiving the heartbeat time phase information and landmark position information of the subject. Next, blood vessel information having heartbeat time phase information substantially equal to the heartbeat time phase information is read out from the blood vessel information in a plurality of heartbeat time phases stored in advance in the blood vessel information storage unit 34, and further added to the blood vessel information. The position of the blood vessel information is corrected based on a comparison result between the position information of the current landmark and the landmark position information directly supplied from the landmark position detection unit 33 to generate a three-dimensional blood vessel marker.

  FIG. 4 is a diagram for schematically explaining position correction of blood vessel information. FIG. 14A shows three-dimensional image data generated at t = t1 where blood vessel information is normally detected. On the other hand, the blood vessel information (position information of the blood vessel central axis) C1 of the blood vessel P of interest detected by the blood vessel information detection unit 32 and the landmark position detection unit 33 and stored in advance in the blood vessel information storage unit 34, and the blood vessel information C1 A landmark LM1 at coordinates (x1, y1) that are separated by a distance D is shown.

  FIG. 4B shows the blood vessel of interest detected in the same manner for the three-dimensional image data generated at the actual observation time t = t2 (t2> t1) where the blood vessel information is not normally detected. The blood vessel information C2 of P and the landmark LM2 at the coordinates (x2, y2) are shown. However, the broken line in FIG. 4B indicates the blood vessel P of interest and blood vessel information C2 that are difficult to detect in the three-dimensional image data due to the outflow of the ultrasound contrast agent.

  On the other hand, FIG. 4C shows the three-dimensional blood vessel marker Cx generated by the blood vessel marker generation unit 36, and the coordinates (x2, x2) of the landmark LM2 at t = t2 detected by the landmark position detection unit 33. y2) is set as the reference point P, and a three-dimensional blood vessel marker Cx based on the blood vessel information C1 at t = t1 is generated at a position away from the reference point P by the distance D.

  Note that a three-dimensional blood vessel marker generated using t = t1 blood vessel information stored in advance in the blood vessel information storage unit 34 is superimposed on the three-dimensional image data of the blood vessel of interest collected at the actual observation time t = t2. At the time of display, the blood vessel marker generation unit 36 compares the landmark position information supplied from the landmark position detection unit 33 at t = t2 and the landmark position information at t = t1 read from the blood vessel information storage unit 34. If there is a large difference between them, the generation of the three-dimensional blood vessel marker or the supply to the data synthesis unit 4 is stopped.

  As shown in FIG. 4, the position of the blood vessel information C1 at t = t1 stored in the blood vessel information storage unit 34 is corrected based on the position information of the landmark LM1 at t = t1 and the landmark LM2 at t = t2. Accordingly, it is possible to correct an error caused by a relative position change or direction change of the ultrasonic probe 11 with respect to the subject, and always accurately superimpose a three-dimensional blood vessel marker on the three-dimensional image data of the blood vessel of interest. Can do.

  In addition, a 3D blood vessel marker is generated by selecting blood vessel information to which heartbeat time phase information corresponding to the heartbeat time phase of the subject measured in real time is added from a plurality of previously stored blood vessel information. By doing so, it is possible to accurately superimpose the three-dimensional blood vessel marker on the three-dimensional image data of the beating blood vessel.

  Next, the data synthesis unit 4 includes an arithmetic circuit and a storage circuit (not shown), and the B-mode three-dimensional image data and the Doppler mode three-dimensional image data generated by the image data generation unit 24 and the blood vessel marker generation unit 36 Display data is generated by superimposing a three-dimensional blood vessel marker and adding subject information or the like as necessary.

  On the other hand, the display unit 5 includes a conversion circuit and a monitor (not shown). The conversion circuit converts the display data generated in the data synthesis unit 4 into a predetermined display format, and then performs D / A conversion and television format conversion. And display on the monitor such as CRT or liquid crystal.

  FIG. 5 shows a display example of the blood vessel marker on the monitor of the display unit 5. In this monitor, the region of interest setting unit 31 selects from the input unit 7 for the three-dimensional image data including the blood vessel BL. The target blood vessel region Rb and the target tissue region Rt set based on the signal are displayed, and the landmark LM detected by the landmark position detection unit 33 for the target tissue region, and the blood vessel marker generation unit 36 uses the blood vessel information. The blood vessel marker Mb of the blood vessel wall and the blood vessel marker Ma of the blood vessel central axis generated based on the blood vessel information of the three-dimensional image data supplied from the detection unit 32 are displayed superimposed on the three-dimensional image data. However, the display of the blood vessel marker is not limited to the method shown in FIG. 5. For example, only one of the blood vessel marker Mb and the blood vessel marker Ma may be displayed, and the landmark LM may be displayed. It is not always necessary.

  Returning to FIG. 1 again, the heartbeat time phase measurement unit 6 includes an ECG unit that collects the electrocardiogram waveform (ECG signal) of the subject, and an arithmetic circuit that measures the heartbeat time phase based on the electrocardiogram waveform (both are shown in FIG. 1). Not shown). The ECG unit A / D converts an electrocardiogram waveform detected by an ECG electrode attached to the chest of the subject, and the arithmetic circuit, for example, converts the R wave of the electrocardiogram waveform converted into a digital signal. Measure the heartbeat time phase based on. Then, the obtained heartbeat time phase information is supplied to the blood vessel information storage unit 34 and the blood vessel marker generation unit 36 of the marker generation unit 3. Although the time elapsed from the R wave of the electrocardiographic waveform is suitable as the above-described heartbeat time phase, it is not limited to this.

  On the other hand, the input unit 7 is an interactive interface including an input device such as a keyboard, a trackball, and a mouse on the operation panel and a display panel. The input unit 7 inputs subject information, sets ultrasonic transmission / reception conditions, and an image data collection mode. In addition, the blood vessel marker display mode is selected, the blood vessel region of interest and the tissue region of interest are set for the image data, and various command signals are input.

  The system control unit 8 includes a CPU and a storage circuit (not shown), and performs overall control of each unit and overall system control based on an instruction signal from the input unit 7. In particular, the delay time in the transmission delay circuit 122 of the transmission unit 12 and the reception delay circuit 132 of the reception unit 13 shown in FIG. 2 is controlled, and three-dimensional ultrasonic scanning is performed on the subject.

(Display procedure of blood vessel marker)
Next, the display procedure of the blood vessel marker in the present embodiment will be described with reference to the flowchart of FIG. Prior to the generation of image data, the operator of the ultrasonic diagnostic apparatus 100 inputs subject information at the input unit 7, and further, an image data collection mode (that is, B-mode three-dimensional image data by sector scanning and three-dimensional Doppler mode). After selecting the image data acquisition mode), selecting the blood vessel marker display mode, setting the ultrasound transmission / reception conditions, etc. (step S1 in FIG. 6), the ECG electrode of the heartbeat time phase measuring unit 6 is attached to the chest. An ultrasound contrast agent is administered to the subject (step S2 in FIG. 6).

  When this ultrasonic contrast agent reaches the blood vessel of interest or in the vicinity thereof, the operator places the distal end portion of the ultrasonic probe 11 on the body surface of the subject, and issues an image data collection start command at the input unit 7. input. Then, when this command signal is supplied to the system control unit 8, the generation and display of B-mode 3D image data and Doppler mode 3D image data is started.

  When generating the above-described image data, the rate pulse generator 121 of the transmission unit 12 shown in FIG. 2 repeats the transmission ultrasonic wave radiated into the body of the subject according to the control signal supplied from the system control unit 8. A rate pulse for determining a cycle (rate cycle) is generated and supplied to the transmission delay circuit 122. The transmission delay circuit 122 has a delay time for focusing the transmission ultrasonic wave based on the control signal supplied from the system control unit 8 and a delay time for transmitting in the first scanning direction (θ1, φ1) as the rate. This rate pulse is supplied to the drive circuit 123 for the Nx channel. Next, the drive circuit 123 generates a drive signal based on the rate pulse supplied from the transmission delay circuit 122, supplies this drive signal to the Nx ultrasonic transducer elements in the ultrasonic probe 11, and supplies the signal of the subject. Transmits ultrasonic waves to the body.

  A part of the transmitted ultrasonic wave is reflected at the boundary between tissues with different acoustic impedances, and the frequency of the ultrasonic wave reflected by blood cells moving in the blood vessel is subjected to Doppler shift. Then, it is converted into an image signal (reception signal) by the ultrasonic vibration element of the ultrasonic probe 11. Next, this received signal is converted into a digital signal by the A / D converter 131 of the receiving unit 13, and then the delay time for focusing the received ultrasonic wave from a predetermined depth in the Nx channel reception delay circuit 132. And a delay time for setting a strong reception directivity with respect to the received ultrasonic waves from the scanning direction (θ1, φ1), and the adder 133 performs phasing addition.

  Then, the B-mode data generation unit 21 in the data generation unit 2 of FIG. 3 to which the reception signal after the phasing addition is supplied performs envelope detection and logarithmic conversion on the reception signal to generate B-mode data. Then, it is stored in the B-mode data storage area in the volume data generation unit of the image data generation unit 24.

  When the generation and storage of the B-mode data in the scanning direction (θ1, φ1) is completed, the system control unit 8 controls the delay time in the transmission delay circuit 122 of the transmission unit 12 and the reception delay circuit 132 of the reception unit 13. Thus, the ultrasonic scanning direction is sequentially updated by Δθ in the θ direction and Δφ in the φ direction (θp, φq) (θp = θ1 + (p−1) Δθ (p = 2 to P), φq = φ1 + (q− 1) Three-dimensional ultrasonic scanning is performed for each of Δφ (q = 2 to Q)) by transmitting and receiving ultrasonic waves in the same procedure. Then, the B mode data obtained in each scanning direction is sequentially stored in the B mode data storage area of the volume data generation unit to generate B mode volume data.

  Further, the system control unit 8 substantially parallels the ultrasonic transmission / reception for the purpose of generating B-mode data for the scanning direction (θp, φq) (p = 1 to P, q = 1 to Q) described above. Ultrasonic transmission / reception for the purpose of generating Doppler mode data in the scanning direction is performed.

  That is, the system control unit 8 first controls the transmission delay time in the transmission delay circuit 122 of the transmission unit 12 and the reception delay time in the reception delay circuit 132 of the reception unit 13 to transmit / receive ultrasonic waves in the scanning direction (θ1, φ1). Is repeated a predetermined number of times (L times), and the reception signal obtained from the reception unit 13 in each ultrasonic transmission / reception is supplied to the Doppler signal detection unit 22 of the data generation unit 2. The received signal is quadrature detected by the Doppler signal detection unit 22 to detect the Doppler signal, and is temporarily stored in the Doppler signal storage unit 231 of the Doppler mode data generation unit 23.

  When the storage of the Doppler signal obtained by the predetermined number of times (L times) of ultrasonic transmission / reception in the scanning direction (θ1, φ1) is completed, the system control unit 8 stores the Doppler signal stored in the Doppler signal storage unit 231. The L Doppler signals corresponding to a predetermined position (depth) are sequentially read out from the signal and supplied to the MTI filter 232. The MTI filter 232 filters the supplied Doppler signal to extract a blood flow Doppler component, and supplies it to the autocorrelation calculator 233.

  The autocorrelation calculator 233 performs autocorrelation calculation using the Doppler signal supplied from the MTI filter 232, and further calculates blood flow information based on the calculation result. Such calculation is also performed for other positions (depths) in the scanning direction θ1, and the blood flow information in the calculated scanning directions (θ1, φ1) is stored in the Doppler mode data storage area of the data storage unit 24. To do.

  Next, the system control unit 8 performs ultrasonic transmission / reception in the scanning direction (θp, φq) (p = 2 to P, q = 2 to Q) in the same procedure. The Doppler mode data obtained in each scanning direction is sequentially stored in the Doppler mode data storage area in the volume data generation unit of the image data generation unit 24 to generate Doppler mode volume data.

  On the other hand, the rendering processing unit of the image data generation unit 24 reads the B mode volume data stored in the B mode data storage area of the volume data generation unit and the Doppler mode volume data stored in the Doppler mode data storage area, respectively. Rendering processing based on the opacity and tone information set by the transparency / color tone setting unit is performed to generate B-mode 3D image data and Doppler mode 3D image data.

  Next, the data synthesis unit 4 in FIG. 1 generates display data by synthesizing the B-mode 3D image data and the Doppler mode 3D image data supplied from the image data generation unit 24 and displays them on the monitor of the display unit 5. (Step S3 in FIG. 6).

  On the other hand, the operator selects the interested blood vessel region and the interested tissue region with respect to the display data displayed in real time on the monitor using the input device of the input unit 7, and the interested region setting unit 31 of the marker generating unit 3 Based on this selection signal, a blood vessel region and a tissue region of interest are set for the three-dimensional image data (that is, at least one of B-mode three-dimensional image data and Doppler mode three-dimensional image data) in the image data generation unit 24 ( Step S4 in FIG.

  Next, the signal detection unit 1 and the data generation unit 2 generate three-dimensional image data by the same procedure as in step 3 (step S5 in FIG. 6), and the blood vessel information detection unit 32 of the marker generation unit 3 The three-dimensional image data in the blood vessel region of interest set by the region-of-interest setting unit 31 is extracted from the three-dimensional image data supplied from the second image data generation unit 24. Then, the position information of the blood vessel wall or the blood vessel central axis in the obtained three-dimensional image data is detected as blood vessel information and supplied to the blood vessel information storage unit 34, the detection possibility determination unit 35, and the blood vessel marker generation unit 36 (step in FIG. 6). S6).

  On the other hand, the landmark position detection unit 33 extracts three-dimensional image data in the tissue region of interest set by the region-of-interest setting unit 31 from the three-dimensional image data supplied from the image data generation unit 24. The coordinates of the pixel (voxel) having the maximum pixel value in the data are detected as landmark position information. Then, the detected landmark position information is supplied to the blood vessel information storage unit 34 and the blood vessel marker generation unit 36 (step S7 in FIG. 6).

  The heartbeat time phase measurement unit 6 performs A / D conversion on the electrocardiogram waveform collected by the ECG electrode attached to the subject's chest, and then measures the heartbeat time phase using the R wave as a reference. The marker generation unit 3 To the blood vessel information storage unit 34 and the blood vessel marker generation unit 36 (step S8 in FIG. 6).

  Next, the detection possibility determination unit 35 of the marker generation unit 3 continuously monitors the detection result of the blood vessel information output from the blood vessel information detection unit 32, and the blood vessel information is normal based on the continuity and reproducibility. It is determined whether or not it has been detected (step S9 in FIG. 6). Then, the determination result is supplied to the blood vessel information storage unit 34 and the blood vessel marker generation unit 36 to control these units.

  That is, when the blood vessel information detection unit 32 determines that the blood vessel information is normally detected, the detection availability determination unit 35 performs the landmark position detection unit on the blood vessel information supplied from the blood vessel information detection unit 32. The landmark position information supplied from 33 and the heartbeat time phase information of the subject supplied from the heartbeat time phase measurement unit 6 are added and stored in the blood vessel information storage unit 34 (step S10 in FIG. 6).

  Further, the blood vessel marker generation unit 36 to which the above determination result is supplied from the detection possibility determination unit 35 is based on the blood vessel information supplied from the blood vessel information detection unit 32 directly and in time series, and the three-dimensional blood vessel marker for the blood vessel of interest. Is generated (step S11 in FIG. 6).

  On the other hand, if it is determined by the detectability determination unit 35 that blood vessel information is not normally detected for the three-dimensional image data supplied from the image data generation unit 24, the determination result is supplied from the detectability determination unit 35. The blood vessel marker generation unit 36 thus received receives the heartbeat time phase information and landmark position information of the subject supplied in time series from the heartbeat time phase measurement unit 6 and the landmark position detection unit 33.

  Next, the blood vessel marker generation unit 36 stores in advance in the blood vessel information storage unit 34 blood vessel information having heartbeat time phase information substantially equal to the heartbeat time phase information directly supplied from the heartbeat time phase measurement unit 6 in step S8 described above. Extracted from the plurality of blood vessel information (step S12 in FIG. 6), and further, the landmark position information added to the blood vessel information and the direct supply from the landmark position detection unit 33 in the above-described step S7. The position of the blood vessel information is corrected by comparing the landmark position information to generate a three-dimensional blood vessel marker for the blood vessel of interest (steps S13 and S14 in FIG. 6).

  At this time, the blood vessel marker generation unit 36 recognizes a large difference between the landmark position information directly supplied from the landmark position detection unit 33 and the landmark position information read from the blood vessel information storage unit 34. The generation of the blood vessel marker or the supply to the data synthesis unit 4 is stopped.

  If the blood vessel marker is generated by the above procedure, the data synthesis unit 4 superimposes the three-dimensional blood vessel marker generated by the blood vessel marker generation unit 36 on the three-dimensional image data generated by the image data generation unit 24, and Furthermore, display data is generated by adding subject information or the like as necessary. Then, the display unit 5 performs a predetermined conversion process on the display data to generate a video signal and display it on the monitor (step S15 in FIG. 6).

  According to the embodiment of the present invention described above, since the blood vessel marker generated based on the image data obtained from the subject can be displayed superimposed on the blood vessel of interest in the image data, the position of the blood vessel And shape can be easily grasped.

  In addition, even when real-time collection of blood vessel information on a blood vessel of interest is temporarily difficult due to the outflow of an ultrasound contrast agent, the blood vessel marker can be stabilized by using the blood vessel information of the blood vessel of interest collected in advance. It is possible to display.

  Furthermore, when displaying blood vessel markers generated using pre-collected vascular information of the blood vessel of interest in a superimposed manner on image data collected in real time, it is always detected stably without depending on the presence of an ultrasound contrast agent. Is collected together with the blood vessel information, and the position is corrected based on the landmark position information added to the stored blood vessel information and the landmark position information detected at the actual observation time. Since the blood vessel marker is generated using the blood vessel information, the blood vessel marker and the image data can be accurately superimposed and displayed.

  In addition, when displaying a blood vessel marker generated using the blood vessel information of the blood vessel of interest collected in advance on the image data collected in real time, the heartbeat time phase of the subject is collected together with the blood vessel information, and the actual observation time Since the blood vessel marker is generated based on the blood vessel information to which the heartbeat time phase information corresponding to the heartbeat time phase is added, the blood vessel marker can be accurately superimposed on the beating blood vessel.

  Furthermore, it is possible to automatically determine whether or not to generate a blood vessel marker based on the stored blood vessel information based on the detection accuracy of the blood vessel information.

  For the above reasons, it is possible to efficiently perform highly accurate diagnosis or treatment on the blood vessel of interest or its nearby tissue, and not only improve the safety for treatment / diagnosis, but also reduce the burden on the subject and the operator. be able to.

  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, as described above, in the above-described embodiment, the case where a three-dimensional blood vessel marker is superimposed and displayed on the three-dimensional image data collected in the blood vessel region of interest has been described. However, a two-dimensional blood vessel marker is added to the three-dimensional image data. The display may be superimposed and a two-dimensional or three-dimensional blood vessel marker may be superimposed and displayed on the two-dimensional image data. Further, a two-dimensional or three-dimensional blood vessel marker may be superimposed and displayed on the two-dimensional image data or the three-dimensional image data of the blood vessel region of interest to which no ultrasound contrast agent is administered.

  Further, the case where the blood vessel marker is superimposed on the synthesized B-mode image data and Doppler mode image data has been described. However, the blood vessel marker may be superimposed on either the B-mode image data or the Doppler mode image data. A blood vessel marker may be superimposed on image data of another mode such as a mode.

  Furthermore, although the case where the blood vessel marker is superimposed and displayed on the image data of the blood vessel region of interest has been shown, the image data and the blood vessel marker may be displayed in parallel.

  Moreover, although the case where the heartbeat time phase is measured based on the electrocardiogram waveform has been described, the heartbeat time phase may be measured based on other biological signals such as a heart waveform and a brain waveform instead of the electrocardiogram waveform.

  On the other hand, in the above-described embodiment, the blood vessel marker is detected using the blood vessel information whose position is corrected based on the comparison result between the landmark position information stored together with the blood vessel information and the landmark position information detected at the actual observation time. Although the generation of the blood vessel marker is stopped when there is a significant difference between the two landmark position information described above, the present invention is not limited to this method. For example, the ultrasonic probe 11 There may be provided a probe position detector that measures the position and angle of the probe, and further the scanning section direction and the like, and the blood vessel marker may be generated based on the probe position information detected by the probe position detector.

  Specifically, a probe position detector having a magnetic transmitter disposed in the vicinity of the subject and a magnetic sensor attached to the ultrasonic probe 11 is newly provided, and measurement is performed based on a magnetic signal detected by the magnetic sensor. The probe position information of the ultrasonic probe 11 is added to the image data and stored. Then, the blood vessel information is corrected based on the comparison result between the probe position information stored together with the blood vessel information and the probe position information detected at the actual observation time, and a blood vessel marker is generated using the corrected blood vessel information. To do. If there is a significant difference between the two probe position information, the generation of the blood vessel marker or the supply to the data synthesis unit 4 is stopped.

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 structure of the signal detection part with which the ultrasonic diagnosing device of the Example was equipped. The block diagram which shows the structure of the image data generation part with which the ultrasonic diagnosing device of the Example was equipped. The figure which shows typically the position correction of the blood vessel information in the Example. The figure which shows the example of a display of the blood-vessel marker in the Example. The flowchart which shows the display procedure of the blood vessel marker in the Example.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 ... Signal detection part 11 ... Ultrasonic probe 12 ... Transmission part 13 ... Reception part 2 ... Data generation part 21 ... B mode data generation part 22 ... Doppler signal detection part 23 ... Doppler mode data generation part 24 ... Image data generation part 3 ... Marker generator 31 ... Region of interest setting part 32 ... Blood vessel information detection part 33 ... Landmark position detection part 34 ... Blood vessel information storage part 35 ... Detectability determination part 36 ... Blood vessel marker generation part 4 ... Data composition part 5 ... Display part 6 ... heart rate time phase measurement unit 7 ... input unit 8 ... system control unit 100 ... ultrasonic diagnostic apparatus

Claims (12)

An ultrasonic probe having an ultrasonic vibration element for transmitting and receiving ultrasonic waves to and from a subject;
Transmitting means for driving the ultrasonic vibration element and transmitting ultrasonic waves to the subject;
Receiving means for receiving a reflected signal from the subject obtained by transmitting the ultrasonic wave;
Scanning control means for controlling a direction of ultrasonic transmission / reception to scan a predetermined region of the subject;
Image data generating means for generating time-series image data based on a received signal obtained by the ultrasonic transmission / reception;
Blood vessel information detecting means for detecting blood vessel information in a blood vessel of interest in the image data;
Blood vessel information storage means for storing the detected blood vessel information;
A blood vessel marker generating means for generating a blood vessel marker for the blood vessel of interest based on the blood vessel information;
Display means for displaying the blood vessel marker in correspondence with the image data;
When the blood vessel information cannot be detected by the blood vessel information detection unit, the blood vessel marker generation unit generates the blood vessel marker using blood vessel information stored in advance in the blood vessel information storage unit. Ultrasonic diagnostic equipment.   Detecting availability determination means for determining whether the blood vessel information can be detected by the blood vessel information detection means, wherein the blood vessel marker generation means is detected by the blood vessel information detection means in substantially real time based on a determination result of the detection availability determination means. The ultrasonic diagnostic apparatus according to claim 1, wherein the blood vessel marker is generated by selecting either the blood vessel information or the blood vessel information stored in the blood vessel information storage unit.   The ultrasonic diagnostic apparatus according to claim 2, wherein the detection possibility determination unit performs detection determination based on reproducibility or stability of the blood vessel information detected by the blood vessel information detection unit.   2. The ultrasonic diagnosis according to claim 1, further comprising: a region of interest setting unit, wherein the blood vessel information detecting unit detects the blood vessel information in the region of interest of the blood vessel set by the region of interest setting unit with respect to the image data. apparatus.   The ultrasonic diagnostic apparatus according to claim 1, wherein the blood vessel information detecting unit detects position information of at least one of a blood vessel wall and a blood vessel central axis in the blood vessel of interest as the blood vessel information.   Data synthesizing means, wherein the data synthesizing means generates display data by superimposing or arranging the blood vessel markers on the image data generated by the image data generating means, and displays the display data on the display means. The ultrasonic diagnostic apparatus according to claim 1.   A region-of-interest setting unit and a landmark position detection unit; and the blood vessel information storage unit adds the location information of the landmark in the tissue region of interest set by the region-of-interest setting unit to the blood vessel information and stores the information. The marker generation unit compares the landmark position information detected by the landmark position detection unit in substantially real time with the landmark position information added to the blood vessel information stored in the blood vessel information storage unit. The ultrasonic diagnostic apparatus according to claim 1, wherein the blood vessel information is generated by correcting the position of the blood vessel information based on the information.   The blood vessel marker generation means includes the landmark position information detected by the landmark position detection means in substantially real time, and the landmark position information added to the blood vessel information stored in the blood vessel information storage means. The ultrasonic diagnostic apparatus according to claim 7, wherein generation of the blood vessel marker is stopped when there is a significant difference between the two.   Comprising a heartbeat time phase measuring means for measuring a heartbeat time phase of the subject, and the blood vessel information storage means adds and stores information on the heartbeat time phase measured by the heartbeat time phase measurement means to the blood vessel information, The blood vessel marker generation means reads out the blood vessel information to which the heartbeat time phase information corresponding to the heartbeat time phase of the subject detected by the heartbeat time phase measurement means in substantially real time is added from the blood vessel information storage means. The ultrasonic diagnostic apparatus according to claim 1, wherein the blood vessel marker is generated.   Probe position detection means, wherein the blood vessel information storage means appends and stores the position information of the ultrasonic probe detected by the probe position detection means to the blood vessel information, and the blood vessel marker generation means includes the probe position Based on a comparison result between the position information of the ultrasonic probe detected by the detection means in substantially real time and the position information of the ultrasonic probe added to the blood vessel information stored in the blood vessel information storage means, the blood vessel information is obtained. The ultrasonic diagnostic apparatus according to claim 1, wherein the blood vessel marker is generated by correcting the position.   The blood vessel marker generation means includes the ultrasonic probe position information detected by the probe position detection means in substantially real time, and the position information of the ultrasonic probe added to the blood vessel information stored in the blood vessel information storage means. The ultrasonic diagnostic apparatus according to claim 10, wherein generation of the blood vessel marker is stopped when there is a significant difference between the two. An image data generating means for generating image data based on a received signal obtained by transmitting and receiving ultrasonic waves to and from a subject;
A step of detecting blood vessel information in the blood vessel of interest in the image data and storing the blood vessel information in the blood vessel information storage means;
A step for determining whether the blood vessel information is detected by the blood vessel information detecting unit;
A blood vessel marker generation unit selects either the blood vessel information detected by the blood vessel information detection unit based on the determination result of the detection possibility or the blood vessel information stored in advance in the blood vessel information storage unit, and the blood vessel for the blood vessel of interest Generating a marker;
A blood vessel marker display method, comprising: a step of displaying the blood vessel marker in correspondence with the image data.

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