JP2009279290A - Medical image diagnostic apparatus - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To achieve a medical image diagnostic apparatus capable of displaying blood flow information in an image in a three-dimensional manner. <P>SOLUTION: After mounting a synchronization measurement device to a subject, 4D high-speed imaging is started by using an MRI apparatus. A contrast medium is injected by synchronizing with biological monitor information, and a time-series blood flow 4D image is obtained (Steps 101-104). Image processing is performed in each time phase, and a blood flow vector by a pixel is visualized. Navigation is activated. The blood flow 4D image information is loaded, and surgery is started (Steps 105-109). 4D navigation is displayed by synchronizing with the biological synchronization measurement device, and the blood flow information is displayed by superimposing on the 4D navigation (Steps 110, 111). A position of a surgical instrument is detected, and three-dimensional blood flow information around a distal end of a needle of the surgical instrument is calculated. The blood flow flowing toward the needle and the blood flow flowing off the needle are displayed in different colors. The amount of the blood flow is calculated from the blood flow vector and a volume. When the surgical instrument comes close to a blood vessel with a blood flow value exceeding a set blood flow value, an alert is issued (Step 112, 113). The surgical instrument reaches to a target site by navigation, so that a treatment is started (Steps 114, 115). <P>COPYRIGHT: (C)2010,JPO&INPIT

Description

  The present invention relates to a medical image diagnostic apparatus such as a magnetic resonance imaging apparatus.

  A nuclear magnetic resonance imaging apparatus (MRI apparatus), which is a medical diagnostic imaging apparatus, continuously measures nuclear magnetic resonance signals (MR signals) from hydrogen, phosphorus, etc. in a subject, and distributes nuclear density distribution and relaxation time distribution. Etc. are visualized.

  In an I-MRI apparatus (interventional-MRI apparatus or an abbreviated name of Intraperactive-MRI apparatus) used for cardiac imaging using an MRI apparatus, puncture monitoring during surgery, percutaneous treatment, etc. There is a desire to set the surface arbitrarily. As a method for arbitrarily selecting a tomographic plane to be imaged, a method of displaying an MRI image on a graphical user interface, clicking a button on the screen, and determining a tomographic plane to be imaged next (Non-Patent Document 1), A method using a three-dimensional mouse or the like (Patent Document 1) has been proposed.

  In these methods, since the position and orientation of the tomographic plane to be imaged must be adjusted and set by an input means such as a mouse, the MRI apparatus can adjust the position and orientation of the tomographic plane to be imaged more easily. It is desirable that it can be set. As such a technique, there has been proposed an MRI apparatus that determines a tomographic plane to be imaged using a tomographic plane indicating device (such as a pointer) disclosed in Patent Document 2 and Patent Document 3.

  In Patent Document 2, a light-emitting diode is provided on a pointer that is a tomographic plane indicating device, and an infrared camera detects the position pointed to by the operator, or a pointer is provided at the tip of an arm provided with a sensor at a joint. The position of the pointer is detected based on the angle of the joint of the arm and the tomographic plane is automatically adjusted based on the detected position. Japanese Patent Laid-Open No. 2004-228561 automatically determines and images a tomographic plane instructed using two infrared cameras and a pointer provided with three reflecting spheres. A large number of systems that are actually at a practical level have been published at academic societies and the like for clinical application results (Patent Document 4).

  In addition, a surgical navigation system using a position detection device and volume data captured in the past is a tomographic image in which a position designated by a pointer or the like to a patient at the time of surgery is taken as a cross section of each of three orthogonal planes of the patient including the position. It is a system for navigating surgical operations by displaying them on top, and is applied to high-precision surgical operations such as neurosurgery.

  Here, a tomographic image of a patient in such a surgical navigation system is generated in advance by volume data that is three-dimensional data captured by an MRI apparatus. On the other hand, methods for detecting the position of the pointer required for determining the designated position by the pointer include methods such as a mechanical method, an optical method, a magnetic method, and an ultrasonic method.

  In addition, a system has also been proposed in which a 4D image corresponding to a biological rhythm (respiration, pulse wave, heartbeat, etc.) is acquired in advance and the 4D image is displayed during surgery (Patent Document 5).

  As one application of the high-speed imaging sequence, a real-time dynamic imaging method called fluoroscopy (perspective imaging) is being clinically applied. In fluoroscopy, by repeating imaging and image reconstruction with a period of about 1 second or less, it can be used to extract the dynamics of internal tissues and to grasp the position of an instrument inserted from the outside like a fluoroscopic imaging. Generate and display dynamic images.

  This application is also applied to three-dimensional high-speed imaging. As a method, there is a technique in which Raw data is thinned and imaged, and complemented and reconstructed using previous data (Patent Document 6). For example, if TR = 1, Phase Encode = 20, and Slice Encode = 20, one volume of three-dimensional images can be continuously acquired every 400 ms.

  In addition, there is an ultrasonic diagnostic apparatus as a medical image diagnostic apparatus, and a two-dimensional ultrasonic image or a three-dimensional ultrasonic image is formed on a diagnostic region using a reflected echo signal obtained by transmitting and receiving ultrasonic waves in a subject. Are displayed. The ultrasonic diagnostic apparatus includes an ultrasonic probe including a transducer element that irradiates and receives an ultrasonic wave on a subject, an ultrasonic transmission / reception unit that transmits / receives an ultrasonic signal, and a two-dimensional ultrasonic wave based on the received signal. An ultrasonic image composing unit that forms an image (B-mode image) or a three-dimensional ultrasonic image, a display unit that displays an ultrasonic image formed by the ultrasonic image composing unit, a control unit that controls these, and a control And a control panel for giving instructions to the unit.

  At present, the technique of ultrasonic image processing is advancing, and there is a color Doppler method that displays the blood flow in the direction toward the probe in red and the blood flow in the direction away from the probe in blue (Patent Document 7). As an advantage, the blood flow can be evaluated by not only displaying the fast blood flow and the slow blood flow at the same time, but also adjusting the color gain to display the brighter as the speed increases.

US Pat. No. 5,512,827 US Pat. No. 5,365,927 US Pat. No. 6,063,315 International Publication No. 03/026505 Pamphlet JP 2007-185278 A US Pat. No. 6,044,290 Japanese Patent No. 3029706 Magnetic Resonance in Medicine: Real-time interactive MRI on a conventional scanner; AB. Kerr et al., 38, pp. 355-367 (1997)

  Since the image by the color Doppler method can browse real-time blood flow information using an ultrasonic two-dimensional image, it is a function that plays an important role not only in diagnosis but also in the surgical field.

  However, the displayed blood flow information is a two-dimensional image, and browsing the blood flow information in three dimensions such as depth information has not yet been realized. Moreover, since the current color Doppler function is a function attached to the ultrasonic apparatus, there is a demerit that can be drawn only within a range where the ultrasonic wave can reach.

  An object of the present invention is to realize a medical image diagnostic apparatus capable of displaying blood flow information three-dimensionally.

  In order to achieve the above object, the present invention is configured as follows.

  In a medical image diagnostic apparatus having an imaging means for imaging three-dimensional image information of a subject, a surgical instrument detection means, and an image display means for displaying a cross-sectional image of the subject and a surgical instrument, the imaging means and the surgical instrument detection And a control calculation means for controlling the image display means, the control calculation means calculates a blood flow vector of the blood vessel from the three-dimensional image information of the subject obtained by the imaging means, and detects it by the surgical instrument detection means. The blood flow direction of the blood vessel with respect to the distal end position of the surgical instrument is calculated based on the blood flow vector, and a color predetermined for the calculated blood flow direction is added to the blood vessel portion of the cross-sectional image of the subject. The three-dimensional image is displayed on the image display means together with the surgical instrument.

  A medical image diagnostic apparatus capable of displaying blood flow information three-dimensionally can be realized.

  Hereinafter, embodiments of the present invention will be described in detail with reference to the accompanying drawings.

  FIG. 1 is an operation flowchart in a position embodiment of the present invention, and FIG. 2 is a schematic configuration diagram of an MRI apparatus to which the present invention is applied.

  First, the MRI apparatus 1 shown in FIG. 2 will be described. The MRI apparatus 1 is, for example, a vertical magnetic field type 0.3T permanent magnet type MRI apparatus, and connects the upper magnet 3 and the lower magnet 5 that generate a vertical static magnetic field, and supports the upper magnet 3. Support column 7, position detection device 9, arm 11, monitors 13 and 14, monitor support unit 15, reference tool 17, personal computer 19, bed 21, and control unit 23.

  A gradient magnetic field generation unit (not shown) of the MRI apparatus 1 generates a gradient magnetic field in a pulse manner, has a maximum gradient magnetic field strength of 15 mT / m, and a slew rate of 20 mT / m / ms. Furthermore, the MRI apparatus 1 includes an RF transmitter (not shown) for generating nuclear magnetic resonance in the subject 24 in a static magnetic field, and an RF receiver (not shown) that receives a nuclear magnetic resonance signal from the subject 24. These are 12.88 MHz resonant coils.

  The position detection device (surgical instrument detection means) 9 includes two infrared cameras 25 and a light emitting diode (not shown) that emits infrared light, and detects the position and posture of a pointer 27 that is a tomographic plane indicating device. Further, the position detection device 9 is connected to the upper magnet 3 so as to be movable by the arm 11, and the arrangement relative to the MRI apparatus 1 can be appropriately changed as shown in FIG.

  The monitor 13 displays an image of the tomographic plane of the subject 24 indicated by the pointer 27 held by the operator 29, and is connected to the upper magnet 3 by the monitor support unit 15 similarly to the infrared camera 25. . The reference tool 17 links the coordinate system of the infrared camera 25 and the coordinate system of the MRI apparatus 1, includes three reflecting spheres 35, and is provided on the side surface of the upper magnet 3.

  The position of the pointer 27 detected and calculated by the infrared camera 25 is transmitted to the personal computer 19 via the RS232C cable 33 as position data, for example. The control unit 23 includes a workstation and controls an RF transmitter, an RF receiver, and the like (not shown). The control unit 23 is connected to the personal computer 19. In the personal computer 19, the position of the pointer 27 detected and calculated by the infrared camera 25 is converted into position data usable by the MRI apparatus 1 and transmitted to the control unit 23. The position data is reflected on the imaging section of the imaging sequence. An image acquired with a new imaging section is displayed on the liquid crystal monitor 13.

  The personal computer 19 and the control unit 23 constitute control calculation means.

  The image is simultaneously recorded in the video recording device (image storage means) 34. For example, when the pointer 27 which is a tomographic plane indicating device is attached to the puncture needle 36 or the like and configured so that the position where the puncture needle 36 is located is always the imaging section, the monitor 13 displays a section that always includes the needle. Become. A synchronous measuring device (biological information acquisition means) 38 is attached to the subject 24. The biological information (respiration, pulse, heartbeat, etc.) measured by the synchronous measurement device 38 is measured, and a 4D volume image is acquired.

  FIG. 3 is an explanatory diagram of a 4D volume image acquisition example. In FIG. 3, biological information (respiration, pulse wave, heartbeat, etc.) is acquired from the synchronous measurement device 38 attached to the patient (process 301). Here, the respiratory information of the subject is monitored, and an example of 3 phases of inspiration / inspiration-expiration intermediate / expiration is shown. The 3D imaging 305 synchronized with the inhalation phase 302, the 3D imaging 306 synchronized with the inhalation-expiration intermediate phase, and the 3D imaging 307 synchronized with the expiration phase are performed in time series and recorded on the memory 34 (process 308).

  FIG. 4 is an explanatory diagram of a 4D volume image reconstruction example. In FIG. 4, the biological information is acquired by the biological synchronization measuring device 405 attached to the subject 401, the position of the surgical instrument 402 is detected by the three-dimensional position detection camera 403, and the imaging section 404 is calculated. Here, there are three patterns of biological information (breathing information): inspiration 407, expiration 409, and intermediate 408, and since each 3D volume image 410-412 is recorded on the memory, it is synchronized with the breathing information at the time of surgery. The image 413 can be provided in real time.

  The operation of the embodiment of the present invention using the MRI apparatus shown in FIG. 2 will be described with reference to FIG.

  In FIG. 1, a synchronous measurement device 38 for monitoring is mounted on the subject 24 (step 101), and 4D high-speed imaging is started by the MRI apparatus 1 (step 102). A contrast medium is injected in synchronization with the biological monitor information (step 103), and a time-series blood flow 4D image is acquired (step 104). Image processing in each time phase is performed (step 105), and blood flow vectors in units of pixels are drawn (step 106).

  Next, navigation is started (step 107), blood flow 4D image information is read (step 108), and surgery is started (step 109). Since the biological synchronization measuring device 38 can acquire biological information in real time, 4D navigation is displayed in synchronization with the biological information (step 110), and blood flow information is superimposed and displayed thereon (step 111).

  Here, the position of the surgical instrument 36 is detected by a three-dimensional surgical instrument position detection device (17, 25, etc.), and three-dimensional blood flow information centered on the needle tip of the surgical instrument 36 is calculated in real time. The blood flow flowing toward and the blood flow information moving away are displayed in different colors (step 112). Further, the blood flow volume is calculated from the blood flow vector and the volume, and a warning is displayed on the image display means 13 and 14 when the surgical instrument approaches a blood vessel exceeding a preset blood flow value within a certain distance (step 113). Then, the target part is reached using various navigations (step 114), and then treatment is started (step 115).

  FIG. 5 is an explanatory diagram of a blood flow vector rendering method using 3D high-speed imaging. In FIG. 5, the imaging sequence is generally single echo gradient echo or multi-echo echo planner (EPI) 3D imaging. Simultaneously with the application of the RF pulse 701, an encode pulse 702 for determining the slice width and an encode pulse 704 for determining the slice position are applied. Further, the phase encode pulses 705 and 706 are controlled, and the echo is acquired by the readout pulse 703 for acquiring the echo. The acquired data 707 is reconstructed in the k space, but only the center data 708 is continuously imaged in order to perform high-speed imaging, and the peripheral data is complemented using past data.

  For example, since the respiratory motion has a period of about 4 seconds, if the number of time phases is 4, an imaging time of 1 second can be secured for one time phase. If TR = 1, Phase Encode = 30, and Slice Encode = 30, one volume of a three-dimensional image can be acquired in 900 ms, and 3D imaging (that is, 4D imaging) is performed according to the time phase.

  Here, FIG. 5 shows an example when the contrast medium 710 is injected into the artery (or vein). When the contrast agent 710 flows into the 3D image 711 during continuous imaging, the inflow portion 713 is detected on the 3D image 712 in the next scan. By repeating this imaging (images 714 and 716), time-series images and blood flow information 715 and 717 are drawn.

  FIG. 6 is an explanatory diagram of a blood flow vector rendering method. In FIG. 6, by calculating the difference between the 3D volume image 801 obtained in time series and the 3D image 802 acquired immediately before, a blood flow vector in pixel units (one scan unit) can be drawn (image 803). To show). By adding those obtained by repeating this calculation a plurality of times (a plurality of images 804), a blood flow vector in units of pixels in the volume can be obtained (shown in an image 805).

  FIG. 12 is a diagram illustrating an example of 4D imaging timing (four time phases) at the time of contrast medium injection according to an embodiment of the present invention. The example shown in FIG. 12 is an example of four time phases of exhalation 1502, intermediate (1) 1503, inspiration 1504, and intermediate (2) 1505. First, contrast medium is injected at the timing of expiration (time 1530, expiration (time 1502)), intermediate (1) (1503, data 1512), inspiration 1504 (data 1518), intermediate (2) (1505, data 1524) Data is acquired at the timing.

  The acquired data is reconstructed as raw data in the k space (data 1509, 1515, 1521, 1527). Further, if necessary, multi-slice imaging can be performed, and data at different slice positions can be captured at the next timing (data 1507, 1508) and stored as raw data (data 1510, 1511).

  Similarly, acquisition data 1513 and 1514 and Raw data 1516 and 1517 for the intermediate (1), acquisition data 1519 and 1520 and Raw data 1522 and 1523 for the intake air, and acquisition data 1525 and 1526 and Raw for the intermediate (2). The relationship between the data 1528 and 1529 is established and recorded in the memory.

  FIG. 13 is a diagram illustrating a 4D image rearrangement example according to an embodiment of the present invention. Here, an example of three time phases of an expiration 1601, an intermediate 1602, and an inspiration 1603 with respect to the respiratory waveform is shown. In FIG. 13, a contrast medium is injected at the timing of expiration (time 1604), and volume images are acquired at the timing of expiration (time 1601), intermediate (time 1602), and inspiration (time 1603) (images 1605 to 1607).

  However, in the image reconstruction (rearrangement), the exhalation image 1608, the intermediate image 1609, and the inspiration image 1610 are stored on the memory. At the next contrast timing, a contrast medium is injected at an intermediate timing between expiration and inspiration, and volume images are acquired (images 1612 to 1614). Similarly to the above, in the image reconstruction (rearrangement), the exhalation image 1615, the intermediate image 1616, and the inspiration image 1617 are stored in the memory.

  Here, by performing difference processing from the previous volume data, a blood flow vector is calculated, and a vector component in pixel units is extracted. In the third contrast (time 1621), contrast is performed at the timing of expiration, volume images 1622 to 1624 are acquired, and image reconstruction (rearrangement) is performed so that the expiration image 1625, intermediate image 1626, and inspiration image 1627 are stored in the memory. Save to. Similarly to the above, a blood flow vector is calculated by performing a difference process from the previous volume data, and a vector component in pixel units is extracted. By adding these pieces of information, 4D images corresponding to the number of time phases are obtained (images 1631 to 1633).

  FIG. 7 is an explanatory diagram of a clinical GUI display example and a color Doppler display method according to an embodiment of the present invention.

  In FIG. 7, the operator 902 approaches the subject 901 from the right side. Since the operator 902 approaches the surgical instrument 903 from the right side of the subject 901, the surgical instrument 909 is displayed on the GUI 904 on images 905 to 907 on a triaxial section and a Volume Rendering image 908. Here, the relationship between the blood flow directions is calculated in pixel units in real time with the distal end of the surgical instrument 909 as a reference, the blood flow in the direction toward the distal end is indicated by the red display portion 911, and the blood flow moving away is indicated by the blue display portion 910. Yes.

  That is, the direction vector of the surgical instrument 909 (the vector toward the distal end of the surgical instrument group 909 along the length direction of the surgical instrument 909) and whether the blood flow is directed toward or away from the distal end of the surgical instrument 909. Judging. If the blood flow direction and the length direction of the surgical instrument 909 are orthogonal to each other and it is difficult to determine whether the blood flow direction is toward or away from the distal end of the surgical instrument 909, the blood vessel part can be displayed in yellow. is there.

  FIG. 8 shows a state where the operator 1002 approaches the subject 1001 from the left side. Similarly to the above, since the surgeon 1002 approaches the surgical instrument 1003 from the right side of the subject 1001, the surgical instrument 1009 is displayed on the GUI 1004 on the images 1005 to 1007 on the three-axis cross section and the Volume Rendering image 1008. Is displayed.

  Here, the relationship of the blood flow direction is calculated in pixel units in real time with the distal end of the surgical instrument 1002 as a reference, the blood flow in the direction toward the distal end of the surgical instrument 1002 is displayed with the red display unit 1010, and the blood flow away is the blue display unit. This is indicated by 1011.

  8 differs from the example shown in FIG. 7 in that the blood flow information is reversed due to the reverse direction of the surgical instrument, that is, the red display portion and the blue display portion are reversed. . This is because blood flow information is displayed following the position of the surgical instrument 1002.

  The operator can easily determine whether the blood vessel is an artery or a vein based on the tomographic image and the direction of blood flow.

  FIG. 9 is a diagram showing a preoperative GUI display example according to an embodiment of the present invention. In FIG. 9, an entire screen 1100 includes a screen portion 1127 indicating patient monitor information in addition to a screen portion 1130 indicating the state of device information, patient information, function information, and surgical tool information. Also, by setting the number of time phases with the time phase number setting button 1101, division information for one period 1126 is displayed on the patient monitor information (time points 1121 to 1125).

  Further, by pressing the 4D imaging buttons 1102 and 1103 and the contrast agent injection button 1104, volume imaging corresponding to each time phase is automatically performed on the monitor and displayed as a list (display units 1111 to 1119). Further, by pressing the 4D blood flow analysis button 1105, it can be displayed together with the blood flow information.

  A 4D navigation button 1106, a 4D color Doppler button 1107, a 2D navigation button 1108, and a three-dimensional position information button 1109 are also displayed.

  FIG. 10 is a diagram showing a GUI display example 1201 during surgery. In FIG. 10, when the 4D navigation button 1106 is pressed, images 1203 to 1205 and a Volume Rendering image 1206 on the three-axis cross section are displayed on the GUI 1201, and the surgical instrument 1209 is displayed.

  Further, when the 4D color Doppler button 1107 is pressed, the current state 1213 and the real-time waveform 1212 are displayed on the biological information monitor 1211, and the blood flow in the direction toward the distal end of the surgical instrument is displayed on the red display unit 1208 in synchronization therewith. The blood flow that moves away is displayed on the blue display unit 1207.

  If necessary, a 2D navigation button 1108 is pressed to display a real-time imaging section including the surgical instrument 1222 on the screen 1221, and a 3D position information button 1109 is pressed to display a 3D stereoscopic screen 1231. Surgical instrument information 1232 and 1233 and segmentation information 1234 to 1236 are displayed, and the screen is configured so that the three-dimensional solid position configuration can be seen at a glance.

  FIG. 11 is a diagram showing a time chart at the time of surgery in one embodiment of the present invention. In FIG. 11, a living body monitor is attached to the subject (step 1301), and then a contrast medium is injected (step 1302), and 4D imaging is performed (step 1303). A blood flow vector is calculated from the difference image (step 1304), surgery is started (step 1305), and then the surgical instrument position is detected (step 1306).

  On the other hand, 4D navigation is displayed in synchronization with the biological monitor (step 1307), and the blood flow information can be superimposed and displayed on the monitor by calculating a real-time blood flow vector based on the surgical instrument position information. (Step 1308). Specifically, the blood flow direction is displayed in different colors with the surgical instrument tip position as the center (step 1309), and a warning function can be activated if necessary (step 1310). This function is repeated until treatment is started (step 1311).

  As described above, according to an embodiment of the present invention, in the MRI apparatus, a contrast medium is injected in synchronization with the obtained biological information (each time phase) to perform 4D imaging, and a blood flow vector is obtained by image processing. It is calculated and blood flow information is superimposed and displayed during surgical navigation. In addition, the surgical navigation is configured to display a 4D image in synchronization with biological information and to color-display the blood flow direction as viewed from the surgical instrument tip position.

  As a result, 3D display (four-dimensional) can be used to visualize 4D fluid information, and in addition to the 4D navigation function that is generally performed, the amount of surgery information can be increased, which improves surgical accuracy. Can provide support.

  In addition to the superimposed display of blood flow information, the present invention can also simultaneously depict soft tissue that cannot be supplemented by an ultrasonic device, so there is also an advantage of finding a target disease, reducing stress on the operator / patient and operating time Minimally invasive due to shortening can be expected.

  The above-described example is an example in which the blood flow direction of the blood vessel is displayed in a three-dimensional manner. However, since fluid information such as the blood vessel can be imaged, not only the blood vessel but also the flow direction of lymph fluid and cerebrospinal fluid is visualized. It is also possible to do.

  The above-described example is an example in which the present invention is applied to an MRI apparatus. However, the present invention is applicable not only to an MRI apparatus but also to other medical image diagnostic apparatuses capable of three-dimensional imaging such as a CT apparatus. Applicable.

  Here, an example different from the present invention regarding 4D imaging timing will be described. This is done for comparison with the present invention.

  FIG. 14 is a diagram showing 4D imaging timing by a method different from the present invention. The example shown in FIG. 14 is an example that is synchronized with the respiratory waveform 1401 of the subject, and is divided into four parts: exhalation 1402, intermediate (1) 1403, inspiration 1404, and intermediate (2) 1405. Here, although high-speed imaging is performed, the data acquisition method acquires data 1406 at the timing of expiration, and the next data is in order of intermediate (1) data 1407, inspiration data 1408, and intermediate (2) data 1409. The data acquisition is performed, and the process returns to the acquisition of the first exhalation data 1410.

  However, the data to be acquired is acquired by controlling the phase encoding pulse to acquire data different from the previous data (data 1410 to 1413). By repeating this a predetermined number of times, four-dimensional two-dimensional data can be acquired (data 1410 to 1421). Further, slice encoding is applied in the kz direction, and two-dimensional data is acquired again (data 1430 to 1432). By performing the processing 1440 of repeating this a predetermined number of times, 3D volume images for four time phases are finally obtained (data 1450 to 1453), and as a result, 4D data 1441 is obtained.

  In the example shown in FIG. 14, not only the center data but also the peripheral data is acquired. However, in the embodiment of the present invention shown in FIG. 12, only the center data is acquired. That is, in the embodiment of the present invention, as shown in FIG. 12, only the center data is acquired in order to execute the high-speed imaging method.

It is an operation | movement flowchart of one Embodiment of this invention. 1 is a schematic structural diagram of an MRI apparatus to which an embodiment of the present invention is applied. It is explanatory drawing of the example of 4D volume image acquisition. It is explanatory drawing of the example of 4D volume image reconstruction. It is explanatory drawing of the blood-flow vector extraction method by the high-speed 3D imaging method in one Embodiment of this invention. It is explanatory drawing of the blood-flow vector extraction method by the high-speed 3D imaging method in one Embodiment of this invention. It is explanatory drawing of the GUI display example at the time of clinical in one Embodiment of this invention, and a color Doppler display method. It is explanatory drawing of the GUI display example at the time of clinical in one Embodiment of this invention, and a color Doppler display method. It is a GUI (preoperative) schematic diagram in one embodiment of the present invention. It is a GUI (intraoperative) schematic diagram in one Embodiment of this invention. It is an operation | movement time chart at the time of the surgery in one Embodiment of this invention. It is a figure which shows an example of the 4D imaging timing at the time of contrast agent injection | pouring in one Embodiment of this invention. It is a figure which shows the example of 4D image rearrangement in one Embodiment of this invention. It is a figure which shows 4D imaging timing by the method different from this invention.

Explanation of symbols

  DESCRIPTION OF SYMBOLS 1 ... MRI apparatus, 3 ... Upper magnet, 5 ... Lower magnet, 7 ... Support | pillar, 9 ... Position detection device, 11 ... Arm, 13, 14 ... Monitor, 15・ ・ ・ Monitor support unit, 17 ... Reference tool, 19 ... Personal computer, 21 ... Bed, 23 ... Control unit, 24 ... Subject, 25 ... Infrared camera, 27 ..Pointer 29 ... Operator 34 ... Video recording device 35 ... Reflective sphere 36 ... Surgery tool 38 ... Synchronous measuring device

Claims (8)

In a medical image diagnostic apparatus including an imaging unit that captures three-dimensional image information of a subject, a surgical instrument detection unit, and an image display unit that displays a cross-sectional image of the subject and a surgical instrument.
A control operation unit that controls the imaging unit, the surgical instrument detection unit, and the image display unit, and calculates a blood flow vector of the blood vessel from the three-dimensional image information of the subject obtained by the imaging unit, and the surgical instrument detection unit The blood flow direction of the blood vessel with respect to the detected tip position of the surgical instrument is calculated based on the blood flow vector, and a color predetermined for the calculated blood flow direction is added to the blood vessel portion of the cross-sectional image of the subject. And a medical image diagnostic apparatus comprising control arithmetic means for causing the image display means to display a three-dimensional image together with the surgical instrument.   2. The medical image diagnostic apparatus according to claim 1, further comprising biological information acquisition means for acquiring biological information of the subject, wherein the control calculation means is a cross section of the subject synchronized with the biological information acquired by the biological information acquisition means. A medical image diagnostic apparatus, wherein an image is displayed on the image display unit together with a blood vessel portion to which the color is added and the surgical instrument.   The medical image diagnostic apparatus according to claim 2, wherein the control calculation unit divides a cycle of a biological rhythm obtained from the biological information, causes the cross-sectional image of the subject to be captured at the time of the division, and causes the image display unit to perform imaging. A medical image diagnostic apparatus characterized by being displayed.   4. The medical image diagnostic apparatus according to claim 3, further comprising an image storage unit, wherein the biological information is respiratory information, and the inspiration, the interval between inspiration and expiration, and the expiration time in one cycle of the respiratory information are divided time points, and each divided time point is determined. A medical image diagnostic apparatus, wherein a cross-sectional image of each subject is stored in the image storage means.   2. The medical image diagnostic apparatus according to claim 1, wherein the control calculation means captures a plurality of three-dimensional images of the subject in time series, and subtracts images that are temporally forward and backward from each other to subtract blood flow directions of blood vessels. A medical image diagnostic apparatus characterized by calculating a vector.   3. The medical image diagnosis apparatus according to claim 2, wherein the control calculation unit displays the biological information acquired by the biological information acquisition unit and the three-dimensional image of the subject on the image display unit. Diagnostic imaging device.   2. The medical image diagnostic apparatus according to claim 1, wherein the control calculation means calculates a blood flow volume from a blood vessel volume and the blood flow vector from the three-dimensional image information of the subject, and determines a predetermined constant blood flow. A medical image diagnostic apparatus characterized in that a warning is displayed on the display means when the surgical instrument approaches a blood vessel at a certain distance. Static magnetic field generation means, gradient magnetic field generation means, high frequency signal transmission / reception means, image display means, control of the static magnetic field generation means, gradient magnetic field generation means, high frequency signal transmission / reception means and image display means, and transmission / reception of the high frequency signal Control means for acquiring three-dimensional image information of the subject based on the nuclear magnetic resonance signal received by the means, reconstructing the image of the subject and displaying the image on the image display means, and a surgical instrument detection means In a magnetic resonance imaging apparatus,
The control calculation means calculates a blood flow vector of the blood vessel from the three-dimensional image information of the subject, and sets the blood flow direction of the blood vessel with respect to the distal end position of the surgical tool detected by the surgical tool detection means as the blood flow vector. And a predetermined color for the calculated blood flow direction is added to the blood vessel portion of the cross-sectional image of the subject, and a three-dimensional image is displayed on the image display means together with the surgical instrument. Magnetic resonance imaging device.

Images