CN101449976B - Diagnostic imaging apparatus, magnetic resonance imaging apparatus, and X-ray CT apparatus - Google Patents
Diagnostic imaging apparatus, magnetic resonance imaging apparatus, and X-ray CT apparatus Download PDFInfo
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Abstract
The invention provides a diagnostic imaging apparatus, a magnetic resonance imaging apparatus and an X-ray CT apparatus. The diagnostic imaging apparatus includes a ventricular volume-variation measuring unit that measures sequential variations in a size of a ventricle within at least one heart beat, from images of a heart scanned in each of a plurality of time phases; a scanning-condition setting unit that specifies a time phase of little cardiac motion based on variations in the size of the ventricle measured by the ventricular volume-variation measuring unit, and sets scanning conditions so as to collect data in the specified time phase; and an imaging unit that collects data based on the scanning conditions set by the scanning-condition setting unit, and reconstructs an image from the collected data.
Description
The application enjoys the rights and interests of priority of the Japanese patent application No. 2008-272448 of the Japanese patent application No. 2007-317613 of December in 2007 application on the 7th and application on October 22nd, 2008, and quotes the full content of this Japanese patent application in this application.
Technical field
The present invention relates to set imaging conditions and carry out synchronously that data (data) are collected and the image diagnosing system, nuclear magnetic resonance (imaging) device and X ray CT (the Computed Tomography that make a video recording with ecg wave form with subject, computer tomography) device, be particularly related to and need not to append special shooting and based on judgement of operator etc., and the technology of the timing (timing) that is used for automatically determining cardiac motion few.
Background technology
In the past, utilizing the heart shooting of MR imaging apparatus, particularly coronary artery shooting etc. requires in the camera method of high spatial resolution, the deterioration in image quality that causes for the action that suppresses owing to heart is arranged, and optionally carrying out the method for data collection, the few time phase of the heartbeat in cardiac cycle (, waits " Submillimeter Three-dimensional Coronary MR Angiography with Real-TimeNavigator Correction:Comparison of NavigatorLocations. " Radiology 1999 for example with reference to Stuber M; 212:579-587.).In the method, (window (window)) makes a video recording during preestablishing certain time delay that the R ripple that obtains with the ecg wave form from the patient is a starting point and certain data collection, but the few time-dependent of known above-mentioned time delay and heartbeat is in beats of patient etc.
Therefore, following method has been proposed: make a video recording at heart, particularly in the coronary artery shooting, in order to ensure picture quality, carry out to know animation (cine) shooting etc. of short time of degree of the action of the tremulous pulse that becomes object in advance, the operator visually judge heartbeat few during, set during this period and make a video recording and (, wait " Three-Dimensional Coronary MR Angiography Performed withSubject-Specific Cardiac Acquisition Window and Motion-adoptedRespiratory Gating. " AJR 2003 for example with reference to Plein S at each patient; 180:505-512.).
But, in above-mentioned previous methods, need with a series of inspection independently, position again, append the animation shooting of depicting section coronarius, and then the operator is by the visual periodic setting of making a video recording.Therefore, in previous methods, the review time is extended, and operator and patient's etc. burden increases, and produces the problem of unstable because the shooting timing offset that is caused by the operator and picture quality become.
Summary of the invention
The image diagnosing system of a mode of the present invention possesses: ventricle variable quantity measurement portion, from measure at each and the cardiac image of making a video recording of a plurality of time phases ventricle size at least heart beating through the time change; The time phase that above-mentioned cardiac motion is few is determined according to the variation of the above-mentioned ventricle size of being measured by above-mentioned ventricle variable quantity measurement portion in the imaging conditions configuration part, and the setting imaging conditions is to collect the data of determined time phase; And image pickup portion, collect data according to the imaging conditions of setting by above-mentioned imaging conditions configuration part, and from collected data reconstruction image.
In addition, the MR imaging apparatus of alternate manner of the present invention possesses: ventricle variable quantity measurement portion, from the ventricle size at least heart beating of image measurement of each and the heart of making a video recording of a plurality of time phases through the time change; The time phase that above-mentioned cardiac motion is few is determined according to the variation of the above-mentioned ventricle size of being measured by above-mentioned ventricle variable quantity measurement portion in the imaging conditions configuration part, and the setting imaging conditions is to collect the data of determined time phase; And image pickup portion, collect data according to the imaging conditions of setting by above-mentioned imaging conditions configuration part, and from collected data reconstruction image.
In addition, the X ray CT device of alternate manner of the present invention possesses: ventricle variable quantity measurement portion, from the size of the ventricle at least heart beating of image measurement of each and the heart of making a video recording of a plurality of time phases through the time change; The time phase that above-mentioned cardiac motion is few is determined according to the variation of the above-mentioned ventricle size of being measured by above-mentioned ventricle variable quantity measurement portion in the imaging conditions configuration part, and the setting imaging conditions is to collect the data of determined time phase; And image pickup portion, collect data according to the imaging conditions of setting by above-mentioned imaging conditions configuration part, and from collected data reconstruction image.
Description of drawings
Fig. 1 is the figure that is used for illustrating the method for data capture of MRI device in the past.
Fig. 2 is the flow chart (flowchart) that the flow process of heart MR inspection in the past is shown.
Fig. 3 is the integrally-built figure that the MRI device of present embodiment is shown.
Fig. 4 is the figure that is used to illustrate the profile extraction that utilizes ventricle variable quantity measurement portion.
Fig. 5 is the figure that the relation of the time phase that obtained by ventricle variable quantity measurement portion and left ventricular volume is shown.
Fig. 6 is the figure that the relation of the time phase that obtained by ventricle variable quantity measurement portion and left ventricular volume variable quantity is shown.
Fig. 7 is used to illustrate the figure that utilizes the imaging conditions configuration part to determine time phase.
Fig. 8 is the flow chart that explanation utilizes the flow process that the heart MR of the MRI device of present embodiment checks.
Fig. 9 is the flow chart that the treatment step of imaging conditions setting shown in Figure 8 is shown.
Figure 10 is the figure of structure that the X ray CT device of embodiment 2 is shown.
The specific embodiment
Following with reference to accompanying drawing, the preferred embodiment of image diagnosing system of the present invention, MR imaging apparatus and X ray CT device is elaborated.In addition, in embodiment shown below, MR imaging apparatus is called " MRI (Magnetic ResonanceImaging) device ".
At first, before carrying out the explanation relevant, the flow process of method of data capture in the MRI device in the past and cardiac MRI inspection is in the past described with the MRI device of embodiment 1.
At first, the method for data capture in the MRI device is in the past described.Fig. 1 is the figure that is used for illustrating the method for data capture of MRI device in the past.The collection that Fig. 1 illustrates in the above-mentioned non-patent literature 1 record is the example of camera method of MRI device of the data in the specific cardiac time stage in the cardiac cycle of representative with the coronary artery shooting.
Shown in " ecg wave form " and " pulse train (pulse sequence) " of Fig. 1, for example, MRI device in the past utilizes examinee's's (subject) ecg wave form to detect the R ripple, begin data collection after the Td certain time delay having passed through, thereby only collect the few time phase of cardiac motion, be commonly referred to as the ventricular dilatation phase or slowly flow into the data of the time phase of phase.
Herein, Fig. 1 " left ventricular volume " as with an example of the action physical quantity corresponding of heart, the variation of expression left ventricular volume in a cardiac cycle.As shown in this " left ventricular volume ", the flat of ventricular volume, can suppress because the picture quality reduction that the influence of cardiac motion causes by carrying out data collection during this period corresponding to the few time phase of cardiac motion.
Particularly, this MRI device as shown in Figure 1, till the Ts zero hour that tails off from cardiac motion plays the moment Te that heart begins to move once more during, carry out data collection.Pulse train when creating shooting so that be starting point with the R ripple, Ts begins data collection in the moment, during Tw carry out data collection, collect in moment Te end data.Herein, Tw=Te-Ts.Be configured to Ts from Td time delay of R ripple, if the reciprocal time of pulse train is made as TR, data line (data line) the number N that then can collect in a heart beating becomes N=Tw/TR.
For example, consider to carry out the situation that three-dimensional data is collected.(slice) number coding (encode) number Kz that promptly cut into slices are made as 60 if will cut into slices, and matrix (matrix) the number Ky of phase-encoding direction are made as 120, and then required number of data lines is Kz * Ky=60 * 120=7200 in the image reconstruction.Herein, when will be in a cardiac cycle cardiac motion few during Te-Ts when being made as 100 milliseconds, if the reciprocal time TR of pulse train is 5 milliseconds, the data that in a heart beating, can collect the 100/5=20 line then.Therefore, in order to collect all required in image reconstruction data, required heart beating number of times becomes 7200/20=360 heart beating, if a heart beating was made as 1 second, then finishes shooting at 360 seconds=6 minutes.
In addition, general except the action of heart, also need to consider the action that the breathing by the patient causes, if the method combination of few data with optionally collecting the moving influence of the body that is caused by breathing, then Shi Ji camera time also prolonged than this time.In addition, under situations such as coronary artery shooting and myocardial delayed radiography, inversion pulse (inversion pulse), the T2 that prepared to be used to improve the contrast (contrast) of image before data collection emphasize priming pulse (preparation pulse), MTC (Magnetization Transfer Contrast, magnetization transfer contrast) pulse, be used to promote the puppet that arrives steady statue take (dummy shot), be used to suppress fat signal the fat suppression pulse, be used to detect and breathe the moving pulse of gonosome etc.In Fig. 1, prepulsing (pre-pulse) will be expressed as between these stage of preparation.
Herein, known heartbeat diminish during Ts to Te depend on examinee's beats.Therefore, as the method that is used to obtain stable picture quality, propose to set required Td of pulse train and the method for Tw created at each patient as record in the above-mentioned non-patent literature 2.In the method, before coronary artery shooting etc., collection can the visuognosis heart the animated image of section of action, visually confirm the time phase that skew coronarius is little and obtain above-mentioned Td, Tw and N, thereby check by the operator at each and to be set camera parameter (parameter) into the pulse train of this shooting.
Generally, the situation that the coronary artery shooting is carried out separately self in heart MR checks is less.For example, check at the MRI that is used for the diagnosis of ischemic heart disease, usually in once checking, carrying out (1) in groups is used to carry out the evaluation of local myocardial wall motion and animation shooting, (2) that cardiac function is measured and is used to estimate to radiography perfusion (perfusion) shooting and (3) of the blood supply of cardiac muscle and is used to carry out the myocardial delayed radiography shooting of myocardial infarction diagnosis and carries out comprehensive cardiac image diagnosis, and then for the narrow positions coronarius of the reason of determining to become ischemic heart disease, and append the shooting of (4) coronary artery.
According to the inspection policy of the performance of the hardware (hardware) of employed device and software (software), this facility, to review time of each patient's cost etc., and whether decision comprises the shooting of (4) coronary artery in a series of inspection.In addition, owing to need stress test and do not establish evaluation methodology, so it is also more not implement the situation that (2) myocardial perfusion checks to image.In addition, for (3) myocardial delayed radiography, though technical difficulty is lower, owing to must use contrast agent, so do not implement sometimes.Compare with them, make a video recording for (1) animation, owing to need not contrast agent and can use most of device to estimate the action and the cardiac function etc. of cardiac muscle simply, so be the most basic shooting of in the MR of ischemic heart disease checks, under all situations roughly, all implementing.
Next, the flow process that in the past heart MR is checked describes.Fig. 2 is the flow chart that the flow process of heart MR inspection in the past is shown.Fig. 2 illustrates an example of a succession of ischemic heart medical diagnosis on disease MR inspection of the inspection of carrying out above-mentioned (1) to (4).As shown in Figure 2, for example, the MRI device at first collected the location with image after (step S1), from heart base portion to apex till to carrying out animation shooting (step S2) with the corresponding a plurality of so-called short-axis slice of the cross section of left ventricle.
Next, the MRI device carries out myocardial perfusion (step S3) and postpones radiography shooting (step S4).At these myocardial perfusions and postpone in the radiography shooting, to looking like to make a video recording with the same minor axis of animation shooting.
Herein, in inspection method in the past, before carrying out the coronary artery shooting, the MRI device is to looking like to confirm that four chamber sections coronarius etc. position the action picture shooting (step S5) of going forward side by side according to minor axis, the operator shows continuously with by the few time phase of visual judgement action coronarius the image of being made a video recording, and will be used for the time delay of coronary artery shooting and the data collection time in the heart beating and set imaging conditions (step S6) for.Afterwards, the MRI device carries out coronary artery shooting (step S7) according to the imaging conditions that sets.
In above-mentioned heart MR checks, in the operation (step S6) of setting imaging conditions, usually, need one side to compare the image of the expansionary phase in the image in each the cardiac time stage about 20-50 opens successively, on one side by visual judgement artery position with low uncertainty during such operation, thereby generation will constrain in the so unsuitable situation of time lengthening in the device as the patient of subject.In addition, because this judgement depends on the operator, so sometimes the stability of the picture quality of coronary artery shooting is exerted an influence.And then, in this operation, also need according to the result who obtains herein, set the such operation of imaging conditions as the coronary artery shooting of camera parameter at each inspection (each patient) with above-mentioned Td and Tw, for the shortening of general inspection time and the repeatability of guaranteeing the coronary artery inspection, expectation is with this process automation.
In order to solve such problem, in embodiment 1, be not before carrying out the coronary artery shooting, to carry out the animation shooting as in the past again, the operator visually judge heartbeat few during and set imaging conditions, but the MRI device is automatically set imaging conditions according to an animated image of all implementing under all situations roughly in heart MR checks.
Particularly, the MRI device of embodiment 1 from cardiac image (animated image), measure by each and the subject P that makes a video recording a plurality of time phases ventricle size at least heart beating through the time variable quantity, and determine the time phase that cardiac motion is few according to measured variable quantity, set imaging conditions according to determined time phase.
Thus, in embodiment 1, need not to append special shooting and judge etc., just can automatically determine the timing that cardiac motion is few by the operator.
Below, above-mentioned MRI device is elaborated.At first, the structure to the MRI device of embodiment 1 describes.Fig. 3 is the figure of structure that the MRI device 100 of embodiment 1 is shown.As shown in Figure 3, this MRI device 100 possesses static field magnet 1, gradient magnetic field coil (coil) 2, leaning magnetic field power supply 3, bed 4, bed control part 5, sends RF coil 6, sending part 7, receives RF coil 8, acceptance division 9 and computer system (system) 10.
Gradient magnetic field coil 2 is the coils that form the drum of hollow, is disposed at the inboard of static field magnet 1.This gradient magnetic field coil 2 makes up with mutually orthogonal X, Y, each three corresponding coil of Z and forms, these three coils are from leaning magnetic field power supply 3 described later received current supply independently, and the generation magnetic field intensity is along the leaning magnetic field of X, Y, each variation of Z.In addition, Z-direction for example is made as the direction identical with magnetostatic field.
Herein, each leaning magnetic field of X, the Y that is taken place by gradient magnetic field coil 2, Z for example corresponds respectively to that section is selected with leaning magnetic field Gs, phase code is with leaning magnetic field Ge and read (read out) and use leaning magnetic field Gr.Section is selected to be used for arbitrary decision shooting section with leaning magnetic field Gs.Phase code is used for changing according to the locus phase place of magnetic resonance signal with leaning magnetic field Ge.Read the frequency that is used for changing magnetic resonance signal with leaning magnetic field Gr according to the locus.
Leaning magnetic field power supply 3 is devices of gradient magnetic field coil 2 being supplied with electric current.Bed 4 is the devices that possess the top board 4a of mounting subject P, according to the control that utilizes bed control part 5 described later, with top board 4a with mounting the state of subject P be inserted in the cavity (shooting mouthful) of gradient magnetic field coil 2.Usually, this 4 central axes that is configured to length direction and static field magnet 1.
Sending part 7 is the devices that are built-in with oscillating portion, phase place selection portion, frequency conversion part, Modulation and Amplitude Modulation portion, high frequency power enlarging section etc.The high-frequency signal of inherent resonant frequency in the object atoms nuclear in the oscillating portion generation magnetostatic field.The phase place selection portion is selected the phase place of above-mentioned high-frequency signal.The frequency conversion part conversion is from the frequency of the high-frequency signal of phase place selection portion output.Modulation and Amplitude Modulation portion for example modulates the amplitude from the high-frequency signal of frequency modulation(PFM) portion output according to the sinc function.Amplify from the high-frequency signal of Modulation and Amplitude Modulation portion output the high frequency power enlarging section.As the result of the action of these each ones, sending part 7 sends and the corresponding high-frequency impulse of Larmor (Larmor) frequency to sending RF coil 6.
Receiving RF coil 8 is the coils that are disposed at the inboard of gradient magnetic field coil 2, receives owing to the influence of above-mentioned high frequency magnetic field from the magnetic resonance signal of subject P emission.The output signal that is received by this reception RF coil 8 is imported into acceptance division 9.Acceptance division 9 is according to the device that generates magnetic resonance signal data from the output signal that receives RF coil 8.
The Signal Processing portion of interface portion 11 exchange between each one of these connections and computer system 10 that is input and output.On this interface portion 11, be connected with leaning magnetic field power supply 3, bed control part 5, sending part 7, receive RF coil 8 and acceptance division 9 etc.
Data collection portion 12 collects from numeral (digital) the Signal Processing portion of acceptance division 9 outputs via interface portion 11.This data collection portion 12 stores collected digital signal, is magnetic resonance signal data to storage part 14.
Reconstructing part 13 be carry out post processing to being stored in magnetic resonance signal data in the storage part 14, be reconstruct such as Fourier (Fourier) conversion, and generate the handling part of the desired images data in the subject P.
Storage part 14 is storage parts of the magnetic resonance signal data collected by data collection portion 12 at each patient storage and the view data that generated by reconstructing part 13 etc.For example, in this storage part 14, preserve the animated image of a plurality of sections of making a video recording etc. by animation.
Control part 17 is to have not shown CPU (Central Processing Unit, CPU), memorizer (memory) etc., and controls the handling part of the MRI device 100 of present embodiment generally.For example, the imaging conditions that this control part 17 is set by operator and imaging conditions described later configuration part 17b by basis etc. drives each one, and control MRI device 100, to carry out the heart shooting synchronous with ecg wave form.As with the related function portion of this heart shooting, control part 17 has ventricle variable quantity measurement 17a of portion and imaging conditions configuration part 17b.
The ventricle variable quantity measurement 17a of portion be from cardiac image, measure by each and the subject P that makes a video recording a plurality of time phases ventricle size at least heart beating through the time handling part that changes.Particularly, this ventricle variable quantity measurement 17a of portion at first reads by each the continuous minor axis animated image of the left ventricle of shooting a plurality of time phases from storage part 14, and automatically extracts myocardial contours from the animated image of being read.
As being used for the method that the ventricle variable quantity measurement 17a of portion automatically extracts myocardial contours, for example use the such known method of Japan Patent disclosed method No. 3668629 herein.Particularly, utilize steady state free precession (SSFP (Steady State Free Precession)) method to collect the animation shooting usually, because the contrast height between cardiac muscle and the chambers of the heart inner blood, so this method is easy to automatically extract profile.
Fig. 4 is the figure that is used to illustrate the profile extraction that utilizes the ventricle variable quantity measurement 17a of portion.Fig. 4 illustrates the animated image from the apex of left ventricle to a plurality of time phases of a plurality of sections (" 1 " shown in Figure 4～" N ") of heart base portion respectively and the profile of the myocardium of left ventricle inner membrance that extracts by said method.As shown in Figure 4, the ventricle variable quantity measurement 17a of portion looks like to extract the profile of myocardium inner membrance from all left ventriculographies of a plurality of sections and a plurality of time phases.
Next, the ventricle variable quantity measurement 17a of portion by each section, calculates the area of the inboard of inner membrance profile for a time phase, the area that is calculated be multiply by slice thickness, thereby calculate the left ventricular volume of each section.Then, the ventricle variable quantity measurement 17a of portion calculates the left ventricular volume under this time phase by adding up to each left ventricular volume of all sections calculated.
Afterwards, the ventricle variable quantity measurement 17a of portion carries out the calculating of the left ventricular volume of above-mentioned explanation by at all time phases, and generates the information of the relation of express time stage and left ventricular volume.Fig. 5 is the figure that the relation of the time phase that obtained by the ventricle variable quantity measurement 17a of portion and left ventricular volume is shown.The ventricle variable quantity measurement 17a of portion generate as shown in Figure 5 be illustrated in left ventricular volume in the heart beating through the time information that changes.In addition, this information is one of parameter of reflection cardiac function, be with embodiment 1 in the purpose general parameter of measuring in cardiac work up independently.
Next, the ventricle variable quantity measurement 17a of portion is according to the information of the relation of the time phase of representing above-mentioned generation and left ventricular volume, at each time phase, calculate the absolute value of the difference of left ventricular volume under this time phase and the left ventricular volume under the last time phase, thereby generate the information of the relation of express time stage and left ventricular volume variable quantity.Fig. 6 is the figure that the relation of the time phase that obtained by the ventricle variable quantity measurement 17a of portion and left ventricular volume variable quantity is shown.The ventricle variable quantity measurement 17a of portion generate left ventricular volume variable quantity in as shown in Figure 6 the heart beating of expression through the time information that changes.
In curve shown in Figure 6, the left ventricular volume variable quantity at the time change with low uncertainty during (" quiescent period " shown in Figure 6) become the few time phase of cardiac motion.
Imaging conditions configuration part 17b determines the time phase that cardiac motion is few according to the variation of the ventricle size of being measured by the ventricle variable quantity measurement 17a of portion, and sets the handling part of imaging conditions according to determined time phase.Particularly, this imaging conditions configuration part 17b is according to the information of the relation of time phase of representing to be generated by the ventricle variable quantity measurement 17a of portion and left ventricular volume variable quantity, determine the time phase that cardiac motion is few, and, set the imaging conditions in the heart shooting according to determined time phase.
Fig. 7 is used to illustrate the figure that utilizes imaging conditions configuration part 17b to determine time phase.Fig. 7 illustrates the time phase that is generated by the ventricle variable quantity measurement 17a of portion shown in Figure 6 and the relation of left ventricular volume variable quantity.For example, imaging conditions configuration part 17b is by on curve shown in Figure 7, determine after having passed through certain hour ((1) shown in Figure 7) from timeorigin, the left ventricular volume variable quantity becomes the moment of the value (shown in Figure 7 (2)) littler than predetermined value, thereby calculates suitable with Ts shown in Figure 1 and Te during the R ripple.
Then, imaging conditions configuration part 17b sets the imaging conditions in the heart shooting according to Ts that is calculated and Te.For example, under the situation of carrying out the coronary artery shooting, imaging conditions configuration part 17b by Td=Ts and N=Tw/TR (herein, calculate Tw by Tw=Te-Ts as shown in Figure 7) calculate respectively and set the required Td and the number of data lines N in heart beating time delay of imaging conditions from the R ripple, use the Td that calculated and the value of N to set imaging conditions.
Next, the flow process that the heart MR of the MRI device 100 that utilizes embodiment 1 is checked describes.Fig. 8 is the flow chart that explanation utilizes the flow process that the heart MR of the MRI device 100 of embodiment 1 checks.In addition, check that with MR shown in Figure 2 the situation of same inspection describes to carrying out herein.
As shown in Figure 8, in heart MR checks, the MRI device 100 of embodiment 1 at first collect the location with image after (step S11), from heart base portion to apex till to carrying out animation shooting (step S12) with the corresponding a plurality of so-called short-axis slice of the cross section of left ventricle.
Next, MRI device 100 carries out myocardial perfusion (step S13) and postpones radiography shooting (step S14).In these myocardial perfusions and the shooting of delay radiography, the minor axis identical with the animation shooting looked like to make a video recording.
Herein, MRI device 100 is with above-mentioned myocardial perfusion and postpone the radiography shooting concurrently, the imaging conditions (step S15) in the coronary artery shooting of proceeding after being set in.Setting to this imaging conditions is elaborated in the back.Then, MRI device 100 carries out coronary artery shooting (step S16) according to the imaging conditions that sets.
Next, the treatment step that imaging conditions shown in Figure 8 is set describes.Fig. 9 is the flow chart that the treatment step of imaging conditions setting shown in Figure 8 is shown.As shown in Figure 9, in this imaging conditions is set, in computer system 10, the ventricle variable quantity measurement 17a of portion extracts the profile (step S21) of myocardium of left ventricle inner membrance from the minor axis animated image of left ventricle, calculate left ventricular volume (step S22) at each time phase, so measure left ventricular volume through the time change (step S23).
Then, imaging conditions configuration part 17b according to the left ventricular volume of measuring by the ventricle variable quantity measurement 17a of portion through the time change, determine the few time phase of cardiac motion (step S24),, set the imaging conditions (step S25) in the coronary artery shooting according to determined time phase.
Like this, MRI device 100 according to embodiment 1, be not that as shown in Figure 2 heart MR in the past detects to carry out the animation shooting like that again before carrying out the coronary artery shooting, the operator visually judges the time period that heartbeat is few and sets imaging conditions, automatically sets imaging conditions but can make a video recording according to an animation of all implementing under all situations roughly in heart MR checks.
As mentioned above, in embodiment 1, the ventricle variable quantity measurement 17a of portion from measure by each and the cardiac image of the subject P that makes a video recording a plurality of time phases ventricle size at least heart beating through the time change.In addition, imaging conditions configuration part 17b determines the time phase that cardiac motion is few according to the variation of the ventricle size of being measured by the ventricle variable quantity measurement 17a of portion, and sets imaging conditions according to determined time phase.Therefore, need not to append special shooting and judge etc., can automatically determine the timing that cardiac motion is few by the operator.
Thus, for example can save: the shooting of appending and the wherein required positioning time that are used to observe action coronarius; And then save Visual Confirmation few time of action coronarius, and set the time of imaging conditions.In addition, by automatically setting imaging conditions, can suppress because the picture quality change that operator's judgement difference causes.
In addition, in the foregoing description 1, illustrated the picture picture aroused in interest (animated image of heart) of a plurality of sections of covering (cover) left ventricle integral body has been made a video recording, measured the volumetrical situation of left ventricle, but the invention is not restricted to this.That is, in automatically judging the such purpose of the present invention of the little time phase of cardiac motion, might not need volumetrical data.Therefore, for example also can use a section or a plurality of section of left-ventricular short-axis to make area of section curve, and use this area of section curve to replace volume curve.
In addition, according to checking agreement (protocol), carry out the situation of minor axis animation shooting in addition in addition.In this case, for example can also replace by the area of measuring long axis of left ventricle or the left ventricle area of measuring four chamber sections.And then, under the situation of the picture aroused in interest of not making a video recording fully, before coronary artery shooting, a section of left-ventricular short-axis is made a video recording, and extract automatically according to profile and to measure area and get final product.In this case, a section is only appended in the special shooting that will be used for the imaging conditions setting of coronary artery shooting, if but compare the effect of the repeatability of obtain shortening the review time, raising being made a video recording with the judgement based on visual in the past.
In addition, in the foregoing description 1, the situation of setting the imaging conditions in the coronary artery shooting is illustrated, but the invention is not restricted to this, even synchronously carry out also can similarly using under the situation of the imaging conditions in other shootings of data collection setting with ecg wave form.As synchronously carrying out the shooting of data collection, the non-radiography blood vessel shooting of the FBI of being called as (Fresh Blood Imaging, fresh blood imaging) is for example arranged with ecg wave form.
In this FBI, at first, use the MRI device, collect the data of a plurality of time phases in same section after, the preparation of carrying out the different a plurality of images of time phase are carried out shooting is with scanning (scan).Afterwards, from a plurality of images of being made a video recording, behind decision systole and the appropriate time phase of expansionary phase, the image of Syst image and expansionary phase is made a video recording respectively.By making difference image that obtain like this, image, can separately make the image and the venous image of tremulous pulse respectively.In above-mentioned FBI,, then can shorten the review time of FBI, and obtain the blood-vessel image of stable image quality if in scanning, use the present invention in above-mentioned preparation.
In addition, in the foregoing description 1, use predetermined threshold value to determine that the situation of the time phase that cardiac motion is few is illustrated to imaging conditions configuration part 17b.But, because there is individual differences in the variation of ventricle size, thus threshold value is being made as under the situation of fixed value, when the subject of the variable quantity overgauge of ventricle size is made a video recording, might can't detect variable quantity less than threshold value during.
Therefore, for example the 17b ratio (for example 10% etc.) that also can multiply by regulation by the maximum to the variable quantity of the variation of expression ventricle size in imaging conditions configuration part calculates less than after this peaked value, with the value that calculated as threshold value.Thus, threshold value changes according to the variable quantity of ventricle size, so can wait the timing that determines that rightly cardiac motion is few according to the body constitution and the symptom of each subject.
And then, for example, also can be under the situation during the variable quantity of variation that imaging conditions configuration part 17b detects a plurality of expression ventricle sizes is less than threshold value, with detected a plurality of during in the most long-term between be specified to the few time phase of cardiac motion.Thus, can collect data, can obtain the better image of picture quality with the most stable time phase of cardiac motion.
And then, also can be under the situation during the variable quantity of variation that imaging conditions configuration part 17b does not detect expression ventricle size is less than threshold value, increase detection during and meanwhile threshold value is carried out repeatedly gradually, up to detect more than one during till.In this case, for example, imaging conditions configuration part 17b at first measures the maximum of the variable quantity of ventricle size under certain heart beating, will set threshold value for this peaked 10% suitable value.Then, imaging conditions configuration part 17b is not detecting under the situation of variable quantity during less than the threshold value that sets, on one side the initial relatively peaked ratio of measuring is increased by 1% one by one, on one side interimly carry out the setting of threshold value repeatedly, up to detect more than one during till.Thus, can tackle the individual differences of subject more neatly.
More than, as embodiment 1, the situation that applies the present invention to the MRI device is illustrated, but the invention is not restricted to this, can also similarly be applied to other image diagnosing system.Therefore, below, as embodiment 2, the situation that applies the present invention to X ray CT device is described.
Figure 10 is the figure of structure that the X ray CT device 200 of embodiment 2 is shown.As shown in figure 10, this X ray CT device 200 possesses bench frame apparatus 210, bed apparatus 220 and control station device 230.
210 couples of subject P of bench frame apparatus shine X ray and collect data for projection.This bench frame apparatus 210 has high voltage generating unit 211, X-ray tube 212, X-ray detector 213, data collection portion 214, rotating frame (flame) 215 and stand drive division 216.
211 pairs of X-ray tubes of high voltage generating unit 212 are supplied with high voltage.X-ray tube 212 utilizes the high voltage generation X ray of being supplied with by high voltage generating unit 211.X-ray detector 213 detects the X ray that sees through subject P.Data collection portion 214 uses by X-ray detector 213 detected X ray and generates data for projection.
Rotating frame 215 forms circular, rotates at a high speed and continuously.This rotating frame 215 is to clip the opposed mode support X ray of subject P pipe 212 and X-ray detector 213.Stand drive division 216 is driven in rotation by making rotating frame 215, and X-ray tube 212 and X-ray detector 213 are circled round on the circular orbit that with subject P is the center.
Bed apparatus 220 moves to camera position in the bench frame apparatus 210 with subject P.This bed apparatus 220 has top board 221 and bed driving device 222.Top board 221 is the plates of mounting subject P when implementing shooting.Bed driving device 222 tangential section directions move top board 221.
Control station device 230 receives the various indications relevant with the operation of X ray CT device 200 from the operator, and the data for projection reconstructed image from utilizing bench frame apparatus 210 to collect.This control station device 230 has input equipment 231, display device 232, scan control section 233, pretreatment portion 234, data for projection storage part 235, image reconstruction process portion 236, image data storage portion 237 and systems control division 238.
Input equipment 231 has mouse, keyboard etc., from the indication of operator's reception to X ray CT device 200.For example, this input equipment 231 begins indication from input or reception shooting that the operator receives imaging conditions when shooting.The tube current of in the alleged herein imaging conditions, for example comprise the irradiation interval, photography time of X ray, supplying with to X-ray tube etc.
Display device 232 has LCD display (display) such as (Liquid Crystal Display, liquid crystal displays), shows various information.For example, this display device 232 shows by the view data of image data storage described later portion 237 storages and is used for receiving from the operator GUI (Graphical User Interface, graphic user interface) etc. of various indications.
Scan control section 233 is by the control according to systems control division 238 described later, drive high voltage generating unit 211, data collection portion 214, stand drive division 216 and bed driving device 222 according to photography conditions from systems control division 238 indications, and the heart of subject P is shone X ray, collect data for projection.
234 pairs of data for projection that generated by data collection portion 214 of pretreatment portion carry out pretreatment such as sensitivity rectification.235 storages of data for projection storage part are by pretreatment portion 234 pretreated data for projection.Image reconstruction process portion 236 is according to the control of systems control division 238 described later, from the data for projection reconstructed image data by 235 storages of data for projection storage part.
237 storages of image data storage portion are by the view data of image reconstruction process portion 236 reconstruct.For example, in this image data storage portion 237, preserve animated image at the heart of each and the subject P that makes a video recording in a plurality of time phases etc.
Systems control division 238 carries out the integral body control of X ray CT device 200 by the action of control station rack device 210, bed apparatus 220 and control station device 230.In embodiment 2, this systems control division 238 has ventricle variable quantity measurement 238a of portion and imaging conditions configuration part 238b especially.
The ventricle variable quantity measurement 238a of portion has the same function of the ventricle variable quantity measurement 17a of portion with explanation in embodiment 1.Particularly, this ventricle variable quantity measurement 238a of portion is from the animated image of image data storage portion 237 sensing pins to each left-ventricular short-axis of making a video recording continuously a plurality of time phases, according to the animated image of being read, with the ventricle variable quantity measurement 17a of portion similarly, measure the ventricle size through the time change.
Herein, for example, the ventricle variable quantity measurement 238a of portion will be used as the animated image of heart by the heart general image that the X ray of the dosage lower than this shooting of irradiation in the preparation shooting of carrying out is made a video recording before this shooting.In addition, the ventricle variable quantity measurement 238a of portion also can with in the shooting of the preparation by before this shooting, carrying out to compare cardiac component image that narrow scope irradiation X ray makes a video recording animated image with this shooting as heart.Under any situation, can reduce by checking amount to the X ray of subject P irradiation.
Imaging conditions configuration part 238b has the same function of imaging conditions configuration part 17b with explanation in embodiment 1.Particularly, this imaging conditions configuration part 238b is according to the variation of the ventricle size of being measured by the ventricle variable quantity measurement 238a of portion, similarly determine the few time phase of cardiac motion with imaging conditions configuration part 17b, and set imaging conditions according to determined time phase.
Herein, for example, imaging conditions configuration part 238b sets imaging conditions so that when when collecting the data of determined time phase, the dosage of the X ray of subject P irradiation being higher than the data in the stage At All Other Times in collecting a heart beating to the dosage of the X ray of subject P irradiation.Perhaps, imaging conditions configuration part 238b sets imaging conditions, so that the dosage to the X ray of subject irradiation becomes zero (zero) during the data in the stage At All Other Times in collecting a heart beating.Thus, the amount to the X ray of subject P irradiation can be suppressed to required minimum.
As mentioned above, in embodiment 2, the ventricle variable quantity measurement 17a of portion from by the ventricle size of image measurement at least heart beating of the heart of each and the subject P that makes a video recording a plurality of time phases through the time change.In addition, imaging conditions configuration part 17b determines the time phase that cardiac motion is few according to the variation of the ventricle size of being measured by the ventricle variable quantity measurement 17a of portion, and sets imaging conditions according to determined time phase.Therefore, similarly to Example 1, need not to append special shooting and judge etc., and can automatically determine the timing that cardiac motion is few by the operator.
In addition, each structural element of illustrated in the above-described embodiments each device is the structure of concept of function, and must constitute like that as shown physically.That is, dispersion/comprehensive concrete mode of each device is not limited to diagram, and can be according to various loads and behaviour in service etc., functional or physical property ground disperses with arbitrary unit/comprehensive above-mentioned all or part of and constitute.
As mentioned above, image diagnosing system of the present invention, MR imaging apparatus and X ray CT device are useful setting under imaging conditions synchronously carries out data collection with the ecg wave form with subject the situation, are particularly suitable for requiring shortening the general inspection time to guarantee and the situation of the repeatability that crown tremulous pulse is checked.
Claims (24)
1. image diagnosing system is characterized in that possessing:
Ventricle variable quantity measurement portion, from image, measure at each and the heart of making a video recording a plurality of time phases ventricle size at least heart beating through the time change;
The time phase that above-mentioned cardiac motion is few is determined according to the variation of the above-mentioned ventricle size of being measured by above-mentioned ventricle variable quantity measurement portion in the imaging conditions configuration part, and the setting imaging conditions is to collect the data of determined time phase; And
Data are collected according to the imaging conditions of being set by above-mentioned imaging conditions configuration part by image pickup portion, and according to collected data reconstruction image,
Wherein, the variable quantity of variation that the above-mentioned ventricle size of expression is detected in above-mentioned imaging conditions configuration part less than defined threshold during, will be defined as the few time phase of above-mentioned cardiac motion during detected.
2. image diagnosing system according to claim 1 is characterized in that, above-mentioned ventricle variable quantity measurement portion calculates the index of the volume of this ventricle as the size of the above-mentioned ventricle of expression, and measure calculated volumetrical through the time change.
3. image diagnosing system according to claim 1 is characterized in that, above-mentioned ventricle variable quantity measurement portion calculates the index of the area of section of this ventricle as the size of the above-mentioned ventricle of expression, and measure the area of section that calculated through the time change.
4. image diagnosing system according to claim 2, it is characterized in that, the variable quantity of variation that the above-mentioned ventricle size of expression is detected in above-mentioned imaging conditions configuration part less than defined threshold during, will be defined as the few time phase of above-mentioned cardiac motion during detected.
5. image diagnosing system according to claim 3, it is characterized in that, the variable quantity of variation that the above-mentioned ventricle size of expression is detected in above-mentioned imaging conditions configuration part less than defined threshold during, will be defined as the few time phase of above-mentioned cardiac motion during detected.
6. image diagnosing system according to claim 1, it is characterized in that, above-mentioned imaging conditions configuration part calculates less than this peaked value by the ratio that the maximum to the variable quantity of the variation of representing above-mentioned ventricle size multiply by regulation, and with the value that calculated as above-mentioned threshold value.
7. image diagnosing system according to claim 4, it is characterized in that, above-mentioned imaging conditions configuration part calculates less than this peaked value by the ratio that the maximum to the variable quantity of the variation of representing above-mentioned ventricle size multiply by regulation, and with the value that calculated as above-mentioned threshold value.
8. image diagnosing system according to claim 5, it is characterized in that, above-mentioned imaging conditions configuration part calculates less than this peaked value by the ratio that the maximum to the variable quantity of the variation of representing above-mentioned ventricle size multiply by regulation, and with the value that calculated as above-mentioned threshold value.
9. image diagnosing system according to claim 1, it is characterized in that, under the situation of above-mentioned imaging conditions configuration part during the variable quantity of the variation that detects the above-mentioned ventricle size of a plurality of expressions is less than above-mentioned threshold value, with detected a plurality of during in the longest during be defined as the few time phase of above-mentioned cardiac motion.
10. image diagnosing system according to claim 4, it is characterized in that, under the situation of above-mentioned imaging conditions configuration part during the variable quantity of the variation that detects the above-mentioned ventricle size of a plurality of expressions is less than above-mentioned threshold value, with detected a plurality of during in the longest during be defined as the few time phase of above-mentioned cardiac motion.
11. image diagnosing system according to claim 5, it is characterized in that, under the situation of above-mentioned imaging conditions configuration part during the variable quantity of the variation that detects the above-mentioned ventricle size of a plurality of expressions is less than above-mentioned threshold value, with detected a plurality of during in the longest during be defined as the few time phase of above-mentioned cardiac motion.
12. image diagnosing system according to claim 6, it is characterized in that, above-mentioned imaging conditions configuration part the variable quantity of the variation that detects the above-mentioned ventricle size of expression less than the situation during above-mentioned threshold value a plurality of under, with detected a plurality of during in the longest during be defined as the few time phase of above-mentioned cardiac motion.
13. image diagnosing system according to claim 7, it is characterized in that, above-mentioned imaging conditions configuration part the variable quantity of the variation that detects the above-mentioned ventricle size of expression less than the situation during above-mentioned threshold value a plurality of under, with detected a plurality of during in the longest during be defined as the few time phase of above-mentioned cardiac motion.
14. image diagnosing system according to claim 1, it is characterized in that, under the situation of above-mentioned imaging conditions configuration part during the variable quantity that does not detect the variation of representing above-mentioned ventricle size is less than above-mentioned threshold value, increase on one side the detection during above-mentioned threshold value is carried out repeatedly on one side interimly, up to detect more than one during till.
15. image diagnosing system according to claim 4, it is characterized in that, under the situation of above-mentioned imaging conditions configuration part during the variable quantity that does not detect the variation of representing above-mentioned ventricle size is less than above-mentioned threshold value, increase on one side the detection during above-mentioned threshold value is carried out repeatedly on one side interimly, up to detect more than one during till.
16. image diagnosing system according to claim 5, it is characterized in that, under the situation of above-mentioned imaging conditions configuration part during the variable quantity that does not detect the variation of representing above-mentioned ventricle size is less than above-mentioned threshold value, increase on one side the detection during above-mentioned threshold value is carried out repeatedly on one side interimly, up to detect more than one during till.
17. image diagnosing system according to claim 6, it is characterized in that, under the situation of above-mentioned imaging conditions configuration part during the variable quantity that does not detect the variation of representing above-mentioned ventricle size is less than above-mentioned threshold value, increase on one side the detection during above-mentioned threshold value is carried out repeatedly on one side interimly, up to detect more than one during till.
18. image diagnosing system according to claim 7, it is characterized in that, under the situation of above-mentioned imaging conditions configuration part during the variable quantity that does not detect the variation of representing above-mentioned ventricle size is less than above-mentioned threshold value, increase on one side the detection during above-mentioned threshold value is carried out repeatedly on one side interimly, up to detect more than one during till.
19. a MR imaging apparatus is characterized in that possessing:
Ventricle variable quantity measurement portion, from image, measure at each and the heart of making a video recording a plurality of time phases ventricle size at least heart beating through the time change;
The time phase that above-mentioned cardiac motion is few is determined according to the variation of the above-mentioned ventricle size of being measured by above-mentioned ventricle variable quantity measurement portion in the imaging conditions configuration part, and the setting imaging conditions is to collect the data of determined time phase; And
Data are collected according to the imaging conditions of being set by above-mentioned imaging conditions configuration part by image pickup portion, and according to collected data reconstruction image,
Wherein, the variable quantity of variation that the above-mentioned ventricle size of expression is detected in above-mentioned imaging conditions configuration part less than defined threshold during, will be defined as the few time phase of above-mentioned cardiac motion during detected.
20. an X ray CT device is characterized in that possessing:
Ventricle variable quantity measurement portion, from image, measure at each and the heart of making a video recording a plurality of time phases ventricle size at least heart beating through the time change;
The time phase that above-mentioned cardiac motion is few is determined according to the variation of the above-mentioned ventricle size of being measured by above-mentioned ventricle variable quantity measurement portion in the imaging conditions configuration part, and the setting imaging conditions is to collect the data of determined time phase; And
Data are collected according to the imaging conditions of being set by above-mentioned imaging conditions configuration part by image pickup portion, and according to collected data reconstruction image,
Wherein, the variable quantity of variation that the above-mentioned ventricle size of expression is detected in above-mentioned imaging conditions configuration part less than defined threshold during, will be defined as the few time phase of above-mentioned cardiac motion during detected.
21. X ray CT device according to claim 20, it is characterized in that, above-mentioned imaging conditions is set in above-mentioned imaging conditions configuration part so that when when collecting the data of determined time phase, the dosage of the X ray of subject irradiation being higher than the data in the stage At All Other Times in collecting a heart beating to the dosage of the X ray of subject irradiation.
22. X ray CT device according to claim 21, above-mentioned imaging conditions is set in above-mentioned imaging conditions configuration part, so that the dosage of the X ray that when collecting the data in above-mentioned stage At All Other Times subject is shone becomes zero.
23. X ray CT device according to claim 20, it is characterized in that the image of the heart integral body that above-mentioned ventricle variable quantity measurement portion will make a video recording by the X ray of the dosage lower than above-mentioned shooting of irradiation in the preparation shooting of carrying out is as the image of above-mentioned heart before this shooting.
24. X ray CT device according to claim 20, it is characterized in that, above-mentioned ventricle variable quantity measurement portion will by in the preparation shooting of before this shooting, carrying out to the parts of images of comparing the heart that narrow scope irradiation X ray makes a video recording with above-mentioned shooting image as above-mentioned heart.
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| JP5751738B2 (en) * | 2007-12-07 | 2015-07-22 | 株式会社東芝 | Magnetic resonance imaging system |
| JP5689595B2 (en) * | 2009-10-21 | 2015-03-25 | 株式会社東芝 | Magnetic resonance imaging system |
| CN102665560B (en) * | 2009-11-04 | 2014-10-15 | 株式会社日立医疗器械 | X-ray computed tomography device and image display method based thereon |
| JP2011139748A (en) * | 2010-01-06 | 2011-07-21 | Shimadzu Corp | Radiographic apparatus |
| US9241645B2 (en) | 2010-10-13 | 2016-01-26 | Kabushiki Kaisha Toshiba | Multiple MR fluid flow imaging at predetermined temporal resolution within selected period of cardiac cycle determined by multiple MR imaging at different temporal resolution |
| US8543187B2 (en) * | 2010-10-13 | 2013-09-24 | Kabushiki Kaisha Toshiba | Non-contrast MRI signal acquisition |
| US9523750B2 (en) | 2011-03-01 | 2016-12-20 | Koninklijke Philips N.V. | Determination of a magnetic resonance imaging pulse sequence protocol classification |
| JP5931642B2 (en) * | 2012-08-09 | 2016-06-08 | 学校法人 聖マリアンナ医科大学 | X-ray CT system |
| US10747847B2 (en) | 2016-02-16 | 2020-08-18 | Canon Medical Systems Corporation | Medical image diagnosis apparatus, server and control method |
| US10159448B2 (en) | 2016-06-06 | 2018-12-25 | Toshiba Medical Systems Corporation | X-ray CT apparatus, medical information processing apparatus, and medical information processing method |
| US11471065B2 (en) * | 2017-05-12 | 2022-10-18 | Canon Medical Systems Corporation | Medical image diagnosis apparatus |
| JP7501166B2 (en) * | 2020-07-03 | 2024-06-18 | オムロン株式会社 | X-ray inspection equipment |
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