CN101711671A - Magnetic resonance diagnostic apparatus and magnetic resonance diagnostic method - Google Patents
Magnetic resonance diagnostic apparatus and magnetic resonance diagnostic method Download PDFInfo
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- CN101711671A CN101711671A CN200910204450A CN200910204450A CN101711671A CN 101711671 A CN101711671 A CN 101711671A CN 200910204450 A CN200910204450 A CN 200910204450A CN 200910204450 A CN200910204450 A CN 200910204450A CN 101711671 A CN101711671 A CN 101711671A
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Abstract
A host computer 16 derives an apparent diffusion coefficient regarding a pixel position for each pixel position included in a region of interest in at least two original images obtained by imaging a same imaging region of a same subject using at least two b-factors which are different from each other, respectively, based on pixel values of each of at least two original images regarding the pixel positions, and estimates a pixel value obtained by using a b-factor which is different from the at least two b-factors, regarding each pixel position included in the region of interest, based on the apparent diffusion coefficient derived for each pixel position.
Description
The cross reference of related application
The Japanese patent application No.2008-251683 formerly that the application submitted to based on JIUYUE in 2008 on the 29th and to require it be priority is incorporated herein its full content as a reference.
Technical field
The present invention relates to the magnetic resonance diagnosing apparatus and the magnetic resonance diagnostic method that utilize the magnetic resonance phenomenon to obtain the subject image.
Background technology
Emphasize in the imaging (diffusion weighted imaging:DWI) in diffusion, when shooting, add a pair of diffusion and detect leaning magnetic field (motion probing gradient:MPG).And, during applying MPG, by obtaining diffusion and emphasize image to carry out imaging according to the signal difference that is occurred because of the spin phase place degree of scatter of the mobile proton of diffusion.
B value (b-factor) is used as the expression MPG big or small value of pulse influence.Increase b value can obtain since spread the contrast that causes enhanced, fully reflected the image of diffusing phenomenon.This b value can show by following formula.
At SE-EPT (the spin echo-echo planar imaging: spin echo-echo-planar imaging) that adopts widely used single-shot in DWI as imaging sequence, and when the MPG pulse was applied on one as the ideal rectangle ripple, the b value can show by following formula.
b＝γ
2G
2δ
2(Δ-δ/3)
In addition, G is that maximum inclination magnetic field intensity, δ are that application time, the Δ of MPG pulse is the time difference at 2 MPG impulse waveform centers.
That is, b value and maximum inclination magnetic field intensity G square or square being directly proportional of the application time of MPG pulse.
For the b value of widely used 1000 degree in DWI, diffusion emphasizes that contrast is low, malignant tumor retouch out level error.Therefore, hope increases the b value and improves diffusion and emphasize contrast.But, when increasing the application time δ of MPG pulse in order to increase the b value, because prolong TE (echo time), thus SNR (signal-to-noise ratio, signal to noise ratio) deterioration, and motion artifacts becomes big.In order to obtain big b value under the fixed situation and when increasing maximum inclination magnetic field intensity G in that TE is remained, need to improve the performance of the hardware of leaning magnetic field system, thus cost up.
In addition, in TOHKEMY communique 2008-12172 (US 2008/0007264 A1), disclosed processing DWI image and generated the technology of shadow of reading with image.
Summary of the invention
The present invention In view of the foregoing finishes, and its purpose is, can obtain and use the diffusion of the b value also bigger than the value corresponding with the application time of maximum magnetic field strength and MPG pulse to emphasize image.
The magnetic resonance diagnosing apparatus of the 1st embodiment of the present invention is characterized in that, comprising:
Lead-out unit, for each location of pixels that is comprised in the care zone at least 2 original images obtaining using at least 2 b values that have nothing in common with each other that the same camera watch region of same subject is made a video recording respectively, according to each pixel value at least 2 above-mentioned original images of this location of pixels, derive the diffusion coefficient that the highlight relevant with this location of pixels represented; And
Infer the unit,,, infer the pixel value that uses the b value different to obtain with above-mentioned at least 2 b values according to the diffusion coefficient that the above-mentioned highlight that each location of pixels is derived is represented for each location of pixels that in above-mentioned care zone, is comprised.
The magnetic resonance method of the 2nd embodiment of the present invention is characterized in that:
For each location of pixels that is comprised in the care zone at least 2 original images obtaining using at least 2 b values that have nothing in common with each other that the same camera watch region of same subject is made a video recording respectively, according to each pixel value at least 2 above-mentioned original images of this location of pixels, derive the diffusion coefficient that the highlight relevant with this location of pixels represented
For each location of pixels that in above-mentioned care zone, is comprised,, infer the pixel value that uses the b value different to obtain with above-mentioned at least 2 b values according to the diffusion coefficient that the above-mentioned highlight that each location of pixels is derived is represented.
The magnetic resonance diagnosing apparatus of the 3rd embodiment of the present invention is characterized in that, comprising:
Image unit uses at least 2 b values that have nothing in common with each other that the same camera watch region of same subject is made a video recording and 2 original images of making a video recording at least respectively; And
Infer the unit,,, infer the pixel value that uses the b value different to obtain with above-mentioned at least 2 b values according to each pixel value at least 2 above-mentioned original images of this location of pixels for each location of pixels that is comprised in the care zone in above-mentioned original image.
To propose other purpose of the present invention and advantage in the following description, partial content can become from the description of description obviously, perhaps can clear and definite foregoing by implementing the present invention.Can realize and obtain objects and advantages of the present invention by means and the combination of hereinafter pointing out in detail.
Description of drawings
The accompanying drawing that is combined in here and constitutes the part of description is described presently preferred embodiments of the invention, and with above-mentioned summary description and following detailed description of the preferred embodiment together is used for illustrating principle of the present invention.
Fig. 1 is the figure that the schematic configuration of the magnetic resonance diagnosing apparatus relevant with an embodiment of the invention is shown.
Fig. 2 is the flow chart of processing sequence that is illustrated in the 1st embodiment of the master computer among Fig. 1.
Fig. 3 is the shooting by 2 actual original images, and the figure at an example of the relation of 2 signal values of same pixel is shown.
Fig. 4 is the figure that an example of the function of determining by the ADC that calculates according to 2 signal values shown in Figure 3 is shown.
Fig. 5 illustrates according to function calculation shown in Figure 4 to go out figure with an example of the situation of the signal value that arbitrarily the b value is relevant.
Fig. 6 is the flow chart of processing sequence that is illustrated in the 2nd embodiment of the master computer among Fig. 1.
Fig. 7 is for being illustrated in the 2nd embodiment figure of an example of canned data table in the memory element in Fig. 1.
Fig. 8 is the flow chart of processing sequence that is illustrated in the 3rd embodiment of the master computer among Fig. 1.
Fig. 9 is for being illustrated in the 3rd embodiment figure of an example of canned data table in the memory element in Fig. 1.
The specific embodiment
Below, with reference to accompanying drawing embodiments of the present invention are described.
Fig. 1 is the figure that the schematic configuration of the magnetic resonance diagnosing apparatus relevant with present embodiment 100 is shown.
This magnetic resonance diagnosing apparatus 100 has: the bed portion of carrying subject 200; The magnetostatic field generating unit of magnetostatic field takes place; Be used for leaning magnetic field generating unit to the electromagnetostatic field additional location information; Send the transmission acceptance division that receives high-frequency signal; And bear the control of entire system and the control operational part of image reconstruction.And, in magnetic resonance diagnosing apparatus 100, structural element as these each ones has: Magnet 1, magnetostatic field power supply 2, shim coil 3, shim coil power supply 4, top board 5, gradient magnetic field coil unit 6, leaning magnetic field power supply 7, RF coil unit 8, transmitter 9T, receptor 9R, sequencer (sequence controller) 10, arithmetic element 11, memory element 12, display 13, loader 14, sound generator 15 and master computer 16.Mutually the electrocardio instrumentation portion of ECG signal of signal connected when in addition, magnetic resonance diagnosing apparatus 100 and instrumentation were as the heart of expression subject 200.
The magnetostatic field generating unit contains Magnet 1 and magnetostatic field power supply 2.As Magnet 1, for example can use superconducting magnet or normal electric conductance magnet.Magnetostatic field power supply 2 provides electric current to Magnet 1.Like this, magnetostatic field B takes place in the magnetostatic field generating unit in the cylindric space of sending into subject 200 (space is used in diagnosis)
0This magnetostatic field B
0Magnetic direction with the diagnosis roughly consistent with spatial direction of principal axis (Z-direction).Also be provided with shim coil 3 in the magnetostatic field generating unit.This shim coil 3 is used to make the magnetic field for correcting of magnetostatic field homogenization by the electric current supply of the shim coil power supply 4 under the control of master computer 16.
The top board 5 that subject 200 will be carried in bed portion is sent to diagnosis and sends top board 5 with the space or from diagnosis with the space.
The leaning magnetic field generating unit contains gradient magnetic field coil unit 6 and leaning magnetic field power supply 7.Gradient magnetic field coil unit 6 is arranged on the inboard of magnet 1.Gradient magnetic field coil unit 6 has 3 groups of coil 6x, 6y, 6 of each leaning magnetic field that is used to take place mutually perpendicular X-direction, Y direction and Z-direction
ZLeaning magnetic field power supply 7 is provided for making the pulse current in coil 6x, coil 6y, coil 6z run-off the straight magnetic field under the control of sequencer 10.The leaning magnetic field generating unit is by controlling the pulse current that is offered coil 6x, 6y, 6z by leaning magnetic field power supply 7, and is synthetic as each leaning magnetic field on 3 (X-axis, Y-axis, Z axle) directions of physical axis, sets mutually perpendicular slice direction leaning magnetic field G arbitrarily
S, phase-encoding direction leaning magnetic field G
EAnd read direction (frequency coding direction) leaning magnetic field G
RTheoretical axial each leaning magnetic field that is constituted.Slice direction, phase-encoding direction and each the leaning magnetic field G that reads direction
S, G
E, G
RWith magnetostatic field B
0Overlapping.
Send acceptance division and contain RF coil unit 8, transmitter 9T and receptor 9R.RF coil unit 8 in diagnosis space, be set at subject 200 near.Transmitter 9T and receptor 9R are connected with RF coil unit 8.Transmitter 9T and receptor 9R move under the control of sequencer 10.Transmitter 9T is provided for producing the RF current impulse of the Larmor frequency (Larmor frequency) of nuclear magnetic resonance, NMR (NMR) to RF coil unit 8.Receptor 9R obtains the received MR signals (high-frequency signal) such as echo-signal of RF coil unit 8, and it is implemented that preposition amplification, intermediate frequency conversion, phase detection, low frequency are amplified or various signal processing such as filtration, carry out the A/D conversion then and generate numerical data (initial data (raw data)).
But RF coil unit 8 also can also can be made of single coil by constituting with the corresponding any coil of various uses.
Control/operational part contains sequencer 10, arithmetic element 11, memory element 12, display 13, loader 14, sound generator 15 and master computer 16.
Sequencer 10 has CPU and memorizer.The pulse train information that sequencer 10 is sent master computer 16 here is stored in the memorizer.The CPU of sequencer 10 is according to the sequence information of storing in the memorizer, and the action of control leaning magnetic field power supply 7, transmitter 9T and receptor 9R, and the initial data of input sink 9R output are sent to arithmetic element 11.At this, sequence information is meant according to a series of pulse trains and makes leaning magnetic field power supply 7, transmitter 9T and necessary all information of receptor 9R action, for example comprises with intensity, the application time of the pulse current that applies to coil 6x, 6y, 6y and applies relevant information such as timing.Sequence information comprises the information that is used to realize DWI.
Arithmetic element 11 is by the initial data of sequencer 10 input sink 9R output.Arithmetic element 11 is arranged on the k space (being also referred to as Fourier (Fourier) space or frequency space) that sets in the internal storage with the initial data of input, to being arranged on Fourier (Fourier) conversion that the spatial data of this k apply 2 dimensions or 3 dimensions, the view data of the reconstruct real space.In addition, arithmetic element 11 also can be implemented the synthetic processing or the calculus of differences processing (also comprising the weighted difference processing) of the data relevant with image as required.Should synthetic handle and comprise that processing, maximum projection (MIP) that each pixel is added pixel value handled etc.In addition, as other examples of above-mentioned synthetic processing, can be after the adjustment of the axle that carries out a plurality of frames on Fourier (Fourier) space, the initial data of synthetic these a plurality of frames obtains the initial data of 1 frame.In addition, addition process comprises simple addition process, summation averaging processing or weighted addition processing etc.
View data after the memory element 12 storage reconstruct, above-mentioned synthetic processing or the view data after the difference processing have been implemented.
Display 13 shows under the control of master computer 16 should be to the various images of user prompt.Can use display devices such as liquid crystal display as display 13.
The desirable synchronization timing of loader 14 input operation persons is selected parameter information, the condition of scanning, pulse train, or the calculus of differences relevant various information such as information synthetic with image of usefulness.Loader 14 sends to the information of input in the master computer 16.Can suitably possess input equipment such as selecting arrangements such as positioners such as mouse and trace ball, mode selector switch or keyboard as loader 14.
Sound generator 15 sends when instruction at master computer 16, begins holding one's breath and the message that finishes of holding one's breath is sent as sound.
Master computer 16 has by carrying out the various functions that predefined software is realized in proper order.These various functions can comprise following various functions.One of this function is, to sequencer 10 command pulse sequence informations, and the action of control device integral body.One of above-mentioned functions is that control sequencer 10 is made a video recording to the same position of same subject to use 2 b values that have nothing in common with each other respectively.One of above-mentioned functions is, respectively to using the location of pixels that is comprised in the care zone in 2 images that above-mentioned 2 b values obtain respectively, according to each pixel value in above-mentioned 2 images relevant, calculate the apparent diffusion coefficient relevant (apparent diffusion contrast:ADC) with this pixel value with this location of pixels.One of above-mentioned functions is that the location of pixels that comprises being concerned about in the zone according to the ADC that each location of pixels is calculated, is inferred and used the b value obtained pixel value different with above-mentioned 2 b values respectively.One of above-mentioned functions is each location of pixels to be arranged the pixel value of inferring respectively generate computed image.One of above-mentioned functions is that control display 13 is to show the aforementioned calculation image.One of above-mentioned functions is, according to the signal value in the original image that uses 1 b value shooting and noise level with diffusion coefficient in related settings in the position of the subject that camera watch region comprised, the SNR (signal to noise ratio) in other original images that other b values of supposition use are made a video recording.
Electrocardio instrumentation portion comprises ECG pick off 17 and ECG unit 18.ECG pick off 17 is attached to the body surface of subject 200, and the ECG signal of subject 200 is detected as the signal of telecommunication (below, be called sensor signal).ECG unit 18 is after implementing to comprise the various processing of digitized processing to sensor signal, to master computer 16 and sequencer 10 outputs.For example can use vectorcardioscope as this electrocardio instrumentation portion.When carrying out, during the scanning of synchronised, in sequencer 10, use sensor signal as required based on this electrocardio instrumentation portion with subject 200 hearts.
(the 1st embodiment)
Below, describe at the action in the 1st embodiment of magnetic resonance diagnosing apparatus 100.
Fig. 2 is the flow chart that the processing sequence in the 1st embodiment of master computer 16 is shown.
In step Sa1, master computer 16 sends indication to sequencer 10, so that predefined care zone is carried out the b value is made as predefined value b
aShooting.Sequencer 10 makes actions such as leaning magnetic field power supply 7, transmitter 9T, receptor 9R and arithmetic element 11 according to this indication, has used and has held value b
aThe shooting of b value.In the following, will be called the 1st original image at the image of this shooting.
In addition, value b
aCan be arbitrary value, get 0 but be preferably.At b
a=0 o'clock, for the shooting among the step Sa1, (spin echo: spin echo) (fast spin echo: fast spin echo) T2 of method emphasized shooting for method or FSE can to use employing SE.Perhaps, also can use the shooting of adopting single-shot isotropic (single-shot isotropism) EPI (echo planarimaging, plane echo-wave imaging) method or STE (stimulated echo: encourage echo) method.By using these camera methods can shorten camera time and improving resolution.
In step Sa2, master computer 16 sends indication to sequencer 10, so that the b value is made as and is worth b carrying out in the above-mentioned care zone
aDifferently predefined value b
bShooting.Sequencer 10 makes actions such as leaning magnetic field power supply 7, transmitter 9T, receptor 9R and arithmetic element 11 according to this indication, use and hold value b
bThe shooting of b value.In the following, will be called the 2nd original image at the image of this shooting.In addition, at value b
aAnd value b
bBe not 0 o'clock, the direction that applies that is preferably the MPG when carrying out shooting of the 1st original image and the shooting of the 2nd original image is no difference.
In step 3, each pixel in 16 pairs of above-mentioned care of the master computer zone derives each ADC respectively.Each signal value at the 1st and the 2nd original image that will be relevant with the pixel of same position is expressed as S (b
a) and S (b
b) time, by below these signal value substitutions, carrying out such scheme in the formula (1).
ADC＝log
n[S(b
b)/S(b
a)]/(b
b-b
a) ...(1)
Wherein, this formula (1) can be obtained by formula (2) below the distortion.
S(b
b)＝S(b
a)·exp[-(b
b-b
a)·ADC]...(2)
In step Sa4, master computer 16 generates the b value value of being made as b
1To being worth b
mThe time each image (below, be called computed image).Value b
1To being worth b
mBe and value b
aAnd value b
bRespectively differently by predefined m kind value.These are worth b
1To being worth b
mFor example be set as with certain value (for example 100) scale and become big value in turn.
Can obtain for example b value=b by calculate the signal value of being concerned about each pixel in the zone according to following formula (3)
1Image.Formula (3) is to obtain on the basis of above-mentioned formula (2).As the ADC in the formula (3), the value that substitution is derived in step Sa3 at each pixel.
S(b
1)＝S(b
a)·exp[-(b
1-b
a)·ADC]...(3)
In addition, value b
aBe worth=0 o'clock, and can replace this formula (3) by following formula (4).
S(b
1)＝S(0)·exp[-b
1·ADC] ...(4)
And master computer 16 will store into respectively in the memory element 12 at m image of this generation.
In addition, the processing among this step Sa4 also can be undertaken by arithmetic element 11 under the control of master computer 16.
In step Sa5, master computer 16 is with variable b
nBe set at initial value b
IniInitial value b
IniCan the value of being set to b
1To being worth b
mIn any one value, the value of typically being b
1, the value b
m, or the value b
1To being worth b
mIntermediary any one value.
In step Sa6, the b value=b in the computed image that master computer 16 will generate in step Sa4
nComputed image be presented on the display 13.
Under the state that like this computed image is presented on the display 13, master computer 16 is waited in step Sa7 and is accepted variable b
nChange request.For b
nChange request, for example accept to get final product by the user of the slider bar that shows on display 13 being operated by loader 14 input.
If changes persuing amount b
nChange, master computer 16 enters step Sa8 from step Sa7.In step Sa8, master computer 16 is according to the above-mentioned requirements change variable b that is carried out
nAnd after this master computer 16 turns back among the step Sa6, and the demonstration of refresh display 13 is equivalent to after changing variable b with demonstration
nThe computed image of b value.
Like this according to the 1st embodiment, at each pixel of being concerned about in the zone, according to 2 signal values for example shown in Figure 3 of obtaining by actual shooting, derive determine as among Fig. 4 with the ADC of the function of curve representation.And, can infer signal value S (x) in any b value for example shown in Figure 5 according to this ADC, can obtain the computed image of any b value as the arrangement of the pixel of the signal value of inferring like this.Like this, can obtain and use the diffusion of the b value bigger to emphasize image than the value corresponding with the application time of the intensity in maximum inclination magnetic field and MPG pulse.
In addition, for big positions of motion such as abdominal paries, come original image is made a video recording by using little b value to suppress motion artifacts, even if the image of big b value also can control to motion artifacts less.
According to the 1st embodiment, operation optionally shows by the b value being made as the value b that varies in size according to the certain value scale according to slider bar
1To being worth b
mAnd the computed image that obtains respectively, so the user can easily observe the difference of the image when the b value is changed.
(the 2nd embodiment)
Below describe at the action of the 2nd embodiment of magnetic resonance diagnosing apparatus 100.
Fig. 6 is the flow chart of processing sequence that the 2nd embodiment of master computer 16 is shown.In addition, additional prosign omits its detailed description in the processing identical with Fig. 2.
In step Sb1, the position of master computer 16 judgements the becoming object of the shooting of carrying out from now on (below, be called the shooting position) be which position in the subject.For the judgement at this shooting position, can be according to for example carrying out via user's appointment of loader 14 inputs.
In step Sb2, master computer 16 sends indication to sequencer 10, so that predefined care zone is carried out the b value is made as the setting value b relevant with the position of making a video recording
aShooting.Sequencer 10 makes startings such as leaning magnetic field power supply 7, transmitter 9T, receptor 9R and arithmetic element 11 according to this indication, hold value b to have used
aThe shooting of b value.In the following, will be called the 1st original image at the image of this shooting.
In addition, for the b value being made as the setting value b relevant with the position of making a video recording
a, information table for example shown in Figure 7 is stored in the memory element 12 in advance.Information table shown in Figure 7 is put down in writing setting value b explicitly with a plurality of positions of human body respectively
a, b
b, b
cAnd setting value b
1, b
2, b
3Wherein, setting value b
cAnd setting value b
2, b
3Can be the state (null (sky) state) that does not have substantive value.The setting value b that this information table is recorded and narrated
a, b
b, b
cAnd setting value b
1, b
2, b
3Can be set at appropriate value based on clinical understanding.And information table was logged in memory element 12 in the fabrication stage of magnetic resonance diagnosing apparatus 100 or the use preparatory stage of magnetic resonance diagnosing apparatus 100.
In step Sb3, master computer 16 makes startings such as leaning magnetic field power supply 7, transmitter 9T, receptor 9R and arithmetic element 11, holds value b to have used
bThe shooting of b value.In the following, will be called the 2nd original image at the image of this shooting.
In step Sb4, master computer 16 confirms to set value b in information table
cWhether be associated with the shooting position.If there is the setting value b that meets
c, master computer 16 enters into step Sb5 from step Sb4.
In step Sb5, main frame is calculated and 16 is made startings such as leaning magnetic field power supply 7, transmitter 9T, receptor 9R and arithmetic element 11, has value b to have used
cThe shooting of b value.In the following, will be called the 3rd original image at the image of this shooting.
If do not have the setting value b that meets among end of the shooting among the Sb5 or the step Sb4
c, master computer 16 enters into step Sb6.Then, in step Sb6,16 pairs of master computers are concerned about that each pixel in the zone derives ADC respectively.In addition, when not carrying out the shooting of the 3rd original image, the derivation of the ADC here can be carried out with the 1st embodiment the samely.When having carried out the shooting of the 3rd original image, derive ADC by the so-called curve approximation that following explanation is such.
B is b
n(n=a, b, the image value S (b of original image c)
n) have relation according to S (0) and the exponential function that ADC determined, be expressed as the formula (5) of face.
S(b
n)＝S(0)·exp[-b
n·ADC]...(5)
At this, for example can pass through the least square approximation method, according to b
a, b
b, b
cAnd S (b
a), S (b
b), S (b
c) calculating S (0) and ADC.Specifically, decision makes actual S (b
a), S (b
b), S (b
c) with the S (0) and the ADC of the quadratic sum minimum of the error of the value that calculates by formula (5).
Perhaps, adopt the logarithm of formula (5), become formula (6)
ln(S(b
n))＝ln(S(0))-b
n·ADC...(6)
In formula (6), if transverse axis is made as b
n, and the longitudinal axis be made as ln (S (b
n)), then become ln (S (0)) as longitudinal axis section, and tilt to be the straight line of-ADC.At this, also can make 3 ln (S (b that are positioned at best on this straight line by the least square method decision
n)) and ADC.
Then, master computer 16 carries out the processing of step Sa4 to Sa8 with the 1st embodiment the samely.Wherein, as value b
1～b
mThe value that employing is recorded and narrated in above-mentioned information table.
In addition, in order to obtain original image regardless of using which type of b value can derive ADC.Yet because according to human body, the influence degree difference of MPG is so according to for obtaining the suitable b value of original image, the precision of the ADC of derivation changes.Therefore, in the 2nd embodiment,, the b value suitable in order to obtain original image changed according to the shooting position.Thus, when made a video recording in any position of subject, can derive ADC accurately, generate more suitably computed image.
In addition, in the 2nd embodiment, can derive ADC according to 3 original images.And this moment, and compare based on the situation of 2 original images, ADC can be derived more accurately, thereby more suitably computed image can be generated.
Moreover, in the 2nd embodiment, for the b value that generates the computed image use also changes accordingly with the shooting position.Therefore, can generate and use the same computed image of image that is applicable to the b value shooting of observing the position of making a video recording.
In addition, even same position, with the symptom at this position (have no abnormal or intensity of anomaly etc.) accordingly the influence degree of MPG have nothing in common with each other.Therefore, also can in information table, record and narrate each setting value explicitly with the combination of image pickup part and symptom.
(the 3rd embodiment)
Below describe at the action of the 3rd embodiment of magnetic resonance diagnosing apparatus 100.
Fig. 8 is the flow chart of processing sequence that the 3rd embodiment of master computer 16 is shown.In addition, additional prosign omits its detailed description in the processing identical with Fig. 2.
Master computer 16 at first in step Sa1 with the 1st embodiment the 1st original image of making a video recording the samely, enter step Sc1 then.
In step Sc1, master computer 16 is judged the shooting position, and obtains the diffusion coefficient D relevant with this shooting position.Diffusion coefficient has nothing in common with each other to the anatomy tissue in the human body, and has known the standard diffusion coefficient of normal structure.Therefore, will organize the information table of the standard diffusion coefficient of having recorded and narrated this tissue explicitly to store in the memory element 12 with the anatomy that can become the shooting position respectively as shown in Figure 9 in advance.And master computer 16 will be obtained as diffusion coefficient D with the corresponding numerical value in shooting position in this information table in step Sc1.
In step Sc2, master computer 16 infer to above-mentioned care zone carry out with the b value as with value b
aThe predefined like that value of difference b
bShooting and SNR in the 2nd original image obtained.Specifically, with the signal value S (a) in the 1st original image when representing, master computer 16 at first can be inferred the signal value S (b) of the 2nd original image by following formula.In addition, the variation of the noise level that is caused by the influence of MPG is less, in the 1st original image and the 2nd original image much at one.Therefore, as the ratio of the noise level in the signal value S (b) that calculates according to following formula and the 2nd original image, can infer the SNR in the 2nd original image.
S(b)＝S(a)·exp(-b
b·D)。
As shown from the above formula, then reduce signal value S (b) because increase the b value, so SNR also descends.
In step Sc3, master computer 16 confirms that the SNR that as above infers is whether more than pre-set threshold.Then, if SNR less than threshold value, then master computer 16 enters Sc4 from step Sc3.
In step Sc4, master computer 16 is set the b value once more, so that SNR is more than threshold value.
When the processing in step Sc4 finishes, or be judged as SNR in step Sc3 when threshold value is above, master computer 16 enters Sc5.
In step Sc5, master computer 16 adopts the shooting of the b value that resets here and obtains the 2nd original image above-mentioned care zone when having carried out step Sc4, when having skipped step Sc4, above-mentioned care zone is carried out the b value as value b
bShooting and obtain the 2nd original image.
After this, the processing of master computer 16 ground the same implementation step Sa3 to Sa8 with the 1st embodiment.
The influence of noise becomes big when having utilized the low original image of SNR, and the correctness of the ADC of derivation reduces.Therefore and the computed image that generates according to the ADC that contains than mistake increases with the error of the image of actual shooting.Yet, in the 3rd embodiment, use the bigger original image of SNR in order to derive ADC, therefore, can derive ADC accurately, thus,, can generate the computed image of the image that is similar to actual shooting according to the 3rd embodiment.
To this embodiment, can implement following various deformation.
Also can judge be concerned about that air portion in the zone be graded according to original image need not the zone, only the pixel in the zone need not the zone except this is carried out the inferring of signal value of the calculating of ADC or any b value.
Also the computed image that can only generate by the specified b value of user is also shown.
Also the computed image that is generated can be outputed on other devices, and be presented on the display of this device.
Also the image by other device shootings can be used as original image.
Those skilled in the art expect other advantage and alter mode easily.Therefore, the present invention is not limited to the detail and the representational embodiment that illustrate and illustrate here with regard to its wideer aspect.Therefore, do not deviate from by appending claims with and the situation of the spirit and scope of the general inventive concept that limits of equivalent under, can carry out various modifications.
Claims (15)
1. a magnetic resonance diagnosing apparatus is characterized in that, comprising:
Lead-out unit, for each location of pixels that is comprised in the care zone at least 2 original images obtaining using at least 2 b values that have nothing in common with each other that the same camera watch region of same subject is made a video recording respectively, according to each pixel value at least 2 above-mentioned original images of this location of pixels, derive the diffusion coefficient that the highlight relevant with this location of pixels represented; And
Infer the unit,,, infer the pixel value that uses the b value different to obtain with above-mentioned at least 2 b values according to the diffusion coefficient that the above-mentioned highlight that each location of pixels is derived is represented for each location of pixels that in above-mentioned care zone, is comprised.
2. magnetic resonance diagnosing apparatus according to claim 1 is characterized in that, also comprises:
The image unit that at least 2 above-mentioned original images are made a video recording.
3. magnetic resonance diagnosing apparatus according to claim 2 is characterized in that:
At least 2 b values that above-mentioned image unit uses the position of the above-mentioned subject that is comprised with above-mentioned camera watch region to set are explicitly respectively made a video recording at least 2 above-mentioned original images respectively.
4. magnetic resonance diagnosing apparatus according to claim 2 is characterized in that, also comprises:
Presumption units, according to the signal value in the 1st above-mentioned original image that uses 1 above-mentioned b value to make a video recording by above-mentioned image unit and noise level and with above-mentioned camera watch region in the diffusion coefficient set explicitly of the position of the above-mentioned subject that comprised, infer the SNR in the 2nd above-mentioned original image that uses other b value shootings
Above-mentioned image unit is under the above-mentioned SNR that is inferred by above-mentioned presumption units is situation more than the pre-set threshold, former state is used above-mentioned other b values and the 2nd above-mentioned original image is made a video recording, under the situation of above-mentioned SNR of inferring by above-mentioned presumption units, use the b value that is set at the value different once more that the 2nd above-mentioned original image is made a video recording with above-mentioned other b values less than above-mentioned threshold value.
5. magnetic resonance diagnosing apparatus according to claim 1 is characterized in that:
One of above-mentioned original image is for being made as the image of making a video recording in b value=0.
6. magnetic resonance diagnosing apparatus according to claim 5 is characterized in that:
The original image of b value=0 is emphasized image for the T2 that uses the shooting of SE method or FSE method.
7. magnetic resonance diagnosing apparatus according to claim 1 is characterized in that:
One of above-mentioned original image is for using the image of STE method shooting.
8. magnetic resonance diagnosing apparatus according to claim 1 is characterized in that:
The isotropic images that the single-shot EPI method that one of above-mentioned original image keeps resolution and SE method or FSE method by fourier transform comparably for use is made a video recording.
9. magnetic resonance diagnosing apparatus according to claim 1 is characterized in that, also comprises:
Thereby will arrange the generation unit that generates computed image by the above-mentioned pixel value of the unit being inferred respectively by each location of pixels of inferring.
10. magnetic resonance diagnosing apparatus according to claim 9 is characterized in that, also comprises:
The display unit that shows the aforementioned calculation image.
11. magnetic resonance diagnosing apparatus according to claim 10 is characterized in that:
The above-mentioned unit of inferring is inferred the pixel value that uses a plurality of b values have nothing in common with each other to obtain respectively,
Above-mentioned generation unit generates respectively and will arrange the aforementioned calculation image that forms by the above-mentioned pixel value that uses same b value that each location of pixels is inferred respectively in the unit of inferring at above-mentioned a plurality of b values,
Above-mentioned display unit shows the specified computed image of user in a plurality of aforementioned calculation images that generate by above-mentioned generation unit.
12. magnetic resonance diagnosing apparatus according to claim 11 is characterized in that:
When above-mentioned display unit changed the operation of b value the user, change was operated the aforementioned calculation image that shows accordingly with this.
13. magnetic resonance diagnosing apparatus according to claim 1 is characterized in that:
The obtained pixel value of b value that the position of using the above-mentioned subject that is comprised with above-mentioned camera watch region is set is explicitly inferred in the above-mentioned unit of inferring.
14. a magnetic resonance diagnostic method is characterized in that:
For each location of pixels that is comprised in the care zone at least 2 original images obtaining using at least 2 b values that have nothing in common with each other that the same camera watch region of same subject is made a video recording respectively, according to each pixel value at least 2 above-mentioned original images of this location of pixels, derive the diffusion coefficient that the highlight relevant with this location of pixels represented
For each location of pixels that in above-mentioned care zone, is comprised,, infer the pixel value that uses the b value different to obtain with above-mentioned at least 2 b values according to the diffusion coefficient that the above-mentioned highlight that each location of pixels is derived is represented.
15. a magnetic resonance diagnosing apparatus is characterized in that, comprising:
Image unit uses at least 2 b values that have nothing in common with each other that the same camera watch region of same subject is made a video recording and 2 original images of making a video recording at least respectively; And
Infer the unit,,, infer the pixel value that uses the b value different to obtain with above-mentioned at least 2 b values according to each pixel value at least 2 above-mentioned original images of this location of pixels for each location of pixels that is comprised in the care zone in above-mentioned original image.
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| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101953687A (en) * | 2009-07-16 | 2011-01-26 | 株式会社东芝 | Magnetic resonance diagnostic apparatus |
| US8805473B2 (en) | 2008-09-29 | 2014-08-12 | Kabushiki Kaisha Toshiba | MRI diffusion weighted imaging with estimated motion probing gradient b-factors based on acquired apparent diffusion coefficients for each pixel |
| CN104280704A (en) * | 2013-07-11 | 2015-01-14 | Ge医疗系统环球技术有限公司 | Movement probing gradient impulse wave design method and device for magnetic resonance |
Families Citing this family (2)
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| JP6280881B2 (en) * | 2015-02-17 | 2018-02-14 | ジーイー・メディカル・システムズ・グローバル・テクノロジー・カンパニー・エルエルシー | Scan condition determining apparatus, magnetic resonance apparatus, scan condition determining method, and program |
| JP6358244B2 (en) * | 2015-12-08 | 2018-07-18 | キヤノンマーケティングジャパン株式会社 | MEDICAL IMAGE PROCESSING DEVICE, MEDICAL IMAGE PROCESSING DEVICE CONTROL METHOD, AND PROGRAM |
Citations (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2008147923A1 (en) * | 2007-05-22 | 2008-12-04 | Imaging Biometrics | Method for detecting tumor cell invasion using short diffusion times |
Family Cites Families (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH09173315A (en) * | 1995-12-26 | 1997-07-08 | Hitachi Medical Corp | Magnetic resonance imaging method |
| DE102005028475B4 (en) * | 2005-06-20 | 2008-04-03 | Siemens Ag | Method and device for determining coefficients of a magnetic resonance diffusion tensor |
| JP5127276B2 (en) * | 2006-05-26 | 2013-01-23 | 株式会社東芝 | Image processing apparatus and magnetic resonance imaging apparatus |
| JP5619339B2 (en) * | 2006-09-13 | 2014-11-05 | 株式会社東芝 | Magnetic resonance imaging system |
| JP5481117B2 (en) * | 2008-09-29 | 2014-04-23 | 株式会社東芝 | Magnetic resonance diagnostic apparatus and control method thereof |
-
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Patent Citations (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2008147923A1 (en) * | 2007-05-22 | 2008-12-04 | Imaging Biometrics | Method for detecting tumor cell invasion using short diffusion times |
Non-Patent Citations (2)
| Title |
|---|
| D.XING ET AL: "Optimised diffusion-weighting for measurement of apparent diffusion coefficient(adc) in human brain", 《MAGNETIC RESONANCE IMAGING》 * |
| 康建蕴 伍建林: "影响磁共振弥散加权成像信号的因素", 《大连医科大学学报》 * |
Cited By (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US8805473B2 (en) | 2008-09-29 | 2014-08-12 | Kabushiki Kaisha Toshiba | MRI diffusion weighted imaging with estimated motion probing gradient b-factors based on acquired apparent diffusion coefficients for each pixel |
| CN101953687A (en) * | 2009-07-16 | 2011-01-26 | 株式会社东芝 | Magnetic resonance diagnostic apparatus |
| CN101953687B (en) * | 2009-07-16 | 2013-06-26 | 株式会社东芝 | Magnetic resonance diagnostic apparatus |
| CN104280704A (en) * | 2013-07-11 | 2015-01-14 | Ge医疗系统环球技术有限公司 | Movement probing gradient impulse wave design method and device for magnetic resonance |
| CN104280704B (en) * | 2013-07-11 | 2018-12-18 | Ge医疗系统环球技术有限公司 | Gradient pulse wave design method and device are detected in movement for magnetic resonance |
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| JP2013255854A (en) | 2013-12-26 |
| CN101711671B (en) | 2012-11-28 |
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