CN112858975B - Noise control method for magnetic resonance examination and scan sequence determination method - Google Patents
Noise control method for magnetic resonance examination and scan sequence determination method Download PDFInfo
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Abstract
The embodiment of the invention discloses a noise control method for magnetic resonance examination and a scanning sequence determining method, which comprises the following steps: obtaining mute parameters and determining mute gradient waveforms corresponding to the mute parameters; and scanning the target scanning part based on the mute gradient waveform. The technical scheme of the embodiment of the invention solves the technical problem of larger noise when a user performs magnetic resonance scanning in the prior art, and realizes the technical effect of balancing scanning noise and scanning time in the magnetic resonance scanning process.
Description
Technical Field
The embodiment of the invention relates to the technical field of medical treatment, in particular to a noise control method for magnetic resonance examination and a scanning sequence determining method.
Background
Magnetic resonance imaging is a method of imaging sequences. Magnetic resonance imaging is a newer technique than CT scanning and can provide emerging soft tissue contrast. A typical magnetic resonance imaging system comprises the following components: a magnet, a gradient coil, a radio frequency transmit coil, a radio frequency receive coil, and a signal processing and image reconstruction unit. The hydrogen nuclear spin in the human body can be equivalently a small magnetic needle. In the strong magnetic field provided by the magnet, hydrogen nuclei are converted from a disordered thermal equilibrium state into a partially forward and partially reverse main magnetic field directions. The difference between the two forms a net magnetization vector. The hydrogen nuclei precess around the main magnetic field, with the precession frequency being proportional to the magnetic field strength. The gradient unit generates a magnetic field with a strength that varies with spatial position for spatial encoding of the signal. The radio frequency transmitting coil turns hydrogen nuclei from the main magnetic field direction to a transverse plane and precesses around the main magnetic field. A current signal is induced at the radio frequency receive coil. An image of the imaged tissue is obtained via a signal processing and image reconstruction unit.
That is, the lorentz force acting on the gradient coil is very large and at the same time is constantly changing, and the nuclear magnetic resonance system generates strong noise. When the noise is too large, the hearing of the inspector is affected, and on the other hand, the problem of poor user experience is caused by the large noise.
Disclosure of Invention
The invention provides a noise control method for magnetic resonance examination and a scanning sequence determining method, which are used for realizing the technical effects that the noise degree, namely the mute degree, is set before nuclear magnetic resonance, and the mute degree and the scanning time are balanced from reaching.
In a first aspect, an embodiment of the present invention provides a noise control method for magnetic resonance examination, the method including:
acquiring mute parameters associated with a scanning sequence, and determining a mute gradient waveform corresponding to the mute parameters;
scanning a target scanning part based on the mute gradient waveform;
wherein the mute parameter comprises expected volume or expected scanning time.
In a second aspect, an embodiment of the present invention further provides a noise control apparatus for magnetic resonance examination, the apparatus comprising:
the mute gradient waveform determining module is used for acquiring mute parameters associated with the scanning sequence and determining a mute gradient waveform corresponding to the mute parameters;
The scanning module is used for scanning the target scanning part based on the mute gradient waveform;
wherein the mute parameter comprises expected volume or expected scanning time.
In a third aspect, an embodiment of the present invention further provides a scan sequence determination method for magnetic resonance examination, the method comprising:
selecting a scanning sequence for performing magnetic resonance examination on a detection object; the scan sequence includes gradient pulse parameters;
setting a volume threshold or a scanning time threshold for performing magnetic resonance examination on the detection object based on the scanning sequence;
acquiring expected volume or expected scanning time according to parameters corresponding to the scanning sequence;
when the expected volume exceeds the volume threshold, adjusting gradient pulse parameters of the scanning sequence; or, when the expected scan time exceeds the scan time threshold, adjusting a gradient pulse parameter of the scan sequence;
the adjusted expected volume corresponding to the scanning sequence is in the volume threshold range, and the corresponding expected scanning time is in the scanning time threshold range.
In a fourth aspect, an embodiment of the present invention further provides a scan sequence determination apparatus for magnetic resonance examination, the apparatus comprising:
The scanning sequence area selection module is used for selecting a scanning sequence for performing magnetic resonance examination on the detection object; the scan sequence includes gradient pulse parameters;
a threshold setting module for setting a volume threshold or a scan time threshold for performing magnetic resonance examination on the detection object based on the scan sequence;
the expected time or volume determining module is used for acquiring expected volume or expected scanning time according to parameters corresponding to the scanning sequence;
the parameter adjustment module is used for adjusting gradient pulse parameters of the scanning sequence when the expected volume exceeds the volume threshold; or, when the expected scan time exceeds the scan time threshold, adjusting a gradient pulse parameter of the scan sequence;
and the scanning sequence determining module is used for adjusting the expected volume corresponding to the scanning sequence within the volume threshold range and the expected scanning time corresponding to the scanning sequence within the scanning time threshold range.
According to the technical scheme provided by the embodiment of the invention, the mute gradient waveform corresponding to the mute parameter is determined by acquiring the mute parameter, and the target scanning part is scanned based on the mute gradient waveform, so that the technical problems of high noise and poor user experience in the nuclear magnetic resonance process in the prior art are solved, and the technical effect of adjusting the balance between the scanning time and the scanning noise of the magnetic resonance system according to the preset mute parameter is realized.
Drawings
In order to more clearly illustrate the technical solution of the exemplary embodiments of the present invention, a brief description is given below of the drawings required for describing the embodiments. It is obvious that the drawings presented are only drawings of some of the embodiments of the invention to be described, and not all the drawings, and that other drawings can be made according to these drawings without inventive effort for a person skilled in the art.
Fig. 1 is a schematic flow chart of a noise control method for magnetic resonance examination according to an embodiment of the present invention;
fig. 2 is a flowchart of a scan sequence determining method for magnetic resonance examination according to a second embodiment of the present invention;
fig. 3 is a flowchart of a noise control method for magnetic resonance examination according to a third embodiment of the present invention;
fig. 4 is a schematic diagram of adjusting mute parameters on a display interface according to a third embodiment of the present invention;
fig. 5 is a schematic diagram of a mute gradient waveform transformation according to a third embodiment of the present invention;
fig. 6 is a schematic diagram of a mute gradient waveform transformation according to a third embodiment of the present invention;
fig. 7 is a schematic diagram of a mute gradient waveform transformation according to a third embodiment of the present invention;
Fig. 8 is a schematic diagram of a mute gradient waveform transformation according to a third embodiment of the present invention;
fig. 9 is a schematic diagram of a mute gradient waveform transformation according to a third embodiment of the present invention;
FIG. 10 is a schematic diagram of an interface display according to an embodiment of the present invention;
fig. 11 is a schematic structural diagram of a noise control device for magnetic resonance examination according to a fourth embodiment of the present invention;
fig. 12 is a schematic diagram of a server structure according to a fifth embodiment of the present invention.
Detailed Description
The invention is described in further detail below with reference to the drawings and examples. It is to be understood that the specific embodiments described herein are merely illustrative of the invention and are not limiting thereof. It should be further noted that, for convenience of description, only some, but not all of the structures related to the present invention are shown in the drawings.
Example 1
Fig. 1 is a schematic flow chart of a noise control method for magnetic resonance examination according to an embodiment of the present invention, where the method may be performed by a noise control device for magnetic resonance examination, and the device may be implemented in software and/or hardware.
As shown in fig. 1, the method of this embodiment includes:
s110, acquiring mute parameters associated with the scanning sequence, and determining a mute gradient waveform corresponding to the mute parameters.
The magnetic resonance system selectively excites hydrogen protons in the space by controlling the gradient system in time sequence, and when the space is encoded, only after the radio frequency receiving coil receives enough signals, the image can be reconstructed. In the MR imaging process, the gradient system performs spatial encoding by always and rapidly switching and transforming in a magnet containing a strong magnetic field, and the gradient system can generate strong noise. At present, the reduction of acoustic noise of a magnetic resonance system can be achieved by improving the way gradients are used in the sequence.
The mute parameter can be understood as the scan time of the magnetic resonance system or the noise level of the magnetic resonance system during operation. Noise may be expressed in decibels (dB). The mute gradient waveform includes a gradient application timing, a gradient amplitude, and a gradient ramp rate, and it is exemplarily understood that when a current is applied to a gradient coil in a magnetic resonance system, a current value is converted from zero to a target value, and a waveform corresponding to the conversion of the current value is converted from the target value to zero, as a mute gradient waveform.
Specifically, if the user is displaying the mute parameters of the interface, the server corresponding to the magnetic resonance system may calculate a mute gradient waveform corresponding to the mute parameters, and based on the mute gradient waveform, a scan time corresponding to the mute parameters may be determined.
Determining a mute gradient waveform corresponding to the mute parameter according to the mute parameter, comprising: and acquiring the mute parameters, and determining a mute gradient waveform corresponding to the mute parameters according to a preset scanning sequence.
Wherein the scan sequence can be understood as: a scan sequence required when performing magnetic resonance scan of a region to be scanned. When the scanning sequences are different, the target current values required by the gradient coils are different, namely the current amplitude is uncertain, and correspondingly, the noise generated by the gradient coils is also different. In order to accurately realize the technical effect that noise and scanning time are balanced, after the mute parameters are set, and after the scanning sequence corresponding to the part to be scanned is acquired, the mute parameters and the scanning sequence can be synthesized to determine the mute gradient waveform.
Specifically, the scan sequence corresponding to the part to be scanned and the set mute parameters, namely the noise decibels of the scan, are obtained, and the mute gradient waveforms corresponding to different scan parts can be calculated.
Of course, acquiring the mute parameters, determining the mute gradient waveform corresponding to the mute parameters, includes: and obtaining mute parameters, searching a pre-established mapping relation table, and determining a mute gradient waveform corresponding to the mute parameters.
The pre-established mapping relation table may be: after determining a scanning sequence corresponding to a part to be scanned, setting mute parameters, namely mute degrees (noise decibels), and a server corresponding to the magnetic resonance scanning system, respectively determining mute gradient waveforms corresponding to different mute parameters according to the scanning sequence, and respectively storing the obtained scanning sequence, the mute parameters and the corresponding mute gradient waveforms into a pre-established mapping relation table. When the scanning sequence corresponding to the target user and the mute parameter are determined, the mute gradient waveform corresponding to the scanning sequence and the mute parameter can be directly called from the mapping relation table. Of course, in order to reduce the cost, after performing the magnetic resonance scan, the scan location, the scan sequence, the mute parameters and the corresponding mute gradient waveforms corresponding to the patient may be stored in a mapping relation table established in advance, so as to be called next time.
Specifically, when determining the scanning sequence, different mute degrees can be set according to the requirements of the user, mute gradient waveforms corresponding to the different mute degrees can be determined, and when determining the mute gradient waveforms, the scanning time corresponding to the user can be determined and stored in the mapping relation table of the database. After determining the target scanning sequence and the target mute parameter corresponding to the target user, it can first search whether the mapping table of the database stores the mute gradient waveform corresponding to the target scanning sequence and the target mute parameter, and if yes, call the mute gradient waveform from the database for use.
It should be noted that, determining the mute gradient waveform corresponding to the mute parameter may also be: after the mute parameters and scan sequence are obtained, a calculation formula may be called to determine the mute gradient waveform.
Note that, when determining the mute gradient waveform corresponding to the mute degree, the scan time corresponding to the mute degree may be obtained.
The acoustic noise output of a magnetic resonance system can be generally modeled as a linear time-invariant system, and the acoustic vibration characteristics of the system can be obtained by measuring the frequency response functions of the gradient coils, i.e., the acoustic transfer functions H (x), H (y), H (z), respectively, in advance. When the magnetic resonance system is in operation, the gradient pulse parameters included in the scan sequence apply gradient waveforms G (x), G (y), G (z) on the respective gradient coils, and the predicted acoustic noise can be approximated as: p=h (x) G (x) +h (y) G (y) +h (z) G (z).
Wherein P represents the expected volume; h (X) represents the system response function of the X-axis gradient coil; h (Y) represents the system response function of the Y-axis gradient coil; h (Z) represents the system response function of the Z-axis gradient coil, and x represents the convolution operation.
Based on the formula, the noise corresponding to different scanning sequences can be determined, and then the mute gradient waveform corresponding to the noise can be determined according to the predicted noise.
And S120, scanning the target scanning part based on the mute gradient waveform.
Specifically, after the user triggers the mute degree, the server of the magnetic resonance system can determine the mute gradient waveform corresponding to the mute degree, determine the using mode of the gradient based on the mute gradient waveform, scan the target part, and remarkably reduce the acoustic noise of the magnetic resonance system, thereby realizing the technical effect of balancing the scanning time and the noise.
It should be noted that once the mute program is selected on the operation interface and the confirmation key is clicked, the re-determination of the mute program cannot be changed during the scan of the magnetic resonance system.
On the basis of the technical scheme, after obtaining the scanning time and before scanning the target scanning part based on the mute gradient waveform, the method further comprises the following steps: and when the scanning time exceeds a preset time threshold, adjusting the mute parameter.
In this embodiment, the preset scanning time may be predetermined, and may be selected from five minutes. After the setting of the mute parameters, i.e. the noise decibels is completed, the mute gradient waveform can be determined according to the set noise decibels, and then the scanning time corresponding to the mute parameters is determined. If the scanning time is greater than the preset scanning time by five minutes, the scanning time can be fed back to the display interface, optionally, the calculated scanning time is displayed on the display interface, optionally, 6 minutes, and the worker can readjust the mute parameters according to the time displayed on the display interface, namely the feedback time, optionally, the mute degree is increased, namely the noise is increased a little. After readjusting the mute parameters, the system may determine the mute gradient waveform based on the adjusted mute parameters. If the obtained scanning time is within the preset scanning time range according to the adjusted mute parameters, scanning can be performed according to the adjusted mute gradient waveform.
In order to reach the target gradient in a short time, the gradient is slowly climbed as the scanning time is longer, and the corresponding noise is smaller; conversely, the shorter the scanning time, the faster the gradient rises, and the greater the corresponding noise.
According to the technical scheme provided by the embodiment of the invention, the mute gradient waveform corresponding to the mute parameter is determined by acquiring the mute parameter, and the target scanning part is scanned based on the mute gradient waveform, so that the technical problems of high noise and poor user experience in the nuclear magnetic resonance process in the prior art are solved, and the technical effects of adjusting the scanning time and the scanning noise balance of the magnetic resonance system by setting different mute parameters are realized, thereby improving the user experience.
Example two
Fig. 2 is a diagram showing a scan sequence determining method for magnetic resonance examination according to a second embodiment of the present invention, which uses a flexible balance of scan time and acoustic noise. The method comprises the following steps:
s210, selecting a scanning sequence for performing magnetic resonance examination on the detection object.
Wherein the detection object may be a scanned region. The scan sequence may be a scan sequence corresponding to a scan site. Gradient pulse parameters are included in the scan sequence. The scan sequence of the clock of the present invention includes radio frequency pulses, slice selection gradient fields, phase encoding gradient fields, frequency encoding gradient fields, and MR signals.
Specifically, the magnetic resonance scanning sequence corresponding to the scanning object is obtained according to the detection object, and the settings of the parameters related to the radio frequency pulse, the gradient field, the signal acquisition time and the like and the arrangement thereof on the time sequence are called as the scanning sequence. Exemplary parameters of the rf pulse include rf bandwidth, rf amplitude, application time, and duration; the parameters of the gradient pulse include the gradient field application direction, the gradient field strength, when to apply and the duration. The kind of scanning sequence may be a Free Induction Decay (FID) like sequence, a Spin Echo (SE) like sequence, a gradient echo like sequence or a hybrid sequence of gradient echoes and spin echoes. In some embodiments, the detection object is a heart, and the scan sequence may be a gradient echo cine imaging sequence, a gradient echo cardiac marker cine imaging sequence, or a balanced steady-state precession sequence, or the like. In some embodiments, the detection object is a cranium, and the scan sequence may be a 2D SE T1WI, a 2D FSE (fast spin echo) T2WI, a Diffusion Weighted Imaging (DWI) sequence, a magneto-Sensitive Weighted Imaging (SWI) sequence, or the like.
S220, setting a volume threshold or a scanning time threshold for performing magnetic resonance examination on the detection object based on the scanning sequence.
The volume threshold may be a preset sweep volume threshold. The scan time threshold may be a preset scan time threshold. The volume threshold and the scan time threshold are both set based on the scan sequence.
Specifically, a volume threshold value for performing magnetic resonance examination on the detection object, or a scan time threshold value may be set based on the scan sequence.
It should be noted that, the scanning volume and the scanning time are in inverse proportion, when the scanning volume is lower, the corresponding scanning time is longer, and correspondingly, when the scanning volume is higher, the corresponding scanning time is shorter.
S230, acquiring expected volume or expected scanning time according to parameters corresponding to the scanning sequence.
Specifically, the staff member may drag the progress bar to determine the scanning time, and may adjust the desired volume corresponding to the detection object, or the desired scanning time, based on the feedback of the user.
S240, when the expected volume exceeds the volume threshold, adjusting gradient pulse parameters of the scanning sequence; alternatively, the gradient pulse parameters of the scan sequence are adjusted when the expected scan time exceeds a scan time threshold.
Specifically, after the user determines the expected volume or the expected scanning time threshold, whether the expected volume is within the volume threshold range or not and whether the expected scanning time is within the scanning time threshold range or not can be determined, if so, the current pulse gradient parameter is used as the current pulse gradient parameter; if not, the pulse parameters of the scanning sequence are adjusted.
It should be noted that, the expected volume corresponding to the adjusted scan sequence is within the volume threshold range.
In this embodiment, adjusting the pulse gradient parameter includes at least one of the following adjustment strategies. Optionally, adjusting the gradient pulse parameters of the scan sequence includes one or more of the following adjustment strategies; adjusting the amplitude parameter of the gradient pulse; adjusting gradient pulse inclination rate; the profile of the gradient pulse waveform is adjusted.
The gradient pulse amplitude can be understood as field intensity, has higher requirements on ultra-fast sequences such as plane echo imaging and the like and field intensity of a gradient field by water molecule diffusion weighted imaging, and the high gradient field can shorten callback clearance to accelerate signal acquisition speed, thereby being beneficial to improving signal to noise ratio, and ensuring that the gradient pulse amplitude is unchanged when pulse parameters are regulated under the condition. In adjusting the gradient pulse parameters, the profile of the gradient pulse waveform can also be adjusted, such as a set of gradients with dynamically varying amplitudes, such as phase encoding gradients, and a set of area-like curve gradients can be used to reduce acoustic noise. If multiple adjacent gradients with opposite amplitudes cannot be simply combined into one gradient, the same number of gradient gradients with opposite amplitudes can be used according to different practical requirements, but the total area remains the same or the total area and the curve gradient with the same integral of the area with time are simultaneously maintained to reduce acoustic noise.
Specifically, when the gradient pulse parameters need to be adjusted, the pulse amplitude, the pulse slope and/or the profile of the gradient pulse waveform can be determined and adjusted according to actual requirements.
Optionally, at least two adjustment strategies are respectively adopted as a group of adjustment strategies, and gradient pulse parameters of the scanning sequence are adjusted based on each group of adjustment strategies; respectively calculating the expected volume or the expected scanning time corresponding to the scanning sequence after adjustment based on each group of adjustment strategies; and determining a group of adjustment strategies corresponding to the minimum expected volume or expected scanning time as target adjustment strategies, and taking the scanning sequence corresponding to the target adjustment strategies as a target scanning sequence.
Through the method, a user can set the mute degree or the scan time through the interface, the scan sequence estimates the optimization degree of the gradient waveform according to the set mute degree or the scan time, and then the gradient waveform of the whole scan sequence is accurately calculated to obtain the corresponding scan time length or the mute degree; if the user is not satisfied with the scan time, the user can reset by readjusting the mute level, ultimately achieving a balance between the mute level and the acceptable scan time.
On the basis of the technical scheme, after the gradient pulse parameters corresponding to the detection object are determined, the detection object can be scanned based on the determination of the target scanning sequence, and whether the currently determined target scanning sequence meets the quality requirement of the reconstructed image is further determined.
Optionally, scanning the detection object based on the target scanning sequence, and acquiring a magnetic resonance signal; reconstructing the magnetic resonance signals to obtain a detection image; evaluating the quality of the detected image; and readjusting gradient pulse parameters of the scanning sequence when the quality of the detected image does not meet a quality threshold.
The quality of the detected image may be, among other things, a machine or user may evaluate the quality of the image, including signal-to-noise ratio, image resolution, or image contrast.
Specifically, the detection object is scanned based on the determined target scanning sequence, and magnetic resonance signals are acquired to determine and detect an image based on the magnetic resonance signals. When the quality of the detected image does not meet the preset image quality requirement, it is indicated that the determined gradient pulse parameter does not meet the preset requirement, and S210 to S240 need to be repeatedly executed to determine the gradient pulse parameter, that is, the target scanning sequence.
For example, when it is determined that the current image quality does not meet the diagnostic requirement, an adjustment strategy of the scan sequence may be modified, for example: the adjustment strategy of the scanning sequence in the previous period is to adjust the amplitude parameter of the gradient pulse, and if the corresponding image signal-to-noise ratio does not meet the set threshold, the adjustment strategy of the scanning sequence is to adjust the outline of the gradient pulse waveform; for another example, if the adjustment strategy of the scanning sequence in the previous period is the gradient pulse inclination rate, and it is detected that the corresponding peripheral nerve stimulation value exceeds the regulation threshold, the adjustment strategy of the scanning sequence is adjusted to the mixing strategy (the mixture of multiple adjustment strategies).
In one embodiment, the adjustment of the scan sequence may include a plurality of times, and each adjusted scan sequence performs acquisition of a plurality of sets of magnetic resonance signals. The target signals can be acquired by weighting the plurality of sets of magnetic resonance signals. Alternatively, the weights of each set of magnetic resonance signals may be determined as follows:
the magnetic resonance signals closer to the mass threshold are given a higher weight coefficient, and the magnetic resonance signals greater than the mass threshold are given a higher weight coefficient. In one embodiment, the volume threshold or scan time threshold may be adjusted when the reconstructed image is still unsatisfactory after changing the adjustment policy of the scan sequence. For example, the volume threshold or the scan time threshold is increased over multiple adjustments.
According to the technical scheme provided by the embodiment of the invention, the gradient pulse parameters are adjusted through at least one adjustment strategy, so that the technical problem of poor user experience caused by the fact that gradient scanning noise and scanning time cannot be well balanced in the prior art is solved, and the technical effect of adjusting the balance between the scanning time and the scanning noise is realized.
Example III
As a preferred embodiment of the foregoing embodiments, fig. 3 is a schematic flow chart of a noise control method for magnetic resonance examination according to a third embodiment of the present invention. As shown in fig. 3, the method includes:
s310, setting the mute degree of the gradient.
The mute degree of the gradient can be understood as follows: the patient may receive a decibel of noise while performing a magnetic resonance scan of the target site. Of course, the scan time corresponding to the mute program may also be displayed on the display interface. The target user may determine whether the silence level selected by the operator and the scan time corresponding to the silence level is within its acceptable range, optionally, 20dB (decibel) of scan noise, and the scan time corresponding to the silence level is 4:00 minutes.
Specifically, when performing magnetic resonance scanning on a patient, a worker can select the mute degree of the magnetic resonance system scanning on the control interface, and the magnetic resonance scanning system can determine the scanning time corresponding to the mute degree according to the set mute degree, namely the noise decibel.
For example, referring to fig. 4, a schematic view as shown in fig. 4 may be popped up on the display interface while performing a magnetic resonance scan of the target site. The operator may control the drag bar to determine the degree of silence. The noise is the smallest, and the corresponding scanning time is the longest, which can be quarter and half minutes; when the noise is maximum, the corresponding scanning time is the shortest, which can be two minutes and half minutes.
When the type of the scan sequence is determined, the scan time corresponding to the larger noise is shorter, and the scan time corresponding to the smaller noise is longer.
S320, estimating the optimization degree of the gradient waveforms in the sequence.
Wherein the degree of optimization of the gradient waveforms in the sequence is estimated, i.e. the gradient pulse parameters are adjusted, optionally the gradient pulse amplitude parameters are adjusted, the gradient slope of the gradient pulses is adjusted, and/or the profile of the gradient pulse waveforms is adjusted.
It should be noted that, when the gradient is used more slowly, the noise of the magnetic resonance system is smaller, and in principle, the gradient is used in at least three cases. One is to require the gradient amplitude (i.e. the target current amplitude of the gradient coil) to be constant, where the amplitude can be understood as the field strength. The reason for ensuring the constant amplitude is that the ultrafast sequences such as single excitation relaxation enhanced fast acquisition (SS-RARE), fast gradient echo (Turbo-GRE), plane echo and the like and the water molecule diffusion weighted imaging have higher requirements on the field strength of the gradient field, the high gradient field can select the echo gap to accelerate the signal acquisition speed, thereby being beneficial to improving the signal to noise ratio, and the acoustic noise can be reduced by adjusting the gradient climbing and/or descending slope at the moment, see fig. 5. 5 (a) in fig. 5 shows a gradient waveform with unchanged ramp up and/or ramp down slope, and 5 (b) shows that the ramp up and/or ramp down frequency of the gradient waveform can be adjusted to achieve reduced acoustic noise.
Another case is that when scanning a part to be scanned, the area between the adjusted gradient waveform and the unadjusted gradient waveform is required to be unchanged, namely: the zero order moment of the gradient remains unchanged before and after adjustment, see fig. 6. Fig. 6 (a) shows a gradient waveform before the gradient waveform is not changed, and 6 (b), 6 (c), and 6 (d) show gradient waveforms after the ramp up and/or ramp down slope is changed, respectively. 6 (b) represents reduction of acoustic noise by reducing the amplitude of the gradient, 6 (c) represents constant amplitude of the gradient, reduction of acoustic noise by changing the rising and/or falling slope of the gradient, and 6 (d) reduction of acoustic noise by slowing down the gradient rate of change. The gradient waveform areas of 6 (a), 6 (b), 6 (c), and 6 (d) were unchanged. A third way of reducing noise may be to use the above-described ways in combination, see fig. 7. Wherein 7 (a) represents an unchanged gradient waveform, and 7 (b) represents that when the gradient area requirement is unchanged, the acoustic noise can be reduced by simultaneously reducing the gradient amplitude and gradient climbing and/or falling slope; 7 (c) shows that when the gradient area requirement is unchanged, the acoustic noise can be reduced by simultaneously reducing the amplitude, gradient climbing/descending slope and gradient change rate. Adjusting gradient pulse parameters may also be adjusting the profile of the gradient pulse waveform, a set of amplitude-dynamically changing gradients, such as phase encoding gradients, may use a set of area-like curve gradients to reduce acoustic noise, as shown in fig. 8, a set of amplitude-changing gradients, such as muting of phase encoding gradients; but also a plurality of adjacent gradients of opposite magnitudes, if not simply combined into one gradient, the same number of gradient curves with opposite total areas remaining the same or with the same integral of total area and area over time can be used to reduce noise, as per different requirements, see fig. 9, a pair of gradients of opposite magnitudes, such as a muting process of flow compensated gradients.
After determining the mute degree according to the staff, the system can determine which mode is adopted to determine the optimized gradient waveform corresponding to the mute degree according to the received mute degree. Optionally, whether the gradient of the mute gradient waveform changes, whether the area of the surrounding area of the gradient waveform changes, whether the included angle between the waist of the gradient waveform and the horizontal plane changes, and the like.
S330, recalculating the gradient waveforms of the sequence.
After determining the degree of optimization of the gradient waveform, the gradient waveform can be accurately calculated.
After the staff drags the sliding bar to move to the target position, namely after determining the noise decibels, the mute gradient waveform corresponding to the noise decibels can be calculated. Of course, after determining the mute degree, gradient waveforms identical to the scan sequence and the mute degree can be obtained from the mapping relation table in the database according to the mute degree; if the mute gradient waveform corresponding thereto is not stored in the mapping relation table, the mute gradient waveform corresponding thereto may be calculated.
S340, calculating the scanning time of the sequence.
After determining the degree of silence, and after scanning the sequence, a silence gradient waveform corresponding thereto may be determined. When the mute gradient waveform is determined, a scan time corresponding to the degree of mute can be determined. The staff member can determine whether the target user receives the mute level and the scan time.
When the target user receives the mute degree and the corresponding scanning time, the mute parameter completion key can be clicked, so that the magnetic resonance system scans the part to be scanned of the target user according to the preset mute parameters, namely according to the gradient waveform determined according to the mute parameters. Of course, if the target user believes that the scan time is too long or too noisy, the degree of silence may be reset until the adjusted degree of silence is acceptable to the scan time target user.
S350, finishing mute parameter setting, and starting scanning.
When the target user accepts the mute parameters set by the staff, the confirmation key can be clicked. After the mute parameter setting is completed, a key to start scanning may be triggered to scan the target site.
According to the technical scheme provided by the embodiment of the invention, the mute gradient waveform corresponding to the mute parameter is determined by acquiring the mute parameter, and the target scanning part is scanned based on the mute gradient waveform, so that the technical problems of high noise and poor user experience in the nuclear magnetic resonance process in the prior art are solved, the balance between the scanning time and the scanning noise of the magnetic resonance system is adjusted according to the preset mute parameter, and the technical effect of improving the user experience is achieved.
In another embodiment, the noise control method for magnetic resonance examination also first sets a scan time, which includes the steps of:
firstly, after selecting a scanning sequence for performing magnetic resonance examination on a detection object, a user can set the accepted scanning time through an interface; then, the magnetic resonance system estimates the optimization degree of the gradient waveform of the scanning sequence according to the set scanning time; and finally, calculating a noise value corresponding to the gradient waveform optimized by the scanning sequence. It should be noted that if the user is not satisfied with the noise levels corresponding to the various optimized gradient waveforms, the noise levels can be reset by adjusting the scan time, and finally, the balance between the mute degree and the acceptable scan time is achieved.
On the basis of the above technical solutions, it should be further noted that the server for adjusting the pulse parameters is further connected to a display device, i.e. a display. As shown in fig. 10: it comprises the following steps: the interface area is inspected and the monitoring area is scanned. The scan monitoring area of the present embodiment may include: a SAR (specific absorption rate of RF energy) monitoring strip for monitoring the absorption of the RF energy by the examination object; an electrocardiographic monitoring area (wavy line in the figure) for displaying the heart movement period of the patient; a patient comfort adjustment zone, which may be provided with a volume and scan time adjustment bar as described in fig. 3; the sickbed adjusting area is used for enabling the patient to move to the center of the scanning area, and move in or out of the scanning cavity; when a worker triggers a control on the display, the interface marked as the figure 1 can be switched to the interface marked as the figure 2, and the work such as image browsing, patient management, patient registration, printing, post-processing and the like can be performed. Meanwhile, the monitoring of the scanning related conditions can be performed by scanning the monitoring area. It should be noted that the scan monitoring area may be hidden when there is no scan currently, or when a larger interface is required to do the above-described tasks (image browsing, patient management, patient registration, printing, post-processing).
Example IV
Fig. 11 is a schematic structural diagram of a noise control device for magnetic resonance examination according to a fourth embodiment of the present invention, where the noise control device includes: a mute gradient waveform determination module 1110 and a scan module 1120.
The mute gradient waveform determining module 1110 is configured to obtain mute parameters, and determine a mute gradient waveform corresponding to the mute parameters; and a scanning module 1120, configured to scan the target scan site based on the mute gradient waveform.
According to the technical scheme provided by the embodiment of the invention, the mute gradient waveform corresponding to the mute parameter is determined by acquiring the mute parameter, and the target scanning part is scanned based on the mute gradient waveform, so that the technical problems of high noise and poor user experience in the nuclear magnetic resonance process in the prior art are solved, the balance between the scanning time and the scanning noise of the magnetic resonance system is adjusted according to the preset mute parameter, and the technical effect of improving the user experience is achieved.
On the basis of the technical scheme, the mute gradient waveform determining module is further used for:
a mute parameter corresponding to the scan sequence is determined based on the scan sequence relative to the target scan site.
On the basis of the above technical solutions, the mute gradient waveform determining module is further configured to:
and searching a pre-established mapping relation table according to the acquired mute parameters to determine a mute gradient waveform corresponding to the mute parameters.
On the basis of the technical scheme, the mute gradient waveform determining module is further used for:
and calculating a mute gradient waveform corresponding to the mute parameter according to the pre-selected mute parameter.
On the basis of the technical scheme, the device further comprises a scanning time determining module, and before the mute gradient waveform determining module is used for obtaining the mute parameters and determining the mute gradient waveform corresponding to the mute parameters, the device is further used for:
and obtaining the scanning time corresponding to the target scanning position according to the mute gradient waveform.
On the basis of the above technical solutions, the system further includes a scan time determining module, which is further configured to:
when the scanning time exceeds a preset time threshold, the mute parameter is regulated;
correspondingly, according to the pre-selected mute parameters, determining the mute gradient waveform corresponding to the mute parameters comprises:
and determining a mute gradient waveform corresponding to the adjusted mute parameter according to the adjusted mute parameter.
The magnetic resonance noise control device provided by the embodiment of the invention can execute the magnetic resonance noise control method provided by any embodiment of the invention, and has the corresponding functional modules and beneficial effects of the execution method.
It should be noted that each unit and module included in the above apparatus are only divided according to the functional logic, but not limited to the above division, so long as the corresponding functions can be implemented; in addition, the specific names of the functional units are also only for distinguishing from each other, and are not used to limit the protection scope of the embodiments of the present invention.
Example five
Fig. 12 is a schematic structural diagram of a server according to a fourth embodiment of the present invention. Fig. 12 shows a block diagram of an exemplary server 1200 suitable for use in implementing the embodiments of the invention. The server 1200 shown in fig. 12 is merely an example, and should not be construed as limiting the functionality and scope of use of the embodiments of the present invention.
As shown in fig. 12, the server 1200 is in the form of a general purpose computing device. Components of server 1200 may include, but are not limited to: one or more processors or processing units 1201, a system memory 1202, and a bus 1203 that connects the various system components (including the system memory 1202 and the processing units 1201).
The system memory 1202 may include computer system readable media in the form of volatile memory, such as Random Access Memory (RAM) 1204 and/or cache memory 1205. The server 1200 may further include other removable/non-removable, volatile/nonvolatile computer system storage media. By way of example only, the storage system 1206 may be used to read from or write to non-removable, non-volatile magnetic media (not shown in FIG. 12, commonly referred to as a "hard disk drive"). Although not shown in fig. 12, a magnetic disk drive for reading from and writing to a removable non-volatile magnetic disk (e.g., a "floppy disk"), and an optical disk drive for reading from or writing to a removable non-volatile optical disk (e.g., a CD-ROM, DVD-ROM, or other optical media) may be provided. In such cases, each drive may be coupled to bus 1203 via one or more data media interfaces. Memory 1202 may include at least one program product having a set (e.g., at least one) of program modules configured to carry out the functions of embodiments of the invention.
A program/utility 1208 having a set (at least one) of program modules 1207 may be stored in, for example, memory 1202, such program modules 1207 including, but not limited to, an operating system, one or more application programs, other program modules, and program data, each or some combination of which may include an implementation of a network environment. Program modules 1207 typically carry out the functions and/or methods of the described embodiments of the present invention.
The server 1200 may also communicate with one or more external servers 1209 (e.g., keyboard, pointing device, display 1210, etc.), one or more devices that enable a user to interact with the server 1200, and/or any devices (e.g., network card, modem, etc.) that enable the server 1200 to communicate with one or more other computing devices. Such communication may occur through an input/output (I/O) interface 1211. Also, the server 1200 may communicate with one or more networks such as a Local Area Network (LAN), a Wide Area Network (WAN), and/or a public network, such as the internet, through a network adapter 1212. As shown, network adapter 1212 communicates with other modules of server 1200 via bus 1203. It should be appreciated that although not shown in fig. 12, other hardware and/or software modules may be used in connection with server 1200, including but not limited to: microcode, device drivers, redundant processing units, external disk drive arrays, RAID systems, tape drives, data backup storage systems, and the like.
The processing unit 1201 executes various functional applications and data processing by running a program stored in the system memory 1202, for example, implementing a noise control method for magnetic resonance examination and a scan sequence determination method provided by an embodiment of the present invention.
Example six
A sixth embodiment of the present invention also provides a storage medium containing computer-executable instructions for performing a noise control method for magnetic resonance examination and a scan sequence determination method when executed by a computer processor.
The method comprises the following steps:
obtaining mute parameters and determining mute gradient waveforms corresponding to the mute parameters;
and scanning the target scanning part based on the mute gradient waveform.
The computer storage media of embodiments of the invention may take the form of any combination of one or more computer-readable media. The computer readable medium may be a computer readable signal medium or a computer readable storage medium. The computer readable storage medium can be, for example, but not limited to, an electronic, magnetic, optical, electromagnetic, infrared, or semiconductor system, apparatus, or device, or a combination of any of the foregoing. More specific examples (a non-exhaustive list) of the computer-readable storage medium would include the following: an electrical connection having one or more wires, a portable computer diskette, a hard disk, a Random Access Memory (RAM), a read-only memory (ROM), an erasable programmable read-only memory (EPROM or flash memory), an optical fiber, a portable compact disc read-only memory (CD-ROM), an optical storage device, a magnetic storage device, or any suitable combination of the foregoing. In this document, a computer readable storage medium may be any tangible medium that can contain, or store a program for use by or in connection with an instruction execution system, apparatus, or device.
The computer readable signal medium may include a propagated data signal with computer readable program code embodied therein, either in baseband or as part of a carrier wave. Such a propagated data signal may take any of a variety of forms, including, but not limited to, electro-magnetic, optical, or any suitable combination of the foregoing. A computer readable signal medium may also be any computer readable medium that is not a computer readable storage medium and that can communicate, propagate, or transport a program for use by or in connection with an instruction execution system, apparatus, or device.
Program code embodied on a computer readable medium may be transmitted using any appropriate medium, including but not limited to wireless, wireline, optical fiber cable, RF, etc., or any suitable combination of the foregoing.
Computer program code for carrying out operations for embodiments of the present invention may be written in any combination of one or more programming languages, including an object oriented programming language such as Java, smalltalk, C ++ and conventional procedural programming languages, such as the "C" programming language or similar programming languages. The program code may execute entirely on the user's computer, partly on the user's computer, as a stand-alone software package, partly on the user's computer and partly on a remote computer or entirely on the remote computer or server. In the case of a remote computer, the remote computer may be connected to the user's computer through any kind of network, including a Local Area Network (LAN) or a Wide Area Network (WAN), or may be connected to an external computer (for example, through the Internet using an Internet service provider).
Note that the above is only a preferred embodiment of the present invention and the technical principle applied. It will be understood by those skilled in the art that the present invention is not limited to the particular embodiments described herein, but is capable of various obvious changes, rearrangements and substitutions as will now become apparent to those skilled in the art without departing from the scope of the invention. Therefore, while the invention has been described in connection with the above embodiments, the invention is not limited to the embodiments, but may be embodied in many other equivalent forms without departing from the spirit or scope of the invention, which is set forth in the following claims.
Claims (6)
1. A noise control method for magnetic resonance examination, comprising:
acquiring mute parameters associated with a scanning sequence, and determining a mute gradient waveform corresponding to the mute parameters;
obtaining scanning time corresponding to the target scanning part according to the mute gradient waveform;
when the scanning time exceeds a preset time threshold, the mute parameter is regulated;
determining a mute gradient waveform corresponding to the adjusted mute parameter according to the adjusted mute parameter;
scanning the target scanning part based on the mute gradient waveform corresponding to the adjusted mute parameter;
Wherein the mute parameters comprise noise decibels of the magnetic resonance system when the magnetic resonance system works;
wherein the determining a mute gradient waveform corresponding to the mute parameter includes: searching a pre-established mapping relation table to determine a mute gradient waveform corresponding to the adjusted mute parameter; or alternatively, the process may be performed,
according to a pre-acquired mute parameter, calculating a mute gradient waveform corresponding to the adjusted mute parameter based on a calculating formula of the mute gradient waveform, wherein the expected volume corresponding to the mute gradient waveform corresponding to the mute parameter is in a volume threshold range, and the corresponding expected scanning time is in a preset time threshold range;
the noise decibel is determined by: respectively acquiring system response functions of the X, Y and Z-axis gradient coils; respectively obtaining convolution operation results of each gradient coil and the corresponding applied gradient waveform; and X, Y and the convolution operation result corresponding to the Z-axis gradient coil are added to be the noise decibel.
2. A scan sequence determination method for magnetic resonance examination, comprising:
selecting a scanning sequence for performing magnetic resonance examination on a detection object; wherein the scan sequence includes gradient pulse parameters;
Setting a volume threshold and a scanning time threshold for performing magnetic resonance examination on the detection object based on the scanning sequence;
acquiring expected volume according to parameters corresponding to the scanning sequence;
when the expected volume exceeds the volume threshold, adjusting gradient pulse parameters of the scanning sequence; judging whether the adjusted expected scanning time of the scanning sequence exceeds the scanning time threshold, and adjusting gradient pulse parameters of the scanning sequence in response to the expected scanning time exceeding the scanning time threshold;
the adjusted expected volume corresponding to the scanning sequence is in the volume threshold range, and the corresponding expected scanning time is in the scanning time threshold range;
the expected volume is determined by: respectively acquiring system response functions of the X, Y and Z-axis gradient coils; respectively obtaining convolution operation results of each gradient coil and the corresponding applied gradient waveform; and X, Y and the convolution operation result corresponding to the Z-axis gradient coil are added to be the expected volume.
3. The method of claim 2, wherein adjusting gradient pulse parameters of the scan sequence comprises one or more of the following adjustment strategies:
Adjusting the amplitude parameter of the gradient pulse;
adjusting gradient pulse inclination rate;
the profile of the gradient pulse waveform is adjusted.
4. A method according to claim 3, wherein said adjusting gradient pulse parameters of said scan sequence comprises:
respectively adopting at least two adjustment strategies as a group of adjustment strategies, and adjusting gradient pulse parameters of the scanning sequence based on each group of adjustment strategies;
respectively calculating the expected volume or the expected scanning time corresponding to the scanning sequence after adjustment based on each group of adjustment strategies;
and determining a group of adjustment strategies corresponding to the minimum expected volume or expected scanning time as target adjustment strategies, and taking the scanning sequence corresponding to the target adjustment strategies as a target scanning sequence.
5. The method according to claim 4, wherein the method further comprises:
scanning the detection object based on the target scanning sequence to acquire a magnetic resonance signal;
reconstructing the magnetic resonance signals to obtain a detection image corresponding to the detection object;
and when the quality of the detected image does not accord with the quality threshold, readjusting the gradient pulse parameters of the scanning sequence until the quality of the detected image accords with the quality threshold.
6. The method of claim 5, further comprising, after said readjusting gradient pulse parameters of said scan sequence when the quality of said detected image does not meet a quality threshold:
and adjusting the volume threshold or the scanning time threshold.
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| US16/919,119 US11353527B2 (en) | 2019-07-19 | 2020-07-02 | Systems and methods for waveform determination in magnetic resonance imaging |
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