CN116466279A - Magnetic resonance imaging method, system, electronic equipment and medium for lung - Google Patents
Magnetic resonance imaging method, system, electronic equipment and medium for lung Download PDFInfo
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Abstract
The invention provides a magnetic resonance imaging method, a system, electronic equipment and a medium for lung, wherein the method comprises the following steps: applying a gradient magnetic field in a layer direction to a target to be imaged; when the gradient of the gradient magnetic field starts to climb, hard pulse excitation is carried out on the target to be imaged, and frequency modulation is carried out on the hard pulse based on a preset frequency modulation range, so that a magnetic resonance signal is generated; when the hard pulse excitation is stopped, carrying out spiral acquisition on the magnetic resonance signals to acquire original imaging data of the target to be imaged; and reconstructing the original imaging data based on a preset reconstruction rule to obtain target imaging. The magnetic resonance imaging method, the system, the electronic equipment and the medium for the lung can effectively shorten echo time and imaging time, and have higher signal-to-noise ratio and higher resolution.
Description
Technical Field
The present invention relates to the field of magnetic resonance imaging, and in particular, to a method, a system, an electronic device, and a medium for magnetic resonance imaging of a lung.
Background
At present, the clinical imaging method of the lung mainly comprises the steps of electronic computer tomography (Computed Tomography, CT) and obtaining a sectional image of the examined part of the human body according to the difference of the absorption and the transmittance of the X-rays by different tissues of the human body. CT is radioactive and is particularly unsuitable for children, pregnant women and pulmonary imaging demanding persons who require longitudinal follow-up.
In contrast to CT, magnetic resonance imaging (Magnetic Resonance Imaging, MRI) techniques enable imaging without invasion and without ionizing radiation. In recent years, the development of magnetic resonance imaging technology has been fast, and the magnetic resonance imaging technology is considered as an imaging technology with great application prospect.
The magnetic resonance imaging technology for lung in the prior art mainly has the following schemes: 1. the half pulse excites the ultra-short echo sequence, namely the first half pulse uses positive slice selection gradient, and the second half pulse uses gradient with equal magnitude and opposite direction. Combining two halves of the pulse excitation to form one complete raw data, however, the disadvantage of this approach is that separate excitations may introduce artifacts caused by volume and physiological motion between the two separate excitations, low signal-to-noise ratio, low resolution, and large imaging errors. 2. The pulse-excited ultra-short echo sequence, namely the whole region is excited by the pulse, does not need to select a layer gradient, needs to use three-dimensional track acquisition, and generally uses a spoke-shaped acquisition method, and has the defect that a large number of radial projections are required to meet the Nyquist sampling theorem, so that the imaging time is greatly prolonged. 3. The use of selective radio frequency pulses and selective layer gradients to excite a portion of the object to be imaged has the disadvantage that layer encoding and in-plane encoding require a significant amount of phase encoding time, extending echo time.
Disclosure of Invention
The invention provides a magnetic resonance imaging method, a system, electronic equipment and a medium for lung, which are used for solving the problems of low signal-to-noise ratio, low resolution, long imaging time and long echo time of a magnetic resonance imaging scheme for lung in the prior art.
The invention provides a magnetic resonance imaging method for lungs, comprising:
applying a gradient magnetic field in a layer direction to a target to be imaged;
when the gradient of the gradient magnetic field starts to climb, hard pulse excitation is carried out on the target to be imaged, and frequency modulation is carried out on the hard pulse based on a preset frequency modulation range, so that a magnetic resonance signal is generated;
when the hard pulse excitation is stopped, carrying out spiral acquisition on the magnetic resonance signals to acquire original imaging data of the target to be imaged;
and reconstructing the original imaging data based on a preset reconstruction rule to obtain target imaging.
Optionally, before the step of hard pulse excitation of the object to be imaged when the gradient of the gradient magnetic field starts to climb, the method further comprises:
determining the predicted maximum echo time based on a preset hardware gradient field intensity maximum value, a hardware gradient switching rate maximum value and a hardware pulse duration time;
Determining an expected minimum echo time based on a preset radio frequency switch time and the hard pulse duration;
judging whether the predicted maximum echo time and the predicted minimum echo time accord with a preset echo time threshold range, acquiring a judging result and feeding back; and determining an echo time verification range based on the predicted maximum echo time and/or the predicted minimum echo time, wherein the echo time verification range is used for verifying the acquired actual echo time when the acquisition of the magnetic resonance signals is completed, and adjusting the hard pulse excitation related parameters and the spiral acquisition related parameters based on a verification result.
Optionally, determining the mathematical expression of the predicted maximum echo time based on the preset hardware gradient field intensity maximum value, the hardware gradient switching rate maximum value and the hard pulse duration is:
TE max ＝2×(G/Slew rate)+ΔT Hard /2
wherein TE is max Representing pre-emphasisMaximum echo time is calculated, G represents the maximum value of hardware gradient field intensity, slew rate represents the maximum value of hardware gradient switching rate, and DeltaT Hard Representing hard pulse duration;
based on a preset radio frequency switch time and the hard pulse duration, determining a mathematical expression of the predicted minimum echo time is as follows:
TE min ＝ΔT Hard /2+T s
wherein TE is min Representing the predicted minimum echo time, T s Indicating the rf switching time.
Optionally, when the gradient of the gradient magnetic field starts to climb, the step of hard pulse excitation of the object to be imaged includes:
when the gradient of the gradient magnetic field starts to climb, hard pulse excitation is started to the target to be imaged;
in the process of exciting the hard pulse, controlling the hard pulse to gradually move towards a target direction based on a preset moving step length and moving times; the target direction includes: and when the gradient of the gradient magnetic field is negative, the hard pulse is controlled to move gradually towards the second target direction.
Optionally, the step of frequency modulating the hard pulse based on a preset frequency modulation range, and further generating a magnetic resonance signal includes:
expanding the original frequency range preset by the hard pulse based on the preset frequency modulation range to obtain a target frequency range;
and carrying out hard pulse excitation on the target to be imaged based on the target frequency range, and further generating the magnetic resonance signal with the expanded excitation range.
Optionally, when the hard pulse excitation is stopped, performing spiral acquisition on the magnetic resonance signal, and the step of acquiring the original imaging data of the target to be imaged includes:
when the hard pulse excitation is stopped, performing spiral acquisition on the magnetic resonance signals according to a preset signal acquisition rule, and acquiring the magnetic resonance signals, wherein the signal acquisition rule comprises: the number of the spiral acquisition arms, the number of sampling points of the spiral acquisition arms, the spiral acquisition time, the repetition time and the spiral acquisition track;
and carrying out analog-to-digital conversion on the acquired magnetic resonance signals, acquiring magnetic resonance digital signals, and taking the magnetic resonance digital signals as the original imaging data.
Optionally, based on a preset reconstruction rule, reconstructing the original imaging data, and obtaining the target imaging includes:
based on a preset orthogonal lattice dotting rule, performing orthogonal conversion on the original imaging data to obtain orthogonal original k-space data;
reconstructing the orthogonal original k-space data based on a preset Fourier transform rule, and obtaining a reconstructed multichannel image;
and acquiring the target imaging by combining the multichannel images.
The invention also provides a magnetic resonance imaging system for the lungs, comprising:
the gradient module is used for applying a gradient magnetic field in the layer direction to the target to be imaged;
the hard pulse excitation module is used for carrying out hard pulse excitation on the target to be imaged when the gradient of the gradient magnetic field starts to climb, carrying out frequency modulation on the hard pulse based on a preset frequency modulation range and further generating a magnetic resonance signal;
the acquisition module is used for carrying out spiral acquisition on the magnetic resonance signals when the hard pulse excitation is stopped, and acquiring original imaging data of the target to be imaged;
the reconstruction module is used for reconstructing the original imaging data based on a preset reconstruction rule to acquire target imaging.
The invention also provides an electronic device comprising a memory, a processor and a computer program stored on the memory and executable on the processor, the processor implementing a magnetic resonance imaging method for the lung as described in any of the above when executing the program.
The invention also provides a non-transitory computer readable storage medium having stored thereon a computer program which, when executed by a processor, implements a magnetic resonance imaging method for the lung as described in any of the above.
The invention provides a magnetic resonance imaging method, a system and an electronic equipment medium for lung, which are characterized in that a gradient magnetic field in a layer direction is applied to an object to be imaged; when the gradient of the gradient magnetic field starts to climb, hard pulse excitation is carried out on the target to be imaged, and based on a preset frequency modulation range, the hard pulse is subjected to frequency modulation, so that a magnetic resonance signal is generated; when the hard pulse excitation is stopped, performing spiral acquisition on the magnetic resonance signals to acquire original imaging data of a target to be imaged; reconstructing original imaging data based on a preset reconstruction rule to obtain target imaging; the echo time and imaging time can be effectively shortened, and the signal-to-noise ratio and the resolution ratio are higher.
Drawings
In order to more clearly illustrate the invention or the technical solutions of the prior art, the following description will briefly explain the drawings used in the embodiments or the description of the prior art, and it is obvious that the drawings in the following description are some embodiments of the invention, and other drawings can be obtained according to the drawings without inventive effort for a person skilled in the art.
FIG. 1 is a flow chart of a magnetic resonance imaging method for a lung provided by the present invention;
FIG. 2 is a schematic flow chart of hard pulse excitation in a magnetic resonance imaging method for lung provided by the present invention;
FIG. 3 is a timing diagram of hard pulse excitation, frequency modulation, and applied gradients in a magnetic resonance imaging method for lung provided by the present invention;
FIG. 4 is a flow chart of frequency modulation in a magnetic resonance imaging method for lung provided by the present invention;
figure 5 is a schematic diagram of the principle of frequency modulation in a magnetic resonance imaging method for lung provided by the present invention;
FIG. 6 is a flow chart of acquiring raw imaging data in a magnetic resonance imaging method for lung provided by the present invention;
FIG. 7 is a flow chart of acquiring target images in a magnetic resonance imaging method for lung provided by the present invention;
FIG. 8 is a schematic diagram showing the comparison between the time of encoding the layer direction in the magnetic resonance imaging method for lung and the time of encoding the layer direction in the conventional method;
FIG. 9 is a graph comparing the RF field (magnetic field created by hard pulse excitation) with and without frequency modulation;
FIG. 10 is a graph comparing the frequency ranges of hard pulses with and without frequency modulation;
FIG. 11 is a graph of signal strength versus frequency modulation added versus frequency modulation not added;
FIG. 12 is a graph of signal-to-noise ratio for imaging healthy volunteer lungs using the magnetic resonance imaging method for lungs provided by the present invention versus signal-to-noise ratio using conventional methods;
fig. 13 is a graph of fitting results of T2 obtained by measuring a sponge phantom using the magnetic resonance imaging method for lung provided by the present invention;
figure 14 is a schematic diagram of a magnetic resonance imaging system for the lung provided by the present invention;
fig. 15 is a schematic structural diagram of an electronic device provided by the present invention.
Detailed Description
For the purpose of making the objects, technical solutions and advantages of the present invention more apparent, the technical solutions of the present invention will be clearly and completely described below with reference to the accompanying drawings, and it is apparent that the described embodiments are some embodiments of the present invention, not all embodiments. All other embodiments, which can be made by those skilled in the art based on the embodiments of the invention without making any inventive effort, are intended to be within the scope of the invention.
By way of example, the present invention provides a magnetic resonance imaging method, system, electronic device and medium for lung, as described below in connection with fig. 1-15.
Referring to fig. 1, a magnetic resonance imaging method for lung provided in this embodiment includes:
S101: a gradient magnetic field in the layer direction is applied to the object to be imaged.
Specifically, the target to be imaged refers to a target object which needs to be subjected to magnetic resonance imaging. The layer direction refers to a layer selection direction (generally referred to as a Z-axis direction or an interlayer direction), and also corresponds to an intra-layer direction (generally referred to as a X, Y direction). It will be appreciated that the slice direction (Z-axis direction) extends through each slice (which may be understood as each cross-section of the object to be imaged for imaging data encoding), each slice having corresponding encoded data in the X, Y direction. The X-direction generally refers to the frequency encoding direction and the Y-direction generally refers to the phase encoding direction. Gradient refers to the application of magnetic fields of different magnetic field strengths in the layer direction. By applying a gradient magnetic field in the layer direction to the target to be imaged, spatial positioning can be facilitated, and subsequent hard pulse excitation of the target to be imaged on the basis of the gradient magnetic field can be facilitated.
S102: when the gradient of the gradient magnetic field starts to climb, hard pulse excitation is carried out on the target to be imaged, and based on a preset frequency modulation range, frequency modulation is carried out on the hard pulse, so that a magnetic resonance signal is generated.
When the gradient of the gradient magnetic field starts to climb, the hard pulse excitation is immediately performed on the object to be imaged, and the hard pulse is subjected to frequency modulation based on a preset frequency modulation range, so that the excitation range can be enlarged to a certain extent. Typically, the shorter the duration of a radio frequency pulse, the wider the frequency range of the pulse after fourier transformation, which pulse is typically referred to as a hard pulse, and the longer the duration of a radio frequency pulse, the narrower the frequency range, i.e. the narrower the transmission bandwidth, of the pulse after fourier transformation, which pulse is typically referred to as a soft pulse. In the step, hard pulse excitation is adopted, and the duration of the hard pulse is shortest in different types of radio frequency pulses with the same amplitude in the current excitation, so that the echo time can be shortened as far as possible, the echo time refers to the interval time between the excitation pulse and the echo generation, and the excitation in a 3D range can be realized. In addition, in the step, the hard pulse is excited and simultaneously frequency-modulated based on a preset frequency modulation range, so that the excitation range can be well enlarged, and the signal-to-noise ratio can be improved. And then on the basis of frequency modulation or in combination with frequency modulation, hard pulse excitation is carried out on the target to be imaged, and a magnetic resonance signal with an expanded excitation range is generated.
S103: and when the hard pulse excitation is stopped, carrying out spiral acquisition on the magnetic resonance signals to acquire the original imaging data of the target to be imaged.
When the hard pulse excitation is stopped, the generated magnetic resonance signal is immediately subjected to spiral acquisition, so that the echo time can be shortened well. Compared with the traditional magnetic induction signal acquisition mode, such as Cartesian acquisition, the spiral acquisition is high in acquisition efficiency, and imaging time can be effectively shortened. The raw imaging data are imaging data stored in a preset raw k-space.
S104: and reconstructing the original imaging data based on a preset reconstruction rule to obtain target imaging.
Specifically, the original imaging data is reconstructed based on a preset reconstruction rule, so that target imaging with high accuracy can be obtained.
In order to minimize the echo time, in some embodiments, before the step of hard pulse excitation of the object to be imaged when the gradient of the gradient magnetic field starts to climb, further comprises:
determining the predicted maximum echo time based on a preset hardware gradient field intensity maximum value, a hardware gradient switching rate maximum value and a hardware pulse duration time; determining an expected minimum echo time based on a preset radio frequency switch time and the hard pulse duration;
Judging whether the predicted maximum echo time and the predicted minimum echo time accord with a preset echo time threshold range, acquiring a judging result and feeding back; and determining an echo time verification range based on the predicted maximum echo time and/or the predicted minimum echo time, wherein the echo time verification range is used for verifying the acquired actual echo time when the acquisition of the magnetic resonance signals is completed, and adjusting the hard pulse excitation related parameters and the spiral acquisition related parameters based on a verification result.
In particular, the hardware gradient field strength maximum value represents a maximum value of gradient field strength of a hardware device (magnetic resonance device), such as 80mT/m (millitesla/m), or the like. The hardware gradient switching rate maximum value refers to the gradient switching rate maximum value of the hardware device. The echo time threshold range may be set according to practical situations, e.g. an ultra-short echo sequence typically requires an echo time of less than 100ms (microseconds), the echo time threshold range may be set to (0, 100) microseconds, etc. The method and the device can be used for conveniently and well controlling the echo time required by the current magnetic resonance imaging process by judging whether the current predicted maximum echo time and the predicted minimum echo time are within the preset echo time threshold value range or not, acquiring a judgment result and feeding back. And by determining the echo time verification range based on the predicted maximum echo time and/or the predicted minimum echo time and utilizing the echo time verification range to verify the actual echo time acquired when the magnetic resonance information acquisition is completed subsequently, the adjustment of the hard pulse excitation related parameters and the spiral acquisition related parameters can be better realized, and the echo time is further shortened. The method for acquiring the echo time check range may be to determine an echo time check range by adding or subtracting a preset parameter value based on the predicted maximum echo time; a preset parameter value can be added or subtracted on the basis of the minimum echo time so as to determine an echo time verification range; the average value of the expected maximum echo time and the expected minimum echo time can also be taken, and a preset parameter value can be added or subtracted on the basis of the average value, so that an echo time check range and the like can be determined. The method for acquiring the echo time check range is not limited correspondingly here.
In some embodiments, the hard pulse excitation correlation parameters include: hard pulse frequency, hard pulse amplitude, hard pulse phase, hard pulse duration, hard pulse movement step length, movement times and the like; the spiral acquisition correlation parameters include: the number of spiral acquisition arms, the number of sampling points of the spiral acquisition arms, the spiral acquisition time, the repetition time, the spiral acquisition track and the like.
It should be noted that, based on the preset hardware gradient field intensity maximum value, hardware gradient switching rate maximum value and hard pulse duration, the mathematical expression of determining the predicted maximum echo time is as follows:
TE max ＝2×(G/Slew rate)+ΔT Hard /2
wherein TE is max Represents the predicted maximum echo time, G represents the hardware gradient field intensity maximum, slew rate represents the hardware gradient switching rate maximum, and DeltaT Hard Representing the hard pulse duration.
It should also be noted that, based on the preset rf switch time and the hard pulse duration, the mathematical expression of determining the predicted minimum echo time is:
TE min ＝ΔT Hard /2+T s
wherein TE is min Representing the predicted minimum echo time, T s Indicating the rf switching time. The rf switching time refers to the time required for the hard pulse to turn on or off.
Referring to fig. 2, in some embodiments, when the gradient of the gradient magnetic field starts to climb, the step of hard pulse exciting the object to be imaged includes:
S201: when the gradient of the gradient magnetic field starts to climb, hard pulse excitation is started on the object to be imaged. Namely, when the gradient of the gradient magnetic field starts to climb, a hard pulse is started, and the object to be imaged is subjected to hard pulse excitation.
S202: and in the process of exciting the hard pulse, controlling the hard pulse to gradually move towards the target direction based on a preset moving step length and the moving times. The target direction includes: and when the gradient of the gradient magnetic field is negative, the hard pulse is controlled to move gradually towards the second target direction. The first target direction and the second target direction are different arbitrary directions. In the implementation process, two opposite directions can be selected as the first target direction and the second target direction respectively, so that the coding speed of the layer direction can be accelerated to a certain extent.
It will be appreciated that the gradient may be positive or negative during application of the gradient to the object to be imaged. In the process of exciting the hard pulse, the hard pulse is controlled to gradually move towards the target direction, so that the encoding speed of the layer direction can be better accelerated, and the echo time can be shortened. For example: and when the gradient of the gradient magnetic field is a negative value, the hard pulse is controlled to gradually move to the left.
Figure 3 shows a timing diagram of hard pulse excitation, frequency modulation and (intra-slice direction, slice direction) applied gradients in a magnetic resonance imaging method for lung provided by the present invention.
Four timing curves are included in fig. 3, namely, a timing curve of a hard pulse (radio frequency pulse), a timing curve of frequency modulation, a timing curve of an intra-layer gradient, and a timing curve of a layer-direction gradient. As can be seen from fig. 3, when the gradient of the gradient magnetic field starts to climb, hard pulse excitation is performed on the object to be imaged, the rectangular box in the timing curve of the hard pulse (radio frequency pulse) represents the hard pulse, and the arrow represents the stepwise movement of the hard pulse. And when the excitation of the hard pulse is started, the frequency modulation is started to the hard pulse, so that the excitation range is enlarged, and the signal to noise ratio is improved. The time sequence curve of the gradient in the layer indicates that the corresponding gradient magnetic field is respectively applied to the direction (X/Y direction) in the layer after the gradient in the layer direction is applied or ended.
Referring to fig. 4, in some embodiments, the step of frequency modulating the hard pulse based on a preset frequency modulation range, and further generating a magnetic resonance signal includes:
s401: and expanding the original frequency range preset by the hard pulse based on the preset frequency modulation range to obtain a target frequency range. For example: and (3) increasing the upper limit of the original frequency range preset by the hard pulse and/or reducing the lower limit of the original frequency range based on the preset frequency modulation range to obtain an expanded target frequency range.
S402: and carrying out hard pulse excitation on the target to be imaged based on the target frequency range, and further generating the magnetic resonance signal with the expanded excitation range. The excitation range can be better enlarged and the signal-to-noise ratio can be improved by carrying out frequency modulation on the hard pulse.
FIG. 5 shows a schematic diagram of frequency modulation, and referring to FIG. 5, two lines in FIG. 5 respectively represent the applied gradient field strength G z,1 、G z,2 (units: millitesla per meter) and then larmor precession frequency corresponding to the spatial coordinates. Wherein the abscissa represents the Position (Position) and the ordinate represents the different larmor precession frequencies (frequencies) corresponding to the different positions. In the absence of frequency modulation, the original frequency range of the hard pulse is Δf, and the excitation ranges are ΔZ 1 、ΔZ 2 However, if we add frequency modulation, we mean that the frequency of the hard pulse becomes Δf+Δm (frequency modulation range), intuitively, the excitation range corresponding to the hard pulse is significantly enlarged.
Referring to fig. 6, in some embodiments, when the hard pulse excitation is stopped, performing helical acquisition on the magnetic resonance signal, and acquiring raw imaging data of the object to be imaged includes:
S601: when the hard pulse excitation is stopped, performing spiral acquisition on the magnetic resonance signals according to a preset signal acquisition rule, and acquiring the magnetic resonance signals, wherein the signal acquisition rule comprises: the number of the spiral acquisition arms, the number of sampling points of the spiral acquisition arms, the spiral acquisition time, the repetition time and the spiral acquisition track. By immediately performing magnetic resonance signal acquisition when the hard pulse excitation is stopped, the echo time can be shortened to some extent.
S602: and carrying out analog-to-digital conversion on the acquired magnetic resonance signals, acquiring magnetic resonance digital signals, and taking the magnetic resonance digital signals as the original imaging data. It can be understood that the acquired magnetic resonance signals are analog signals, and the step is convenient for processing the magnetic resonance digital signals by performing analog-to-digital conversion on the acquired magnetic resonance signals.
Referring to fig. 7, in some embodiments, the step of reconstructing the original imaging data based on a preset reconstruction rule to obtain the target imaging includes:
s701: and carrying out orthogonal conversion on the original imaging data based on a preset orthogonal lattice dotting rule to acquire orthogonal original k-space data.
It should be noted that, since the acquisition mode used in the present invention is non-uniform sampling, if the data acquired by non-uniform sampling is to be reconstructed, a large amount of computation is consumed, and a complex algorithm needs to be constructed. Therefore, in order to reduce the complexity and difficulty of data reconstruction, in S701, the original imaging data is subjected to orthogonal transformation based on a preset orthogonal lattice rule, so as to obtain orthogonal original k-space data, thereby facilitating subsequent data reconstruction and reducing the complexity of data reconstruction. The orthogonal lattice dotting rule can uniformly distribute original imaging data which are originally unevenly distributed to a preset k space (k space) in an interpolation sampling mode and the like, and generates orthogonal original k space data.
S702: and reconstructing the orthogonal original k-space data based on a preset Fourier transform rule, and obtaining a reconstructed multichannel image. The fourier transform rule may use an existing fourier calculation formula, etc., and will not be described herein.
S703: and acquiring the target imaging by combining the multichannel images. The target imaging has higher accuracy and higher resolution.
In order to more clearly demonstrate the differences and differences between the present invention and the conventional method, the following explains the effects of the magnetic resonance method provided by the present invention in a comparative manner.
Fig. 8 is a schematic diagram showing the comparison between the layer direction encoding time in the magnetic resonance imaging method for lung and the layer direction encoding time in the conventional method. As shown in FIG. 8, the abscissa K in FIG. 8 z ＝1/L z ，K z Is in units of m -1 M represents rice, L z The field size of the layer direction is indicated. Experiments prove that the time occupied by the layer direction code in the magnetic resonance imaging method provided by the invention is far lower than that occupied by the layer direction code in the traditional method.
Fig. 9 shows a schematic diagram of a comparison of a conventional radio frequency field (magnetic field formed by hard pulse excitation) with and without frequency modulation. As can be seen from fig. 9, the added frequency modulation is the same as the magnitude of the conventional rf field (induced magnetic field generated after adding the hard/rf pulse) without the added rf modulation. On this basis, fig. 10 shows a frequency range comparison diagram of a hard pulse with frequency modulation added to a conventional one without frequency modulation added. As shown in fig. 10, the frequency modulation range after adding frequency modulation is far greater than that of the conventional hard pulse without adding frequency modulation. Further, fig. 11 shows a signal strength comparison diagram of the added frequency modulation versus the conventional non-added frequency modulation. Referring to fig. 11, the signal strength of the field of view in different layer directions after adding frequency modulation is significantly higher than that of the conventional signal without adding frequency modulation. In summary, the addition of frequency modulation can expand the excitation or excitation range of hard pulses, thereby facilitating the realization of more comprehensive acquisition of magnetic resonance signals and improving the signal-to-noise ratio.
Fig. 12 shows a graph of signal-to-noise ratio for lung imaging tests of healthy volunteers using the magnetic resonance imaging method for lung provided by the present invention versus the signal-to-noise ratio using conventional methods. Referring to fig. 12, experiments prove that the signal-to-noise ratio of the magnetic resonance imaging method provided by the invention is obviously higher than that of the conventional method. The three images in fig. 12 correspond to different levels of the same subject, respectively. The abscissa represents the spatial profile (per pixel) and the ordinate represents the signal intensity at the corresponding location.
In order to verify that the magnetic resonance imaging method for lung provided by the present invention can realize magnetic resonance imaging with short transverse relaxation time, the test is performed on T2 x (transverse relaxation time) of the sponge die body in this embodiment, and an experimental data example is shown in fig. 13. In fig. 13, the transverse relaxation time T2 of the magnetic resonance imaging method provided by the present invention is 2.209 ms by performing statistics of echo time and signal-to-noise ratio (a.u.), which illustrates that the magnetic resonance imaging method provided by the present invention can implement magnetic resonance imaging with short transverse relaxation time.
The practical experimental/practical procedure of the magnetic resonance imaging method for lung according to the invention will be further described by way of specific examples.
Embodiment one:
in order to prove that the magnetic resonance imaging method for lung provided by the invention can realize magnetic resonance imaging with short transverse relaxation time and verify the gap between the image signal-to-noise ratio of the method and the traditional magnetic resonance imaging method. In this embodiment, the lung of a healthy volunteer is taken as a target to be imaged, and the magnetic resonance imaging method for lung and the traditional magnetic resonance imaging method provided by the invention are used for respectively performing magnetic resonance imaging on the lung of the healthy volunteer, and experimental results show that the image signal-to-noise ratio of the magnetic resonance imaging method provided by the invention is obviously higher than that of the traditional magnetic resonance imaging method, and the signal-to-noise ratio comparison chart can refer to fig. 12. In the implementation process, related parameters can be set according to practical situations, such as echo time TE is set to 0.07 ms, repetition time TR is set to 65 ms, flip angle is set to 10 degrees, and FOV (field of view, referring to single plane imaging range) is set to 180×180mm 2 The imaging resolution was set to 1.2X1.2X17 mm 3 The number of spiral acquisition arms is set to 64 arms, the number of spiral acquisition readout points is set to 3500, etc., and the details are not repeated here. The magnetic resonance imaging method for the lung provided by the invention in the embodiment is consistent with the parameters used by the traditional method.
Embodiment two:
in order to prove that the magnetic resonance imaging method for lung provided by the invention can realize magnetic resonance imaging with short transverse relaxation time and verify the gap between the image signal-to-noise ratio of the method and the traditional magnetic resonance imaging method. In the embodiment, the sponge die body is used as a target to be imaged, and the magnetic resonance imaging method for the lung and the traditional magnetic resonance imaging method provided by the invention are used for respectively carrying out magnetic resonance imaging on the sponge die body. Referring to fig. 13, experimental results show that the method provided by the invention can realize magnetic resonance imaging with short transverse relaxation time. In the implementation process, the related parameters may be set according to actual situations, please refer to the description of the related parameter setting in the first embodiment, which is not repeated here. The magnetic resonance imaging method for the lung provided by the invention in the embodiment is consistent with the parameters used by the traditional method.
By way of example, the magnetic resonance imaging system for lung provided by the present invention is described below, and the magnetic resonance imaging system for lung described below and the magnetic resonance imaging method for lung described above can be referred to correspondingly with each other.
Referring to fig. 14, a magnetic resonance imaging system for lung provided in this embodiment includes:
gradient module 1401 is configured to apply a gradient magnetic field in a slice direction to an object to be imaged.
The hard pulse excitation module 1402 is configured to perform hard pulse excitation on the object to be imaged when the gradient of the gradient magnetic field starts to climb, and perform frequency modulation on the hard pulse based on a preset frequency modulation range, so as to generate a magnetic resonance signal.
The acquisition module 1403 is configured to perform helical acquisition on the magnetic resonance signal when the hard pulse excitation is stopped, so as to acquire original imaging data of the target to be imaged.
A reconstruction module 1404, configured to reconstruct the raw imaging data based on a preset reconstruction rule, and obtain a target image. The gradient module 1401, the hard pulse excitation module 1402, the acquisition module 1403 and the reconstruction module 1404 are connected. The magnetic resonance imaging system provided by the embodiment can effectively shorten echo time and imaging time, and has higher signal-to-noise ratio and higher resolution.
In some embodiments, the step of hard pulse excitation of the object to be imaged further comprises, when the gradient of the gradient magnetic field starts to climb:
And determining the predicted maximum echo time based on the preset hardware gradient field intensity maximum value, the hardware gradient switching rate maximum value and the hard pulse duration.
And determining the expected minimum echo time based on the preset radio frequency switch time and the hard pulse duration.
Judging whether the predicted maximum echo time and the predicted minimum echo time accord with a preset echo time threshold range, acquiring a judging result and feeding back; and determining an echo time verification range based on the predicted maximum echo time and/or the predicted minimum echo time, wherein the echo time verification range is used for verifying the acquired actual echo time when the acquisition of the magnetic resonance signals is completed, and adjusting the hard pulse excitation related parameters and the spiral acquisition related parameters based on a verification result.
In some embodiments, the mathematical expression of determining the predicted maximum echo time based on the preset hardware gradient field strength maximum, hardware gradient switching rate maximum, and hard pulse duration is:
TE max ＝2×(G/Slew rate)+ΔT Hard /2
wherein TE is max Represents the predicted maximum echo time, G represents the hardware gradient field intensity maximum, slew rate represents the hardware gradient switching rate maximum, and DeltaT Hard Representing the hard pulse duration.
Based on a preset radio frequency switch time and the hard pulse duration, determining a mathematical expression of the predicted minimum echo time is as follows:
TE min ＝ΔT Hard /2+T s
wherein TE is min Representing the predicted minimum echo time, T s Indicating the rf switching time.
In some embodiments, the step of hard pulse excitation module 1402, when the gradient of the gradient magnetic field starts to climb, hard pulse exciting the object to be imaged comprises:
when the gradient of the gradient magnetic field starts to climb, hard pulse excitation is started on the object to be imaged.
In the process of exciting the hard pulse, controlling the hard pulse to gradually move towards a target direction based on a preset moving step length and moving times; the target direction includes: and when the gradient of the gradient magnetic field is negative, the hard pulse is controlled to move gradually towards the second target direction.
In some embodiments, the hard pulse excitation module 1402 frequency modulates the hard pulses based on a preset frequency modulation range, and further generates magnetic resonance signals comprising:
and expanding the original frequency range preset by the hard pulse based on the preset frequency modulation range to obtain a target frequency range.
And carrying out hard pulse excitation on the target to be imaged based on the target frequency range, and further generating the magnetic resonance signal with the expanded excitation range.
In some embodiments, the step of acquiring the raw imaging data of the object to be imaged by the acquisition module 1403 when the hard pulse excitation is stopped includes:
when the hard pulse excitation is stopped, performing spiral acquisition on the magnetic resonance signals according to a preset signal acquisition rule, and acquiring the magnetic resonance signals, wherein the signal acquisition rule comprises: the number of the spiral acquisition arms, the number of sampling points of the spiral acquisition arms, the spiral acquisition time, the repetition time and the spiral acquisition track;
and carrying out analog-to-digital conversion on the acquired magnetic resonance signals, acquiring magnetic resonance digital signals, and taking the magnetic resonance digital signals as the original imaging data.
In some embodiments, the reconstructing module 1404 reconstructs the raw imaging data based on a preset reconstruction rule, and the step of obtaining the target image includes:
and carrying out orthogonal conversion on the original imaging data based on a preset orthogonal lattice dotting rule to acquire orthogonal original k-space data.
And reconstructing the orthogonal original k-space data based on a preset Fourier transform rule, and obtaining a reconstructed multichannel image.
And acquiring the target imaging by combining the multichannel images.
Fig. 15 illustrates a physical structure diagram of an electronic device, as shown in fig. 15, which may include: a processor 1510, a communication interface (Communications Interface) 1520, a memory 1530, and a communication bus 1540, wherein the processor 1510, the communication interface 1520, and the memory 1530 communicate with each other via the communication bus 1540. Processor 1510 may invoke logic instructions in memory 1530 to perform a magnetic induction imaging method for a lung, the method comprising: applying a gradient magnetic field in a layer direction to a target to be imaged; when the gradient of the gradient magnetic field starts to climb, hard pulse excitation is carried out on the target to be imaged, and frequency modulation is carried out on the hard pulse based on a preset frequency modulation range, so that a magnetic resonance signal is generated; when the hard pulse excitation is stopped, carrying out spiral acquisition on the magnetic resonance signals to acquire original imaging data of the target to be imaged; and reconstructing the original imaging data based on a preset reconstruction rule to obtain target imaging.
Further, the logic instructions in the memory 1530 described above may be implemented in the form of software functional units and may be stored on a computer readable storage medium when sold or used as a stand alone product. Based on this understanding, the technical solution of the present invention may be embodied essentially or in a part contributing to the prior art or in a part of the technical solution, in the form of a software product stored in a storage medium, comprising several instructions for causing a computer device (which may be a personal computer, a server, a network device, etc.) to perform all or part of the steps of the method according to the embodiments of the present invention. And the aforementioned storage medium includes: a U-disk, a removable hard disk, a Read-Only Memory (ROM), a random access Memory (RAM, random Access Memory), a magnetic disk, or an optical disk, or other various media capable of storing program codes.
In another aspect, the present invention also provides a computer program product comprising a computer program storable on a non-transitory computer readable storage medium, the computer program, when executed by a processor, being capable of performing the magnetic induction imaging method for the lung provided by the methods described above, the method comprising: applying a gradient magnetic field in a layer direction to a target to be imaged; when the gradient of the gradient magnetic field starts to climb, hard pulse excitation is carried out on the target to be imaged, and frequency modulation is carried out on the hard pulse based on a preset frequency modulation range, so that a magnetic resonance signal is generated; when the hard pulse excitation is stopped, carrying out spiral acquisition on the magnetic resonance signals to acquire original imaging data of the target to be imaged; and reconstructing the original imaging data based on a preset reconstruction rule to obtain target imaging.
In yet another aspect, the present invention also provides a non-transitory computer readable storage medium having stored thereon a computer program which, when executed by a processor, is implemented to perform a magnetic induction imaging method for lungs provided by the methods described above, the method comprising: applying a gradient magnetic field in a layer direction to a target to be imaged; when the gradient of the gradient magnetic field starts to climb, hard pulse excitation is carried out on the target to be imaged, and frequency modulation is carried out on the hard pulse based on a preset frequency modulation range, so that a magnetic resonance signal is generated; when the hard pulse excitation is stopped, carrying out spiral acquisition on the magnetic resonance signals to acquire original imaging data of the target to be imaged; and reconstructing the original imaging data based on a preset reconstruction rule to obtain target imaging.
The apparatus embodiments described above are merely illustrative, wherein the elements illustrated as separate elements may or may not be physically separate, and the elements shown as elements may or may not be physical elements, may be located in one place, or may be distributed over a plurality of network elements. Some or all of the modules may be selected according to actual needs to achieve the purpose of the solution of this embodiment. Those of ordinary skill in the art will understand and implement the present invention without undue burden.
From the above description of the embodiments, it will be apparent to those skilled in the art that the embodiments may be implemented by means of software plus necessary general hardware platforms, or of course may be implemented by means of hardware. Based on this understanding, the foregoing technical solution may be embodied essentially or in a part contributing to the prior art in the form of a software product, which may be stored in a computer readable storage medium, such as ROM/RAM, a magnetic disk, an optical disk, etc., including several instructions for causing a computer device (which may be a personal computer, a server, or a network device, etc.) to execute the method described in the respective embodiments or some parts of the embodiments.
Finally, it should be noted that: the above embodiments are only for illustrating the technical solution of the present invention, and are not limiting; although the invention has been described in detail with reference to the foregoing embodiments, it will be understood by those of ordinary skill in the art that: the technical scheme described in the foregoing embodiments can be modified or some technical features thereof can be replaced by equivalents; such modifications and substitutions do not depart from the spirit and scope of the technical solutions of the embodiments of the present invention.
Claims (10)
1. A method for magnetic resonance imaging of the lungs, comprising:
applying a gradient magnetic field in a layer direction to a target to be imaged;
when the gradient of the gradient magnetic field starts to climb, hard pulse excitation is carried out on the target to be imaged, and frequency modulation is carried out on the hard pulse based on a preset frequency modulation range, so that a magnetic resonance signal is generated;
when the hard pulse excitation is stopped, carrying out spiral acquisition on the magnetic resonance signals to acquire original imaging data of the target to be imaged;
and reconstructing the original imaging data based on a preset reconstruction rule to obtain target imaging.
2. The method for magnetic resonance imaging of the lung according to claim 1, characterized in that before the step of hard pulse excitation of the object to be imaged when the gradient of the gradient magnetic field starts to climb, further comprising:
determining the predicted maximum echo time based on a preset hardware gradient field intensity maximum value, a hardware gradient switching rate maximum value and a hardware pulse duration time;
determining an expected minimum echo time based on a preset radio frequency switch time and the hard pulse duration;
judging whether the predicted maximum echo time and the predicted minimum echo time accord with a preset echo time threshold range, acquiring a judging result and feeding back; and determining an echo time verification range based on the predicted maximum echo time and/or the predicted minimum echo time, wherein the echo time verification range is used for verifying the acquired actual echo time when the acquisition of the magnetic resonance signals is completed, and adjusting the hard pulse excitation related parameters and the spiral acquisition related parameters based on a verification result.
3. The method for magnetic resonance imaging of the lung according to claim 2, characterized in that the mathematical expression of the predicted maximum echo time is determined based on a preset hardware gradient field strength maximum, hardware gradient switching rate maximum and hard pulse duration as:
TE max ＝2×(G/Slew rate)+ΔT Hard /2
wherein TE is max Represents the predicted maximum echo time, G represents the hardware gradient field intensity maximum, slew rate represents the hardware gradient switching rate maximum, and DeltaT Hard Representing hard pulse duration;
based on a preset radio frequency switch time and the hard pulse duration, determining a mathematical expression of the predicted minimum echo time is as follows:
TE min ＝ΔT Hard /2+T s
wherein TE is min Representing the predicted minimum echo time, T s Indicating the rf switching time.
4. The method for magnetic resonance imaging of the lung according to claim 1, characterized in that the step of hard pulse excitation of the object to be imaged when the gradient of the gradient magnetic field starts to climb comprises:
when the gradient of the gradient magnetic field starts to climb, hard pulse excitation is started to the target to be imaged;
in the process of exciting the hard pulse, controlling the hard pulse to gradually move towards a target direction based on a preset moving step length and moving times; the target direction includes: and when the gradient of the gradient magnetic field is negative, the hard pulse is controlled to move gradually towards the second target direction.
5. The method of claim 1, wherein the step of frequency modulating the hard pulses based on a preset frequency modulation range to generate magnetic resonance signals comprises:
expanding the original frequency range preset by the hard pulse based on the preset frequency modulation range to obtain a target frequency range;
and carrying out hard pulse excitation on the target to be imaged based on the target frequency range, and further generating the magnetic resonance signal with the expanded excitation range.
6. The method of magnetic resonance imaging of the lung according to claim 1, characterized in that the step of acquiring raw imaging data of the object to be imaged by helical acquisition of the magnetic resonance signals when the hard pulse excitation is stopped comprises:
when the hard pulse excitation is stopped, performing spiral acquisition on the magnetic resonance signals according to a preset signal acquisition rule, and acquiring the magnetic resonance signals, wherein the signal acquisition rule comprises: the number of the spiral acquisition arms, the number of sampling points of the spiral acquisition arms, the spiral acquisition time, the repetition time and the spiral acquisition track;
and carrying out analog-to-digital conversion on the acquired magnetic resonance signals, acquiring magnetic resonance digital signals, and taking the magnetic resonance digital signals as the original imaging data.
7. The method for magnetic resonance imaging of the lung according to claim 1, wherein reconstructing the raw imaging data based on preset reconstruction rules, the step of obtaining a target image comprises:
based on a preset orthogonal lattice dotting rule, performing orthogonal conversion on the original imaging data to obtain orthogonal original k-space data;
reconstructing the orthogonal original k-space data based on a preset Fourier transform rule, and obtaining a reconstructed multichannel image;
and acquiring the target imaging by combining the multichannel images.
8. A magnetic resonance imaging system for the lungs, comprising:
the gradient module is used for applying a gradient magnetic field in the layer direction to the target to be imaged;
the hard pulse excitation module is used for carrying out hard pulse excitation on the target to be imaged when the gradient of the gradient magnetic field starts to climb, carrying out frequency modulation on the hard pulse based on a preset frequency modulation range and further generating a magnetic resonance signal;
the acquisition module is used for carrying out spiral acquisition on the magnetic resonance signals when the hard pulse excitation is stopped, and acquiring original imaging data of the target to be imaged;
The reconstruction module is used for reconstructing the original imaging data based on a preset reconstruction rule to acquire target imaging.
9. An electronic device comprising a memory, a processor and a computer program stored on the memory and executable on the processor, wherein the processor implements the magnetic resonance imaging method for lungs according to any one of claims 1 to 7 when the program is executed.
10. A non-transitory computer readable storage medium having stored thereon a computer program, which when executed by a processor implements a magnetic resonance imaging method for lungs according to any one of claims 1 to 7.
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| CN117547246B (en) * | 2024-01-12 | 2024-04-09 | 中国科学技术大学先进技术研究院 | Spatial signal saturation method, apparatus, device and computer readable storage medium |
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