CN111317474B - Tissue displacement detection method, system, computing device and storage medium - Google Patents
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Abstract
The invention is applicable to the technical field of computers and provides a tissue displacement detection method, a system, a computing device and a storage medium, wherein the method comprises the following steps: after a first echo signal phase diagram and a second echo signal phase diagram obtained by MR-ARFI are sequentially obtained in a first TR and a second TR, the displacement variation in the tissue is calculated according to the difference value of the first echo signal phase diagram and the second echo signal phase diagram, wherein in the imaging process, radio frequency pulses, gradient fields and focused ultrasonic pulses are applied, a first gradient for out-of-phase and displacement coding is applied to one gradient direction of the gradient fields, and the application of the first gradient and the application of the focused ultrasonic pulses are synchronous in the first TR. Therefore, the first gradient not only can realize the function of refocusing the gradient, but also can realize the function of displacement encoding gradient at the same time, and the moment of the first gradient can be adjusted according to the requirement, so that the setting and calculation processing are simplified.
Description
Technical Field
The invention belongs to the technical field of computers, and particularly relates to a tissue displacement detection method, a system, a computing device and a storage medium.
Background
Magnetic resonance-acoustic radiation force imaging (Magnetic Resonance Acoustic Radiation Force Imaging, MR-ARFI) techniques exploit the motion-sensitive nature of magnetic resonance to encode micrometer-sized displacements generated in tissue during the action of high-intensity focused ultrasound (High Intensity Focused Ultrasound, HIFU) into a magnetic resonance phase map.
As shown in fig. 1, based on MR-ARFI detection of a conventional Gradient-Echo (GRE) sequence, a refocusing Gradient B is set before a readout Gradient a in the readout (Read Out, RO) direction of the conventional GRE sequence, the moment of the refocusing Gradient B is a non-adjustable, smaller fixed value (generally 1/2 of the moment of the readout Gradient a), and when displacement encoding is required, an additional displacement encoding Gradient needs to be added, which makes the setting and calculation processes more complicated.
Other relevant parameters referred to in fig. 1 are listed below (similar to the definition of parameters in other parts of the text below): radio Frequency (RF) pulse, repetition Time (TR) of RF pulse, flip angle alpha of RF pulse, slice Selection (SS) direction, phase Encoding (PE) direction, echo Time (TE), magnitude of displacement encoding gradient G e Time τ of the displacement encoding gradient.
Disclosure of Invention
The invention aims to provide a tissue displacement detection method, a system, a computing device and a storage medium based on echo displacement, which aim to solve the problem of complicated setting and computing processes caused by the fact that a displacement encoding gradient is additionally added for displacement encoding in the prior art.
In one aspect, the present invention provides a method for detecting tissue displacement based on echo displacement, the method comprising:
sequentially obtaining a first echo signal phase diagram and a second echo signal phase diagram which are obtained by magnetic resonance-acoustic radiation force imaging (MR-ARFI) in a first continuous repetition period (TR) and a second TR, wherein in the MR-ARFI process, a radio frequency pulse, a gradient field and a focused ultrasonic pulse are applied, a first gradient for out-of-phase and displacement coding is applied to one gradient direction of the gradient field, and the application of the first gradient is synchronous with the application of the focused ultrasonic pulse in the first TR;
and calculating to obtain the displacement variation in the tissue according to the difference value of the first echo signal phase diagram and the second echo signal phase diagram.
Further, the method further comprises:
and calculating to obtain the temperature change quantity in the tissue according to the first echo signal phase diagram.
Further, a second gradient and a third gradient, which are adjacent to the first gradient in the period time sequence, are applied in the gradient direction, the second gradient has a basic function corresponding to the gradient direction, and the third gradient is a refocusing gradient.
Further, the gradient direction is a readout direction, and the second gradient is a readout gradient; in the cycle sequence, the third gradient, the second gradient and the first gradient are arranged in sequence and are located in the same TR.
Further, the gradient direction is a layer selection direction, and the second gradient is a layer selection gradient; in the cycle timing, the first gradient is located within the first TR, the second gradient is located partially within the first TR, partially within the second TR, and the third gradient is located within the second TR.
Further, the correspondence between the moment of the first gradient and the moment of the second gradient and the moment of the third gradient is:
C＝(n+1)×Q-A/2，B＝-n×Q-A/2，Q＝A+B+C，
wherein A is the moment of the second gradient, B is the moment of the first gradient, C is the moment of the third gradient, n is a natural number greater than or equal to 1, and Q is an adjustable arbitrary value.
Further, the method is combined with a planar echo imaging EPI or a segmented planar echo imaging peepi.
In another aspect, the present invention provides an echo displacement based tissue displacement detection system, the system comprising:
the acquisition unit is used for sequentially acquiring a first echo signal phase diagram and a second echo signal phase diagram which are obtained by magnetic resonance-acoustic radiation force imaging (MR-ARFI) in a first continuous repetition period (TR) and a second TR, wherein in the MR-ARFI process, a radio frequency pulse, a gradient field and a focused ultrasonic pulse are applied, a first gradient for out-of-phase and displacement coding is applied to one gradient direction of the gradient field, and the application of the first gradient is synchronous with the application of the focused ultrasonic pulse in the first TR; the method comprises the steps of,
and the calculating unit is used for calculating the displacement variation in the tissue according to the difference value of the first echo signal phase diagram and the second echo signal phase diagram.
In another aspect, the present invention also provides a computing device, including a memory and a processor, where the processor implements the steps of the method described above when executing a computer program stored in the memory.
In another aspect, the invention also provides a computer readable storage medium storing a computer program which when executed by a processor implements the steps of the method as described above.
According to the invention, after a first echo signal phase diagram and a second echo signal phase diagram obtained by MR-ARFI are sequentially obtained in a first TR and a second TR, the displacement variation in tissues is calculated according to the difference value of the first echo signal phase diagram and the second echo signal phase diagram, wherein radio frequency pulse, gradient field and focused ultrasonic pulse are applied in the imaging process, a first gradient for out-of-phase and displacement coding is applied in one gradient direction of the gradient field, and the application of the first gradient is synchronous with the application of the focused ultrasonic pulse in the first TR. Therefore, the first gradient not only can realize the function of refocusing the gradient, but also can realize the function of displacement encoding gradient at the same time, and the moment of the first gradient can be adjusted according to the requirement, so that the setting and calculation processing are simplified. In addition, since the echo displacement detection sequence itself is sensitive to temperature changes, synchronous detection of displacement and temperature can be achieved by adding focused ultrasound pulses synchronized with the first gradient.
Drawings
FIG. 1 is a timing diagram of a prior art provided MR-ARFI detection based on a conventional GRE sequence;
FIG. 2 is a flow chart of a tissue displacement detection method based on echo displacement according to an embodiment of the present invention;
FIG. 3 is a timing diagram of an MR-ARFI based on an ES sequence in accordance with a third embodiment of the present invention;
FIG. 4 is a timing diagram of an MR-ARFI based on an ES sequence in accordance with a fourth embodiment of the present invention;
FIG. 5 is a schematic diagram of a tissue displacement detection system based on echo displacement according to a seventh embodiment of the present invention;
FIG. 6 is a schematic diagram of a computing device according to an eighth embodiment of the present invention.
Detailed Description
The present invention will be described in further detail with reference to the drawings and examples, in order to make the objects, technical solutions and advantages of the present invention more apparent. It should be understood that the specific embodiments described herein are for purposes of illustration only and are not intended to limit the scope of the invention.
The following describes in detail the implementation of the present invention in connection with specific embodiments:
embodiment one:
fig. 2 shows a flow chart of an implementation of an Echo-shifted (ES) -based tissue displacement detection method according to an embodiment of the present invention, and for convenience of explanation, only the relevant parts of the embodiment of the present invention are shown, which is described in detail below:
in step S201, a first echo signal phase diagram and a second echo signal phase diagram obtained by MR-ARFI imaging are sequentially obtained in a first and a second consecutive repetition period TR, during the MR-ARFI process, a radio frequency pulse α °, a gradient field and a focused ultrasound pulse are applied, a first gradient for out-of-phase and displacement encoding is applied to one gradient direction of the gradient field, and the application of the first gradient is synchronized with the application of the focused ultrasound pulse in the first TR. The displacement variation caused by the encoding of the first gradient is not reflected in the first echo signal phase map but in the second echo signal phase map.
In this embodiment, the MR-ARFI process is approximately: when an external magnetic field is applied, the protons in the tissue to be tested are excited by adopting RF pulses with specific frequency, the protons absorb certain energy to generate resonance, after the transmission of the RF pulses is stopped, the excited protons release the absorbed energy gradually in the form of scanning signals, the scanning signals are collected, the collected scanning signals are processed by adopting an image reconstruction technology, and then a scanning image of the tissue to be tested can be obtained, wherein the scanning image can comprise a corresponding phase diagram. The basic unit of signal processing is a voxel, one voxel may comprise one or more protons, and the object to be processed is the acquired scanning signal for the voxel at the time of image reconstruction. Generally, the external magnetic fields include a main magnetic field and gradient fields including an SS direction, a PE direction, and an RO direction. The focused ultrasound pulse is typically a HIFU pulse.
In the MR-ARFI process, a first gradient having both a refocusing gradient function and a displacement encoding gradient function may be applied in one of gradient directions of a gradient field, which gradient direction may be an SS direction, or an RO direction, or a PE direction, or the like. In order to achieve this first gradient with displacement encoding functionality, the application of HIFU pulses needs to be performed within the first TR in synchronization with the application of the first gradient.
In step S202, the displacement variation in the tissue is calculated according to the difference between the first echo signal phase diagram and the second echo signal phase diagram.
In this embodiment, the reference phase may be acquired prior to tissue displacement monitoring using HIFU pulses. And then can utilize the second echo signal phase diagram
First echo signal phase diagram->
The magnetic rotation ratio gamma, the magnetic moment C of the first gradient, and the like, and calculates the displacement variation delta x in the tissue, wherein the moment C of the first gradient can be calculated by the magnitude G of the first gradient e Product G with time τ e τ may be specifically:
of course, in other embodiments, the intra-tissue displacement variation Δx may be calculated in other ways.
By implementing the embodiment, the first gradient in the first TR not only can realize the function of losing phase (namely, the function of dephasing gradient), but also can simultaneously realize the function of displacement encoding gradient, and the moment of the first gradient can be adjusted according to the requirement, so that the setting and calculating processes are simplified.
Embodiment two:
the present embodiment further provides, based on the first embodiment, the following:
and a second gradient and a third gradient which are adjacent to the first gradient in the period time sequence are applied in the gradient direction applied with the first gradient, the second gradient has a basic function corresponding to the gradient direction, the third gradient is a refocusing gradient, the moment of the first gradient is related to the moment of the second gradient and the moment of the third gradient, and the moment of the second gradient is determined by an imaging protocol.
In this embodiment, since the first gradient with the phase losing function and the third gradient with the phase refocusing function are applied in a gradient direction (may be the RO direction, the SS direction or the PE direction), the echo signal is not collected in the current TR but is collected in the subsequent TR, so that the Effective echo time (Effective TE), that is, the time from the actual RF pulse excitation to the echo generation is greater than TR under a certain condition, the total duration of the scanning process is shorter, which is favorable for rapid imaging, the time resolution of monitoring is improved, and the real-time performance of monitoring is ensured.
Embodiment III:
the present embodiment further provides the following on the basis of the second embodiment:
the gradient direction applied with the first gradient is the RO direction, and the second gradient is the readout gradient; in the periodic sequence, the third gradient, the second gradient and the first gradient are arranged in sequence and are positioned in the same TR.
Referring to fig. 3, a, B, C represent moments of the second, third and first gradients, respectively, and the correspondence of A, B, C is:
C＝(n+1)×Q-A/2，B＝-n×Q-A/2，Q＝A+B+C，
where n is a natural number greater than or equal to 1 (in the example of fig. 3, n is 1), then the echo signal can be generated in the n+1th TR time, Q is an effective dephasing gradient in TR, Q is an adjustable arbitrary value, and q=a+b+c, when used for displacement detection, Q can be adjusted according to the displacement size required to be detected, a is known and is mainly determined by the acquisition bandwidth and the image resolution in the acquisition protocol, and b= -Q-a/2, and c=2q-a/2.
In other examples, n may be any value greater than or equal to 1 to achieve echo shift, but is generally controlled so that n is not too large during actual detection to avoid too weak a detected signal and too low a signal-to-noise ratio.
In the example shown in fig. 3, the intra-tissue displacement variation Δx can be further calculated as:
in this embodiment, since the first gradient with the phase losing function and the third gradient with the phase refocusing function are applied in the RO direction, the echo signal is not acquired in the current TR but acquired in the next TR, so that the Effective echo time (Effective TE), that is, the time from the actual RF pulse excitation to the echo generation is greater than TR under a certain condition, the total duration of the scanning process is shorter, which is favorable for rapid imaging, the time resolution of monitoring is improved, and the real-time performance of monitoring is ensured.
Embodiment four:
the present embodiment further provides the following on the basis of the second embodiment:
the gradient direction applied with the first gradient is the SS direction, and the second gradient is the layer selection gradient; in the periodic sequence, a first gradient (i.e., a dephasing gradient with a displacement encoding function) is located within a first TR, a second gradient is located partially within the first TR, a third gradient (i.e., a refocusing gradient) is located within the second TR.
Referring to fig. 4, as well, A, B, C represents the second gradient, the third gradient and the moment of the second gradient, respectively, and the corresponding relationship of A, B, C is similar to that described in the third embodiment, and the other matters are similar to those described in the third embodiment, and will not be repeated here.
Fifth embodiment:
the present embodiment further provides the following on the basis of the above embodiments:
and calculating to obtain the temperature change quantity in the tissue according to the first echo signal phase diagram.
In this embodiment, since the TR time is short and the duty cycle of the HIFU pulse is high, the phase may be affected by temperature change during this process, and then the reference phase may be acquired before the tissue temperature and displacement are monitored by using the HIFU pulse. Then the first echo signal phase diagram can be utilized
Reference phase->
Magnetic rotation ratio gamma, main magnetic field intensity B 0 Effective echo time TE effect Calculating tissue temperature change amount delta T, wherein the effective echo time TE effect Available from TR and TE, specifically:
example six:
the timing diagrams shown in the above embodiments, i.e. fig. 3 and 4, mainly read signals in a conventional readout manner, and the sequences can also be combined with plane echo imaging (Echo Plane Imaging, EPI) or segmented plane echo imaging (Segmented Echo Plane Imaging, peepi), so that the acting time of HIFU pulses can be effectively shortened, and the time resolution of detection can be effectively improved.
Embodiment seven:
fig. 5 shows the structure of the tissue displacement detection system based on echo displacement according to the seventh embodiment of the present invention, and for convenience of explanation, only the parts related to the embodiment of the present invention are shown, including:
an obtaining unit 501, configured to sequentially obtain a first echo signal phase map and a second echo signal phase map obtained by MR-ARFI (magnetic resonance-acoustic radiation force) imaging in a first repetition period TR and a second repetition period TR, apply a radio frequency pulse, a gradient field, and a focused ultrasound pulse in the MR-ARFI process, apply a first gradient for out-of-phase and displacement encoding in a gradient direction of the gradient field, and synchronize application of the first gradient and application of the focused ultrasound pulse in the first TR; the method comprises the steps of,
the calculating unit 502 is configured to calculate an intra-tissue displacement variation according to a difference between the first echo signal phase map and the second echo signal phase map.
In the embodiment of the present invention, each unit of the tissue displacement detection system may be implemented by a corresponding hardware or software unit, and each unit may be an independent software or hardware unit, or may be integrated into one software or hardware unit, which is not used to limit the present invention.
Example eight:
fig. 6 shows the structure of a computing device provided by the eighth embodiment of the present invention, and only a portion relevant to the embodiment of the present invention is shown for convenience of explanation.
The computing device according to the embodiment of the present invention includes a processor 601 and a memory 602, and the processor 601 implements the steps of the above-described respective method embodiments when executing the computer program 603 stored in the memory 602, for example, steps S201 to S202 shown in fig. 2. Alternatively, the processor 601 when executing the computer program 603 implements the functions of the units in the above-described system embodiment, for example, the functions of the units 501 to 502 shown in fig. 5.
The steps of the method implemented by the processor 601 when executing the computer program 603 in the computing device may refer to the description of the foregoing method embodiments, which are not repeated herein.
Example nine:
in an embodiment of the present invention, there is provided a computer-readable storage medium storing a computer program which, when executed by a processor, implements the steps in the above-described method embodiments, for example, steps S201 to S202 shown in fig. 2. Alternatively, the computer program, when executed by a processor, performs the functions of the units in the above-described system embodiment, for example, the functions of the units 501 to 502 shown in fig. 5.
The computer readable storage medium of embodiments of the present invention may include any entity or device capable of carrying computer program code, recording medium, such as ROM/RAM, magnetic disk, optical disk, flash memory, and so on.
The foregoing description of the preferred embodiments of the invention is not intended to be limiting, but rather is intended to cover all modifications, equivalents, and alternatives falling within the spirit and principles of the invention.
Claims (9)
1. A method for detecting tissue displacement based on echo displacement, the method comprising:
sequentially obtaining a first echo signal phase diagram and a second echo signal phase diagram which are obtained by magnetic resonance-acoustic radiation force imaging (MR-ARFI) in a first continuous repetition period (TR) and a second TR, wherein in the MR-ARFI process, a radio frequency pulse, a gradient field and a focused ultrasonic pulse are applied, a first gradient for out-of-phase and displacement coding is applied to one gradient direction of the gradient field, and the application of the first gradient is synchronous with the application of the focused ultrasonic pulse in the first TR;
calculating to obtain displacement variation in the tissue according to the difference value of the first echo signal phase diagram and the second echo signal phase diagram;
a second gradient and a third gradient which are adjacent to the first gradient in the period time sequence are applied to the gradient direction, the second gradient has a basic function corresponding to the gradient direction, and the third gradient is a refocusing gradient;
the correspondence between the moment of the first gradient and the moment of the second gradient and the moment of the third gradient is:
C＝(n+1)×Q-A/2，B＝-n×Q-A/2，Q＝A+B+C，
wherein A is the moment of the second gradient, B is the moment of the first gradient, C is the moment of the third gradient, n is a natural number greater than or equal to 1, and Q is an adjustable arbitrary value; the moment of the first gradient can be adjusted as desired.
2. The method of claim 1, wherein the method further comprises:
and calculating to obtain the temperature change quantity in the tissue according to the first echo signal phase diagram.
3. The method of claim 1, wherein the gradient direction is a readout direction and the second gradient is a readout gradient; in the cycle sequence, the third gradient, the second gradient and the first gradient are arranged in sequence and are located in the same TR.
4. The method of claim 1, wherein the gradient direction is a layer selection direction and the second gradient is a layer selection gradient; in the cycle timing, the first gradient is located within the first TR, the second gradient is located partially within the first TR, partially within the second TR, and the third gradient is located within the second TR.
5. The method of claim 1, in combination with a planar echo imaging EPI.
6. The method according to claim 1, in combination with segmented planar echo imaging, peepi.
7. An echo displacement based tissue displacement detection system, the system comprising:
the acquisition unit is used for sequentially acquiring a first echo signal phase diagram and a second echo signal phase diagram which are obtained by magnetic resonance-acoustic radiation force imaging (MR-ARFI) in a first continuous repetition period (TR) and a second TR, wherein in the MR-ARFI process, a radio frequency pulse, a gradient field and a focused ultrasonic pulse are applied, a first gradient for out-of-phase and displacement coding is applied to one gradient direction of the gradient field, and the application of the first gradient is synchronous with the application of the focused ultrasonic pulse in the first TR; the method comprises the steps of,
the calculating unit is used for calculating and obtaining the displacement variation in the tissue according to the difference value of the first echo signal phase diagram and the second echo signal phase diagram;
a second gradient and a third gradient which are adjacent to the first gradient in the period time sequence are applied to the gradient direction, the second gradient has a basic function corresponding to the gradient direction, and the third gradient is a refocusing gradient;
the correspondence between the moment of the first gradient and the moment of the second gradient and the moment of the third gradient is:
C＝(n+1)×Q-A/2，B＝-n×Q-A/2，Q＝A+B+C，
wherein A is the moment of the second gradient, B is the moment of the first gradient, C is the moment of the third gradient, n is a natural number greater than or equal to 1, and Q is an adjustable arbitrary value; the moment of the first gradient can be adjusted as desired.
8. A computing device comprising a memory and a processor, wherein the processor performs the steps of the method of any of claims 1 to 6 when executing a computer program stored in the memory.
9. A computer readable storage medium storing a computer program, characterized in that the computer program when executed by a processor implements the steps of the method according to any one of claims 1 to 6.
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