CN109480844B - Method, device, equipment and storage medium for synchronously monitoring tissue displacement and temperature - Google Patents

Method, device, equipment and storage medium for synchronously monitoring tissue displacement and temperature Download PDF

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CN109480844B
CN109480844B CN201811610504.XA CN201811610504A CN109480844B CN 109480844 B CN109480844 B CN 109480844B CN 201811610504 A CN201811610504 A CN 201811610504A CN 109480844 B CN109480844 B CN 109480844B
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郑海荣
刘新
邹超
许宗为
乔阳紫
程传力
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Abstract

The embodiment of the invention discloses a method, a device, equipment and a storage medium for synchronously monitoring tissue displacement and temperature. The method comprises the following steps: when a sequence in magnetic resonance acoustic radiation force imaging (MR-ARFI) meets the condition that the ratio of echo time to transverse relaxation time is smaller than a preset first threshold value and the ratio of repetition time to longitudinal relaxation time is larger than a preset second threshold value, scanning a tissue based on the MR-ARFI technology to acquire an image of the tissue; and synchronously monitoring the displacement and the temperature of the tissue at the current moment according to the amplitude of the image at the current moment, the accumulated phase of the image at each moment, the amplitude of the image at the initial moment and the temperature of the tissue. The technical scheme of the embodiment of the invention can synchronously monitor the displacement and the temperature of the tissue at the current moment, and ensures the safety of the FUS focusing process.

Description

Method, device, equipment and storage medium for synchronously monitoring tissue displacement and temperature
Technical Field
The embodiment of the invention relates to the field of biomedical signal processing, in particular to a method, a device, equipment and a storage medium for synchronously monitoring tissue displacement and temperature.
Background
Magnetic resonance acoustic radiation force imaging (MR-ARFI) technology can detect micron-scale displacement of biological tissues, is used for reflecting tissue elasticity, and is an important means for focal point positioning in Focused Ultrasound (FUS) treatment. However, when repeated ARFI measurements, such as FUS with continuous adjustment of the acoustic beam phase, heat accumulation in tissue in the local region of the focus may become significant. Therefore, there is a need to monitor both the displacement and temperature of the tissue to ensure the safety of the FUS treatment process.
The Gradient echo ARFI (GRE-ARFI) technology based on proton resonance frequency drift utilizes the linear relation between the resonance frequency of hydrogen protons in water and temperature to carry out temperature imaging, and can simultaneously monitor the change of temperature and displacement. However, the temperature increase of focal domain tissue usually occurs at tissue interfaces such as subcutaneous adipose tissue, where the hydrogen protons are not sensitive to temperature. Therefore, GRE-ARFI can only achieve simultaneous monitoring of the displacement and temperature of the remaining tissues other than adipose tissue, and is not suitable for application to temperature imaging of adipose-containing tissues.
Disclosure of Invention
The embodiment of the invention provides a method, a device, equipment and a storage medium for synchronously monitoring tissue displacement and temperature, which solve the problem that the displacement and the temperature of adipose tissue cannot be monitored simultaneously in the existing scheme.
In a first aspect, an embodiment of the present invention provides a method for synchronously monitoring tissue displacement and temperature, where the method may include:
when a sequence in magnetic resonance acoustic radiation force imaging (MR-ARFI) meets the condition that the ratio of echo time to transverse relaxation time is smaller than a preset first threshold value and the ratio of repetition time to longitudinal relaxation time is larger than a preset second threshold value, scanning a tissue based on the MR-ARFI technology to acquire an image of the tissue;
and synchronously monitoring the displacement and the temperature of the tissue at the current moment according to the amplitude of the image at the current moment, the accumulated phase of the image at each moment, the amplitude of the image at the initial moment and the temperature of the tissue.
Optionally, the synchronously monitoring the displacement and the temperature of the tissue at the current time according to the amplitude of the image at the current time, the accumulated phase of the image at each time, and the amplitude of the image and the temperature of the tissue at the initial time may include:
acquiring an accumulated phase of an image at each moment, and converting the accumulated phase into the displacement of the tissue at the current moment according to a preset displacement conversion function;
and monitoring the temperature of the tissue at the current moment according to the amplitude of the image at the current moment, the amplitude of the image at the initial moment and the temperature of the tissue.
Optionally, monitoring the temperature of the tissue at the current time according to the amplitude of the image at the current time, and the amplitude of the image at the initial time and the temperature of the tissue may include:
the temperature T of the tissue at the present moment is monitored by the following formula:
Figure BDA0001924635150000021
where p is a preset scaling factor, S (T) is the amplitude of the image at the current time, S (T)0) Is the amplitude, T, of the image at the initial moment0Is the temperature of the tissue at the initial moment.
Optionally, the scaling factor p is determined by:
controlling the temperature of the tissue based on a preset temperature control method and a preset coil, and monitoring at least two temperatures of the tissue based on a preset temperature monitoring method;
and respectively obtaining the amplitude of the image corresponding to each temperature, and obtaining a proportionality coefficient p through linear fitting.
Optionally, obtaining the scaling factor p by linear fitting may include:
at least two temperatures TcAnd the amplitude S (T) of the image corresponding to each temperaturec) Substituting the following formula, and converting into a proportionality coefficient p through linear fitting:
S(Tc)＝A*Tc+B
wherein A is a first predetermined coefficient, B is a second predetermined coefficient, and
Figure BDA0001924635150000031
optionally, the step of determining the scaling factor p may further include:
and repeatedly executing temperature control on the tissue based on a preset temperature control method and a preset coil until a preset execution finishing condition is met, calculating the average value of each proportional coefficient p, and updating the calculation result into the proportional coefficient p.
Optionally, obtaining the accumulated phase of the image at each time, and converting the accumulated phase into the displacement of the tissue at the current time according to a preset displacement conversion function, may include:
acquiring a phase difference delta phi of an image at the current moment based on a preset positive and negative polarity motion coding gradient, and converting the phase difference delta phi into a displacement delta x of a tissue at the current moment through the following formula:
Figure BDA0001924635150000032
wherein t is the motion encoding time, gamma is the gyromagnetic ratio, and G is the motion encoding gradient.
In a second aspect, an embodiment of the present invention further provides a device for synchronously monitoring tissue displacement and temperature, where the device may include:
the tissue image acquisition module is used for scanning the tissue based on the MR-ARFI technology to acquire an image of the tissue when a sequence in the MR-ARFI meets the condition that the ratio of echo time to transverse relaxation time is smaller than a preset first threshold and the ratio of repetition time to longitudinal relaxation time is larger than a preset second threshold;
and the synchronous monitoring module of the tissue displacement and the temperature is used for synchronously monitoring the displacement and the temperature of the tissue at the current moment according to the amplitude of the image at the current moment, the accumulated phase of the image at each moment, the amplitude of the image at the initial moment and the temperature of the tissue.
In a third aspect, an embodiment of the present invention further provides an apparatus, where the apparatus may include:
one or more processors;
a memory for storing one or more programs,
when executed by one or more processors, cause the one or more processors to implement the method for simultaneous monitoring of tissue displacement and temperature provided by any of the embodiments of the present invention.
In a fourth aspect, the embodiments of the present invention further provide a computer-readable storage medium, on which a computer program is stored, where the computer program, when executed by a processor, implements the method for synchronously monitoring tissue displacement and temperature provided in any embodiment of the present invention.
According to the technical scheme of the embodiment of the invention, when a sequence in magnetic resonance acoustic radiation force imaging (MR-ARFI) meets the condition that the ratio of echo time to transverse relaxation time is less than a preset first threshold value and the ratio of repetition time to longitudinal relaxation time is greater than a preset second threshold value, an image of a tissue acquired based on the MR-ARFI technology comprises amplitude information and phase information; moreover, based on the amplitude of the image at the current moment acquired by the sequence, the accumulated phase of the image at each moment, the amplitude of the image at the initial moment and the temperature of the tissue, the displacement and the temperature of the tissue at the current moment can be synchronously monitored, and the safety of the FUS focusing process is ensured.
Drawings
FIG. 1 is a flow chart of a method for synchronously monitoring tissue displacement and temperature according to one embodiment of the present invention;
FIG. 2 is a flow chart of a method for synchronously monitoring tissue displacement and temperature according to a second embodiment of the present invention;
FIG. 3 is a flowchart of an exemplary illustration in a second embodiment of the invention;
FIG. 4a is a graph of actual temperature versus predicted temperature for 8 trials in a second embodiment of the present invention;
FIG. 4b is a graph of actual temperature versus predicted temperature for 3 trials in example two of the present invention;
FIG. 5a is a schematic phase diagram of an image of adipose tissue according to a second embodiment of the present invention;
FIG. 5b is a schematic temperature curve of an image of adipose tissue according to a second embodiment of the present invention;
FIG. 6 is a block diagram of a synchronous tissue displacement and temperature monitoring device according to a third embodiment of the present invention;
fig. 7 is a schematic structural diagram of an apparatus according to a fourth embodiment of the present invention.
Detailed Description
The present invention will be described in further detail with reference to the accompanying drawings and examples. It is to be understood that the specific embodiments described herein are merely illustrative of the invention and are not limiting of the invention. It should be further noted that, for the convenience of description, only some of the structures related to the present invention are shown in the drawings, not all of the structures.
Example one
Fig. 1 is a flowchart of a method for synchronously monitoring tissue displacement and temperature according to an embodiment of the present invention. The embodiment can be applied to the condition of synchronously monitoring the displacement and the temperature of the tissue, in particular to the condition of synchronously monitoring the displacement and the temperature of the fat tissue in focused ultrasound FUS treatment. The method can be executed by the synchronous monitoring device for tissue displacement and temperature provided by the embodiment of the invention, and the device can be realized by software and/or hardware. Referring to fig. 1, the method of an embodiment of the present invention includes the steps of:
s110, when the sequence in the magnetic resonance acoustic radiation force imaging MR-ARFI meets the condition that the ratio of echo time to transverse relaxation time is smaller than a preset first threshold value and the ratio of repetition time to longitudinal relaxation time is larger than a preset second threshold value, scanning the tissue based on the MR-ARFI technology, and acquiring the image of the tissue.
Wherein, Acoustic Radiation Force (ARF) is the phenomenon that the sound wave produced at the inside propagation process of material, and when the sound wave frequency reaches megahertz level promptly ultrasonic wave, the sound wave can produce two kinds of phenomena in propagating the material inside: momentum exchange occurs in the direction of sound wave propagation and heat is generated. Wherein, momentum exchange can generate an acting force to push the propagation substance to generate a certain displacement which can reflect the elasticity of the propagation substance; and the heat generation causes the temperature inside the substance to increase.
Magnetic resonance acoustic radiation force imaging (MR-ARFI) is a Magnetic resonance focused ultrasound elastography technique that uses acoustic radiation force generated by focused ultrasound beams within a safe power range to make a local region of biological tissue generate micro-deformation, adds a displacement encoding gradient in a Magnetic resonance sequence and carries out displacement encoding on the micro-deformation, and finally uses the encoded phase change to estimate the tissue displacement of a focal region. The imaging technology can be applied to the aspects of breast cancer detection, diagnosis of artery porridge-like plaque, safety monitoring of focused ultrasound treatment and the like.
Sequences commonly used in the MR-ARFI monitoring process comprise a one-dimensional line scanning ARFI sequence, a Spin Echo (SE-ARFI) sequence, a plane Echo (EPI-SE-ARFI) sequence, a gradient Echo sequence and the like. Wherein, the 180 DEG radio frequency pulse specific to the SE-ARFI sequence can effectively eliminate the spin dephasing caused by the magnetic field nonuniformity and the magnetic susceptibility. It will be appreciated that each sequence comprises an echo Time (EchoTime, TE), i.e. the Time interval from the middle point of a pulse of the macroscopic transverse magnetisation vector to the middle point of the echo, and a Repetition Time (TR), i.e. the interval Time between two excitation pulses. In addition, the tissue includes a transverse relaxation time T2, i.e. the time constant for the disappearance of the transverse magnetization, and a longitudinal relaxation time T1, i.e. the time constant for the recovery of the longitudinal magnetization.
When the sequence in MR-ARFI satisfies the following condition: ratio of echo time to transverse relaxation time
Figure BDA0001924635150000063
Less than a preset first threshold, and the ratio of repetition time to longitudinal relaxation time
Figure BDA0001924635150000062
If the temperature is greater than the preset second threshold, the temperature and displacement of the tissue can be synchronously monitored. In other words, in general, when the sequence satisfies TE < T2 and TR > T1, for example, when the tissue is adipose tissue, TE < 30ms, TR > 600ms, T2 ═ 60, T1-. Therefore, the tissue is scanned based on the MR-ARFI technique including a sequence satisfying the above conditions, and an image of the tissue is acquired. It is understood that the above method is based on the common property of tissues, and thus the above tissues may be adipose tissues, i.e., tissues containing fat, or non-adipose tissues containing neither fat.
And S120, synchronously monitoring the displacement and the temperature of the tissue at the current moment according to the amplitude of the image at the current moment, the accumulated phase of the image at each moment, the amplitude of the image at the initial moment and the temperature of the tissue.
The image acquired based on the MR-ARFI technology comprises phase information and amplitude information, the displacement of the tissue focus can be monitored according to the phase information, and the temperature of the tissue can be monitored according to the amplitude information. The acquired images comprise images of at least two moments in time, considering that MR-ARFI techniques can scan tissue continuously. It will be appreciated that the image at each time instant includes both phase information and amplitude information. Moreover, the image at the initial time may be considered as the first image acquired, i.e., the initially acquired image; the image at the present moment may be regarded as the last image that has been acquired, i.e., the image that has been finally acquired. Then, based on the amplitude of the image at the current time, the accumulated phase of the image at each time, the amplitude of the image at the initial time, and the temperature of the tissue at the initial time, the displacement and temperature of the tissue at the current time can be synchronously monitored.
An optional solution, after acquiring the image of the tissue, the method may further comprise: and smoothing the image of the tissue, and taking the smoothed image as the image of the tissue. Specifically, a preset region in the image can be used as the region of interest, the region of interest is smoothed, and the amplitude information and the phase information acquired according to the smoothed image are favorable for reflecting the average level of the image.
According to the technical scheme of the embodiment of the invention, when a sequence in magnetic resonance acoustic radiation force imaging (MR-ARFI) meets the condition that the ratio of echo time to transverse relaxation time is less than a preset first threshold value and the ratio of repetition time to longitudinal relaxation time is greater than a preset second threshold value, an image of a tissue acquired based on the MR-ARFI technology comprises amplitude information and phase information; moreover, based on the amplitude of the image at the present time, the accumulated phase of the image at each time, and the amplitude of the image at the initial time and the temperature of the tissue acquired in the above sequence, the displacement and temperature of the tissue at the present time can be synchronously monitored. By the technical scheme, the displacement and the temperature of any tissue, especially adipose tissue, can be synchronously monitored, and the safety of the FUS focusing process is ensured.
Example two
Fig. 2 is a flowchart of a method for synchronously monitoring tissue displacement and temperature according to a second embodiment of the present invention. The embodiment is optimized based on the technical scheme. In this embodiment, "synchronously monitoring the displacement and temperature of the tissue at the current moment according to the amplitude of the image at the current moment, the accumulated phase of the image at each moment, and the amplitude of the image and the temperature of the tissue at the initial moment" is specifically optimized to "obtain the accumulated phase of the image at each moment, and convert the accumulated phase into the displacement of the tissue at the current moment according to a preset displacement conversion function; the temperature of the tissue at the current time is monitored based on the amplitude of the image at the current time, as well as the amplitude of the image and the temperature of the tissue at the initial time. The same or corresponding terms as those in the above embodiments are not explained in detail herein. Correspondingly, as shown in fig. 2, the method of this embodiment may specifically include the following steps:
s210, when a sequence in the magnetic resonance acoustic radiation force imaging MR-ARFI meets the condition that the ratio of echo time to transverse relaxation time is smaller than a preset first threshold value and the ratio of repetition time to longitudinal relaxation time is larger than a preset second threshold value, scanning the tissue based on the MR-ARFI technology, and acquiring an image of the tissue.
S220, acquiring the accumulated phase of the image at each moment, and converting the accumulated phase into the displacement of the tissue at the current moment according to a preset displacement conversion function.
The phase information in the image can be considered as a specific phase difference caused by the encoding gradient in the ARFI sequence, that is, the FUS focusing process displaces the tissue while encoding the motion. And the encoding gradient can be a bipolar repeated displacement encoding gradient, a unipolar motion encoding gradient, an inverse positive-negative polarity motion encoding gradient and the like. Applying encoding gradients in the ARFI sequence can translate the macroscopic displacement of hydrogen protons in tissue caused by focused ultrasound FUS into an amount of change in the proton resonance frequency, producing an accumulated phase in the phase map of the image. Specifically, the accumulated phase φ may be generated by the following equation:
Figure BDA0001924635150000091
wherein T is the motion encoding time, Δ ω is the change amount of the proton resonance frequency, G is the motion encoding gradient, γ is the gyromagnetic ratio and γ/2 pi is 42.58MHz/T, and r is the proton displacement. Specifically, the frequencies at different locations in the tissue are different, and the frequencies can be calculated according to the motion encoding time t, and further, the accumulated phase can be obtained according to the frequencies. Furthermore, the accumulated phase may be converted into a displacement of the tissue at the current time according to a preset displacement conversion function, for example, a phase difference may be obtained according to a difference of the phases at different motion encoding gradients.
And S230, monitoring the temperature of the tissue at the current moment according to the amplitude of the image at the current moment, the amplitude of the image at the initial moment and the temperature of the tissue.
The temperature of the tissue is related to many factors in the magnetic resonance image, for example, the proton density is linear with the temperature in a certain temperature range; the transverse relaxation time T2 is linear with temperature; the amplitude signal of an image of a fast spin echo (TSE) sequence weighted based on T1 has a linear relationship with temperature; the amplitude S of the image is related to the initial amplitude S0, the repetition time TR, the echo time TE, etc. Also, the magnitude of the image, S, can be expressed as:
Figure BDA0001924635150000092
when the echo time TE is short, namely TE < T2; and the repetition time TR is very long, namely TR > > T1, S is proportional to S0. Since the amplitude of the image is different at different temperatures T and the proton density is linear with respect to the temperature T, the initial amplitude S0 can be expressed as: s0(T) ═ a × T + b; where a and b are preset coefficients in a linear relationship, T can be considered to be the temperature of the tissue at the time corresponding to the initial amplitude S0.
If the amplitude S is equal toThe positive proportionality coefficient between the initial amplitudes S0 is K, and considering the influence Q of the distance and the different coil sensitivities, the amplitude S (t) of the image at the current moment can be expressed as: s (t) ═ K × Q (aT + B) ═ aT + B; wherein A is a first preset coefficient, and B is a second preset coefficient. Then, the temperature of the tissue at the initial moment is T0The amplitude S (T) of the image at the initial moment0) Can be expressed as: s (T)0)＝K*Q(aT0+b)＝AT0+ B. According to the derivation process, the amplitude S (T) of the image at the current moment and the amplitude S (T) of the image at the initial moment can be obtained0) And temperature T of tissue0The temperature T of the tissue at the present time can be monitored.
According to the technical scheme of the embodiment of the invention, the displacement of the tissue at the current moment can be determined by acquiring the accumulated phase of the image at each moment; the temperature of the tissue at the current moment can be monitored according to the amplitude of the image at the current moment, the amplitude of the image at the initial moment and the temperature of the tissue, and accurate and synchronous monitoring of the displacement and the temperature of the tissue is really realized.
An optional technical solution is that the obtaining of the accumulated phase of the image at each time and the converting of the accumulated phase into the displacement of the tissue at the current time according to a preset displacement conversion function may include: acquiring a phase difference delta phi of an image at the current moment based on a preset positive and negative polarity motion coding gradient, and converting the phase difference delta phi into a displacement delta x of a tissue at the current moment through the following formula:
Figure BDA0001924635150000101
wherein t is the motion encoding time, gamma is the gyromagnetic ratio, and G is the motion encoding gradient.
When the motion encoding gradients applied to the sequence are positive and negative motion encoding gradients, respectively, a phase diagram of an image acquired based on the positive motion encoding gradient, that is, a positive accumulated phase, and a phase diagram of an image acquired based on the negative motion encoding gradient, that is, a negative accumulated phase, may be acquired, respectively, and then a difference between the two sets of phase diagrams is a phase difference Δ Φ. The phase difference Δ Φ at this time corresponds to 2 times the value of the displacement Δ x of the image at the current time.
Specifically, the implementation process of the above scheme may be: respectively adding a positive polarity motion coding gradient and a negative polarity motion coding gradient before and after a 180-degree echo pulse of the EPI-SE-ARFI, and determining a start-stop time point of a focused ultrasonic pulse under the positive and negative polarity motion coding gradients; respectively acquiring two groups of phase diagrams corresponding to motion coding gradients with opposite polarities when a focused ultrasonic pulse works, wherein echo times corresponding to the two groups of phase diagrams are different; the displacement Δ x of the tissue at the current time is determined according to the above formula, where Δ Φ is the phase difference of the two sets of phase maps applying motion encoding gradients of the same intensity and duration and opposite polarity. The step setting has the advantages that the displacement of the image at the current moment can be indirectly monitored based on the positive and negative polarity motion coding gradients applied to the sequence, and the implementation process is simple.
It can be understood that, in order to better avoid the influence of the field effect and improve the accuracy of displacement monitoring, optionally, after the phase difference of the image at the current time is obtained, the phase difference may be subtracted from the phase map of the image when ultrasound is not turned on, or the phase difference may be subtracted from the baseline phase map, and the phase difference is updated according to the subtraction result. The calculation process of the baseline phase map may be: dividing an image of the tissue at the current moment into a region of interest, namely a region with displacement in the tissue, and a reference region, namely a region without displacement in the tissue; and performing polynomial analog fitting on the phase diagram in the reference region, and interpolating by using the obtained polynomial coefficient to obtain a baseline phase diagram.
In addition, it will be appreciated that monitoring of displacement may still be achieved based on single polarity motion encoding gradients, such as positive polarity motion encoding gradients or negative polarity motion encoding gradients. Likewise, the phase map of the image acquired based on the unipolar motion encoding gradients may also be subtracted from the phase map of the image when ultrasound is not turned on, or from the baseline phase map, to avoid the effects of field effects.
An alternative solution is based on the amplitude of the image at the current time, andthe amplitude of the image and the temperature of the tissue at the initial time monitoring the temperature of the tissue at the current time may include: the temperature T of the tissue at the present moment is monitored by the following formula:
Figure BDA0001924635150000111
where p is a preset scaling factor, S (T) is the amplitude of the image at the current time, S (T)0) Is the amplitude, T, of the image at the initial moment0Is the temperature of the tissue at the initial moment.
Wherein, according to S (T) ═ K × Q (aT + B) ═ aT + B and S (T)0)＝K*Q(aT0+b)＝AT0The ratio of + B can be obtained:
Figure BDA0001924635150000121
when in use
Figure BDA0001924635150000122
Can be converted into
Figure BDA0001924635150000123
The temperature T of the tissue at the present moment can then be expressed as:
Figure BDA0001924635150000124
Figure BDA0001924635150000125
it is understood that images acquired based on a sequence satisfying the condition that the ratio of the echo time to the transverse relaxation time is less than a preset first threshold value and the ratio of the repetition time to the longitudinal relaxation time is greater than a preset second threshold value are determined by proton density, which may be referred to as a proton density weighted image. Specifically, the proton density is linear with temperature, and the proton density weighted image is proportional to the proton density in a certain temperature range. (T) is the amplitude of the proton density weighted image at temperature T, S (T)0) Is at a temperature T0Amplitude of the proton density weighted image of time, tissue bits may be synchronously monitored based on the ARFI sequence weighted by proton densityAnd (4) shifting the temperature. Moreover, the displacement and the temperature can be monitored by only 1 image in consideration of proton density weighted image, the imaging speed is high, and the real-time performance of monitoring is guaranteed.
It should be noted that, by using the above-mentioned synchronous monitoring method for tissue displacement and temperature, synchronous monitoring of tissue displacement and temperature can be achieved based on T1 or T2 weighted ARFI sequence, or based on T2 or proton density obtained by fitting ARFI sequence set as different TEs, or based on T1 obtained by fitting ARFI sequence set as different TRs.
An optional technical solution, the scaling factor p may be determined by the following steps: controlling the temperature of the tissue based on a preset temperature control method and a preset coil, and monitoring at least two temperatures of the tissue based on a preset temperature monitoring method; and respectively obtaining the amplitude of the image corresponding to each temperature, and obtaining a proportionality coefficient p through linear fitting.
The amplitude S (T) of the image at the current time and the amplitude S (T) of the image at the initial time0) And the temperature T of the tissue at the initial moment0Are directly measurable and therefore, the determination of the proportionality coefficient p is of crucial importance in order to accurately monitor the temperature of the tissue. Considering that the temperature of the tissue may be increased due to the application of ultrasonic waves during the FUS treatment, but the temperature cannot be directly measured under the action of the ultrasonic waves, the temperature of the tissue can be controlled based on a preset temperature control method, for example, the temperature of the tissue can be controlled by a water bath circulation device. And the preset temperature monitoring method in the experimental process can be based on a fiber thermometer to measure the temperature of the tissue.
The determination process of the scaling factor p may specifically be: controlling the temperature of the tissue based on a preset temperature control method and a preset coil, collecting the amplitude values of the tissue at different temperatures, and determining a proportionality coefficient p in a linear fitting mode. It will be appreciated that the amplitude of the tissue at different temperatures may be acquired based on a preset time interval, and the amplitude of the tissue at different temperatures may also be acquired based on a preset temperature interval. The preset coil can be a small flexible coil or a neck coil.
An optional technical solution, the step of determining the scaling factor p may further include: and repeatedly executing temperature control on the tissue based on a preset temperature control method and a preset coil until a preset execution finishing condition is met, calculating the average value of each proportional coefficient p, and updating the calculation result into the proportional coefficient p.
In order to determine the scaling factor p more accurately, the above technical solution may be repeatedly executed, and each execution may be regarded as one test. For example, the operation of acquiring the amplitude of the tissue at different temperatures is repeatedly performed under the same coil, and each linear fitting may obtain one p-value, and an average value is calculated for each p-value as the proportionality coefficient p. Of course, the operation of acquiring the amplitude of the tissue at different temperatures may be repeatedly performed by using different coils, and the average value of the p values obtained by linear fitting may be calculated. In addition, the preset execution end condition may be the number of trials, and may also be a convergence condition. In general, the proportionality coefficient p of the average obtained through multiple experiments tends to be stable, and can be suitable for monitoring the temperature of tissues of different individuals.
An optional technical solution, obtaining the proportionality coefficient p by linear fitting, may specifically include: at least two temperatures TcAnd the amplitude S (T) of the image corresponding to each temperaturec) Substituting into the following formula S (T)c)＝A*Tc+ B, converting into a proportionality coefficient p through linear fitting; wherein A is a first predetermined coefficient, B is a second predetermined coefficient, and
Figure BDA0001924635150000131
wherein, the temperature TcAnd the amplitude S (T) of the image corresponding theretoc) Is in a one-to-one correspondence relationship, and the temperature and the amplitude having the correspondence relationship have the same time. Respectively at least two temperatures TcAnd the amplitude S (T) of the image corresponding to each temperaturec) Substituting the first preset coefficient A and the second preset coefficient B into the formula, and obtaining the first preset coefficient A and the second preset coefficient B through linear fitting. Further in accordance with
Figure BDA0001924635150000144
The scaling factor p can be found. It will be appreciated that it is more generally applicable to find the scaling factor p by way of a linear fit.
In order to better understand the specific implementation process of the above steps, the method of the present embodiment is exemplarily described below with reference to a specific example "simultaneous monitoring of displacement and temperature of adipose tissue of excised pork based on ARFI sequence weighted by proton density".
Illustratively, referring to fig. 3, before scanning the tissue, parameters of the sequence need to be set, such as: TE and TR are set such that TE < T2 and TR > T1, and Motion coding gradient (MEG) time. The scale factor p needs to be calibrated before the simultaneous monitoring of displacement and temperature of the tissue. Adipose tissues were heated using a water bath circulation device and temperature was monitored by a fiber optic thermometer inserted into the adipose tissues. After the reading of the optical fiber thermometer is stable, acquiring images of corresponding layers of the optical fiber thermometer at different temperatures, and taking the average value of the amplitudes of the images around the optical fiber thermometer as S (T)c) The index of the fiber thermometer is taken as TcSubstituting into the formula S (T)c)＝A*Tc+B，
Figure BDA0001924635150000141
In (3), linear fitting yields a proportionality coefficient p. In order to stabilize the proportionality coefficient p, 4 times of tests are carried out by adopting a small flexible coil, and 4 times of tests are carried out by adopting a neck coil, and 8 groups of tests are carried out in total to obtain the average value of the proportionality coefficient p.
In order to verify the accuracy of the calibrated proportionality coefficient p, the temperature T of the tissue at the initial moment is taken as the first data set of the fiber thermometer0And, with T0Amplitude S (T) of the corresponding image0) Substituting each data point S (T) and a proportionality coefficient p of each group of experiments into a formula as the amplitude of the initial moment image
Figure BDA0001924635150000142
Figure BDA0001924635150000143
In this way, the temperature T of the tissue at the current time is obtained. It will be appreciated that the indication for the light thermometer is the actual temperature T of the adipose tissuecThe solved temperature is the predicted temperature T of the adipose tissue. As shown in fig. 4a, the abscissa is the actual temperature, the ordinate is the predicted temperature, and the reference line is the case where the actual temperature and the predicted temperature are equal. It can be seen that fig. 4a is a graph of the relationship between the actual temperature and the predicted temperature at each data point in 8 experiments, for example, the actual temperature and the predicted temperature at each data point are equal, or the actual temperature is greater than the predicted temperature, or the actual temperature is less than the predicted temperature. It can be seen that each data point is uniformly distributed around the reference line, which indicates that the proportionality coefficient p obtained by linear fitting is more accurate, and the difference between the predicted temperature and the actual temperature monitored based on the proportionality coefficient p is very small. To more clearly show the data points in each set of tests, only the first test of the small flexible loop, the second test of the small flexible loop, and the first test of the neck loop are shown as an example, as shown in fig. 4 b. Of course, it can be understood that the proportionality coefficient p only needs to be calibrated once, and can be suitable for monitoring the temperature and displacement of different tissues.
To validate the feasibility of simultaneous proton density weighted ARFI-based sequence monitoring of fat tissue displacement and temperature in FUS, fat tissue was scanned based on a one-dimensional line scan sequence of the following parameters: b0 ═ 3T, TR ═ 300ms, TE ═ 30ms, acquisition time 9.6s, resolution 1.5 × 1.5mm2The thickness of the adipose tissue layer is 5mm, the flip angle is 90 degrees, the motion coding time is 15.22ms, the included angle between the excitation plane and the convergence plane is 55 degrees, and the power of the FUS is 18W. When the sequence is during motion encoding, the operation of the FUS causes the displacement of the adipose tissue, which is calculated from the phase of the acquired image. As shown in fig. 5a, the phase map 20 of the image includes a focus area 10, the phase value S of each data point in the focus area 10 may be 3 or 4, and the phase value outside the focus area may be 0. Thus, only the tissue of the focal region is displaced.
In view ofThe thermal effect is not significant under normal ARFI conditions, and continuous FUS was used in order to observe significant temperature rise. Specifically, 100 image scans were performed at 18W fixed power FUS, with the 6 th to 25 th image scans being performed while FUS is active and the remaining image scans being performed while FUS is inactive. The temperature T of adipose tissue at room temperature was used as the initial time023 ℃. Substituting the amplitude S (T) of the acquired image into a formula
Figure BDA0001924635150000151
And obtaining the temperature change curve of the adipose tissue at the ultrasonic focus. As shown in fig. 5b, the abscissa is the number of scans of the image and the ordinate is the predicted temperature at the focus. It can be seen that the temperature rise of the adipose tissue during the 6 th to 25 th scans, i.e., during the FUS operation, can be directly monitored by the method. In connection with fig. 5a and 5b, it is directly demonstrated that the method allows for simultaneous monitoring of the displacement and temperature of the tissue.
EXAMPLE III
Fig. 6 is a structural block diagram of a synchronous tissue displacement and temperature monitoring device according to a third embodiment of the present invention, which is used for implementing the synchronous tissue displacement and temperature monitoring method according to any of the embodiments described above. The device and the synchronous monitoring method of tissue displacement and temperature of the above embodiments belong to the same inventive concept, and details which are not described in detail in the embodiments of the synchronous monitoring device of tissue displacement and temperature may refer to the embodiments of the synchronous monitoring method of tissue displacement and temperature. Referring to fig. 6, the apparatus may specifically include: a tissue image acquisition module 310 and a synchronous monitoring module 320 of tissue displacement and temperature.
The tissue image acquisition module 310 is configured to scan a tissue based on an MR-ARFI technique to acquire an image of the tissue when a sequence in the MR-ARFI satisfies a condition that a ratio of echo time to transverse relaxation time is smaller than a preset first threshold and a ratio of repetition time to longitudinal relaxation time is greater than a preset second threshold;
and a tissue displacement and temperature synchronous monitoring module 320, configured to synchronously monitor the displacement and temperature of the tissue at the current time according to the amplitude of the image at the current time, the accumulated phase of the image at each time, and the amplitude of the image and the temperature of the tissue at the initial time.
Optionally, the module 320 for synchronously monitoring tissue displacement and temperature specifically includes:
the tissue displacement monitoring unit is used for acquiring the accumulated phase of the image at each moment and converting the accumulated phase into the displacement of the tissue at the current moment according to a preset displacement conversion function;
and the tissue temperature monitoring unit is used for monitoring the temperature of the tissue at the current moment according to the amplitude of the image at the current moment, the amplitude of the image at the initial moment and the temperature of the tissue.
Optionally, the tissue temperature monitoring unit may monitor the temperature T of the tissue at the current time by the following formula:
Figure BDA0001924635150000171
where p is a preset scaling factor, S (T) is the amplitude of the image at the current time, S (T)0) Is the amplitude, T, of the image at the initial moment0Is the temperature of the tissue at the initial moment.
Optionally, the apparatus may further include a scaling factor determining module, where the scaling factor determining module may determine the scaling factor p by:
the temperature monitoring unit is used for controlling the temperature of the tissue based on a preset temperature control method and a preset coil and monitoring at least two temperatures of the tissue based on a preset temperature monitoring method;
and the proportionality coefficient p determining unit is used for respectively acquiring the amplitude of the image corresponding to each temperature and obtaining the proportionality coefficient p through linear fitting.
Optionally, the scaling factor p determining unit may specifically determine at least two temperatures TcAnd the amplitude S (T) of the image corresponding to each temperaturec) Substituting the following formula, and converting into a proportionality coefficient p through linear fitting:
S(Tc)＝A*Tc+B
wherein A is a first predetermined coefficient, B is a second predetermined coefficient, and
Figure BDA0001924635150000172
optionally, the scaling factor p determining module may further include:
and the proportional coefficient p average value calculating unit is used for repeatedly executing temperature control on the tissue based on a preset temperature control method and a preset coil until a preset execution finishing condition is met, calculating the average value of each proportional coefficient p, and updating the calculation result into the proportional coefficient p.
Optionally, the tissue displacement monitoring unit may include:
the tissue displacement monitoring subunit is used for acquiring a phase difference delta phi of the image at the current moment based on a preset positive and negative polarity motion coding gradient, and converting the phase difference delta phi into a displacement delta x of the tissue at the current moment through the following formula:
Figure BDA0001924635150000181
wherein t is the motion encoding time, gamma is the gyromagnetic ratio, and G is the motion encoding gradient.
In the synchronous monitoring device for tissue displacement and temperature provided by the third embodiment of the invention, the tissue image which can be acquired by the tissue image acquisition module comprises amplitude information and phase information; moreover, the tissue displacement and temperature based synchronous monitoring module can synchronously monitor the displacement and temperature of the tissue at the current moment. The device realizes the synchronous monitoring of the displacement and the temperature of any tissue, particularly adipose tissue, and ensures the safety of the FUS focusing process.
The synchronous monitoring device for tissue displacement and temperature provided by the embodiment of the invention can execute the synchronous monitoring method for tissue displacement and temperature provided by any embodiment of the invention, and has corresponding functional modules and beneficial effects of the execution method.
It should be noted that, in the embodiment of the synchronous monitoring device for tissue displacement and temperature, the units and modules included in the device are only divided according to functional logic, but are not limited to the above division, as long as the corresponding functions can be realized; in addition, specific names of the functional units are only for convenience of distinguishing from each other, and are not used for limiting the protection scope of the present invention.
Example four
Fig. 7 is a schematic structural diagram of an apparatus according to a fourth embodiment of the present invention, as shown in fig. 7, the apparatus includes a memory 410, a processor 420, an input device 430, and an output device 440. The number of processors 420 in the device may be one or more, and one processor 420 is taken as an example in fig. 7; the memory 410, processor 420, input device 430, and output device 440 of the apparatus may be connected by a bus or other means, such as by bus 450 in fig. 7.
The memory 410 is a computer readable storage medium, and can be used for storing software programs, computer executable programs, and modules, such as program instructions/modules corresponding to the synchronous monitoring method for tissue displacement and temperature in the embodiment of the present invention (for example, the tissue image acquisition module 310 and the synchronous monitoring module 320 for tissue displacement and temperature in the synchronous monitoring device for tissue displacement and temperature). The processor 420 executes various functional applications of the device and data processing by executing software programs, instructions and modules stored in the memory 410, namely, implementing the above-described synchronous monitoring method of tissue displacement and temperature.
The memory 410 may mainly include a storage program area and a storage data area, wherein the storage program area may store an operating system, an application program required for at least one function; the storage data area may store data created according to use of the device, and the like. Further, the memory 410 may include high speed random access memory, and may also include non-volatile memory, such as at least one magnetic disk storage device, flash memory device, or other non-volatile solid state storage device. In some examples, memory 410 may further include memory located remotely from processor 420, which may be connected to devices through a network. Examples of such networks include, but are not limited to, the internet, intranets, local area networks, mobile communication networks, and combinations thereof.
The input device 430 may be used to receive input numeric or character information and generate key signal inputs related to user settings and function controls of the device. The output device 440 may include a display device such as a display screen.
EXAMPLE five
An embodiment of the present invention provides a storage medium containing computer-executable instructions, which when executed by a computer processor, perform a method for synchronous monitoring of tissue displacement and temperature, the method comprising:
when a sequence in magnetic resonance acoustic radiation force imaging (MR-ARFI) meets the condition that the ratio of echo time to transverse relaxation time is smaller than a preset first threshold value and the ratio of repetition time to longitudinal relaxation time is larger than a preset second threshold value, scanning a tissue based on the MR-ARFI technology to acquire an image of the tissue;
and synchronously monitoring the displacement and the temperature of the tissue at the current moment according to the amplitude of the image at the current moment, the accumulated phase of the image at each moment, the amplitude of the image at the initial moment and the temperature of the tissue.
Of course, the storage medium provided by the embodiments of the present invention contains computer-executable instructions, and the computer-executable instructions are not limited to the operations of the method described above, and may also perform related operations in the method for synchronously monitoring tissue displacement and temperature provided by any embodiment of the present invention.
From the above description of the embodiments, it is obvious for those skilled in the art that the present invention can be implemented by software and necessary general hardware, and certainly, can also be implemented by hardware, but the former is a better embodiment in many cases. With this understanding, the technical solutions of the present invention may be embodied in the form of a software product, which can be stored in a computer-readable storage medium, such as a floppy disk, a Read-Only Memory (ROM), a Random Access Memory (RAM), a FLASH Memory (FLASH), a hard disk or an optical disk of a computer, and includes instructions for enabling a computer device (which may be a personal computer, a server, or a network device) to execute the methods according to the embodiments of the present invention.
It is to be noted that the foregoing is only illustrative of the preferred embodiments of the present invention and the technical principles employed. 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, although the present invention has been described in greater detail by the above embodiments, the present invention is not limited to the above embodiments, and may include other equivalent embodiments without departing from the spirit of the present invention, and the scope of the present invention is determined by the scope of the appended claims.

Claims (10)

1. A method for simultaneously monitoring tissue displacement and temperature, comprising:
when a sequence in magnetic resonance acoustic radiation force imaging (MR-ARFI) meets the condition that the ratio of echo time to transverse relaxation time is smaller than a preset first threshold value and the ratio of repetition time to longitudinal relaxation time is larger than a preset second threshold value, scanning a tissue based on the MR-ARFI technology to acquire an image of the tissue;
and synchronously monitoring the displacement and the temperature of the tissue at the current moment according to the amplitude of the image at the current moment, the accumulated phase of the image at each moment, the amplitude of the image at the initial moment and the temperature of the tissue.
2. The method of claim 1, wherein the synchronously monitoring the displacement and temperature of the tissue at the current time based on the amplitude of the image at the current time, the accumulated phase of the image at each time, and the amplitude of the image at the initial time and the temperature of the tissue comprises:
acquiring an accumulated phase of an image at each moment, and converting the accumulated phase into the displacement of the tissue at the current moment according to a preset displacement conversion function;
and monitoring the temperature of the tissue at the current moment according to the amplitude of the image at the current moment, the amplitude of the image at the initial moment and the temperature of the tissue.
3. The method of claim 2, wherein monitoring the temperature of the tissue at the current time based on the magnitude of the image at the current time, and the magnitude of the image at the initial time and the temperature of the tissue comprises: monitoring the temperature T of the tissue at the present time by the formula:
Figure FDA0001924635140000011
where p is a preset scaling factor, S (T) is the amplitude of the image at the current time, S (T)0) Is the amplitude, T, of the image at the initial moment0Is the temperature of the tissue at the initial moment.
4. A method according to claim 3, characterized in that the scaling factor p is determined by:
controlling the temperature of the tissue based on a preset temperature control method and a preset coil, and monitoring at least two temperatures of the tissue based on a preset temperature monitoring method;
and respectively obtaining the amplitude of the image corresponding to each temperature, and obtaining a proportionality coefficient p through linear fitting.
5. The method of claim 4, wherein the obtaining the scaling factor p by linear fitting comprises: at least two temperatures TcAnd the amplitude S (T) of the image corresponding to each of the temperaturesc) Substituting the following formula, and converting the ratio coefficient p into the proportionality coefficient through linear fitting:
S(Tc)＝A*Tc+B
wherein A is a first predetermined coefficient, B is a second predetermined coefficient, and
Figure FDA0001924635140000021
6. the method of claim 4, wherein the step of determining the scaling factor p further comprises:
and repeatedly executing temperature control on the tissue based on a preset temperature control method and a preset coil until a preset execution ending condition is met, calculating the average value of each proportionality coefficient p, and updating the calculation result into the proportionality coefficient p.
7. The method of claim 2, wherein the obtaining of the accumulated phase of the image at each time and the converting of the accumulated phase into the displacement of the tissue at the current time according to a preset displacement conversion function comprises:
obtaining a phase difference delta phi of an image at the current moment based on a preset positive and negative polarity motion coding gradient, and converting the phase difference delta phi into a displacement delta x of the tissue at the current moment through the following formula:
Figure FDA0001924635140000022
wherein t is the motion encoding time, gamma is the gyromagnetic ratio, and G is the motion encoding gradient.
8. A device for simultaneously monitoring tissue displacement and temperature, comprising:
the tissue image acquisition module is used for scanning the tissue based on the MR-ARFI technology to acquire an image of the tissue when a sequence in the MR-ARFI meets the condition that the ratio of echo time to transverse relaxation time is smaller than a preset first threshold and the ratio of repetition time to longitudinal relaxation time is larger than a preset second threshold;
and the synchronous monitoring module of the tissue displacement and the temperature is used for synchronously monitoring the displacement and the temperature of the tissue at the current moment according to the amplitude of the image at the current moment, the accumulated phase of the image at each moment, the amplitude of the image at the initial moment and the temperature of the tissue.
9. An apparatus, characterized in that the apparatus comprises:
one or more processors;
a memory for storing one or more programs;
when executed by the one or more processors, cause the one or more processors to implement the method of simultaneous monitoring of tissue displacement and temperature of any one of claims 1-7.
10. A computer-readable storage medium, on which a computer program is stored which, when being executed by a processor, carries out a method for simultaneous monitoring of tissue displacement and temperature according to any one of claims 1-7.
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