CN105435380B - The methods of risk assessment of HIFU Treatment equipment based on reverse heat transfer - Google Patents
The methods of risk assessment of HIFU Treatment equipment based on reverse heat transfer Download PDFInfo
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Abstract
The invention discloses a kind of methods of risk assessment of the HIFU Treatment equipment based on reverse heat transfer, comprise the following steps：1) temperature change of measurement simulation human body soft tissue, and default focal regions position；2) reverse conduction optimization determines the exact position of supersonic beam；3) Temperature Distribution inside and outside focal regions is determined：According to supersonic beam actual focal position (xf, yf, zf), the temperature change in simulation human body soft tissue is determined, so that it is determined that the Temperature Distribution inside and outside focal regions, and obtain the distribution of the ultrasonic power in tissue；4) risk assessment conclusion is obtained：Temperature Distribution value inside and outside the focal regions that step 3) is obtained is compared with standard value or safety value, if meeting standard value or in the range of safety value, may continue as Clinical practice, on the contrary then need to be overhauled.Avoid shining directly into supersonic beam on thermocouple, alleviate influence of the thermocouple fever to tissue temperature measurement, so as to improve the precision of temperature survey, reduce the cost of risk assessment.
Description
Technical Field
The invention relates to the field of medical equipment maintenance, in particular to a risk assessment method of HIFU treatment equipment based on reverse heat conduction.
Background
HIFU (High intensity focused ultrasound) is a focused ultrasound source composed of a unit transducer or a multi-element transducer array, and after the emitted ultrasound passes through a sound transmission medium, the ultrasound penetrates through the body surface of a patient with sound intensity acceptable by normal tissues of a human body, and energy is gathered on a target tissue to cause coagulation necrosis (or instant inactivation). The therapeutic principle is that the heat effect generated by the high-intensity ultrasound focused in the biological tissue is utilized to make the tissue at the focal region instantly rise to 60-100 ℃, so that protein denaturation and irreversible coagulation necrosis of tissue cells are caused, the tissue outside the focal region has no obvious damage, and the coagulation necrosis tissue can be gradually absorbed or scarred.
Because of its advantages of non-invasiveness, little side effect, low incidence, no increase of tumor metastasis risk, and the like, HIFU has been clinically used for local palliative inactivation treatment of breast tumors, tumors of limbs and superficial tissues, or osteosarcomas, liver, kidney, and pelvic solid tumors, and can also be used as a thermotherapy device for radiotherapy and chemotherapy sensitization after a proper power reduction.
The core technology of the HIFU treatment system is hard software and functions thereof, which can realize accurate positioning of the focus in vivo to be treated on the premise of considering the non-uniformity of the human body structure, realize accurate time-space control of the sound output of the HIFU system, monitor and guide the whole process from the normal body temperature to the denaturation critical temperature of the target tissue in real time and detect and judge whether the target tissue has coagulation necrosis on line. The measurement and display of the target area temperature are important means for the HIFU treatment process monitoring, but are still a big challenge of the HIFU treatment system at present.
It can be seen that temperature monitoring is an important content of HIFU therapy system performance detection and risk assessment. Magnetic Resonance Imaging (MRI) has good imaging quality and high contrast for soft tissues, and the position and range of a focus can be observed by using a temperature-sensitive fast gradient echo sequence in treatment, so that the MRI is one of ideal monitoring means for HIFU clinical treatment. On the basis of real-time temperature measurement, the MRI system calculates and obtains the heat deposited in the tissue by the HIFU irradiation, and compares the heat with the threshold value causing tissue damage, so that the range of necrotic tissue can be judged, and the real-time monitoring of target treatment is realized. After the treatment is finished, the enhanced magnetic resonance imaging is carried out for determining the treatment effect.
However, the cost of monitoring the temperature by magnetic resonance imaging is too high, and particularly, the cost of maintenance is greatly increased when the magnetic resonance imaging temperature detection device is equipped for preventive maintenance and risk assessment of the HIFU treatment system, so that a low-cost risk assessment and monitoring method is urgently needed. Therefore, a method for detecting the temperature by inserting a thermocouple into the examined tissue, which is proposed by the inventor, belongs to an invasive method, namely, the thermocouple is placed near an artificial blood vessel, and the influence of the blood flow on the temperature change of the tissue caused by the HIFU is studied. The method has the advantages of economy, simplicity and feasibility, and has the defect that the thermocouple is heated due to the fact that the ultrasonic beam directly irradiates on the thermocouple, the actually measured temperature is higher than the temperature of a tissue which only absorbs ultrasonic energy, and the heat effect can be obtained by solving a Khokhlov-Zabolotskaya-Kuznetsov (KZK) equation. In addition, artificial errors are easily introduced when the ultrasonic beam is focused on the thermocouple, and the actually measured temperature can be underestimated; and the thermocouple can measure only the temperature at a specific point, not the temperature of the entire focal region.
Disclosure of Invention
In view of the above, the present invention provides a risk assessment method for HIFU therapy apparatus based on reverse thermal conduction, which is directed to the problems of inaccurate measured temperature and high assessment cost in the prior art.
The technical solution of the present invention is to provide a risk assessment method of a HIFU treatment apparatus based on reverse thermal conduction, comprising the following steps:
1) Measuring the temperature change of the simulated human soft tissue, and presetting the focal region position: arranging filament thermocouples in the simulated human soft tissue in layers, focusing an ultrasonic beam of high-intensity focused ultrasound tumor treatment equipment near the center of one of the filament thermocouples in a certain layer, moving a transducer of the equipment in a small amplitude, respectively recording temperature rise changes in the same time period at a plurality of different positions of the filament thermocouples, recording the maximum temperature rise value as the center of the filament thermocouple, determining the center of one of the filament thermocouples in the other layer in the same way, and determining a certain position between the centers of the two filament thermocouples as a preset focal region position;
2) Back-conduction optimization determines the precise location of the ultrasound beam: according to the preset focal domain position determined in the step 1), giving an initial value (x) to the ultrasonic beam focusing position 0 ，y 0 ，z 0 ) And solving a heat conduction equation through the initial value to obtain the temperature changes of at least three filament thermocouples:and the three filament thermocouples are not in the same layer;
wherein the sound pressure p (r, z) is obtained by solving a linear form of Khokhlov-Zabolotskaya-Kuznetsov (KZK) wave equation of an axisymmetric ultrasound beam in the z direction:
deposition rateAlpha is the absorption coefficient of the tissue,<&representing taking time average, c is sound velocity in the tissue, r is radial distance from the center of the ultrasonic beam to the tissue, and D is sound diffusivity of the tissue; c. C p Is the specific heat capacity, T is the temperature, k is the thermal diffusion coefficient, T = T '-z/c, T is the lag time, T' is the time;
by usingCalculated value (T) representing change in tissue temperature 1 ) And measured value (T) 0 ) The error is calculated iteratively by using a global optimization algorithm until the delta value at the position of the ultrasonic beam is minimum, so that the accurate actual focusing position (xf, yf, zf) of the ultrasonic beam is obtained;
3) Determining the temperature distribution inside and outside the coke domain: according to the actual focusing position (x) of the ultrasonic beam f ，y f ，z f ) Determining the temperature change in the simulated human soft tissue so as to determine the temperature distribution inside and outside the focal region; and according to the actual focusing position (x) of the ultrasonic beam f ，y f ，z f ) Ultrasonic power distribution in the tissue is obtained by combining ultrasonic power focused by the HIFU equipment, and double risk assessment is carried out by combining the ultrasonic power distribution and temperature distribution;
4) Obtaining a risk assessment conclusion: comparing the temperature distribution value inside and outside the focal region obtained in the step 3) with a standard value or a safety value, if the temperature distribution value meets the standard value or is within the safety value range, judging that the high-intensity focused ultrasound tumor treatment equipment can be continuously used for clinic, otherwise, carrying out maintenance.
Compared with the prior art, the method has the following advantages that: by adopting the invention, a temperature measurement method based on reverse heat conduction provides a new scheme for risk evaluation of the high-intensity focused ultrasound tumor treatment equipment, experimental measurement is carried out by simulating human soft tissues and filament thermocouples, and an accurate actual focusing position of an ultrasonic beam is obtained by combining a reverse heat conduction algorithm so as to obtain actual temperature distribution and compare the actual temperature distribution with a standard value or a safety value. The following beneficial effects are thereby produced: (1) The ultrasonic beam is prevented from being directly irradiated on the thermocouple, the influence of the heating of the thermocouple on the measurement of the tissue temperature is reduced, and the precision of the temperature measurement is improved; (2) The position of the ultrasonic beam is obtained by utilizing the thermocouple array measurement value, so that human errors are avoided, and the algorithm precision for predicting the surrounding tissue temperature is high; (3) An iterative optimization algorithm with the spatial position of the ultrasonic beam as known information can be further used for the measurement of the ultrasonic power; (4) the cost of risk assessment is reduced.
As an improvement, in the step 1), the number of the layers for arranging the filament thermocouples comprises an upper layer and a lower layer, each layer comprises three filament thermocouples, an ultrasonic beam is focused near the center of the middle filament thermocouple of the upper layer, the transducer is moved in a small amplitude, the temperature rise change in the same time period is recorded at a plurality of different positions of the filament thermocouples respectively, the time period comprises a temperature rise section and a cooling section, and the maximum value of the temperature rise is recorded as the center of the filament thermocouple; the center position of the middle filament thermocouple of the lower layer is determined by the same method, and the midpoint between the centers of the two filament thermocouples is determined as the preset focal region position. Considering that three points determine the spatial position, the arrangement of an upper layer structure, a lower layer structure and three filament thermocouples in each layer is adopted, so that the temperature rise change of tissues can be conveniently analyzed, and the position of a preset focal region can be quickly established.
As an improvement, in the step 2), solving a heat conduction equation through the initial value of the focal region position to obtain the temperature change of three filament thermocouples, wherein the three filament thermocouples comprise two of two sides of a lower layer and one of the middle of an upper layer or two of two sides of an upper layer and one of the middle of a lower layer; in step 3), the actual focus position (x) is determined according to the ultrasonic beam f ，y f ，z f ) The temperature of the remaining filament thermocouple is calculated and compared to the measured temperature to verify the actual focus position (x) f ，y f ，z f ) The accuracy of (2).
As an improvement, the standard value or the safety value is obtained by magnetic resonance imaging temperature measurement and is calibrated when leaving a factory or after maintenance. Therefore, the equipment can adopt the thermocouple with lower cost to measure the temperature, achieves the purpose of risk assessment, and does not need to be provided with more expensive magnetic resonance imaging temperature measurement equipment.
As an improvement, the global optimization algorithm is a particle swarm optimization algorithm or a simulated annealing method, and from a random solution, the global optimum is obtained by iteratively searching and following the currently searched optimal value. The method is suitable for solving the problem of the optimal solution of the spatial domain formed by three points, and has the advantages of high precision and quick convergence.
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FIG. 1 is a flowchart illustrating a risk assessment method of a HIFU treatment apparatus based on reverse thermal conduction according to the present invention;
FIG. 2 is a view showing the arrangement of filament thermocouples in the present invention;
Detailed Description
The invention will be further described with reference to the drawings and specific examples, but the invention is not limited to these examples.
The invention is intended to cover alternatives, modifications, equivalents and alternatives which may be included within the spirit and scope of the invention. In the following description of the preferred embodiments of the present invention, specific details are set forth in order to provide a thorough understanding of the present invention, and it will be apparent to those skilled in the art that the present invention may be practiced without these specific details.
As shown in fig. 1, illustrating the process steps of the present invention, the risk assessment method of a HIFU treatment apparatus based on reverse thermal conduction of the present invention includes the following steps:
1) Measuring the temperature change of the simulated human soft tissue, and presetting the focal region position: arranging filament thermocouples in the simulated human soft tissue in layers, focusing an ultrasonic beam of high-intensity focused ultrasound tumor treatment equipment near the center of one of the filament thermocouples in a certain layer, moving a transducer of the equipment in a small amplitude, respectively recording temperature rise changes in the same time period at a plurality of different positions of the filament thermocouples, recording the maximum temperature rise value as the center of the filament thermocouple, determining the center of one of the filament thermocouples in the other layer in the same way, and determining a certain position between the centers of the two filament thermocouples as a preset focal region position;
2) Back-conduction optimization determines the precise location of the ultrasound beam: according to the preset focal domain position determined in the step 1), giving an initial value (x) to the ultrasonic beam focusing position 0 ，y 0 ，z 0 ) And solving a heat conduction equation through the initial value to obtain the temperature changes of at least three filament thermocouples:and the three filament thermocouples are not in the same layer;
wherein the sound pressure p (r, z) is obtained by solving a linear form of Khokhlov-Zabolotskaya-Kuznetsov (KZK) wave equation of an axisymmetric ultrasound beam in the z direction:
a deposition rate Q ofα is the absorption coefficient of the tissue, c is the speed of sound in the tissue, r is the radial distance of the ultrasound beam center to the tissue, D is the acoustic diffusivity of the tissue:
by usingCalculated value (T) representing change in tissue temperature 1 ) And measured value (T) 0 ) And (4) carrying out iterative calculation on the error by using a global optimization algorithm until the delta value at the position of the ultrasonic beam is minimum, thereby obtaining the accurate actual focusing position (x) of the ultrasonic beam f ，y f ，z f )；
3) Determining the temperature distribution inside and outside the coke domain: according to the actual focusing position (x) of the ultrasonic beam f ，y f ，z f ) Determining the temperature change in the simulated human soft tissue so as to determine the temperature distribution inside and outside the focal region; and according to the actual focusing position (x) of the ultrasonic beam f ，y f ，z f ) Ultrasonic power distribution in the tissue is obtained by combining ultrasonic power focused by the HIFU equipment, and double risk assessment is carried out by combining the ultrasonic power distribution and temperature distribution;
4) Obtaining a risk assessment conclusion: comparing the temperature distribution value inside and outside the focal region obtained in the step 3) with a standard value or a safety value, if the temperature distribution value meets the standard value or is within the safety value range, judging that the high-intensity focused ultrasound tumor treatment equipment can be continuously used for clinic, otherwise, carrying out maintenance.
As shown in fig. 2, in step 1), the number of layers for arranging the filament thermocouples includes an upper layer and a lower layer, each layer includes three filament thermocouples, the lower layer is T1, T2 and T3, the upper layer is T4, T5 and T6, the HIFU transducer focuses an ultrasonic beam near the center of the middle filament thermocouple (T5) of the upper layer, the transducer is moved by a small amplitude, temperature rise changes in the same time period are recorded at different positions of the filament thermocouple, the time period includes a temperature rise section and a cooling section, and the maximum temperature rise position is recorded as the center of the filament thermocouple T5; the center position of the middle filament thermocouple (T2) of the lower layer is determined by the same method, and the midpoint between the centers of the two filament thermocouples is determined as the preset focal zone position.
In the step 2), solving a heat conduction equation through the initial value of the focal region position to obtain the temperature change of three filament thermocouples (T1, T3 and T5), wherein the three filament thermocouples comprise two of the two sides of the lower layer and one of the middle of the upper layer or two of the two sides of the upper layer and one of the middle of the lower layer; in step 3), the temperature of the remaining filament thermocouples (T2, T4, T6) is calculated from the actual focal position (xf, yf, zf) of the ultrasound beam and compared with the measured temperature to verify the accuracy of the actual focal position (xf, yf, zf), i.e. the position of the ultrasound beam is calculated by calculating the values at T2, T4 and T6And the average value is taken, so that the accuracy of the temperature change calculation value can be quantitatively evaluated.
The standard value or the safety value is obtained by magnetic resonance imaging temperature measurement and is calibrated when leaving a factory or after maintenance. The equipment can adopt the thermocouple with lower cost to measure the temperature, and achieves the purpose of risk assessment without being equipped with more expensive magnetic resonance imaging temperature measurement equipment.
The global optimization algorithm is a particle swarm optimization algorithm or a simulated annealing method, and from a random solution, the global optimum is obtained by iteratively searching and following the currently searched optimal value.
The risk assessment of the HIFU equipment is mainly based on the key element of temperature measurement, namely, a new idea and a new method for temperature detection are provided, but the risk assessment of the HIFU equipment has many other methods and means, and is not limited to temperature measurement and monitoring.
The foregoing is illustrative of the preferred embodiments of the present invention only and is not to be construed as limiting the claims. The present invention is not limited to the above embodiments, and the specific structure thereof is allowed to vary. In general, all changes which come within the scope of the invention as defined by the independent claims are intended to be embraced therein.
Claims (4)
1. A risk assessment method of a HIFU treatment device based on reverse heat conduction comprises the following steps:
1) Measuring the temperature change of the simulated human soft tissue, and presetting the focal region position: arranging filament thermocouples in the simulated human soft tissue in layers, focusing an ultrasonic beam of high-intensity focused ultrasound tumor treatment equipment near the center of one of the filament thermocouples in a certain layer, moving a transducer of the equipment in a small amplitude, respectively recording temperature rise changes in the same time period at a plurality of different positions of the filament thermocouples, recording the maximum temperature rise value as the center of the filament thermocouple, determining the center of one of the filament thermocouples in the other layer in the same way, and determining a certain position between the centers of the two filament thermocouples as a preset focal region position;
2) Back-conduction optimization determines the precise location of the ultrasound beam: according to the preset focal domain position determined in the step 1), giving an initial value (x) to the ultrasonic beam focusing position 0 ，y 0 ，z 0 ) And solving a heat conduction equation through the initial value to obtain the temperature changes of at least three filament thermocouples:and the three filament thermocouples are not in the same layer;
wherein the sound pressure p (r, z) is obtained by solving a linear form of Khokhlov-Zabolotskaya-Kuznetsov (KZK) wave equation of an axisymmetric ultrasound beam in the z direction:
deposition rateα is the absorption coefficient of the tissue, < > represents time averaging, c is the sound velocity in the tissue, r is the radial distance of the center of the ultrasound beam to the tissue, D is the sound diffusivity of the tissue; c. C p Is the specific heat capacity, T is the temperature, k is the thermal diffusion coefficient, T = T '-z/c, T is the lag time, T' is the time;
by usingCalculated value (T) representing change in tissue temperature 1 ) And measured value (T) 0 ) And (3) carrying out iterative calculation on errors by utilizing a particle swarm optimization algorithm or a simulated annealing method until the delta value at the position of the ultrasonic beam is minimum, thereby obtaining the accurate actual focusing position (x) of the ultrasonic beam f ，y f ，z f )；
3) Determining the temperature distribution inside and outside the coke domain: according to the actual focusing position (x) of the ultrasonic beam f ，y f ，z f )，Determining the temperature change in the simulated human soft tissue so as to determine the temperature distribution inside and outside the focal region; and according to the actual focusing position (x) of the ultrasonic beam f ，y f ，z f ) Ultrasonic power distribution in the tissue is obtained by combining ultrasonic power focused by the HIFU equipment, and double risk assessment is carried out by combining the ultrasonic power distribution and temperature distribution;
4) Obtaining a risk assessment conclusion: comparing the temperature distribution value inside and outside the focal region obtained in the step 3) with a standard value or a safety value, if the temperature distribution value meets the standard value or is within the safety value range, judging that the high-intensity focused ultrasound tumor treatment equipment can be continuously used for clinic, otherwise, carrying out maintenance.
2. The risk assessment method of a reverse thermal conduction-based HIFU treatment apparatus according to claim 1, wherein: in the step 1), the layer number for arranging the filament thermocouples comprises an upper layer and a lower layer, each layer comprises three filament thermocouples, an ultrasonic beam is focused near the center of the middle filament thermocouple on the upper layer, the transducer is moved in a small amplitude, the temperature rise change in the same time period is respectively recorded at a plurality of different positions of the filament thermocouples, the time period comprises a temperature rise section and a cooling section, and the maximum value of the temperature rise is recorded as the center of the filament thermocouple; the center position of the middle filament thermocouple of the lower layer is determined by the same method, and the midpoint between the centers of the two filament thermocouples is determined as the preset focal region position.
3. The risk assessment method of a reverse thermal conduction-based HIFU treatment apparatus according to claim 1 or 2, wherein: in the step 2), solving a heat conduction equation through the initial value of the focal region position to obtain the temperature change of three filament thermocouples, wherein the three filament thermocouples comprise two of the two sides of the lower layer and one of the middle of the upper layer or two of the two sides of the upper layer and one of the middle of the lower layer; in step 3), the actual focus position (x) is determined according to the ultrasonic beam f ，y f ，z f ) The temperature of the remaining filament thermocouple is calculated and compared to the measured temperature to verify the actual focus position (x) f ，y f ，z f ) The accuracy of (2).
4. The risk assessment method of a HIFU therapy apparatus based on reverse thermal conduction of claim 1, wherein: the standard value or the safety value is obtained by magnetic resonance imaging temperature measurement and is calibrated when leaving a factory or after maintenance.
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| Publication number | Priority date | Publication date | Assignee | Title |
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| CN1215616A (en) * | 1998-01-25 | 1999-05-05 | 重庆医科大学附属第二医院 | High-intensity focus supersonic tumor scanning therapy system |
| US6425867B1 (en) * | 1998-09-18 | 2002-07-30 | University Of Washington | Noise-free real time ultrasonic imaging of a treatment site undergoing high intensity focused ultrasound therapy |
| CN201969218U (en) * | 2010-12-27 | 2011-09-14 | 天津医科大学 | Concave spherical surface eight-ring phased array high-intensity focused ultrasound energy converter |
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| CN1215616A (en) * | 1998-01-25 | 1999-05-05 | 重庆医科大学附属第二医院 | High-intensity focus supersonic tumor scanning therapy system |
| US6425867B1 (en) * | 1998-09-18 | 2002-07-30 | University Of Washington | Noise-free real time ultrasonic imaging of a treatment site undergoing high intensity focused ultrasound therapy |
| CN201969218U (en) * | 2010-12-27 | 2011-09-14 | 天津医科大学 | Concave spherical surface eight-ring phased array high-intensity focused ultrasound energy converter |
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