CN111227865A - Ultrasonic resonance imaging system - Google Patents
Ultrasonic resonance imaging system Download PDFInfo
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- CN111227865A CN111227865A CN202010049650.0A CN202010049650A CN111227865A CN 111227865 A CN111227865 A CN 111227865A CN 202010049650 A CN202010049650 A CN 202010049650A CN 111227865 A CN111227865 A CN 111227865A
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/44—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device
- A61B8/4411—Device being modular
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N7/00—Ultrasound therapy
- A61N7/02—Localised ultrasound hyperthermia
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N7/00—Ultrasound therapy
- A61N2007/0004—Applications of ultrasound therapy
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N7/00—Ultrasound therapy
- A61N2007/0082—Scanning transducers
Abstract
The invention relates to an ultrasonic resonance imaging system, comprising: the difference frequency vibration sound generating mechanism is used for forming incremental or degressive difference frequency vibration sound and stimulating the confocal area to organize to generate echo signals; it is characterized by also comprising: the vibration sound signal acquisition, analysis and display system is used for receiving and analyzing echo signals generated by the tissues in the confocal area and acquiring the resonance frequency and the resonance amplitude of the tissues in the confocal area; and the resonance acoustic image analysis and display system is used for receiving and analyzing the resonance frequency and the resonance amplitude of a plurality of continuous tissues in the confocal area in the target area to form a distribution diagram of the resonance frequency and the resonance amplitude of the target area. The system adopts a mode of detecting 'resonant frequency and amplitude' to obtain a resonant peak frequency and amplitude distribution diagram of the target region tissue, obviously improves the imaging accuracy, and more accurately reflects various physical properties of elasticity, machinery, resonance and the like of the target region tissue.
Description
Technical Field
The invention relates to the technical field of medical instruments, in particular to an ultrasonic resonance imaging system.
Background
In recent years, with the development of non-invasive ultrasound systems, it is a mainstream research direction to rapidly and accurately image deep tissues of a human body by using an ultrasound system, and further find a target point for disease treatment and perform specific treatment.
High Intensity Focused Ultrasound (HIFU) is used as a non-invasive, effective and safe treatment mode, plays an important role in the comprehensive treatment of solid tumors such as liver cancer, adrenal tumor and the like in middle and late stages, and can obviously improve the clinical symptoms and long-term prognosis of patients. The conventional HIFU still has the following disadvantages: 1. integration cannot be realized, and other image systems such as ultrasonic images are required to guide and position; 2. the focus positions of part of patients are deep, the ultrasonic image positioning is interfered by various factors, so that the positioning imaging effect is poor, on one hand, the focus tissue ablation is not complete, the curative effect is affected, and on the other hand, the normal tissue damage caused by excessive ablation can be caused; 3. the traditional HIFU has larger power during ablation, mainly plays a therapeutic role through a thermal effect, lacks tissue specificity, and can cause damage of an acoustic conduction path and important tissue blood vessel damage around a focus due to larger ablation energy. There remains a need to explore an ultrasound imaging system for guiding focused ultrasound ablation.
The applicant long-term focuses on the research of the difference frequency focused ultrasound, and explores the role of the difference frequency focused ultrasound in the aspects of imaging and intervention of deep tissues of a human body, and the specific contents are as follows: the ultrasonic transducers with different frequencies but a common focus (better coaxial) are adopted to transmit ultrasonic simultaneously, the frequencies (f1 and f2) of two sets of ultrasonic have slight difference (namely difference frequency (delta f) ═ f1-f2, delta f is about 1% of the dominant frequency), and low-frequency vibration (or called beat frequency) radiation force working with the difference frequency (delta f) is generated at the focus based on the fluctuation interference principle. Based on the principle, the applicant already applied for a patent (CN2019109021190), in which stress generated by low-frequency vibration generated at a focal point by focused ultrasound is used as a mapping source, then the difference frequency vibration at the focal point generates stress to "tap" the tissue of the focal point, and the "loudness" and the vibration sound amplitude generated on the tissue of the focal point are used to distinguish the sound intensity of a detection point, and the sound intensity of the detection point and the hardness of the detection point are in one-to-one correspondence, so as to obtain the hardness characteristic of the detection point through the sound intensity of the detection point, and further pick up a physical signal of the low-frequency vibration acting on a target nerve according to a plurality of hardness characteristics to obtain a hardness distribution map; the hardness distribution diagram shows the anatomical structure of the target and the distribution state of the nerves of the target, so that a detection surface of the target nerves is obtained.
The applicant research is continued, and the aim is to design an ultrasonic resonance detection imaging system which has higher imaging accuracy and comprises a plurality of physical properties such as elasticity, mechanics, resonance and the like.
Disclosure of Invention
The invention aims to provide an ultrasonic resonance imaging system which can be applied to internal tissues of a human body and has higher imaging precision aiming at the defects in the prior art.
In order to achieve the purpose, the invention adopts the technical scheme that:
an ultrasonic resonance imaging system comprising: the ultrasonic generating mechanism is used for forming continuous variable frequency vibration sound and stimulating the confocal area tissues to generate echo signals; it is characterized by also comprising: the vibration sound signal acquisition, analysis and display system is used for receiving and analyzing echo signals generated by the tissues in the confocal area and acquiring the resonance frequency and the resonance amplitude of the tissues in the confocal area; and the resonance acoustic image analysis and display system is used for receiving and analyzing the resonance frequency and the resonance amplitude of a plurality of continuous tissues in the confocal area in the target area to form a distribution diagram of the resonance frequency and the resonance amplitude of the target area.
Preferably, the ultrasonic wave generating mechanism comprises a dual-frequency ultrasonic signal generator for generating two groups of different frequency signals, and the two groups of different frequency signals form two groups of confocal ultrasonic beams with different frequencies through the difference frequency focusing ultrasonic transducer; and the sweep frequency control system is associated with the main control computer, and generates continuously increasing or decreasing difference frequency vibration sound by regulating and controlling the frequency difference (delta f) of the two groups of confocal ultrasonic beams.
Preferably, the system for acquiring, analyzing and displaying the vibration sound signal comprises: the vibration sound signal acquisition system is used for receiving the echo signals generated by the texture of the confocal area; and the vibration sound signal analysis and display system is used for acquiring the resonance frequency and the resonance amplitude of the tissues in the confocal area by analyzing the received echo signals.
Preferably, the vibration sound signal analysis and display system comprises a vibration sound signal display system and a vibration sound signal analysis system, wherein the vibration sound signal display system converts the echo signal into a digital signal and displays the digital signal; the vibration sound signal analysis system obtains the formant of the tissue in the confocal area by analyzing the sound pressure amplitude of the echo signal, and obtains the resonance frequency corresponding to the formant by associating with the sweep frequency control system.
Preferably, the vibration acoustic signal display system includes: a preamplifier, a filter and a digital display.
Preferably, the system further comprises a three-dimensional motion scanning system, which controls the difference frequency focusing ultrasonic transducer to perform three-dimensional arbitrary surface motion relative to the target region, so as to scan an arbitrary surface of the target region.
The invention has the advantages that:
1. the invention relates to an ultrasonic resonance imaging system, which forms a focus at the deep part of an organism by high-frequency focused ultrasound, forms a 'knocking' force by using a difference frequency focused ultrasound interference principle and generating mechanical stress of low-frequency vibration sound at the focus, adjusts the frequency difference (delta f) of two groups of focused ultrasound beams by a sweep frequency control system to adjust the mechanical stress frequency of tissues in a confocal area, detects the resonance frequency and the resonance amplitude of the tissues and images by continuously scanning a specific frequency band, and creates a 'resonance frequency imaging' positioning method at the deep part of the organism by using the difference frequency focused ultrasound.
2. In a certain frequency band, the tissue of a certain confocal area is stimulated and scanned by ultrasound with different difference frequencies, and the observed vibration amplitude of the tissue of the confocal area is increased in a geometric progression under a specific resonance frequency, and a sharp resonance peak appears. In the case of a confocal zone sized, the resonant frequency is related to the tissue elastic modulus, tissue ultrasound absorption and scattering properties, and thus different tissues have their specific resonant frequencies. The acoustic resonance system adopts a mode of detecting 'resonance frequency and amplitude' to obtain a resonance peak frequency and amplitude distribution diagram of the tissue of a target area, obviously improves the imaging accuracy, more accurately reflects various physical properties of elasticity, mechanics, resonance and the like of the tissue of the target area, and forms a new imaging method which is characterized in that the tissue generates resonance.
3. The ablation target tissue in the target area resonates under the action of the difference frequency vibration sound with the same resonant frequency as the ablation target tissue, the vibration amplitude of the target tissue is obviously increased compared with other types of tissues, and the mechanical effect is obviously enhanced. Therefore, the target tissue can be specifically intervened by giving lower treatment power under the resonance frequency of the target tissue, the damage to other tissues caused by mechanical effect and thermal effect is reduced to a greater extent, and the effectiveness and the safety of focused ultrasound intervention are further improved.
4. The resonance imaging system controls the ultrasonic signal generator through the main control computer frequency sweeping control system, and adjusts the frequency difference (delta f) of the two groups of confocal ultrasonic beams to detect the resonance frequency of the tissues in the confocal area. The mapping source is carried out in vitro, good acoustic coupling can be achieved without any electrode or catheter entering the body, and the anatomical structure and tissue distribution information of deep tissues can be obtained through resonance frequency imaging.
5. The resonance imaging system is provided with a three-dimensional motion scanning system, and when the resonance frequency and the amplitude are detected, the focused ultrasonic transducer is controlled to carry out three-dimensional arbitrary surface motion relative to a target area, and arbitrary three-dimensional scanning can be carried out on a part to be detected, so that the vibration sound signal acquisition and analysis system obtains a more comprehensive resonance frequency and amplitude distribution diagram, and a detection surface is accurately obtained. When the physiological signal is detected, the focus is not limited by an anatomical structure, and two-dimensional or three-dimensional scanning can be performed at any point of the solid tissue, so that the same focus is realized during mapping and ablation treatment. However, in the conventional physiological detection, due to the absence of a three-dimensional motion scanning system, the stimulation of the physiological detection in the blood vessel is limited by space, and the physiological detection cannot be detected if the nerve is far away from the blood vessel.
Drawings
In order to more clearly illustrate the embodiments of the present application or the technical solutions in the prior art, the drawings used in the description of the embodiments or the prior art will be briefly introduced below, the drawings in the following description are only some embodiments described in the present application, and other drawings can be obtained by those skilled in the art without creative efforts.
Fig. 1 is a block diagram of an ultrasound resonance imaging system according to various embodiments of the present invention.
Fig. 2 is a block diagram of a vibration acoustic signal analysis display system according to various embodiments of the present invention.
Fig. 3 is a block diagram of a physiological signal mapping system according to various embodiments of the present invention.
FIG. 4 is a chart of formants in the confocal region for various embodiments of the present invention.
FIG. 5 is a graph of resonance frequency and amplitude distribution for a target region for various embodiments of the present invention.
The following detailed description of the present invention will be made with reference to the accompanying drawings.
The reference numerals and components referred to in the drawings are as follows:
1. main control computer 2. frequency sweep control system
3. Ultrasonic signal generator 4. three-dimensional motion system
5. Difference frequency focusing ultrasonic transducer 6 degassing water circulation system
7. Vibration sound signal acquisition system 8. vibration sound signal analysis display system
81. Vibration sound signal display system 811 preamplifier
812. Filter 813 digital oscilloscope
82. Vibration sound signal analysis system
9. Resonance sonogram analysis display system 10 treatment planning unit
11. Basic image unit 12, image superposition unit
13. Physiological signal detection system 131. multichannel physiological recorder
132. Auxiliary discrimination System 14. region of renal artery
15. Region of arterial renal ganglion 16 region of fat
17. Ganglion formant region 18. adipose tissue formant region
Detailed Description
In order to make those skilled in the art better understand the technical solutions in the present application, the technical solutions in the embodiments of the present application will be clearly and completely described below with reference to the drawings in the embodiments of the present application, and it is obvious that the described embodiments are only a part of the embodiments of the present application, and not all embodiments. All other embodiments, which can be derived by a person skilled in the art from the embodiments given herein without making any creative effort, shall fall within the protection scope of the present application.
Example 1
For more clear description of the technical solution, "target point" and "target area" are defined in the following schemes, target area: contains specific body tissues of 'target points'.
As shown in fig. 1, an ultrasound resonance imaging system includes: the difference frequency vibration sound generating mechanism is used for forming incremental or degressive difference frequency vibration sound and stimulating the confocal area to organize to generate echo signals; the vibration sound signal acquisition, analysis and display system is used for receiving and analyzing echo signals generated by the tissues in the confocal area and acquiring the resonance frequency and the resonance amplitude of the tissues in the confocal area; and the resonance acoustic image analysis and display system 9 is used for receiving and analyzing the resonance frequency and the resonance amplitude of a plurality of continuous tissues in the confocal area in the target area to form a distribution diagram of the resonance frequency and the resonance amplitude of the target area.
Further, the ultrasonic wave generating mechanism comprises a dual-frequency ultrasonic signal generator 3 for generating two groups of different frequency signals, and the two groups of different frequency signals form two groups of confocal ultrasonic beams with different frequencies through a difference frequency focusing ultrasonic transducer 5.
The ultrasonic signal generator 3 in this embodiment is a dual-frequency ultrasonic signal generator, and includes a dual-channel ultrasonic signal generating and amplifying circuit with consistent use performance, and the circuit can adopt various pulse repetition frequencies and short pulse transmission modes, has stable power output under low-power and power working modes, can select a same-frequency and accurate difference frequency working mode, and has accurate difference frequency accuracy to phase control.
The ultrasonic signal generator 3 is used to generate two sets of different frequency signals in this embodiment, form two sets of confocal ultrasonic beams with different frequencies through the differential frequency focusing ultrasonic transducer 5, and generate an interference effect in a confocal region to generate a low-frequency vibration sound (USAE), so as to provide a low-frequency vibration radiation force for the biological tissue in the confocal region, and enable the tissue in the confocal region to vibrate back and forth along the incident wave sound axis under the vibration radiation force.
The difference frequency focusing ultrasonic transducer 5 in the embodiment is connected with the ultrasonic signal generator 3, and the difference frequency focusing ultrasonic transducer 5 adopts spherical geometric focusing or phased array electronic sound hole focusing, so that the geometric size and power requirements required by mapping and treatment of large animals and human beings are met. Meanwhile, the difference frequency focusing ultrasonic transducer 5 has a stable power emission range, a sufficient focal length and a moderate opening angle. The difference frequency focusing ultrasonic transducer 5 can adopt a symmetrical double-frequency mode, and has higher electrical conversion efficiency and stable service life. Preferably, the difference frequency focusing ultrasonic transducer 5 can also adopt a petal type or a multi-array element type. Furthermore, the ultrasonic wave generating mechanism also comprises a sweep frequency control system 2, and continuous increasing or decreasing difference frequency vibration sound is generated by regulating and controlling the frequency difference of the two groups of confocal ultrasonic beams. In the embodiment, one end of a frequency sweep control system 2 is connected with a main control computer 1, the other end of the frequency sweep control system is connected with an ultrasonic signal generator 3, the frequency sweep control system 2 actively regulates and controls the frequency difference of two groups of ultrasonic waves emitted by the ultrasonic signal generator 3, and the difference frequency formed by the two groups of ultrasonic waves generates low-frequency vibration echo signals with different degrees under the action of difference frequency vibration sound with different degrees generated in a confocal area by a difference frequency focusing ultrasonic transducer 5. Furthermore, the frequency sweeping control system 2 adjusts the frequency of the vibration sound by adjusting and controlling the frequency difference (delta f) of the two groups of confocal ultrasonic beams, and generates the difference frequency vibration sound of the fast short pulses with different frequency differences.
Furthermore, the sweep frequency control system 2 rapidly obtains the stimulating sound signals of different frequencies by adjusting and controlling parameters such as the adjusting range of the difference frequency, the frequency difference stepping and the like, and covers at least one formant of the target tissue, so as to realize that the continuously increasing or decreasing difference frequency vibration sound is adopted to stimulate the tissue in the confocal area within the adjusting range of the difference frequency.
Specifically, in order to generate low-frequency vibrations with different frequency differences in the confocal region, firstly, a sweep frequency control system 2 sends an instruction to an ultrasonic signal generator 3 from low to high in a certain frequency difference step within a certain frequency range to generate ultrasonic signals with different frequency differences, the ultrasonic signals are transmitted to a difference frequency focusing ultrasonic transducer 5, and two groups of difference frequency focusing ultrasonic waves with different frequency differences are generated by the difference frequency focusing ultrasonic transducer 5 (which may include a first transducer group and a second transducer group … … N). Alternatively, the sweep frequency control system 2 commands the ultrasonic signal generator 3 from high to low in steps of a certain frequency difference.
Preferably, the focusing mode of the difference frequency focusing ultrasonic transducer 5 is a melon-petal structure or a ring-shaped array structure or an even number element structure. The melon petal structure divides the concave spherical surface ceramic into 8 array elements with the same size, and the odd array elements and the even array elements are respectively connected in parallel. The annular array divides the concave spherical ceramic in the axial direction and cuts the concave spherical ceramic into 2 array elements with the same area. The multi-array element structure is characterized in that hundreds of small-diameter array elements are uniformly distributed on a framework of a concave spherical surface and controlled by geometric distance or computer electronic sound holes, so that the focusing target is achieved.
The ultrasound resonance imaging system of the present embodiment further includes: the system comprises a vibration sound signal acquisition system 7, a vibration sound signal analysis and display system 8 and a resonance acoustic image analysis and display system 9.
The vibration acoustic signal acquisition system 7 in this embodiment is configured to acquire an echo signal emitted by a low-frequency vibration tissue; the vibration sound signal analysis and display system 8 obtains the resonance frequency and the resonance amplitude of the tissues in the confocal area by analyzing the received echo signals; the resonance acoustic image analysis and display system 9 receives the vibration signal and analyzes the resonance frequency and amplitude of a plurality of continuous confocal areas input by the display system 8 to form a resonance frequency and amplitude distribution diagram of the target area.
The vibration sound signal acquisition, analysis and display system in this embodiment is used for receiving and analyzing echo signals emitted to the surroundings by the confocal area tissue under the difference frequency vibration sound stimulation, and acquiring the resonance frequency and the resonance amplitude of the confocal area tissue.
Specifically, the vibration acoustic signal acquisition, analysis and display system in this embodiment includes: a vibration sound signal acquisition system 7 and a vibration sound signal analysis and display system 8. The vibration sound signal acquisition system 7 is used for receiving echo signals of tissues in a confocal area and transmitting the echo signals to the vibration sound signal analysis and display system 8 for processing. The vibro-acoustic signal analysis display system 8 includes a vibro-acoustic signal display system 81 and a vibro-acoustic signal analysis system 82, and the vibro-acoustic signal display system 81 includes a preamplifier 811, a filter 812, and a digital oscilloscope 813. The vibration sound signal acquisition system 7 can be arranged around the machine body, can be a hydrophone, can adopt two receiving modes of a water tank signal and a body signal, and lays flexible sound absorption rubber on the water surface for reducing the influence of surface reflection. Preferably, the hydrophone is provided with a water tank, and sound absorption rubber is paved on the water surface of the water tank, so that the influence of surface reflection is reduced conveniently.
In the present embodiment, the vibration acoustic signal collection system 7 is configured to receive echo signals generated after the confocal area focuses the ultrasound stimulation at the difference frequency with different frequency differences, and convert the echo signals into digitized echo signals in the vibration signal display system 81. Specifically, the echo signal received by the vibro-acoustic signal acquisition system 7 is transmitted to a preamplifier 811 in the vibro-acoustic signal display system 81 for amplification, the echo signal is further transmitted to a filter 812 unit in the vibro-acoustic signal display system 81, the filter 812 filters clutter signals in the echo signal by low-pass/high-pass or other methods, and finally the echo signal is transmitted to a digital oscilloscope 813 in the vibro-acoustic signal display system 81 for imaging and displaying, as shown in fig. 5. The resonant frequency and the resonant amplitude of each confocal area are obtained by associating the vibration sound signal analysis system 82 with a main control computer. Referring to fig. 4, a formant map of the confocal region of the present embodiment shows the relationship between USAE sound pressure amplitude and difference frequency, where the region 17 is a ganglion formant region, the region 18 is an adipose tissue formant region, and the corresponding frequencies are the respective formant frequencies.
The resonance acoustic image analysis and display system 9 of the present embodiment obtains the resonance frequency and amplitude distribution map of the target region by acquiring and analyzing the resonance frequencies of a plurality of continuous confocal areas of the target region in the body transmitted by the vibration acoustic signal analysis system 82, see fig. 5.
The acoustic resonance system of the embodiment uses stresses of different degrees generated by low-frequency vibration of different frequencies generated by mutual cooperation of the sweep frequency control system and the ultrasonic signal generator as a mapping source, and uses the mapping source to continuously tap the confocal area tissue, the confocal area tissue vibrates back under the action of the stress frequencies of different degrees and emits corresponding low-frequency echo signals to the periphery, and the vibration acoustic signal acquisition system receives the echo signals to obtain the resonance frequency and the resonance amplitude of the confocal area. In the case of confocal zone sizing, the resonant frequency is related to the tissue elastic modulus, tissue ultrasound absorption and scattering properties, and thus different tissues have their specific resonant frequencies. The target region is continuously detected at multiple points in the above manner, so that the respective resonance frequency of each confocal region in the target region can be obtained, and finally, the tissue-specific resonance frequency and amplitude distribution map of the target region can be obtained by analyzing and imaging through the resonance sonogram analysis and display system 9, referring to fig. 5. The distribution map reflects various physical properties of tissues in a target area, such as elasticity, mechanics, resonance and the like, and forms a novel imaging method which is characterized by the resonance generated by the tissues.
In this embodiment, a three-dimensional motion scanning system 4 is provided, and the three-dimensional motion scanning system 4 includes a motion controller; the motion controller comprises a digital processing chip (DSP), the digital processing chip is matched with the main control computer 1 and receives the instruction of the main control computer 1, the focusing ultrasonic transducer is controlled to carry out three-dimensional arbitrary surface motion relative to the target area, and meanwhile, the arbitrary surface of the target area with the target point is scanned.
In the three-dimensional motion scanning system 4 in this embodiment, when performing physical detection, the focused ultrasound transducer is controlled to perform three-dimensional arbitrary surface motion relative to the target region, and arbitrary three-dimensional scanning can be performed on a to-be-detected part, so that the vibro-acoustic acquisition and analysis system obtains a more comprehensive resonance frequency and amplitude distribution map, thereby accurately obtaining a detection surface. When the physiological signal is detected, the focus is not limited by an anatomical structure, and two-dimensional or three-dimensional scanning can be performed at any point of the solid tissue, so that the same focus is realized during mapping and ablation treatment. In the conventional physiological detection, due to the absence of the three-dimensional motion scanning system 4, the stimulation of the physiological detection in the blood vessel is limited by space, and the physiological detection cannot be detected if the nerve is far away from the blood vessel.
When the difference frequency focusing ultrasonic transducer 5 works, the high-power ultrasonic transducer works at high power and is easy to generate heat, and bubbles can appear in water at high temperature to perform ultrasonic image processing. Therefore, in this embodiment, a degassing water circulation system 6 is further provided, which is used to cool the difference frequency focused ultrasound transducer 5 and remove bubbles.
The ultrasound resonance imaging system of the present embodiment further includes: a treatment planning unit 10, a basic imaging unit 11, an image overlaying unit 12 and a physiological signal detection system 13.
The treatment planning unit 10 in this embodiment obtains a target point by comparing the target region resonance frequency and amplitude distribution map with the resonance frequency and amplitude of the common tissue of the human body prestored in the main control computer; the physiological detection system 13 obtains the mapping points by receiving the physiological signals of the excitable tissues acted on the detection surface by the low-frequency vibration, and monitors the responsiveness of the target tissues to the vibration sound stimulation before and after ablation.
The treatment planning unit 10 analyzes and displays the resonance frequency and amplitude distribution diagram of the target area transmitted by the system 9 through receiving the resonance acoustic image, compares the resonance frequency and amplitude distribution diagram with the resonance frequency and amplitude of the common tissues of the human body pre-stored in the treatment planning unit 10, displays the anatomical structure and the tissue distribution state of the target area through gray level images, three-dimensional histograms, pseudo-color images and the like, and visually displays the treatment plan for suggesting an intervention point or an intervention area. The treatment plan comprises therapeutic means such as ablation, liquefaction, acoustic power, physical therapy, interventional operation and the like.
The basic image unit 11 comprises an ultrasonic image probe and an ultrasonic image host, and further, the basic image unit 11 comprises an ultrasonic image probe, a magnetic resonance coil, a nuclear medicine detector and an imaging display unit; the ultrasonic image probe is arranged on the difference frequency focusing ultrasonic transducer 5, can flexibly turn, and can perform two-dimensional and three-dimensional Doppler blood flow imaging when the difference frequency ultrasonic works; ultrasound, magnetic resonance or radionuclide imaging is formed as a base image of the system.
The overlay image unit 12 overlays and combines the gray-scale image, the three-dimensional histogram, the pseudo-color image outputted by the treatment planning unit 10 and the doppler blood flow imaging outputted by the basic image unit 11, and is used for providing image support during ablation, searching a treatment target point and a scanning plane, and setting a delivery site of treatment energy through the three-dimensional motion of the treatment unit by using a virtual focus of the treatment target point and the scanning plane.
The main control computer 1 of the embodiment receives the image from the super-basic image unit and the tissue resonance frequency and amplitude distribution diagram containing the proposed ablation target point so as to send a detection signal or a working signal of a difference frequency focusing transducer required by treatment; the main control computer 1 sends a three-dimensional motion or scanning motion signal to the three-dimensional motion scanning system 4, and simultaneously sends a difference frequency detection or treatment same frequency to the difference frequency focusing ultrasonic transducer by using the frequency scanning control system 2 to control the ultrasonic transducer to work; the main control computer 1 also automatically controls the start, record and analysis of the degassing water circulation system 6, the vibration sound signal acquisition and analysis display system and the physiological signal detection system 13.
The ultrasonic resonance imaging system constructs a resonance frequency and amplitude distribution diagram by acquiring the resonance frequency and amplitude of each confocal area in the target area, and compares the resonance frequency and amplitude with the resonance frequency and amplitude of common tissues of a human body prestored in the system, so that the tissue distribution state of the target area and the accurate position of an ablation target point are accurately reflected. Wherein, in the case of confocal zone sizing, the resonant frequency is related to the tissue elastic modulus, tissue ultrasound absorption and scattering properties, and thus different tissues have their specific resonant frequencies. The system receives the difference frequency vibration sound with different frequency differences to carry out plane or three-dimensional continuous scanning on a target area to obtain the resonance frequency and the resonance amplitude, compares the resonance frequency and the resonance amplitude with the resonance frequency and the resonance amplitude of common tissues of a human body preset in the system, can determine the tissue distribution state of the target area, carries out two-dimensional or three-dimensional display on different tissue compositions and tissue function states in the modes of gray scale, histogram, pseudo color and the like, and finally visually presents a target point needing intervention.
A physiological signal detection system 13 is further included in the present embodiment, and fig. 3 is a block diagram of the physiological signal detection system 13. In this embodiment, a vibro-acoustic physiological signal recording and analyzing system is provided, and the physiological signal detecting system 13 includes a multi-channel physiological recorder 131; the multi-channel physiological recorder 131 is provided with various sensors, can acquire various physiological parameters in real time, can be used for acquiring various invasive or non-invasive physiological signals, and can acquire various physiological parameters in real time. Specifically, the multi-channel physiological recorder 131 is provided with various sensors, can acquire various physiological parameters in real time, and has the functions of invasive or non-invasive blood pressure recording, respiratory movement recording, standard electrocardiogram recording, limb electromyogram recording, a body position movement sensor, a body surface resistance sensor, a computer physiological signal analysis system, physiological signal change dynamic analysis and the like.
In this embodiment, the physiological signal detection system 13 is further provided with a vibration acoustic physiological signal auxiliary judgment system 132; the vibration acoustic physiological signal auxiliary judging system 132 is used for assisting in judging the positive mapping points and the distribution state of the target ganglia.
The specific principle of the physiological signal detection system 13 is as follows: the excitable tissue of the living body responds to certain stimuli, and whether the site to which the stimulus is applied is at the correct point is evaluated by applying the stimulus to the excitable tissue and observing whether the biological tissue exhibits a specific response. The ultrasonic resonance system of the embodiment constructs a resonance frequency and amplitude distribution diagram by acquiring the resonance frequency and amplitude of each confocal area in the target area, and compares the resonance frequency and amplitude with the resonance frequency and amplitude of common tissues of a human body prestored in the system, so that the tissue distribution state of the target area and the accurate position of an ablation target point are accurately reflected. Preferably, the physiological signal detection system 13 in this embodiment is configured to pick up a physiological signal of the low-frequency vibration acting on the target point to obtain a target point, and further perform accurate mapping on the target point.
Example 2 ultrasound resonance imaging System guidance for ablation of aorticorenal ganglion for treatment of refractory hypertension
According to the diagnosis result of the ultrasonic resonance imaging system of the above embodiment 1, the accurate position of the ablation target point and the resonance frequency of the target point can be determined, so on the basis of this embodiment 1, the present application embodiment 2 provides an ultrasonic resonance imaging system for guiding the ablation of the aorticorenal ganglion to treat the refractory hypertension. The ultrasonic resonance imaging system of the embodiment constructs a resonance frequency and amplitude distribution diagram by acquiring the resonance frequency and amplitude of each confocal area in the target area, and compares the resonance frequency and amplitude with the resonance frequency and amplitude of common tissues of a human body pre-stored in the system, so as to accurately reflect the tissue distribution state and the ablation target position of the target area, namely the accurate position of the aorticorenal ganglion.
In the present embodiment, when refractory hypertension is treated, the distribution state of aorticorenal ganglion in fat (perirenal fat capsule) background can be displayed through the resonance frequency and amplitude distribution diagram. As illustrated with reference to fig. 5, the differently colored regions represent different resonant frequencies, and in fig. 5 the target region includes a region 14 having a resonant frequency of 42 khz, a region 15 having a resonant frequency of 44khz, and a region 16 having a resonant frequency of 45 khz. Wherein, the region 14 is the position of renal artery blood vessel, the region 15 is the position of renal ganglion of artery, and the region 16 is the position of fat.
In addition, in this embodiment, since the aorticorenal ganglion is excitable tissue, the physiological mapping verification can be performed on the ablation target site by the physiological signal detection system 13. And further, the accurate position of the aorticorenal in the target area is determined through the resonance frequency and the amplitude distribution diagram, and the position of the aorticorenal ganglion is verified again through physiological stimulation.
For example, in this embodiment, when refractory hypertension is treated, the system releases a moderate amount of acoustic energy to act on aorticorenal ganglion, which causes sympathetic excitation, and causes symptoms such as increased blood pressure, increased heart rate, decreased heart rate variability, altered respiration, increased muscle tone, cutaneous vasoconstriction, sweating, and increased myoelectrical excitation. Obtaining a blood pressure change response through an invasive pressure sensor; the electrocardio recorder records the heart rate and can analyze the heart rate variability; the motion sensor acquires respiratory motion and muscle motion information; the skin temperature and impedance sensor can obtain information such as vasoconstriction and sweating; the myoelectric sensor can record myoelectric information and the like, and the physiological information has great expandability. When the region of interest is detected point by point in two or three dimensions, some points can be found to respond to one or more indexes, which indicates that the stimulation points accurately stimulate the aorticorenal ganglion, otherwise, the stimulation points are not distributed in the position of the ganglion.
In this embodiment, the physiological signal detecting system 13 further includes a vibration acoustic physiological signal auxiliary determining system 132, which is mainly used to further refine the position of the aorticorenal ganglion and reduce the interference of other factors.
In this embodiment, the physiological signal detecting system 13 is used to record whether the specific response of the observed biological tissue occurs to evaluate whether the stimulation site is at the correct point, and can detect whether the ablation is complete at the ablation stage. And after the focused ultrasound ablation is carried out on the stimulation positive point, stimulating the point again, if no response exists, indicating that the aorticorenal ganglion tissues of the point are ablated completely, otherwise, indicating that the ablation is incomplete.
The ultrasonic resonance imaging system takes stress generated by low-frequency vibration generated by the dual-frequency ultrasonic transducer as a mapping source, adjusts the frequency of the stress of the mapping source by regulating and controlling the frequency difference of two groups of confocal ultrasonic beams through the sweep frequency control system, and performs 'tapping' on confocal area tissues at different frequencies. The mapping source is carried out in vitro, good acoustic coupling can be realized without any electrode or catheter entering the body, and noninvasive treatment of deep target tissues can be realized.
On the other hand, if the resonance is not well controlled during the ultrasonic diagnosis or the ultrasonic therapy, unnecessary tissue damage may be caused to the patient, causing injury. In this case, in the ultrasound resonance imaging system of this embodiment, the resonance frequency of the aorticorenal ganglion is found while the precise position of the aorticorenal ganglion is found by the dual-frequency focusing ultrasound resonance imaging system, and during the interventional therapy, the resonance frequency of the aorticorenal ganglion, in this embodiment, the resonance frequency of 44kHz, is selected, and the lower therapy power is selected to ablate the aorticorenal ganglion. During the ablation, strong mechanical effect, cavitation effect and thermal effect are generated only in the region of the aorticorenal ganglion, obvious damage is generated to the aorticorenal ganglion, and non-specific damage to surrounding tissues is further reduced. The tissue-specific diagnosis and treatment are achieved by adjusting the physical parameters, thereby reducing side effects and improving the curative effect of the treatment.
The tissue of the ablation target point in the target area resonates under the action of difference frequency vibration sound with the same resonant frequency as the tissue of the ablation target point, the vibration amplitude of the tissue of the target is obviously increased compared with other types of surrounding tissues, and the mechanical effect is obviously enhanced. Therefore, the target tissue can be specifically ablated by giving lower treatment power under the resonance frequency, the damage to other tissues caused by mechanical effect and thermal effect is reduced to a greater extent, and the effectiveness and the safety of the focused ultrasound ablation treatment are further improved. For example, in the treatment of refractory hypertension, specific ablation of aorticorenal ganglia can be achieved at the resonance frequency and treatment power of the ganglion tissue, further reducing the damage of the focused ultrasound to the surrounding fat and vascular tissue in the non-resonance state.
In the case of confocal zone sizing, the resonance frequency is related to the tissue elastic modulus, tissue ultrasound absorption and scattering properties, and therefore different tissues have their specific resonance frequency and resonance amplitude. Receiving, analyzing and imaging the resonance frequency and amplitude of a plurality of continuous confocal areas of the target area to obtain a resonance frequency and amplitude distribution map of the target area, and then comparing the resonance frequency and amplitude with the resonance frequency and amplitude of common tissues of the human body prestored in the system to reflect the tissue distribution state of the target area; the resonance frequency and amplitude distribution diagram is displayed in two-dimensional or three-dimensional manner by means of gray scale or pseudo color according to the resonance frequency and amplitude of each confocal area. The treatment plan of the proposed ablation is visually displayed in pseudo-color after the resonance frequency and amplitude signals of the aorticorenal ganglion are acquired in large quantities.
The information image is superposed on a two-dimensional and three-dimensional Doppler blood flow image of a target area to provide image support during intervention, and a virtual focus of the information image is utilized to set a delivery site of treatment energy through three-dimensional motion of a treatment unit.
The degassing water circulation system 6 in this embodiment is provided with a degassing membrane; the degassing membrane is a polypropylene hollow fiber membrane filled with hydrophobicity. The scheme of degassing by adopting a degassing membrane, wherein the degassing membrane is a polypropylene hollow fiber membrane filled with hydrophobicity, and has the characteristics of large filling density, large contact area and uniform water distribution. The liquid phase and the gas phase are in contact with each other on the surface of the membrane, and since the membrane is hydrophobic, water cannot permeate the membrane, but gas can easily permeate the membrane. The degassing is achieved by gas migration through concentration differences. The hydrophobic hollow fiber degassing membrane is adopted, and the degassing speed is more than 20L/h. The deoxidation rate is less than 3 ppm.
Example 2 ultrasonic resonance imaging System guidance ablation treatment of Primary liver cancer
Primary liver cancer accounts for 18% of all malignant tumors, with the second mortality rate. The primary liver cancer has hidden onset, rapid progress and high malignancy, and once the primary liver cancer is found to lose operation chances, the radiotherapy and chemotherapy effect is not ideal. HIFU as a non-invasive, effective and safe treatment method plays an important role in the comprehensive treatment of middle and late stage liver cancer patients, and can improve the 1-year survival rate to about 50%. On one hand, the deep position of part of the liver cancer focus has the problems of insufficient sperm positioning and damage of surrounding adjacent tissues depending on the guidance of ultrasonic images; on the other hand, the focused ultrasound ablation energy is large, the heat effect is obvious, and the damage to the surrounding normal liver tissues and important blood vessels can also be caused. Therefore, there is still a need for a method of ablation of liver cancer with better imaging effect and more selective treatment.
For more clear description of the technical solution, "target point" and "target area" are defined in the following schemes, target area: specific body tissues containing the "target site" include: in primary liver cancer treatment, the target region refers to liver tissue containing complete liver cancer tissue, and the target spot refers to liver cancer tissue.
In the embodiment of the present application, in order to generate low-frequency vibrations with different frequency differences that continuously increase or decrease in a target region inside a body, a sweep control system 2 sends an instruction to an ultrasonic signal generator 3 from low to high in a certain frequency difference step by step within a certain frequency range to generate ultrasonic signals with different frequency differences, the ultrasonic signals are transmitted to a difference frequency focused ultrasonic transducer 5, and the difference frequency focused ultrasonic transducer 5 (which may include a first and a second … … nth transducer groups) generates two groups of difference frequency focused ultrasound with different frequency differences.
The frequency-sweep control system 2 adjusts the lower difference frequency focusing ultrasonic transducer 5 to emit focusing acoustic beams with different frequency differences, and after the focusing acoustic beams act on a confocal area of a target area, different echo signals are generated due to different radiation force frequencies of difference frequency vibration sound; the echo signal is received by the vibration acoustic signal acquisition system 7, and after being amplified by the preamplifier 811 and filtered by the filter 812 in the vibration acoustic signal display system 81, the echo signal is finally converted into a digitized echo signal, and is displayed on the digital oscilloscope 813, and is associated with the main control computer 1 through the vibration acoustic signal analysis system 82, so as to obtain the resonance frequency and the resonance amplitude of each confocal area. Further, the vibration acoustic signal acquisition system 7 is a hydrophone, and can adopt two receiving modes of a water tank signal and a body signal.
The vibration acoustic signal analysis system 82 of this embodiment transmits the resonance frequency and amplitude of each continuous confocal area in the target area obtained by analysis to the resonance acoustic image analysis display system 9, and performs conversion operation to obtain the resonance frequency and amplitude distribution map of the target area; the target region resonance frequency and amplitude distribution map is compared with the human body common tissue resonance frequency and amplitude pre-stored in the treatment planning unit 10 to determine the distribution state of various anatomical tissues in the target region, and the distribution state is displayed in two dimensions or three dimensions in the gray scale, histogram, pseudo color and other ways, so that the target point to be treated, in this embodiment, the primary liver cancer tissue, is finally visually presented.
The image superposition unit 12 superposes and combines the gray-scale image, the three-dimensional histogram, the pseudo-color image and the doppler blood flow image output by the ultrasound image unit 11, which are output by the treatment planning unit 10, and is used for providing image support during further physiological mapping, and finding a mapping target point and a scanning plane.
Imaging of the resonance frequency and amplitude distribution diagram of the target region is completed, the target point is determined, namely after the distribution condition and the resonance frequency of the liver cancer tissue in the target region are determined, an operator selects the target point suitable for ablation, an ablation instruction is sent out through the main control computer 1, the ablation instruction can be ablated according to the resonance frequency and specific treatment power of the liver cancer tissue, the instruction is transmitted to the ultrasonic signal generator 3, two or more focused ultrasonic sound beams with the same frequency are generated, and ultrasonic ablation is carried out on the target point according to a synthetic image generated by the basic image unit 11 and the image superposition unit 12.
Example 3 ultrasound resonance imaging System for directing reperfusion therapy in ischemic stroke
Acute thrombosis or thromboembolism is the main cause of ischemic stroke, and early reperfusion therapy is the key to successful treatment of ischemic stroke. The existing reperfusion therapy modes of ischemic stroke mainly comprise intravenous thrombolysis and cerebrovascular interventional therapy. On one hand, due to the fact that the bleeding risk of part of cerebral apoplexy patients is high, clear thrombolytic contraindications exist; on the other hand, the cerebrovascular interventional therapy operation is difficult, so that the operation is not widely performed in most hospitals nationwide at present. Therefore, there is still an urgent need to find a safe, effective and convenient reperfusion therapy for ischemic stroke.
For more clear description of the technical solution, "target point" and "target area" are defined in the following schemes, target area: specific body tissues containing the "target site" include: in reperfusion therapy of ischemic stroke, the target region refers to brain tissue containing diseased blood vessels and thrombus, and the target site refers to thrombus.
In the embodiment of the present application, in order to generate low-frequency vibrations with different frequency differences that continuously increase or decrease in a target region inside a body, a sweep control system 2 sends an instruction to an ultrasonic signal generator 3 from low to high in a certain frequency difference step by step within a certain frequency range to generate ultrasonic signals with different frequency differences, the ultrasonic signals are transmitted to a difference frequency focused ultrasonic transducer 5, and the difference frequency focused ultrasonic transducer 5 (which may include a first and a second … … nth transducer groups) generates two groups of difference frequency focused ultrasound with different frequency differences.
The frequency-sweep control system 2 adjusts the lower difference frequency focusing ultrasonic transducer 5 to emit focusing acoustic beams with different frequency differences, and after the focusing acoustic beams act on a confocal area of a target area, different echo signals are generated due to different radiation force frequencies of difference frequency vibration sound; the echo signal is received by the vibration acoustic signal acquisition system 7, and after being amplified by the preamplifier 811 and filtered by the filter 812 in the vibration acoustic signal display system 81, the echo signal is finally converted into a digitized echo signal, and is displayed on the digital oscilloscope 813, and is associated with the main control computer 1 through the vibration acoustic signal analysis system 82, so as to obtain the resonance frequency and the resonance amplitude of each confocal area. Further, the vibration acoustic signal acquisition system 7 is a hydrophone, and can adopt two receiving modes of a water tank signal and a body signal.
The vibration acoustic signal analysis system 82 of this embodiment transmits the resonance frequency and amplitude of each continuous confocal area in the target area obtained by analysis to the resonance acoustic image analysis display system 9, and performs conversion operation to obtain the resonance frequency and amplitude distribution map of the target area; the target region resonance frequency and amplitude distribution map is compared with the human body common tissue resonance frequency and amplitude pre-stored in the treatment planning unit 10 to determine the distribution state of various anatomical tissues in the target region, and the distribution state is displayed in two-dimensional or three-dimensional manner in gray scale, histogram, pseudo-color and other manners, so that the target point to be treated, namely the thrombus tissue in the embodiment, is finally visually presented.
The image superposition unit 12 superposes and combines the gray-scale image, the three-dimensional histogram, the pseudo-color image and the doppler blood flow imaging output by the ultrasound imaging unit 11, which are output by the treatment planning unit 10, for further guiding the sonothrombolysis treatment.
Imaging of the resonance frequency and amplitude distribution diagram of the target area is completed, the target point is determined, namely after the distribution condition and the resonance frequency of the thrombus tissue in the target area are determined, an operator selects the target point suitable for ablation, an ablation instruction is sent out through the main control computer 1, the ablation instruction can be used for thrombolysis according to the resonance frequency and specific treatment power of the thrombus tissue, the instruction is transmitted to the ultrasonic signal generator 3 to generate two or more focused ultrasonic sound beams with the same frequency, and ultrasonic thrombolysis is carried out on the target point according to a synthetic image generated by the basic image unit 11 and the image superposition unit 12.
The ultrasonic resonance imaging system of the invention forms a focus at the deep part of an organism by high-frequency focused ultrasound, forms a 'knocking' force by using a difference frequency confocal ultrasonic interference principle to generate mechanical stress of low-frequency vibration sound at the focus, adjusts the frequency difference (delta f) of two confocal ultrasonic beams by a sweep frequency control system to adjust the frequency of the mechanical stress of a tissue in a confocal area so as to detect the resonance frequency and amplitude of the tissue and perform imaging, creates a 'resonance frequency imaging' positioning method at the deep part of the organism by using the difference frequency focused ultrasound, combines the monitoring of a physiological detection system, guides a focused ultrasound energy treatment and curative effect verification system method, and provides wide application prospects for mapping, regulation, ablation treatment and the like of the deep part of the organism. The acoustic resonance system employs a method of detecting the "resonance frequency and amplitude" to obtain a formant frequency and amplitude profile of the tissue in the target region. The distribution map reflects various physical properties of tissues in a target area, such as elasticity, mechanics, resonance and the like, and forms a novel imaging method which is characterized by the resonance generated by the tissues. The tissue of the target point of ablation in the target area resonates under the action of the difference frequency vibration sound with the same resonant frequency as the tissue of the target area, the vibration amplitude of the target tissue is obviously increased compared with other types of tissue, and the mechanical effect is obviously enhanced. Therefore, the target tissue can be specifically intervened by applying lower treatment power under the resonance frequency of the target tissue, the damage to other tissues caused by mechanical effect and thermal effect is reduced to a greater extent, and the effectiveness and safety of focused ultrasound intervention are further improved. The resonance imaging system controls the ultrasonic signal generator through the main control computer frequency sweeping control system, and adjusts the frequency difference (delta f) of the two groups of confocal ultrasonic beams to detect the resonance frequency of the tissues in the confocal area. The mapping source is carried out in vitro, good acoustic coupling can be realized without any electrode or catheter entering the body, and noninvasive treatment of deep target tissues can be realized; anatomical and tissue distribution information of deep tissue can be obtained by resonance frequency imaging. The resonance imaging system is provided with a three-dimensional motion scanning system, and when the resonance frequency and the amplitude are detected, the focused ultrasonic transducer is controlled to carry out three-dimensional arbitrary surface motion relative to a target area, and arbitrary three-dimensional scanning can be carried out on a part to be detected, so that the vibration sound signal acquisition and analysis system obtains a more comprehensive resonance frequency and amplitude distribution diagram, and a detection surface is accurately obtained. When the physiological signal is detected, the focus is not limited by an anatomical structure, and two-dimensional or three-dimensional scanning can be performed at any point of the solid tissue, so that the same focus is realized during mapping and ablation treatment. However, in the conventional physiological detection, due to the absence of a three-dimensional motion scanning system, the stimulation of the physiological detection in the blood vessel is limited by space, and the physiological detection cannot be detected if the nerve is far away from the blood vessel.
The above description is only a preferred embodiment of the present invention, and it should be noted that, for those skilled in the art, several modifications and additions can be made without departing from the method of the present invention, and these modifications and additions should also be regarded as the protection scope of the present invention.
Claims (8)
1. An ultrasonic resonance imaging system comprising: the difference frequency vibration sound generating mechanism is used for forming incremental or degressive difference frequency vibration sound and stimulating the confocal area to organize to generate echo signals; it is characterized by also comprising: the vibration sound signal acquisition, analysis and display system is used for receiving and analyzing echo signals generated by the tissues in the confocal area and acquiring the resonance frequency and the resonance amplitude of the tissues in the confocal area; and the resonance acoustic image analysis and display system (9) is used for receiving and analyzing the resonance frequency and the resonance amplitude of a plurality of continuous confocal area tissues in the target area to form a distribution map of the resonance frequency and the resonance amplitude of the target area.
2. The ultrasonic resonance imaging system of claim 1, wherein the ultrasonic wave generating means comprises a dual-frequency ultrasonic signal generator (3) for generating two sets of different frequency signals, and the two sets of different frequency signals are focused by a difference frequency focusing ultrasonic transducer (5) to form two sets of different frequency confocal ultrasonic beams; and the sweep frequency control system (2) is associated with the main control computer (1) and generates continuous increasing or decreasing difference frequency vibration sound by regulating and controlling the frequency difference of the two groups of confocal ultrasonic beams.
3. The ultrasonic resonance imaging system of claim 2, wherein the vibro-acoustic signal acquisition, analysis and display system comprises: a vibroacoustic signal acquisition system (7) for receiving the echo signals generated by the confocal area tissue; and a vibration sound signal analysis and display system (8) for acquiring the resonance frequency and the resonance amplitude of the tissues in the confocal area by analyzing the received echo signals.
4. The ultrasonic resonance imaging system of claim 3, wherein the vibro-acoustic signal analysis and display system (8) comprises a vibro-acoustic signal display system (81) and a vibro-acoustic signal analysis system (82), wherein the vibro-acoustic signal display system (81) converts the echo signals into digitized signals and displays them; the vibration sound signal analysis system (82) obtains the formant of the tissue in the confocal area by analyzing the sound pressure amplitude of the echo signal, and obtains the resonance frequency corresponding to the formant by associating with the sweep frequency control system (2).
5. The ultrasonic resonance imaging system of claim 4, wherein the vibrating acoustic signal display system (81) comprises: a preamplifier (811), a filter (812), and a digital display (813).
6. The ultrasonic resonance imaging system of claim 2, further comprising a three-dimensional motion scanning system (4) for controlling the difference frequency focused ultrasonic transducer (5) to perform three-dimensional arbitrary surface motion relative to the target region to scan an arbitrary surface of the target region.
7. The ultrasonic resonance imaging system of claim 2, further comprising a treatment planning unit (10) for analyzing and displaying the distribution map of the resonance frequency and the resonance amplitude in the target region transmitted by the system (9) by receiving the resonance sonogram, and comparing and analyzing the distribution map with the resonance frequency and the resonance amplitude of the common tissues of the human body in advance to determine the distribution of the target point in the target region.
8. An ultrasound resonance imaging system according to claim 2, further comprising a degassing water circulation system (6) provided with a degassing membrane; the degassing membrane is a polypropylene hollow fiber membrane filled with hydrophobicity.
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