CN113143326B - Forward-looking 3D endoscopic ultrasonic system and imaging method - Google Patents
Forward-looking 3D endoscopic ultrasonic system and imaging method Download PDFInfo
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Classifications
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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
- A61B8/12—Diagnosis using ultrasonic, sonic or infrasonic waves in body cavities or body tracts, e.g. by using catheters
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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
- A61B8/08—Detecting organic movements or changes, e.g. tumours, cysts, swellings
- A61B8/0891—Detecting organic movements or changes, e.g. tumours, cysts, swellings for diagnosis of blood vessels
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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
- A61B8/4483—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device characterised by features of the ultrasound transducer
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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
- A61B8/48—Diagnostic techniques
- A61B8/483—Diagnostic techniques involving the acquisition of a 3D volume of data
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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
- A61B8/58—Testing, adjusting or calibrating the diagnostic device
Abstract
The invention relates to a forward-looking 3D endoscopic ultrasonic system and an imaging method, wherein the endoscopic ultrasonic system comprises a host, a display, an endoscopic catheter and a communicating vessel, wherein the endoscopic catheter comprises an inner catheter and an outer sleeve which are coaxially and relatively rotatably arranged, the forward-looking 3D endoscopic ultrasonic system also comprises an ultrasonic transducer arranged at the front end of the inner catheter and an end plate arranged at the front end part of the outer sleeve, the working surface of the ultrasonic transducer faces towards the end plate and is arranged close to the inner wall of the end plate, stripes are formed on the end plate, the transmission path of ultrasonic waves emitted by the ultrasonic transducer through the stripe areas changes along with the change of the stripes, and phase delay is formed. According to the invention, through the arrangement of the inner catheter and the outer sleeve which rotate relatively, and the single ultrasonic transducer with the working surface facing the stripes, under a plurality of relative rotation angles, the data information of ultrasonic excitation and echo signal receiving is obtained, so that the 3D image is accurately reconstructed, and the three-dimensional image reconstruction device is simple in structure and low in cost.
Description
Technical Field
The invention belongs to the technical field of clinical medical treatment, and particularly relates to a forward-looking 3D endoscopic ultrasonic system and an imaging method of the forward-looking 3D endoscopic ultrasonic system.
Background
As is well known, in vivo ultrasound imaging, which mainly includes intravascular ultrasound imaging, digestive ultrasound endoscopy, ultrasound bronchoscopy, etc., has become an important tool for diagnosis of cardiovascular diseases, digestive and respiratory diseases and assisting in minimally invasive treatment at present. The 3D imaging can display the tissue structure more stereoscopically, can provide more visual information for the vascular stenosis, plaque distribution, tumor lesion volume, infiltration range and the like, and becomes a trend of development of related products in recent years.
However, there are two main approaches to ultrasound 3D imaging in vivo: a mechanical retraction mode 3D imaging is mostly mechanical rotation retraction of a single array element probe to form a 3D image, for example, an intravascular ultrasound and a high-frequency ultrasound endoscope mostly adopt the scheme, if the probe is a ring array or a linear array probe, rotation is not needed, but retraction or mechanical swabbing is also needed to form the 3D image; another is 3D imaging using electronic scanning, which requires an area or matrix probe to do so.
Therefore, regardless of which scheme is employed for 3D imaging, there are the following disadvantages:
1) Aiming at the components needing mechanical retraction, the real-time 3D imaging can not be realized, only a side view image can be formed, and a front view image can not be formed;
2) Aiming at the electronic scanning mode, the area array probe is required, the size of the area array probe is difficult to be made small, the price is quite high, in-vivo ultrasonic imaging is limited by volume limitations of blood vessels, alimentary tracts, bronchus and the like, and most of the area array probe is disposable, so that the area array probe is difficult to popularize and apply.
However, forward looking 3D images have a great clinical need, such as chronic total occlusion of the coronary arteries (cT 0), or imaging catheters that cannot be inserted through the lumen in the presence of an intraluminal thrombus, and imaging and diagnostic treatments. Meanwhile, in-vitro diagnostic methods such as CT cannot assess specific severity due to the inability to angiography after occlusion.
Disclosure of Invention
The invention aims to overcome the defects of the prior art and provide a forward-looking 3D endoscopic ultrasonic system.
Meanwhile, the invention also relates to an imaging method of the forward-looking 3D endoscopic ultrasonic system.
In order to solve the technical problems, the invention adopts the following technical scheme:
the utility model provides a forward-looking 3D endoscopic ultrasound system, it includes host computer, a display, the endoscopic catheter, and be used for being connected the intercommunication ware of host computer and endoscopic catheter, wherein the endoscopic catheter includes coaxial and relative rotation setting's inside pipe and outside sleeve pipe, forward-looking 3D endoscopic ultrasound system is still including setting up the ultrasonic transducer of inside pipe front end, the end plate of setting in outside sleeve pipe front end portion, wherein the working face of ultrasonic transducer is towards the end plate, and be close to the inner wall setting of end plate, be formed with the stripe on the end plate, the transmission path that the ultrasonic wave sent from ultrasonic transducer passed the stripe region changes along with the change of stripe, and form phase delay.
Preferably, the ultrasound transducer is fixed to the front end of the inner catheter and is arranged parallel to the end plate.
Preferably, the ultrasonic transducer has an operating frequency in the range of 1 to 60MHz and a diameter less than 3mm.
Specifically, the ultrasonic transducer is a piezoelectric ceramic, piezoelectric single crystal, piezoelectric composite or micro-capacitance sensor, and the sensor can emit and receive ultrasonic waves.
According to a specific and preferred aspect of the invention, a rotating handle is also provided at the rear end of the outer sleeve. Here, by rotating the rotating handle, the outer sleeve and the striped end plate are rotated to an angular position therewith, at which time the relative orientation of the stripes to the transducer has been changed, and the ultrasonic excitation and reception of echo signals by the ultrasonic transducer; and then, the rotation handle is rotated to the next angle position, the relative azimuth of the stripe board is changed again, the ultrasonic excitation and the echo signal receiving of the ultrasonic transducer are performed, and the like until the rotation handle is rotated for N angles, the ultrasonic excitation and the signal receiving of the echo signal of one rotation period are completed, so that under the N angles, a 3D image of the forward looking direction of the probe is reconstructed according to N groups of data information.
Meanwhile, in order to improve the imaging speed, the angle rotation of the imaging device can be realized by connecting and fixing the rotating handle with the motor and controlling the rotation of the motor.
According to yet another specific and preferred aspect of the present invention, the acoustic impedance of the stripes in the stripe region is different, mainly stripes, and may be formed by printing, ink-jetting, vapor-depositing, and bonding materials (such as fuel, paint, ink, metal, plastic, rubber, ceramic, silicon, etc.) with different thicknesses; the template structure can also be formed by laser etching and casting and has different thicknesses composed of the same material or mixed materials. The acoustic impedance of the material is different from that of the transducer, the periphery of the catheter and the medium of the working environment (such as blood in blood vessels, mucus in stomach and trachea, physiological saline and the like), so that the material is more beneficial to acquiring accurate data information under the angle corresponding to each rotating handle, and further the 3D image is accurately reconstructed.
Further, the end plate is further provided with a through hole for communicating the inner cavity of the outer sleeve with the outside from the front end portion. Therefore, the end plate can be used as a stripe structure on one hand, and on the other hand, the operation of water injection and the like of the guide pipe from the through hole can be facilitated.
In addition, for the convenience of subsequent clinical operation, a certain metal marker is arranged in the top area of the outer sleeve of the catheter, so that the position of the front end of the catheter can be conveniently observed and positioned in real time under CT and X-ray images. Meanwhile, if the catheter is used in an intravascular scenario, the catheter is small in size and inconvenient to deliver. A certain annular or perforated structure can be designed on the external sleeve, so that the catheter can quickly reach a diagnosis area along the interventional guide wire during operation. While the alimentary canal or bronchus with a larger space does not require the guide wire guiding structure.
Preferably, a coaxial cable is arranged in the inner catheter, and the ultrasonic transducer is communicated with the host computer through the coaxial cable. Not only is attractive in appearance, but also is more beneficial to data transmission.
The other technical scheme of the invention is as follows: an imaging method of a forward-looking 3D endoscopic ultrasonic system adopts the forward-looking 3D endoscopic ultrasonic system, and the imaging method comprises the following steps:
1) Firstly, a hydrophone is used for sound field test and calibration of a forward-looking 3D endoscopic ultrasonic system, specifically, the hydrophone arranged behind a striped end plate is opposite to an ultrasonic transducer in an excitation state, and the distance between the hydrophone and the forward-looking 3D endoscopic ultrasonic system is z 0 Recording the sound field intensity p of each position of its section 0 (x，y，z 0 And t), calculating the sound field intensity of each position of the sound field space behind the sound field by using the angular spectrum theory:
wherein F is 3D { } sumIs the fourier transform and inverse transform of the three-dimensional space,sgn (f) is a signed operation;
2) Convolving the obtained sound field intensity with the impulse response h (t) of the hydrophone according to the scattering sub-model and the sound field linear propagation theory to obtain the impulse echo signals corresponding to each position of the sound field space:
the obtained pulse echo signals are formed into a single space measurement matrixRotating the stripe board, changing the sound field distribution, repeating the above process to obtain multiple single space measurement matrixes +.>All matrices are combined into an integral spatial measurement matrix:
3) Selecting proper sparse matrix psi according to the compressed sensing theory to obtain a space sensing matrix
H＝ΦΨ (4)
Subsequently, the echo signals of the object to be measured are acquired by using the 3D imaging device, and the specific operation is as described above, so as to obtain N angle measurement signals r j (j=1, 2,., N), constitutes the observation signal
4) Substituting the observation signal u and the perception matrix H into a signal reconstruction equation, selecting a proper compressed perception reconstruction algorithm to solve the reconstruction equation, and reconstructing an original signal v:
u＝Hv (5)
wherein the method comprises the steps ofAnd theta are the reconstructed and original sparse signals respectively, θ=ψv and the sum of the values, I 1 And | I 2 Respectively 1 norm and 2 norm, epsilon being the defined acceptable reconstruction error magnitude;
5) And according to the reciprocity theorem, mapping the original signal and the spatial pixel distribution by using a linear inversion method to obtain the 3D ultrasonic image.
Due to the implementation of the technical scheme, compared with the prior art, the invention has the following advantages:
according to the invention, through the arrangement of the inner catheter and the outer sleeve which rotate relatively, and the single ultrasonic transducer with the working surface facing the stripes, under a plurality of relative rotation angles, the data information of ultrasonic excitation and echo signal receiving is obtained, so that the 3D image is accurately reconstructed, and the three-dimensional image reconstruction device is simple in structure and low in cost.
Drawings
FIG. 1 is a schematic front view of a front view 3D endoscopic ultrasound system of the present invention;
FIG. 2 is an enlarged partial schematic view of FIG. 1;
wherein: 1. a host; 2. a display; 3. an endoscopic catheter; 30. an inner conduit; 31. an outer sleeve; 4. a communicating vessel; 5. an ultrasonic transducer; 6. an end plate; 60. stripes; 61. a through hole; 7. the handle is rotated.
Detailed Description
The present invention will be described in detail with reference to the drawings and the detailed description, so that the above objects, features and advantages of the present invention can be more clearly understood. In the following description, numerous specific details are set forth in order to provide a thorough understanding of the present invention. The present invention may be embodied in many other forms than described herein and similarly modified by those skilled in the art without departing from the spirit of the invention, whereby the invention is not limited to the specific embodiments disclosed below.
In the description of the present invention, it should be understood that the terms "center", "longitudinal", "lateral", "length", "width", "thickness", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", "clockwise", "counterclockwise", "axial", "radial", "circumferential", etc. indicate orientations or positional relationships based on the orientations or positional relationships shown in the drawings are merely for convenience in describing the present invention and simplifying the description, and do not indicate or imply that the device or element being referred to must have a specific orientation, be configured and operated in a specific orientation, and therefore should not be construed as limiting the present invention.
Furthermore, the terms "first," "second," and the like, are used for descriptive purposes only and are not to be construed as indicating or implying a relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defining "a first" or "a second" may explicitly or implicitly include at least one such feature. In the description of the present invention, the meaning of "plurality" means at least two, for example, two, three, etc., unless specifically defined otherwise.
In the present invention, unless explicitly specified and limited otherwise, the terms "mounted," "connected," "secured," and the like are to be construed broadly, and may be, for example, fixedly connected, detachably connected, or integrally formed; can be mechanically or electrically connected; either directly or indirectly, through intermediaries, or both, may be in communication with each other or in interaction with each other, unless expressly defined otherwise. The specific meaning of the above terms in the present invention can be understood by those of ordinary skill in the art according to the specific circumstances.
In the invention, unless expressly stated or limited otherwise, a first feature "up" or "down" a second feature may be the first and second features in direct contact, or the first and second features in indirect contact through an intervening medium. Moreover, a first feature being "above," "over" and "on" a second feature may be a first feature being directly above or obliquely above the second feature, or simply indicating that the first feature is level higher than the second feature. The first feature being "under", "below" and "beneath" the second feature may be the first feature being directly under or obliquely below the second feature, or simply indicating that the first feature is less level than the second feature.
It will be understood that when an element is referred to as being "fixed" or "disposed" on another element, it can be directly on the other element or intervening elements may also be present. When an element is referred to as being "connected" to another element, it can be directly connected to the other element or intervening elements may also be present. The terms "vertical," "horizontal," "upper," "lower," "left," "right," and the like are used herein for illustrative purposes only and are not meant to be the only embodiment.
As shown in fig. 1, the front-view 3D endoscopic ultrasound system according to the present embodiment includes a main body 1, a display 2, an endoscopic catheter 3, and a communicator 4 for connecting the main body 1 and the endoscopic catheter 3.
Specifically, the endoscopic catheter 3 includes an inner catheter 30 and an outer sleeve 31 coaxially and relatively rotatably disposed, and the forward-looking 3D endoscopic ultrasound system further includes an ultrasound transducer 5 disposed at a front end of the inner catheter 30, and an end plate 6 disposed at a front end of the outer sleeve 31, wherein a coaxial cable is disposed in the inner catheter 30, and the ultrasound transducer 5 is communicated with the host 1 through the coaxial cable. Not only is attractive in appearance, but also is more beneficial to data transmission.
As shown in connection with fig. 2, the working surface of the ultrasonic transducer 5 is directed towards the end plate 6 and is arranged close to the inner wall of the end plate 6.
In this example, the ultrasonic transducer 5 is fixed to the front end of the inner catheter 30 and is disposed parallel to the end plate 6.
Specifically, the working frequency range of the ultrasonic transducer 5 is 1-60 MHz, and the diameter is smaller than 3mm.
Meanwhile, the ultrasonic transducer is a piezoelectric ceramic, piezoelectric monocrystal, piezoelectric composite or micro-capacitance sensor, and the sensor can emit and receive ultrasonic waves.
In this example, the end plate 6 has the fringes 60 formed thereon, and the transmission path of the ultrasonic wave emitted from the ultrasonic transducer 5 through the fringe region changes with the change of the fringes, and a phase delay is formed.
The acoustic impedances formed by the stripes in the stripe areas are different, mainly the stripes, and can be formed by printing, ink-jetting, vapor-depositing and bonding materials with different thicknesses (such as fuel, paint, ink, metal, plastic, rubber, ceramic, silicon and the like); the template structure can also be formed by laser etching and casting and has different thicknesses composed of the same material or mixed materials. The acoustic impedance of the material is different from that of the transducer, the periphery of the catheter and the medium of the working environment (such as blood in blood vessels, mucus in stomach and trachea, physiological saline and the like), so that the material is more beneficial to acquiring accurate data information under the angle corresponding to each rotating handle, and further the 3D image is accurately reconstructed.
The end plate 6 is further provided with a through hole 61 for communicating the inner cavity of the outer sleeve 31 from the distal end portion to the outside. Thus, the end plate 6 can be made into a stripe structure, and the water injection operation of the conduit from the through hole 61 can be facilitated.
In this example, a rotation handle 7 is further provided at the rear end of the outer sleeve 31 in order to facilitate the change of the transmission path between the outer sleeve 31 and the streak region of the end plate 6.
By rotating the rotary handle 7, the outer sleeve 31 and the striped end plate 6 are rotated to an angular position, and the relative orientation of the stripes to the transducer is changed, and the ultrasonic wave of the ultrasonic transducer excites and receives echo signals; and then, the rotation handle is rotated to the next angle position, the relative azimuth of the stripe board is changed again, the ultrasonic excitation and the echo signal receiving of the ultrasonic transducer are performed, and the like until the rotation handle is rotated for N angles, the ultrasonic excitation and the signal receiving of the echo signal of one rotation period are completed, so that under the N angles, a 3D image of the forward looking direction of the probe is reconstructed according to N groups of data information.
Meanwhile, in order to improve the imaging speed, the angle rotation of the imaging device can be realized by connecting and fixing the rotating handle with the motor and controlling the rotation of the motor.
In summary, the imaging method of the forward-looking 3D endoscopic ultrasound system of the present embodiment includes the following steps:
1) Firstly, a hydrophone is used for sound field test and calibration of a forward-looking 3D endoscopic ultrasonic system, specifically, the hydrophone arranged behind a striped end plate is opposite to an ultrasonic transducer in an excitation state, and the distance between the hydrophone and the forward-looking 3D endoscopic ultrasonic system is z 0 Recording the sound field intensity p of each position of its section 0 (x，y，z 0 And t), calculating the sound field intensity of each position of the sound field space behind the sound field by using the angular spectrum theory:
wherein F is 3D { } sumIs the fourier transform and inverse transform of the three-dimensional space,sgn (f) is a signed operation;
2) Convolving the obtained sound field intensity with the impulse response h (t) of the hydrophone according to the scattering sub-model and the sound field linear propagation theory to obtain the impulse echo signals corresponding to each position of the sound field space:
the obtained pulse echo signals are formed into a single space measurement matrixRotating the stripe board, changing the sound field distribution, repeating the above process to obtain multiple single space measurement matrixes +.>All matrices are combined into an integral spatial measurement matrix:
3) Selecting proper sparse matrix psi according to the compressed sensing theory to obtain a space sensing matrix
H＝ΦΨ (4)
Subsequently, the echo signals of the object to be measured are acquired by using the 3D imaging device, and the specific operation is as described above, so as to obtain N angle measurement signals r j (j=1, 2,., N), constitutes the observation signal
4) Substituting the observation signal u and the perception matrix H into a signal reconstruction equation, selecting a proper compressed perception reconstruction algorithm to solve the reconstruction equation, and reconstructing an original signal v:
u＝Hv (5)
wherein the method comprises the steps ofAnd theta are the reconstructed and original sparse signals respectively, θ=ψv and the sum of the values, I 1 And | I 2 Respectively 1 norm and 2 norm, epsilon being the defined acceptable reconstruction error magnitude;
5) And according to the reciprocity theorem, mapping the original signal and the spatial pixel distribution by using a linear inversion method to obtain the 3D ultrasonic image.
Therefore, the present embodiment has the following advantages:
1) The internal catheter and the external sleeve which rotate relatively are arranged, and the single ultrasonic transducer with the working face facing the stripes is matched, so that the data information of ultrasonic excitation and echo signal receiving is obtained under a plurality of relative rotation angles, and a 3D image is accurately reconstructed, so that the structure is simple, and the cost is low;
2) The end plate can be used as a stripe structure on one hand, and on the other hand, the operation of water injection and the like of the guide pipe from the through hole can be facilitated;
3) The top area of the outer sleeve of the catheter is provided with a certain metal marker, so that the position of the front end of the catheter can be observed and positioned in real time under CT and X-ray images;
4) If the catheter is used in an intravascular scene, the catheter has small size, and when the catheter is inconvenient to deliver, a certain annular or perforated structure can be designed on the external sleeve, so that the catheter can quickly reach a diagnosis area along an interventional guide wire during operation, and the guide wire guide structure is not needed for the alimentary canal or bronchus with a larger space.
The present invention has been described in detail with the purpose of enabling those skilled in the art to understand the contents of the present invention and to implement the same, but not to limit the scope of the present invention, and all equivalent changes or modifications made according to the spirit of the present invention should be included in the scope of the present invention.
Claims (9)
1. The imaging method of a forward-looking 3D endoscopic ultrasonic system, the forward-looking 3D endoscopic ultrasonic system used in it includes host computer, display, endoscopic catheter, and the communicating vessel used for connecting the said host computer with said endoscopic catheter, its characteristic lies in: the endoscopic catheter comprises an inner catheter and an outer sleeve which are coaxially and relatively rotatably arranged, the forward-looking 3D endoscopic ultrasonic system further comprises an ultrasonic transducer arranged at the front end of the inner catheter and an end plate arranged at the front end part of the outer sleeve, wherein the working face of the ultrasonic transducer faces towards the end plate and is close to the inner wall of the end plate, stripes are formed on the end plate, the transmission path of ultrasonic waves emitted by the ultrasonic transducer through the stripe areas changes along with the change of the stripes, phase delay is formed, and meanwhile, the imaging method comprises the following steps:
1) Firstly, a hydrophone is used for carrying out sound field test and calibration of a forward-looking 3D endoscopic ultrasonic system, specifically, the hydrophone arranged behind a striped end plate is opposite to an ultrasonic transducer in an excitation state, and the hydrophone and the forward-looking 3D endoscopic ultrasonic system are connected through a signal lineD distance z of endoscopic ultrasound system 0 Recording the sound field intensity p of each position of its section 0 (x，y，z 0 And t), calculating the sound field intensity of each position of the sound field space behind the sound field by using the angular spectrum theory:
wherein F is 3D { } sumIs the fourier transform and inverse transform of the three-dimensional space,sgn (f) is a signed operation;
2) Convolving the obtained sound field intensity with the impulse response h (t) of the hydrophone according to the scattering sub-model and the sound field linear propagation theory to obtain the impulse echo signals corresponding to each position of the sound field space:
the obtained pulse echo signals are formed into a single space measurement matrixRotating the stripe board, changing the sound field distribution, repeating the above process to obtain multiple single space measurement matrixes +.>All matrices are combined into an integral spatial measurement matrix:
3) Selecting proper sparse matrix psi according to the compressed sensing theory to obtain a space sensing matrix
H＝ΦΨ (4)
Subsequently, the echo signals of the object to be measured are acquired by using the 3D imaging device, and the specific operation is as described above, so as to obtain N angle measurement signals r j (j=1, 2,., N), constitutes the observation signal
4) Substituting the observation signal u and the perception matrix H into a signal reconstruction equation, selecting a proper compressed perception reconstruction algorithm to solve the reconstruction equation, and reconstructing an original signal v:
u＝Hv (5)
wherein the method comprises the steps ofAnd theta are the reconstructed and original sparse signals respectively, θ=ψv and the sum of the values, I 1 And | I 2 Respectively 1 norm and 2 norm, epsilon being the defined acceptable reconstruction error magnitude;
5) And according to the reciprocity theorem, mapping the original signal and the spatial pixel distribution by using a linear inversion method to obtain the 3D ultrasonic image.
2. The method of imaging a forward-looking 3D endoscopic ultrasound system of claim 1, wherein: the ultrasonic transducer is fixed at the front end of the inner catheter and is arranged in parallel with the end plate.
3. The method of imaging a forward-looking 3D endoscopic ultrasound system according to claim 1 or 2, wherein: the working frequency range of the ultrasonic transducer is 1-60 MHz, and the diameter is smaller than 3mm.
4. The method of imaging a forward-looking 3D endoscopic ultrasound system of claim 3, wherein: the ultrasonic transducer is a piezoelectric ceramic, piezoelectric monocrystal, piezoelectric composite or micro-capacitance sensor, wherein the sensor can emit and receive ultrasonic waves.
5. The method of imaging a forward-looking 3D endoscopic ultrasound system of claim 1, wherein: the rear end of the outer sleeve is also provided with a rotary handle.
6. The method of imaging a forward-looking 3D endoscopic ultrasound system of claim 1, wherein: the acoustic impedances formed by the fringes in the fringe areas are different.
7. The method of imaging a forward-looking 3D endoscopic ultrasound system of claim 6, wherein: the stripe printing, ink-jet, vapor plating, bonding, laser etching and casting mold are formed on the end plate.
8. The method of imaging a forward-looking 3D endoscopic ultrasound system of claim 7, wherein: the end plate is also provided with a through hole which communicates the inner cavity of the outer sleeve with the outside from the front end part.
9. The method of imaging a forward-looking 3D endoscopic ultrasound system of claim 1, wherein: the front end part of the outer sleeve is also provided with a metal marker.
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| CN202110308475.7A CN113143326B (en) | 2021-03-23 | 2021-03-23 | Forward-looking 3D endoscopic ultrasonic system and imaging method |
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| CN1065999A (en) * | 1991-04-24 | 1992-11-11 | 赵伟 | Endoscopic ultrasonic leading catheter |
| CN103462644A (en) * | 2012-06-07 | 2013-12-25 | 中国科学院深圳先进技术研究院 | Photoacoustic endoscope |
| CN108618758A (en) * | 2018-04-27 | 2018-10-09 | 华南师范大学 | Intravascular photoacoustic-optical coherence tomography-near infrared light multi-modality imaging apparatus and method |
| CN109620162A (en) * | 2019-01-18 | 2019-04-16 | 华南师范大学 | A kind of optoacoustic endoscopy lens device and imaging method based on bessel beam extended focal depth |
| CN211749715U (en) * | 2020-02-20 | 2020-10-27 | 苏州希声科技有限公司 | Self-guiding type endoscopic system |
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| US20080051660A1 (en) * | 2004-01-16 | 2008-02-28 | The University Of Houston System | Methods and apparatuses for medical imaging |
| US20050245824A1 (en) * | 2004-04-20 | 2005-11-03 | Acoustic Marketing Research, A Colorado Corporation, D/B/A Sonora Medical Systems, Inc. | High-intensity focused-ultrasound hydrophone |
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| CN1065999A (en) * | 1991-04-24 | 1992-11-11 | 赵伟 | Endoscopic ultrasonic leading catheter |
| CN103462644A (en) * | 2012-06-07 | 2013-12-25 | 中国科学院深圳先进技术研究院 | Photoacoustic endoscope |
| CN108618758A (en) * | 2018-04-27 | 2018-10-09 | 华南师范大学 | Intravascular photoacoustic-optical coherence tomography-near infrared light multi-modality imaging apparatus and method |
| CN109620162A (en) * | 2019-01-18 | 2019-04-16 | 华南师范大学 | A kind of optoacoustic endoscopy lens device and imaging method based on bessel beam extended focal depth |
| CN211749715U (en) * | 2020-02-20 | 2020-10-27 | 苏州希声科技有限公司 | Self-guiding type endoscopic system |
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