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WO2019119400A1 - Sonde d'imagerie ultrasonore intravasculaire à double fréquence - Google Patents

Sonde d'imagerie ultrasonore intravasculaire à double fréquence Download PDF

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Publication number
WO2019119400A1
WO2019119400A1 PCT/CN2017/117938 CN2017117938W WO2019119400A1 WO 2019119400 A1 WO2019119400 A1 WO 2019119400A1 CN 2017117938 W CN2017117938 W CN 2017117938W WO 2019119400 A1 WO2019119400 A1 WO 2019119400A1
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WIPO (PCT)
Prior art keywords
frequency
transducers
ultrasonic
dual
transducer
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PCT/CN2017/117938
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English (en)
Chinese (zh)
Inventor
邱维宝
苏敏
洪杰韩
张利宁
郑海荣
Original Assignee
深圳先进技术研究院
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Priority to PCT/CN2017/117938 priority Critical patent/WO2019119400A1/fr
Publication of WO2019119400A1 publication Critical patent/WO2019119400A1/fr

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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

Definitions

  • the present invention generally relates to the field of medical ultrasound imaging, and more particularly to a dual frequency intravascular ultrasound imaging probe.
  • Atherosclerosis is a cardiovascular disease with a high mortality rate, and one of the most prominent features is that it is not easily diagnosed before the onset of the disease.
  • the underlying pathological mechanism of more than 75% of acute coronary syndromes is demonstrated as atherosclerotic plaque rupture. Therefore, the detection and characterization of easily ruptured plaques is the most active area in cardiology and biomedical imaging research. One.
  • Angiography is the primary means of detecting atherosclerotic plaques today and is used to determine the location and extent of atherosclerotic stenosis. It quickly injects the contrast agent into the blood vessel under X-ray illumination, because the contrast agent absorbs X-rays and can be developed. From the results of the visualization, blood flow containing the contrast agent can be seen to understand the physiological and anatomical changes of the blood vessel. Angiography is a valuable method for diagnosing vascular-related diseases, but it can only provide lumen contours filled with contrast media, but not the nature and extent of lesions in the wall, most of the vulnerable lesions in the blood vessels. The block was not detected by angiography.
  • Medical ultrasound imaging technology has become an irreplaceable diagnostic technology in modern medical imaging because of its non-invasive, non-radiative, good real-time, high discriminating power, easy to use, and low price. It has become a clinical diagnosis of various diseases. The preferred method.
  • Intravascular ultrasound (IVUS) imaging technology is a special imaging technique specifically used in medical ultrasound imaging for cardiovascular disease detection.
  • the technique uses a miniature ultrasound probe mounted on the tip of the catheter to insert a two-dimensional tissue image into the suspected lesion in the human blood vessel. It not only displays the shape of the inner wall of the blood vessel in real time, but also measures the size of the lesion through tissue analysis and three-dimensional reconstruction, providing a new perspective for understanding the morphology and function of vascular lesions, and also providing more accurate clinical diagnosis and treatment. Reliable information.
  • Intravascular ultrasound imaging In addition to showing the shape of the lumen and the information of the vessel wall, the histomorphological features of the atherosclerotic plaque can be initially determined.
  • the diameter, cross-sectional area and degree of stenosis can be measured by accurate quantitative analysis.
  • Intravascular ultrasound imaging technology also has very important application value in guiding coronary interventional therapy. Because the technology can accurately reflect the internal morphology of the blood vessels, the nature and severity of the lesions, so as to provide a basis for selecting the correct treatment strategy, such as selecting a suitable size of the stent.
  • intravascular ultrasound imaging can be used to evaluate the effect of postoperative stent treatment, such as whether the stent is fully expanded, whether it is completely attached, whether it is evenly spread and completely covers the lesion, etc., which is conducive to timely finding and correcting the existence of the stent after implantation.
  • Intravascular ultrasound imaging is a minimally invasive imaging technique that uses a special catheter with an ultrasound transducer attached to it to perform medical imaging techniques that can display the wall and plaque of the lesion and improve diagnostic accuracy.
  • Intravascular ultrasound transducers used today are mainly high frequency planar single-element intravascular ultrasound transducers and high frequency annular array intravascular ultrasound transducers.
  • Conventional intravascular ultrasound catheters are typically mechanical catheters for single-element transducers and electronic phased-array catheters for linear array transducers. The higher the frequency of the transducer in the intravascular ultrasound catheter, the better the resolution of the ultrasound image.
  • the frequency of traditional electronic phased-array catheter transducers is generally around 20MHz
  • the frequency of mechanical catheter transducers is generally around 40MHz
  • the frequency is relatively low
  • the micro-tissue lesions of the vessel wall and the detection of anterior atherosclerotic plaque cannot be realized. Accurate detection.
  • the present invention provides a dual frequency intravascular ultrasound imaging probe that can simultaneously acquire low frequency and high frequency ultrasound images.
  • the present invention provides a dual-frequency intravascular ultrasound imaging probe comprising two ultrasonic transducers operating at different frequencies, simultaneously or simultaneously transmitting ultrasound for imaging, and simultaneously connecting two of the different frequencies through a coaxial cable.
  • Ultrasonic transducer operating at different frequencies, simultaneously or simultaneously transmitting ultrasound for imaging, and simultaneously connecting two of the different frequencies through a coaxial cable.
  • the two ultrasonic transducers are a low frequency ultrasonic transducer and a high frequency ultrasonic transducer.
  • the low frequency ultrasonic transducer and the high frequency ultrasonic transducer each comprise a matching layer, a piezoelectric layer and a backing layer, and the two ultrasonic transducers may share the backing layer or may not share the backing Floor.
  • the matching layer of each of the ultrasonic transducers is a matching layer or a plurality of matching layers.
  • the ultrasonic transducer has a center frequency ranging from 10 MHz to 120 MHz.
  • the ultrasound imaging probe has a housing, the two ultrasonic transducers being disposed within the housing, the housing being a hollow cylindrical structure having a diameter ranging from 0.3 mm to 3 mm.
  • the side wall of the outer casing of the ultrasonic imaging probe has two oppositely disposed openings, and the two ultrasonic transducers respectively transmit and receive ultrasonic waves through the two openings.
  • the coaxial cable is a single coaxial cable.
  • one pole of the coaxial cable is electrically connected to the matching layer of the two transducers, and the other of the coaxial cables The pole is electrically connected to the backing layer of the two transducers.
  • one pole of the coaxial cable is electrically connected to the side of the backing layer of the piezoelectric layers of the two transducers.
  • the other pole of the coaxial cable is electrically connected to the side of the matching layer of the piezoelectric layers of the two transducers.
  • the material of the piezoelectric layer is a piezoelectric ceramic, a piezoelectric single crystal material, a piezoelectric composite material or other piezoelectric material. .
  • a dual-frequency intravascular ultrasound imaging probe of the present invention uses a low-frequency single-element transducer and a high-frequency single-element transducer, which can be changed simultaneously or simultaneously in two hours.
  • the energy transmitter transmits the excitation signal, enables the transducer to perform ultrasonic transmission and reception, and filters the signal received by the transducer at a later stage to obtain low frequency and high frequency ultrasonic images simultaneously.
  • the present invention employs a dual transducer but uses only one coaxial cable. Compared to a single-element mechanical conduit, the external dimensions are not increased, and a rotary retraction device and signal port are also required at the tail of the catheter.
  • FIG. 1 is an ultrasonic imaging apparatus having a dual-frequency intravascular ultrasound imaging probe of the present invention Schematic diagram of the structure.
  • FIG. 2 is a schematic view showing the structure of a dual-frequency intravascular ultrasound imaging probe of the present invention.
  • FIG. 3 is a schematic view showing the structure of an ultrasonic probe in the dual-frequency intravascular ultrasound imaging probe of the present invention.
  • FIG. 4 is a schematic illustration of the operation of a dual transducer in a dual frequency intravascular ultrasound imaging probe of the present invention.
  • Figure 5 is a schematic diagram of a mixed excitation signal.
  • Figure 6 is a schematic diagram of an ultrasonic excitation and post-processing system module.
  • Figure 7 is a schematic diagram of the bandwidth of a dual frequency transducer.
  • Fig. 8 is a schematic view showing another wiring method of the ultrasonic probe.
  • Figure 9 is a schematic illustration of other arrangements of dual transducers.
  • the ultrasound imaging apparatus comprises a connector 1, a catheter 2 and a dual frequency intravascular ultrasound imaging probe 3 of the present invention.
  • the connector 1 has one end connected to the catheter 2 and the other end connected to an imaging system and a withdrawal device (not shown) for signal transmission and ultrasound probe retraction.
  • the connector 1 has a valve 11 for injecting physiological saline into the ultrasonic catheter, extruding air inside the catheter, and using it as an ultrasonic coupling agent.
  • the catheter 2 has a protective tube 21, a metal hose 22 and a transducer cable (coaxial cable) 23 in order from the outside to the inside, and also has a function of transmitting signals and retracting the probe, and the catheter 2 also has a guide wire 24 (see Figure 2) and positioning ring and other devices (not shown), can be positioned and changed The position of the illuminator and the guiding transducer move within the blood vessel.
  • the ultrasound probe 3 is located at the front end of the catheter 2 (i.e., the end remote from the connector 1) for ultrasound imaging.
  • the ultrasonic probe 3 has a housing 31, and a low frequency ultrasonic transducer 4a and a high frequency ultrasonic transducer 4b fixed in the housing 31.
  • the two ultrasonic transducers 4a, 4b are arranged back to back, simultaneously or in time to transmit ultrasound for imaging.
  • the outer casing 31 is an outer casing of copper or other metallic material.
  • Transducers 4a, 4b (transducer wafers) are secured within housing 31 using biocompatible glue.
  • the entire ultrasonic probe 3 is located inside the protective tube 21, and the metal hose 22 is fixed to one end side of the outer casing 31. In operation, the ultrasonic probe 3 rotates and the protective tube 21 and the guide wire 24 remain stationary.
  • the outer casing 31 of the ultrasonic probe 3 has a hollow cylindrical structure with a diameter of 0.3 mm to 3 mm.
  • the side wall of the outer casing 31 of the ultrasonic probe 3 has two oppositely disposed openings 32, and the two ultrasonic transducers 4a, 4b transmit and receive ultrasonic waves through the two openings 32, respectively.
  • the probe housing 31 can also be of other shapes.
  • the two transducers 4a, 4b may be single-element planar transducers, single-element focusing transducers or multi-element transducers.
  • the two ultrasonic transducers are of a layered structure, and the case of sharing the backing layer is shown in this embodiment, including the first matching layer 41, the first piezoelectric layer 42, the common backing layer 43, and the second piezoelectric layer. 44 and a second matching layer 45.
  • the matching layers 41, 45 and the backing layer 43 are electrically conductive materials.
  • the material of the piezoelectric layer is a piezoelectric ceramic, a piezoelectric single crystal material, a piezoelectric composite material or other piezoelectric materials.
  • the number of the first matching layer and the second matching layer of the two ultrasonic transducers may be one or more layers, respectively.
  • the structure shown in FIG. 3 is a case where the first matching layer and the second matching layer are each a matching layer.
  • the two ultrasonic transducers include a first matching layer, a second matching layer, a first piezoelectric layer, a backing layer, a second piezoelectric layer, a third matching layer, and The fourth matching layer.
  • the specific connection relationship between the coaxial cable 23 and the transducer is shown in FIG.
  • the matching layer (or the first matching layer) and the backing layer of the transducer may be electrically conductive materials
  • the positive and negative electrodes of the coaxial cable 23 and the backing layer the matching layer (or the first matching layer) may be electrically connected. connection.
  • the negative line (or the positive line) can be divided into two pairs of matching layers (or the first matching layer) of the two transducers, respectively, electrically connected by a conductive adhesive, and the positive line (or Negative wire) and backing The layers are electrically connected by a conductive adhesive (when the two transducers share the backing layer).
  • the positive wire (or the negative wire) is divided into two strands, and the backing layers of the two transducers are electrically connected by a conductive adhesive.
  • the matching layer and the backing layer of the transducer are non-conductive materials, it is necessary to directly connect the positive and negative electrodes of the coaxial cable to the front and back sides of the piezoelectric layer. That is, one pole of the coaxial cable 23 is divided into two sides on which the backing layer of the piezoelectric layer of each of the two transducers is electrically connected, and the other pole of the coaxial cable 23 is divided into two. The strands are electrically connected to the side of the matching layer of the piezoelectric layers of the two transducers, respectively.
  • a dual transducer is used, but only one coaxial cable 23 is used, and the single-element mechanical conduit (two cables, the diameter is relatively thick) does not increase the external dimensions (single cable, and the diameter is thin). Also, at the end of the catheter 2, only one rotary retraction device and signal port are required.
  • the two ultrasonic transducers have a common backing layer 43, and by sharing the backing layer, the thickness of the transducer of the multilayer structure can be reduced. Because intravascular ultrasound imaging device devices are highly demanding in thickness, reducing the thickness of the transducer will increase the utility of the device.
  • the backing layer 43 may not be shared, but instead has its own backing layer.
  • the center frequencies of the two ultrasonic transducers 4a, 4b are in the range of 10 MHz to 120 MHz.
  • the center frequency of the high-frequency ultrasonic transducer 4b is more than twice the center frequency of the low-frequency ultrasonic transducer 4a.
  • the low frequency range is 15-45 MHz and the high frequency range is 45-120 MHz. Since the resonant frequencies of the low frequency transducer and the high frequency transducer are greatly different, and when the signals are applied to the two transducers, the amplitude of the transducer corresponding to the frequency of the ultrasonic signal is large and the transducer does not correspond to the frequency of the ultrasonic signal.
  • the amplitude of the device is weak, so low-frequency and high-frequency signals can be applied to the two transducers simultaneously or in time, so that the transducer can transmit and receive ultrasonic waves, and the signal processing can be performed at the same time to obtain low-frequency and high-frequency ultrasonic images simultaneously.
  • FIG. 4 is a schematic illustration of the operation of a dual transducer in a dual frequency intravascular ultrasound imaging probe of the present invention.
  • the two transducers 4a, 4b are rotated about the central axis of the outer casing of the ultrasonic probe, and at the same time or ultrasonically transmitted to perform dual beam imaging work.
  • the dual transducer structure of the present invention the two transducers work simultaneously for ultrasonic transmission and reception, and an ultrasonic image with a larger imaging range and higher resolution can be obtained, which enables more accurate pathological analysis.
  • Figure 5 is a schematic diagram of a dual frequency excitation signal.
  • the left side is a schematic diagram of simultaneous broadband excitation, that is, using a narrow pulse, for example, a negative pulse of less than 10 ns to excite a dual-frequency transducer, The spectrum of the pulse covers a wide frequency range (greater than 100 MHz), which is sufficient to satisfy the operating frequency of the excited dual-frequency transducer, so that the dual-frequency transducer system can stimulate the operation;
  • the right side is a schematic diagram of the system detecting in the vascular tissue;
  • the left side is a schematic diagram of time-division dual-frequency excitation, that is, the high-frequency pulse and the ultra-high frequency pulse are used to excite the dual-frequency transducer, so that the dual-frequency transducer system can stimulate the work;
  • the right side is the system Schematic representation of detection in vascular tissue.
  • Simultaneous operation when the two transducers of the present invention are rotated can increase the imaging frame rate.
  • the system can have two modes of operation: simultaneously transmitting a wideband excitation signal or time-divisionally transmitting a dual frequency excitation signal.
  • the spectrum of the broadband excitation signal includes high-frequency spectral components and ultra-high-frequency spectral components, and the resonant frequencies of the dual-frequency transducers are greatly different, and when the high-frequency signals and ultra-high-frequency signals are applied to the two transducers, the frequency of the ultrasonic signals is
  • the corresponding transducer has a large amplitude and the amplitude of the transducer that does not correspond to the ultrasonic signal frequency is weak, so that the excitation signal and the echo signal of the dual-frequency probe have high fidelity, and two frames can be obtained simultaneously after the digital signal processing. Image.
  • FIG. 6 is a schematic diagram of an ultrasonic excitation and post-processing system module.
  • An excitation pulse signal is generated by an FPGA (Field-Programmable Gate Array), and then the excitation pulse sequence is converted into an analog excitation signal by a digital-to-analog converter, and then amplified by the power amplification module to make it The voltage is sufficient to drive the dual-frequency transducer to operate and obtain an ideal echo amplitude signal.
  • FPGA Field-Programmable Gate Array
  • the amplified signal passes through a transmit/receive control switch (this module is used to prevent the transmitted signal from entering the receive signal processing loop) to the rotary retraction device (the device) Used to extend and pull back the transducer catheter) and sent to the dual-frequency transducer of the present invention (ie, dual-frequency intravascular ultrasound imaging probe); the received echo signal passes through the signal amplifier and is then bandpass filtered The frequency of the echo signal is selected, and then the analog signal is finally sent to the FPGA for mathematical signal processing, and the processed signal is transmitted through a data transmission interface (for example, USB (Universal Serial Bus), PCIE (Peripheral Component Interconnect Express). , high-speed serial computer expansion bus standard), etc., uploaded to the host computer for imaging, while in the memory Store.
  • a data transmission interface for example, USB (Universal Serial Bus), PCIE (Peripheral Component Interconnect Express). , high-speed serial computer expansion bus standard), etc.
  • FIG. 7 is a schematic diagram of the bandwidth of a dual frequency transducer.
  • (a) is a broadband pulse spectrum diagram.
  • the spectrum of the broadband pulse has the center frequency of the low-frequency transducer as HF, and the center frequency of the high-frequency transducer is included in the SHF. After the energy filter, the echo signal is filtered, and the low frequency and high frequency ultrasonic signals can be separately collected.
  • (b) is a dual-frequency pulse spectrum diagram in which the center frequency of the low frequency transducer is HF and the center frequency of the high frequency transducer is SHF. When the center frequencies of the two transducers are sufficiently different, the overlapping portions of the two transducers are very small, and the time division is low. The frequency and high frequency signals excite the transducer, and when one transducer is used to excite the transducer, the other transducer is hardly affected.
  • Fig. 8 is a schematic view showing another wiring method of the ultrasonic probe.
  • an insulating layer 47 is disposed between the two ultrasonic transducers.
  • an insulating layer 47 is disposed between the respective backing layers 43 of the two ultrasonic transducers, which can effectively reduce the two transducing functions. Crosstalk interference between the devices.
  • the coaxial cable is connected to the respective backing layers 43 of the two ultrasonic transducers via the two positive wires 23a, respectively.
  • FIG 9 is a schematic illustration of other arrangements of dual transducers.
  • the two transducers 4a, 4b can be stacked in the housing 31 in a side-by-side manner (ie, radially along the housing and in the horizontal direction), stacked in the same direction (ie, radially along the housing and in the vertical direction, and the transducer Arranged in the same way along the axial direction of the outer casing, and the two transducers are connected at the same time by the same coaxial cable.
  • the transducer arrangement of Figure 2 of the present invention is arranged in the radial direction of the housing and in the vertical direction, and is arranged in such a way that the transducers are oriented in opposite directions.

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Abstract

L'invention concerne une sonde d'imagerie ultrasonore intravasculaire à double fréquence (3), comprenant un transducteur ultrasonore basse fréquence (4a) et un transducteur ultrasonore haute fréquence (4b) pour générer des ultrasons pour effectuer une imagerie simultanément ou à différents instants et connecter simultanément les deux transducteurs ultrasonores (4a, 4b) par l'intermédiaire d'un câble coaxial (23). Pendant le fonctionnement, la sonde (3), en utilisant un transducteur d'élément de réseau unique basse fréquence et un transducteur d'élément de réseau unique haute fréquence, peut envoyer un signal d'excitation aux deux transducteurs (4a, 4b) simultanément ou à différents moments, de façon à permettre aux transducteurs (4a, 4b) d'émettre et de recevoir une onde ultrasonore, et à un étage ultérieur, d'effectuer un traitement tel qu'un filtrage sur le signal reçu par les transducteurs (4a, 4b) pour acquérir simultanément une image ultrasonore basse fréquence et à haute fréquence. En outre, la sonde (3) utilise les deux transducteurs (4a, 4b) tout en utilisant uniquement un câble coaxial (23), de telle sorte que la taille externe n'est pas agrandie par rapport à un cathéter mécanique d'élément de réseau unique, et une partie de queue d'un cathéter (2) nécessite de façon similaire uniquement un dispositif de rétraction rotatif et un port de signal.
PCT/CN2017/117938 2017-12-22 2017-12-22 Sonde d'imagerie ultrasonore intravasculaire à double fréquence WO2019119400A1 (fr)

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Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20080200815A1 (en) * 2004-08-13 2008-08-21 Stichting Voor De Technische Wetenschappen Intravascular Ultrasound Techniques
CN204468134U (zh) * 2015-01-21 2015-07-15 上海爱声生物医疗科技有限公司 具有双频率的单、多阵元ivus换能器
CN105943083A (zh) * 2016-05-27 2016-09-21 苏州佳世达电通有限公司 超音波探头及超音波系统
CN106901777A (zh) * 2017-02-24 2017-06-30 华中科技大学 一种多功能超声探头与微血管成像及血流速度检测方法
CN107007300A (zh) * 2017-03-08 2017-08-04 上海交通大学 一种用于肌肉群运动检测的多频单振元超声换能器
CN108272469A (zh) * 2017-12-22 2018-07-13 深圳先进技术研究院 一种双频率血管内超声成像探头

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20080200815A1 (en) * 2004-08-13 2008-08-21 Stichting Voor De Technische Wetenschappen Intravascular Ultrasound Techniques
CN204468134U (zh) * 2015-01-21 2015-07-15 上海爱声生物医疗科技有限公司 具有双频率的单、多阵元ivus换能器
CN105943083A (zh) * 2016-05-27 2016-09-21 苏州佳世达电通有限公司 超音波探头及超音波系统
CN106901777A (zh) * 2017-02-24 2017-06-30 华中科技大学 一种多功能超声探头与微血管成像及血流速度检测方法
CN107007300A (zh) * 2017-03-08 2017-08-04 上海交通大学 一种用于肌肉群运动检测的多频单振元超声换能器
CN108272469A (zh) * 2017-12-22 2018-07-13 深圳先进技术研究院 一种双频率血管内超声成像探头

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