WO2015010409A1 - 一种血管内光声超声双模成像系统及其成像方法 - Google Patents

一种血管内光声超声双模成像系统及其成像方法 Download PDF

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Publication number
WO2015010409A1
WO2015010409A1 PCT/CN2013/088424 CN2013088424W WO2015010409A1 WO 2015010409 A1 WO2015010409 A1 WO 2015010409A1 CN 2013088424 W CN2013088424 W CN 2013088424W WO 2015010409 A1 WO2015010409 A1 WO 2015010409A1
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ultrasonic
signal
photoacoustic
laser
endoscopic probe
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PCT/CN2013/088424
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English (en)
French (fr)
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宋亮
邹新
白晓淞
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深圳先进技术研究院
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Publication of WO2015010409A1 publication Critical patent/WO2015010409A1/zh

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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
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0033—Features or image-related aspects of imaging apparatus classified in A61B5/00, e.g. for MRI, optical tomography or impedance tomography apparatus; arrangements of imaging apparatus in a room
    • A61B5/0035—Features or image-related aspects of imaging apparatus classified in A61B5/00, e.g. for MRI, optical tomography or impedance tomography apparatus; arrangements of imaging apparatus in a room adapted for acquisition of images from more than one imaging mode, e.g. combining MRI and optical tomography
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0093—Detecting, measuring or recording by applying one single type of energy and measuring its conversion into another type of energy
    • A61B5/0095—Detecting, measuring or recording by applying one single type of energy and measuring its conversion into another type of energy by applying light and detecting acoustic waves, i.e. photoacoustic measurements
    • 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
    • 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
    • A61B8/4416—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device related to combined acquisition of different diagnostic modalities, e.g. combination of ultrasound and X-ray acquisitions
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/46—Ultrasonic, sonic or infrasonic diagnostic devices with special arrangements for interfacing with the operator or the patient
    • A61B8/461—Displaying means of special interest
    • A61B8/463—Displaying means of special interest characterised by displaying multiple images or images and diagnostic data on one display
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/52—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/5269—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving detection or reduction of artifacts

Definitions

  • the invention belongs to the technical field of endoscopes, and in particular relates to an intravascular photoacoustic ultrasonic dual-mode imaging system and an imaging method thereof.
  • Intravascular ultrasound imaging is a non-invasive ultrasound imaging technique combined with minimally invasive catheter technology for cardiovascular disease diagnosis.
  • intravascular ultrasound imaging can accurately detect atherosclerotic plates. Size and structure information.
  • Photoacoustic imaging is a non-destructive medical imaging method developed in recent years. The method uses short pulse (or amplitude modulation) laser as the light source, and uses the spectral absorption difference of the sample to be excited to excite different intensity of photoinduced ultrasound characteristics to ultrasound.
  • the photoacoustic imaging method effectively combines the high contrast of pure optical imaging with the high penetration capability of pure acoustic imaging, enabling the detection depth of the order of centimeter and the imaging resolution of the order of micrometers.
  • Intravascular photoacoustic imaging such as the intravascular photoacoustic endoscopic technique developed by K. Jansen and B. Wang in recent years, which combines intravascular ultrasound imaging with intravascular photoacoustic imaging to detect arteries by intravascular ultrasound imaging.
  • the morphological structure of atherosclerotic plaque provides information on the composition of blood vessels through vascular photoacoustic imaging, and detects the accumulation of fat in plaque by photoacoustic function and quantitative imaging. It has high resolution and no side effects.
  • the disadvantage of this technique is that the photoacoustic excitation light in the intravascular photoacoustic endoscope is not focused (or collimated) through the multimode fiber. Due to the large numerical aperture of the multimode fiber, most of the excitation light fails.
  • the utilization rate of the excitation photoacoustic signal is low; in addition, in the intravascular photoacoustic imaging, since the blood has a strong absorption of the laser, the loss of the laser when irradiated to the inner wall of the lumen is large, resulting in a deeper imaging depth. Shallow, and the signal-to-noise ratio (SNR, Signal to Noise Ratio, the anti-interference ability of the reaction imaging, the response is in the picture quality is whether the picture is clean and noise-free).
  • SNR Signal to Noise Ratio
  • the invention provides an intravascular photoacoustic ultrasonic dual-mode imaging system and an imaging method, aiming at solving the low utilization rate, shallow imaging depth and low signal-to-noise ratio of the existing intravascular photoacoustic endoscopic excitation photoacoustic signal. technical problem.
  • an intravascular photoacoustic ultrasonic dual-mode imaging system including a laser , an endoscopic probe, an ultrasonic emission receiver, a data acquisition system, and an image reconstruction and display system, the laser for outputting a laser beam and emitting a trigger signal, the ultrasonic emission receiver for controlling the emission of the ultrasonic wave according to the trigger signal Simultaneously receiving a photoacoustic signal and an ultrasonic signal, the endoscopic probe for focusing or collimating the laser beam and then laterally reflecting to the lumen sample to generate the photoacoustic signal while laterally transmitting the ultrasonic wave and receiving the lumen
  • the ultrasound signal reflected by the sample, the data acquisition system is configured to acquire a photoacoustic signal and an ultrasound signal of the lumen sample, and reconstruct a photoacoustic image and an ultrasound image of the lumen sample through an image reconstruction and display system.
  • the technical solution of the present invention further includes: further comprising a laser light path and a probe scanning device, wherein the laser light path comprises a pupil, a beam splitter, a photodiode and a focusing lens, wherein the pupil, the beam splitter, the photodiode and the focusing lens are in turn Connected, the probe scanning device comprises an optical slip ring, an axial displacement platform and a slip ring drive motor, wherein the photoelectric slip ring and the slip ring drive motor are fixed on the axial displacement platform, and the photoelectric slip ring is driven by the slip ring drive motor. Turn.
  • the technical solution of the present invention further includes: further comprising a fiber fixing bracket, the endoscope probe further comprising a multimode fiber, a self-focusing lens, a mirror, an ultrasonic transducer, a coaxial cable, a fiber fixing sleeve, a coaxial sleeve
  • the probe package sleeve and the fiber protection sleeve wherein the multimode fiber comprises two segments and is respectively connected to the photoelectric slip ring, and one end of the first segment is fixed to one end of the focus lens through the fiber fixing bracket, and the other end sleeve
  • the fiber protection sleeve one end of the second segment is sleeved in the fiber fixing sleeve and connected to the endoscopic probe, and is sequentially placed coaxially with the autofocus lens and the mirror in the coaxial sleeve, the ultrasonic transducer and the coaxial
  • the sleeve is secured in the probe package sleeve; the ultrasonic transducer is coupled
  • the technical solution of the present invention further includes: a signal delay module, wherein the signal delay module is configured to delay the ultrasonic trigger signal sent by the laser and transmit the ultrasonic trigger signal to the ultrasonic transmitting receiver, and control the ultrasonic transmitting receiver to transmit the ultrasonic wave.
  • the technical solution of the present invention further includes: the imaging mode of the intravascular photoacoustic ultrasonic dual-mode imaging system is: outputting a laser beam by a laser and emitting an ultrasonic trigger signal, and the laser beam is transmitted to the endoscopic probe through the multimode optical fiber,
  • the self-focusing lens in the speculum probe focuses or collimates the laser beam and then laterally reflects the lens beam to the lumen sample to generate a photoacoustic signal, and collects the photoacoustic signal through the data acquisition system
  • the ultrasonic trigger signal is extended by the signal delay module Afterwards, it is transmitted to the ultrasonic transmitting receiver to control the transmitting ultrasonic wave, and the ultrasonic wave is transmitted to the ultrasonic transducer through the coaxial cable to laterally transmit the ultrasonic wave to the lumen sample, and the ultrasonic signal is collected through the data acquisition system; through the image reconstruction and display system The acquired photoacoustic signal and the ultrasonic signal are image reconstructed.
  • the technical solution of the present invention further includes: the laser beam is a short pulse laser or an amplitude modulated laser, The output wavelength range is 400-2400 nm; the beam splitter has a reflection/transmission ratio of 8:92; the endoscopic probe has a diameter of 0.3 to 1.0 mm, and the receiving surface of the ultrasonic transducer and the endoscopic probe The central axis is 5. Placed at ⁇ 40° angle, its center frequency is 5 ⁇ 75MHz.
  • an intravascular photoacoustic ultrasonic dual-mode imaging method comprising: Step a: outputting a laser beam through a laser and emitting an ultrasonic trigger signal;
  • Step b focusing or collimating the laser beam by the endoscopic probe and then laterally reflecting to the lumen sample to generate a photoacoustic signal, while controlling the ultrasonic transmitter to emit ultrasonic waves to the lumen sample and reflecting the ultrasonic signal through the ultrasonic trigger signal ;
  • Step c collecting the photoacoustic signal and the reflected ultrasonic signal excited by the lumen sample, and reconstructing the photoacoustic image and the ultrasonic image of the lumen sample according to the photoacoustic signal and the ultrasonic signal.
  • the technical solution of the present invention further includes: in the step b, the focusing or collimating the laser beam by the endoscopic probe to laterally reflect to the lumen sample to generate the photoacoustic signal further comprises: laser passing the multimode fiber The beam is transmitted to the endoscopic probe, and the laser beam is focused or collimated by the autofocus lens in the endoscopic probe and then laterally reflected by the mirror to the lumen sample to generate a photoacoustic signal; the ultrasonic trigger signal is used to control the ultrasonic emission
  • the specific method for transmitting ultrasonic waves by the receiver includes: transmitting the ultrasonic trigger signal to the ultrasonic transmitting receiver after being delayed, controlling the ultrasonic transmitting receiver to emit ultrasonic waves, and transmitting the ultrasonic waves to the ultrasonic transducer through the coaxial cable, through the ultrasonic transducer Ultrasound is emitted laterally into the lumen sample and ultrasonic signal acquisition is performed through a data acquisition system.
  • the technical solution of the present invention further includes: after the step c, the method further comprises: controlling the endoscopic probe to perform rotation and axial movement scanning by using the probe scanning device, and each time the signal is collected, the endoscopic probe rotates a certain angle to reacquire the signal, and repeats to Rotate once; every time the rotation scans, the endoscopic probe moves axially a certain distance to reacquire the signal, repeating to complete the axial scan.
  • the technical solution of the present invention further includes: the laser beam is a short pulse laser or an amplitude modulated laser, and the output wavelength ranges from 400 to 2400 nm ; the endoscope probe has a diameter of 0.3 to 1.0 mm, and the ultrasonic transducer receives The surface is placed at an angle of 5° to 40° with the central axis of the endoscopic probe, and its center frequency is 5 to 75 MHz.
  • the intravascular photoacoustic ultrasonic dual-mode imaging system and the imaging method of the embodiment of the present invention enhance the utilization of light by focusing or collimating the laser and laterally reflecting it to the inner wall of the lumen. Rate and depth of penetration to the target tissue, which increases the depth and signal-to-noise ratio of photoacoustic imaging, and has better imaging quality.
  • the laser emits a laser beam while emitting an ultrasonic trigger signal, and the trigger signal controls the ultrasonic emission.
  • the receiver emits ultrasonic waves for ultrasound imaging, which realizes simultaneous and in-situ photoacoustic and ultrasound imaging, which is more conducive to early tumors, atherosclerosis, etc. Detection of the disease.
  • FIG. 1 is a schematic structural view of an intravascular photoacoustic ultrasonic dual-mode imaging system of the embodiment:
  • FIG. 2 is a front view showing the structure of the endoscopic probe of the embodiment;
  • Figure 3 is a side view of the endoscope probe structure of the embodiment
  • FIG. 4 is a structural view of an endoscopic probe when the ultrasonic transducer of the embodiment is horizontally placed; and FIG. 5 is a flow chart of the intravascular photoacoustic ultrasonic dual-mode imaging method of the embodiment. detailed description
  • FIG. 1 is a schematic structural view of an intravascular photoacoustic ultrasonic dual-mode imaging system according to an embodiment of the present invention.
  • the intravascular photoacoustic ultrasonic dual-mode imaging system of the embodiment of the present invention includes a laser 10, a laser optical path 20, a fiber fixing bracket 30, a probe scanning device 40, an endoscopic probe 50, an ultrasonic transmitting receiver 60, a data acquisition system 70, and image reconstruction. And display system 80 and signal delay module 90.
  • the laser beam path 20 includes a diaphragm 21, a beam splitter 22, a photodiode 23, and a focus lens 24.
  • the probe scanning device 40 includes an optical slip ring 41, an axial displacement platform 42 and a slip ring drive motor 43.
  • the photoelectric slip ring 41 and the slip ring drive motor 43 are fixed on the axial displacement platform 42 to drive the photoelectric slide through the slip ring drive motor 43.
  • the ring 41 is rotated.
  • FIG. 2 is a front view of the endoscopic probe according to the embodiment of the present invention
  • FIG. 3 is a side view of the endoscopic probe 50 according to the embodiment of the present invention
  • the endoscopic probe 50 includes a multimode fiber 51, a self-focusing lens 52, a mirror 53, an ultrasonic transducer 54, a coaxial cable 55, a fiber fixing sleeve 56, a coaxial sleeve 57, a probe package sleeve 58, and fiber protection.
  • the multimode fiber 51 includes two segments (the first segment and the second segment) respectively connected to the photoelectric slip ring 41. Referring to FIG.
  • one end of the first segment is fixed to one end of the focus lens 24 through the fiber fixing bracket 30.
  • the other end is sleeved in the fiber protection sleeve 59; the second end is sleeved in the fiber fixing sleeve 56, and sequentially and the self-focusing lens 52
  • the mirror 53 is coaxially placed in the coaxial sleeve 57.
  • the multi-mode optical fiber connected to the endoscopic probe 50 can be driven by the photoelectric slip ring 41 to rotate 360° with the endoscope probe 50.
  • the ultrasonic transducer 54 and the coaxial sleeve 57 are fixed in the probe package sleeve 58; the ultrasonic transducer 54 is coupled to the ultrasonic transmitter receiver 60 via a coaxial cable 55.
  • the ultrasonic transducer 54 can be placed at an angle, as shown in Fig. 3, and of course, can also be placed horizontally, as shown in Fig. 4.
  • the laser 10 is 0P0TEK VIBRANT II (the VIBRANT series products are integrated design, the pump laser, 0P0, control circuit, etc. are integrated in an optical structure, and the high-spectral laser output is obtained while maintaining a high 0 ⁇ 3 ⁇ 1
  • the diameter of the optical probe is 0. 3 ⁇ 1 .
  • the optical beam is a short-pulse laser or an amplitude-modulated laser, the output wavelength range is 400-2400nm ; the reflection/transmission ratio of the beam splitter 22 is 8: 92; 0mm, the receiving surface of the ultrasonic transducer 54 is placed at an angle of 5° to 40° with respect to the central axis of the endoscopic probe 50, and its center frequency is 5 to 75 MHz.
  • the working principle of the intravascular photoacoustic ultrasonic dual-mode imaging system of the embodiment of the present invention is as follows:
  • the laser 10 outputs a laser beam and emits an ultrasonic trigger signal, and filters out part of the stray light of the laser beam through the aperture 21, and passes through the beam splitter 22
  • the laser beam is split into two paths, one is irradiated to the photodiode 23 as a reference light, and the other is focused by the focusing lens 24 and coupled into the multimode optical fiber 51 in the endoscopic probe 50, and the laser beam is transmitted to the endoscopic probe through the multimode optical fiber 51.
  • the ultrasonic transducer 54 receives the photoacoustic signal and transforms
  • the photoacoustic electrical signal is transmitted to the ultrasonic transmitting receiver 60 through the coaxial cable 55 for amplification, and then transmitted to the data collecting system 70 for photoacoustic signal acquisition; at the same time, the ultrasonic trigger signal from the laser 10 After being delayed by the signal delay module 90, it is transmitted to the ultrasonic transmitting receiver 60, and the ultrasonic transmitting receiver 60 is controlled to emit ultrasonic waves, and will be transmitted through the coaxial cable 55.
  • the acoustic wave is transmitted to the ultrasonic transducer 54 in the endoscopic probe 50, and the ultrasonic wave is laterally emitted to the lumen sample through the ultrasonic transducer 54, and the ultrasonic wave reflected by the lumen sample is received, and the received ultrasonic wave is converted into an ultrasonic electric signal.
  • the ultrasonic transmitter receiver 60 for amplification, and then transmitting to the data acquisition system 70 for ultrasonic signal acquisition; the image reconstruction and display system 80 reconstructs the acquired photoacoustic signal and the ultrasonic signal to obtain a photoacoustic image of the corresponding sample and Ultrasound image;
  • the endoscopic probe 50 is controlled by the probe scanning device 40 to perform 360-degree rotation and axial movement scanning.
  • the endoscopic probe 50 rotates a certain angle to reacquire the signal, repeating to one rotation; each rotation After one scan, the endoscopic probe 50 moves axially a certain distance to reacquire the signal and repeats until the axial scan is completed.
  • FIG. 5 it is a flowchart of an intravascular photoacoustic ultrasonic dual-mode imaging method according to an embodiment of the present invention.
  • the intravascular photoacoustic ultrasonic dual-mode imaging method of the embodiment of the invention comprises the following steps:
  • Step 500 The laser beam is output by the laser and an ultrasonic trigger signal is emitted.
  • the laser is 0P0TEK VIBRANT II, and the laser beam is a short pulse laser or an amplitude modulated laser with an output wavelength range of 400-2400 nm.
  • Step 510 Filtering part of the stray light of the laser beam through the pupil, and splitting the beam into two paths through a beam splitter, one light is irradiated to the photodiode as a reference light, and the other is focused by a focusing lens and coupled into the multimode fiber.
  • the beam splitter has a reflection/transmission ratio of 8:92.
  • Step 520 transmitting the laser beam to the endoscopic probe through the multimode fiber, focusing or collimating by the self-focusing lens in the endoscopic probe, and then laterally reflecting through the mirror to the lumen sample to generate a photoacoustic signal.
  • step 520 the diameter of the endoscopic probe is 0. 3 1. 0
  • Step 530 Receive a photoacoustic signal through the ultrasonic transducer and convert it into a photoacoustic electrical signal, transmit the photoacoustic electrical signal to the ultrasonic transmitting receiver through a coaxial cable, amplify and transmit to the data collecting system for photoacoustic signal acquisition, and simultaneously
  • the ultrasonic trigger signal from the laser is transmitted to the ultrasonic transmitter receiver after a delay, and the ultrasonic transmitter receiver is controlled to emit ultrasonic waves, and the ultrasonic wave is transmitted to the ultrasonic transducer through the coaxial cable, and the ultrasonic wave is laterally emitted through the ultrasonic transducer.
  • Go to the lumen sample and receive the ultrasound reflected by the lumen sample convert the received ultrasound into an ultrasound electrical signal and return it to the ultrasound transmitter receiver.
  • step 530 the receiving surface of the ultrasonic transducer is placed at an angle of 5° 40 ° to the central axis of the endoscopic probe, and the center frequency is 5 75 MHz.
  • Step 560 Amplify the received ultrasonic electrical signal by an ultrasonic transmitting receiver and transmit it to a data acquisition system for ultrasonic signal acquisition.
  • Step 570 Reconstruct the photoacoustic signal and the ultrasonic signal collected by the data acquisition system through an image reconstruction and display system to obtain a photoacoustic image and an ultrasonic image of the corresponding sample.
  • Step 580 Control the endoscopic probe to perform 360-degree rotation and axial movement scanning by the probe scanning device. After each time the signal is collected, the endoscopic probe rotates at a certain angle to reacquire the signal, repeating to rotate. One turn; one scan per rotation, the endoscopic probe moves axially a certain distance to reacquire the signal, repeating to complete the axial scan.
  • the intravascular photoacoustic ultrasonic dual-mode imaging system and the imaging method of the embodiment of the present invention increase the utilization rate of light and the penetration depth of the target tissue by focusing or collimating the laser to the inner wall of the lumen, thereby increasing The depth and signal-to-noise ratio of photoacoustic imaging have better imaging quality.
  • the laser triggers the laser beam to emit the ultrasonic trigger signal, and the trigger signal controls the ultrasonic transmitter to emit ultrasonic waves for ultrasonic imaging. Photoacoustic and ultrasound imaging in the same area is more conducive to the detection of early tumors, atherosclerosis and other diseases.

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Abstract

一种血管内光声超声双模成像系统及成像方法，所述血管内光声超声双模成像系统包括激光器（10）、内窥探头（50）、超声发射接收器（60）、数据采集系统（70）及图像重建和显示系统（80），所述激光器（10）用于输出激光光束并发出触发信号，所述超声发射接收器（60）用于根据所述触发信号控制发射超声波并同时接收光声信号和超声信号，所述内窥探头（50）用于将激光光束聚焦或准直后侧向反射到管腔样本激发产生所述光声信号，同时侧向发射超声波并接收所述管腔样本反射的所述超声信号，所述数据采集系统（70）用于采集管腔样本光声信号和超声信号，并通过图像重建和显示系统（80）重建管腔样本的光声图像和超声图像。上述血管内光声超声双模成像系统及成像方法提高了光的利用率及对目标组织的穿透深度，增加了光声成像的深度和信噪比，具有更好的成像质量。

Description

一种血管内光声超声双模成像系统及其成像方法
技术领域
本发明属于内窥镜技术领域，尤其涉及一种血管内光声超声双模成像系统 及其成像方法。
背景技术
血管内超声成像，是一种无创的超声成像技术与微创的导管技术相结合的 心血管疾病诊断技术，在动脉粥样硬化程度评估中， 血管内超声成像能够准确 地检测出粥样硬化板块的大小和结构信息。光声成像是近年来发展起来的一种 无损医学成像方法， 该方法以短脉冲（或幅度调制）激光作为光源， 利用被测 样本的光谱吸收差异激发出不同强度的光致超声特性，以超声作为信息载体的 新型成像方法，光声成像方法有效的结合了纯光学成像的高对比度和纯声学成 像的高穿透能力等优点，可以实现厘米量级的探测深度和微米量级的成像分辨 率， 具有无损性、 无辐射等突出特性， 在医学领域的应用越来越广泛。
血管内光声成像， 如 K.Jansen、 B.Wang在近年研发的血管内光声内窥镜 技术， 该技术将血管内超声成像与血管内光声成像相结合， 通过血管内超声成 像检测动脉粥样硬化斑块的形态结构， 通过血管光声成像提供血管的成分信 息， 通过光声功能和量化成像探测斑块中的脂肪堆积程度， 具有分辨率高、 无 副作用等特点。但该技术的缺点在于， 血管内光声内窥镜中光声激发光经过多 模光纤出射未经过聚焦 （或准直）， 由于多模光纤较大的数值孔径， 使大部分 激发光未能照射到目标组织， 激发光声信号的利用率较低； 另外， 在血管内光 声成像时，由于血液对激光具有很强的吸收，激光照射到管腔内壁时损耗较大， 造成成像深度较浅， 且信噪比 （SNR， Signal to Noise Ratio, 反应成像的抗干 扰能力， 反应在画质上就是画面是否干净无噪点） 低。
发明内容
本发明提供了一种血管内光声超声双模成像系统及成像方法，旨在解决现 有的血管内光声内窥镜激发光声信号的利用率低、成像深度浅且信噪比低的技 术问题。
本发明提供的技术方案为： 一种血管内光声超声双模成像系统， 包括激光 器、 内窥探头、 超声发射接收器、 数据采集系统及图像重建和显示系统， 所述 激光器用于输出激光光束并发出触发信号，所述超声发射接收器用于根据所述 触发信号控制发射超声波并同时接收光声信号和超声信号，所述内窥探头用于 将激光光束聚焦或准直后侧向反射到管腔样本激发产生所述光声信号，同时侧 向发射超声波并接收所述管腔样本反射的所述超声信号，所述数据采集系统用 于采集管腔样本光声信号和超声信号，并通过图像重建和显示系统重建管腔样 本的光声图像和超声图像。
本发明的技术方案还包括： 还包括激光光路和探头扫描装置， 所述激光光 路包括光阑、 分束镜、 光电二极管和聚焦透镜， 所述光阑、 分束镜、 光电二极 管和聚焦透镜依次相连， 所述探头扫描装置包括光电滑环、轴向位移平台和滑 环驱动电机， 所述光电滑环和滑环驱动电机固定于轴向位移平台上， 通过滑环 驱动电机带动光电滑环进行转动。
本发明的技术方案还包括： 还包括光纤固定支架， 所述内窥探头还包括多 模光纤、 自聚焦透镜、 反射镜、 超声换能器、 同轴电缆、 光纤固定套管、 共轴 套管、探头封装套管和光纤保护套管， 其中， 所述多模光纤包括两段并分别与 光电滑环相连， 第一段的一端通过所述光纤固定支架固定于聚焦透镜的一端， 另一端套在光纤保护套管内，第二段的一端套在光纤固定套管内与内窥探头相 连， 并顺序与自聚焦透镜及反射镜同轴放置于共轴套管中， 所述超声换能器与 共轴套管固定于探头封装套管中；所述超声换能器通过同轴电缆与超声发射接 收器连接。
本发明的技术方案还包括： 还包括信号延迟模块， 所述信号延迟模块用于 将激光器发出的超声触发信号进行延时后传输到超声发射接收器，控制超声发 射接收器发射超声波。
本发明的技术方案还包括：所述血管内光声超声双模成像系统的成像方式 为： 通过激光器输出激光光束并发出超声触发信号，激光光束经多模光纤传输 到内窥探头中，由内窥探头中的自聚焦透镜将激光光束聚焦或准直后经反射镜 侧向反射到管腔样本激发产生光声信号，并通过数据采集系统进行光声信号采 集；超声触发信号经过信号延迟模块延时后传输到超声发射接收器控制发射超 声波， 通过同轴电缆将超声波传输到超声换能器将超声波侧向发射到管腔样 本， 并通过数据采集系统进行超声信号采集； 通过图像重建和显示系统将采集 到的光声信号和超声信号进行图像重建。
本发明的技术方案还包括： 所述激光光束为短脉冲激光或幅度调制激光， 输出波长范围为 400-2400nm; 所述分束镜的反射 /透射比为 8: 92； 所述内窥 探头的直径为 0.3〜1.0mm， 所述超声换能器的接收面与内窥探头的中心轴线 呈 5。〜40° 角放置， 其中心频率为 5〜75MHz。
本发明提供的另一技术方案， 一种血管内光声超声双模成像方法， 包括： 步骤 a: 通过激光器输出激光光束并发出超声触发信号；
步骤 b : 通过内窥探头将激光光束聚焦或准直后侧向反射到管腔样本激发 产生光声信号，同时通过超声触发信号控制超声发射接收器发射超声波至所述 管腔样本并反射超声信号；
步骤 c: 采集管腔样本被激发的光声信号和反射超声信号， 并根据光声信 号和超声信号重建管腔样本的光声图像和超声图像。
本发明的技术方案还包括： 在所述步骤 b中， 所述通过内窥探头将激光光 束聚焦或准直后侧向反射到管腔样本激发产生光声信号还包括：通过多模光纤 将激光光束传输到内窥探头中，由内窥探头中的自聚焦透镜将激光光束聚焦或 准直后经反射镜侧向反射到管腔样本激发产生光声信号；所述通过超声触发信 号控制超声发射接收器发射超声波的具体方式包括：将超声触发信号经过延时 后传输到超声发射接收器控制超声发射接收器发射超声波，并通过同轴电缆将 超声波传输到超声换能器， 通过超声换能器将超声波侧向发射到管腔样本， 并 通过数据采集系统进行超声信号采集。
本发明的技术方案还包括： 所述步骤 c后还包括： 通过探头扫描装置控制 内窥探头进行旋转和轴向移动扫描，每采集完一次信号， 内窥探头转动一定角 度重新采集信号， 重复至旋转一圈； 每旋转扫描一圈， 内窥探头轴向移动一定 距离重新采集信号， 重复至完成轴向扫描。
本发明的技术方案还包括： 所述激光光束为短脉冲激光或幅度调制激光， 输出波长范围为 400-2400nm; 所述内窥探头的直径为 0.3〜1.0mm， 所述超声 换能器的接收面与内窥探头的中心轴线呈 5°〜40° 角放置，其中心频率为 5〜 75MHz
本发明的技术方案具有如下优点或有益效果：本发明实施例的血管内光声 超声双模成像系统及成像方法通过将激光进行聚焦或准直后侧向反射到管腔 内壁， 提高光的利用率及对目标组织的穿透深度，进而增加了光声成像的深度 和信噪比， 具有更好的成像质量； 另外， 利用激光器输出激光光束的同时发出 超声触发信号， 通过触发信号控制超声发射接收器发射超声波进行超声成像， 实现了同时、 同区域的光声和超声成像， 更有利于早期肿瘤、动脉粥样硬化等 疾病的检测。 附图说明
附图 1是本 ：明实施例的血管内光声超声双模成像系统的结构示意图: 附图 2是本 ：明实施例的内窥探头的结构主视图；
附图 3是本 ：明实施例的内窥探头结构侧视图；
附图 4是本 ：明实施例的超声换能器水平放置时的内窥探头结构图； 附图 5是本 ：明实施例的血管内光声超声双模成像方法的流程图。 具体实施方式
为了使本发明的目的、技术方案及优点更加清楚明白， 以下结合附图及实 施例， 对本发明进行进一步详细说明。应当理解， 此处所描述的具体实施例仅 仅用以解释本发明， 并不用于限定本发明。
请参阅图 1， 图 1是本发明实施例的血管内光声超声双模成像系统的结构 示意图。 本发明实施例的血管内光声超声双模成像系统包括激光器 10、 激光 光路 20、 光纤固定支架 30、 探头扫描装置 40、 内窥探头 50、 超声发射接收器 60、 数据采集系统 70、 图像重建和显示系统 80及信号延迟模块 90。 其中， 激 光光路 20包括光阑 21、 分束镜 22、 光电二极管 23和聚焦透镜 24， 光阑 21、 分束镜 22和聚焦透镜 24依次相连， 光电二极管 23和分束镜 22相连。探头扫 描装置 40包括光电滑环 41、 轴向位移平台 42和滑环驱动电机 43， 光电滑环 41和滑环驱动电机 43固定于轴向位移平台 42上， 通过滑环驱动电机 43带动 光电滑环 41进行转动。
请一并参阅图 2和图 3， 图 2是本发明实施例的内窥探头的主视图， 图 3 是本发明实施例的内窥探头 50的侧视图。 内窥探头 50包括多模光纤 51、 自 聚焦透镜 52、 反射镜 53、 超声换能器 54、 同轴电缆 55、 光纤固定套管 56、 共轴套管 57、 探头封装套管 58和光纤保护套管 59。 多模光纤 51包括分别与 光电滑环 41相连的两段 （第一段和第二段）， 请结合参阅图 1， 其中， 第一段 的一端通过光纤固定支架 30固定于聚焦透镜 24的一端，另一端套在光纤保护 套管 59内； 第二段的一端套在光纤固定套管 56内， 并顺序与自聚焦透镜 52 及反射镜 53同轴放置于共轴套管 57中； 通过光电滑环 41可以带动与内窥探 头 50相连的一段多模光纤随内窥探头 50—起旋转实现内窥镜的 360° 扫描。 超声换能器 54与共轴套管 57固定于探头封装套管 58中；超声换能器 54通过 同轴电缆 55与超声发射接收器 60连接。
可以理解的是， 超声换能器 54可以以一定角度放置， 如图 3所示， 当然， 也可以水平放置， 如图 4所示。
本实施例中， 激光器 10为 0P0TEK VIBRANT II (VIBRANT系列产品采用一 体化设计， 泵浦激光、 0P0、 控制电路等集成在一个光学结构中， 在得到宽光 谱激光输出的同时， 保持了很高的 0P0转换效率）， 激光光束为短脉冲激光或 幅度调制激光， 输出波长范围为 400-2400nm; 分束镜 22的反射 /透射比为 8: 92； 内窥探头 50的直径为 0. 3〜1. 0mm, 超声换能器 54的接收面与内窥探头 50的中心轴线呈 5°〜40° 角放置， 其中心频率为 5〜75MHz。
本发明实施例的血管内光声超声双模成像系统的工作原理为： 激光器 10 输出激光光束并发出超声触发信号，经过光阑 21滤掉激光光束的部分杂散光， 并通过分束镜 22将激光光束分为两路，一路照射到光电二极管 23作为参考光， 另一路经过聚焦透镜 24聚焦后耦合进入内窥探头 50中的多模光纤 51， 激光 光束经多模光纤 51传输到内窥探头 50中， 由内窥探头 50中的自聚焦透镜 52 进行聚焦或准直， 其后经反射镜 53侧向反射到管腔样本激发产生光声信号， 超声换能器 54接收光声信号并转化为光声电信号，通过同轴电缆 55将光声电 信号传输到超声发射接收器 60进行放大，然后传输到数据采集系统 70进行光 声信号采集； 与此同时， 激光器 10发出的超声触发信号经过信号延迟模块 90 延时后传输到超声发射接收器 60， 控制超声发射接收器 60发射超声波， 并通 过同轴电缆 55将超声波传输到内窥探头 50中的超声换能器 54， 通过超声换 能器 54将超声波侧向发射到管腔样本， 并接收管腔样本反射的超声波， 将接 收的超声波转化为超声电信号后回传到超声发射接收器 60进行放大， 再传输 到数据采集系统 70进行超声信号采集；图像重建和显示系统 80将采集到的光 声信号和超声信号进行重建， 得到相应样本的光声图像和超声图像； 通过探头 扫描装置 40控制内窥探头 50进行 360度的旋转和轴向移动扫描，每采集完一 次信号， 内窥探头 50转动一定角度重新采集信号， 重复至旋转一圈； 每旋转 扫描一圈， 内窥探头 50轴向移动一定距离重新采集信号， 重复至完成轴向扫 描。
请参阅图 5， 是本发明实施例的血管内光声超声双模成像方法的流程图。 本发明实施例的血管内光声超声双模成像方法包括以下步骤：
步骤 500: 通过激光器输出激光光束并发出超声触发信号。
在步骤 500中， 激光器为 0P0TEK VIBRANT II， 激光光束为短脉冲激光或 幅度调制激光， 输出波长范围为 400-2400nm
步骤 510: 通过光阑滤掉激光光束的部分杂散光， 并通过分束镜将光束分 为两路， 一路照射到光电二极管作为参考光， 另一路经过聚焦透镜聚焦后耦合 进入多模光纤。
在步骤 510中， 分束镜的反射 /透射比为 8: 92
步骤 520: 通过多模光纤将激光光束传输到内窥探头中， 由内窥探头中的 自聚焦透镜进行聚焦或准直后通过反射镜侧向反射到管腔样本激发产生光声 信号。
在步骤 520中， 内窥探头的直径为 0. 3 1. 0
步骤 530: 通过超声换能器接收光声信号并转化为光声电信号， 通过同轴 电缆将光声电信号传输到超声发射接收器进行放大后传输到数据采集系统进 行光声信号采集，同时激光器发出的超声触发信号经过延时后传输到超声发射 接收器， 控制超声发射接收器发射超声波， 并通过同轴电缆将超声波传输到超 声换能器， 并通过超声换能器将超声波侧向发射到管腔样本， 并接收管腔样本 反射的超声波， 将接收的超声波转化为超声电信号后回传到超声发射接收器。
在步骤 530 中， 超声换能器的接收面与内窥探头的中心轴线呈 5° 40 ° 角放置， 其中心频率为 5 75MHz
步骤 560: 通过超声发射接收器将接收到的超声电信号进行放大， 并传输 到数据采集系统进行超声信号采集。
步骤 570: 通过图像重建和显示系统将数据采集系统采集到的光声信号和 超声信号进行重建， 得到相应样本的光声图像和超声图像。
步骤 580: 通过探头扫描装置控制内窥探头进行 360度的旋转和轴向移动 扫描， 每采集完一次信号， 内窥探头转动一定角度重新采集信号， 重复至旋转 一圈； 每旋转扫描一圈， 内窥探头轴向移动一定距离重新采集信号， 重复至完 成轴向扫描。
本发明实施例的血管内光声超声双模成像系统及成像方法通过将激光进 行聚焦或准直后侧向反射到管腔内壁，提高光的利用率及对目标组织的穿透深 度， 进而增加了光声成像的深度和信噪比， 具有更好的成像质量； 另外， 利用 激光器输出激光光束的同时发出超声触发信号，通过触发信号控制超声发射接 收器发射超声波进行超声成像， 实现了同时、 同区域的光声和超声成像， 更有 利于早期肿瘤、 动脉粥样硬化等疾病的检测。
以上所述仅为本发明的较佳实施例而已，并不用以限制本发明，凡在本发 明的精神和原则之内所作的任何修改、等同替换和改进等， 均应包含在本发明 的保护范围之内。

Claims

权 利 要 求
1、 一种血管内光声超声双模成像系统， 其特征在于， 包括激光器、 内窥 探头、超声发射接收器、 数据采集系统及图像重建和显示系统， 所述激光器用 于输出激光光束并发出触发信号，所述超声发射接收器用于根据所述触发信号 控制发射超声波并同时接收光声信号和超声信号，所述内窥探头用于将激光光 束聚焦或准直后侧向反射到管腔样本激发产生所述光声信号，同时侧向发射超 声波并接收所述管腔样本反射的所述超声信号，所述数据采集系统用于采集所 述光声信号和所述超声信号，并通过所述图像重建和显示系统重建管腔样本的 光声图像和超声图像。
2、 根据权利要求 1所述的血管内光声超声双模成像系统， 其特征在于， 还包括激光光路和探头扫描装置， 所述激光光路包括光阑、 分束镜、光电二极 管和聚焦透镜， 所述光阑、 所述分束镜和所述聚焦透镜依次相连， 所述光电二 极管和所述分光镜相连； 所述探头扫描装置包括光电滑环、轴向位移平台和滑 环驱动电机， 所述光电滑环和所述滑环驱动电机固定于轴向位移平台上， 通过 所述滑环驱动电机带动所述光电滑环进行转动，用于控制所述内窥探头进行三 维扫描。
3、 根据权利要求 2所述的血管内光声超声双模成像系统， 其特征在于， 还包括光纤固定支架， 所述内窥探头还包括多模光纤、 自聚焦透镜、 反射镜、 超声换能器、 同轴电缆、 光纤固定套管、 共轴套管、 探头封装套管和光纤保护 套管， 其中， 所述多模光纤包括分别与光电滑环相连的两段， 第一段的一端通 过所述光纤固定支架固定于所述聚焦透镜的一端， 另一端套在光纤保护套管 内，第二段的一端套在光纤固定套管内与内窥探头相连， 并顺序与自聚焦透镜 及反射镜同轴放置于共轴套管中，所述超声换能器与共轴套管固定于探头封装 套管中， 所述超声换能器通过同轴电缆与超声发射接收器连接。
4、 根据权利要求 3所述的血管内光声超声双模成像系统， 其特征在于， 还包括信号延迟模块，所述信号延迟模块用于将激光器发出的超声触发信号进 行延时后传输到超声发射接收器， 控制超声发射接收器发射超声波。
5、 根据权利要求 4所述的血管内光声超声双模成像系统， 其特征在于， 所述血管内光声超声双模成像系统的成像方式为：
激光器输出激光光束并发出超声触发信号，激光光束经由多模光纤传输到 内窥探头中，由内窥探头中的自聚焦透镜进行聚焦或准直后通过反射镜侧向反 射到管腔样本激发产生光声信号， 数据采集系统进行光声信号采集；
超声触发信号经过信号延迟模块延时后传输到超声发射接收器控制发射 超声波， 同轴电缆将超声波传输到超声换能器，超声换能器将超声波侧向发射 到管腔样本， 数据采集系统进行超声信号采集；
图像重建和显示系统将数据采集系统采集到的光声信号和超声信号进行 图像重建。
6、 根据权利要求 5所述的血管内光声超声双模成像系统， 其特征在于， 所述激光光束为短脉冲激光或幅度调制激光， 输出波长范围为 400-2400nm， 所述分束镜的反射 /透射比为 8 : 92， 所述内窥探头的直径为 0. 3〜1. 0匪， 所 述超声换能器的接收面与内窥探头的中心轴线呈 5°〜40 ° 角放置， 其中心频 率为 5〜75MHz。
7、 一种血管内光声超声双模成像方法， 包括：
步骤 a: 激光器输出激光光束并发出超声触发信号；
步骤 b : 内窥探头将激光光束聚焦或准直后侧向反射到管腔样本激发产生 光声信号，同时超声触发信号控制超声发射接收器发射超声波至所述管腔样本 并反射超声信号；
步骤 c : 采集所述光声信号和所述超声信号， 并根据所述光声信号和所述 超声信号重建管腔样本的光声图像和超声图像。
8、 根据权利要求 7所述的血管内光声超声双模成像方法， 其特征在于， 在所述步骤 b中， 还包括：
多模光纤将激光光束传输到内窥探头中，由内窥探头中的自聚焦透镜进行 聚焦或准直后经反射镜侧向反射到管腔样本激发产生所述光声信号；
超声触发信号经过延时后传输到超声发射接收器，控制超声发射接收器发 射超声波， 同轴电缆将超声波传输到超声换能器，超声换能器将超声波侧向发 射到管腔样本， 并反射所述超声信号。
9、 根据权利要求 8所述的血管内光声超声双模成像方法， 其特征在于， 所述步骤 C后还包括：
探头扫描装置控制内窥探头进行旋转和轴向移动扫描， 每采集完一次信 号， 内窥探头转动一定角度重新采集信号， 重复至旋转一圈；
每旋转扫描一圈， 内窥探头轴向移动一定距离重新采集信号，重复至完成 轴向扫描。
10、根据权利要求 7或 8或 9所述的血管内光声超声双模成像方法，其特 征在于， 所述激光光束为短脉冲激光或幅度调制激光， 输出波长范围为 400-2400nm， 所述内窥探头的直径为 0.3〜1.0mm， 所述超声换能器的接收面 与内窥探头的中心轴线呈 5°〜40° 角放置， 其中心频率为 5〜75MHz。
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Cited By (1)

* Cited by examiner, † Cited by third party
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Families Citing this family (52)

* Cited by examiner, † Cited by third party
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WO2017139728A1 (en) * 2016-02-13 2017-08-17 Purdue Research Foundation Photoacoustic catheter and imaging system using same
CN105769128B (zh) * 2016-05-06 2018-10-19 华南师范大学 一体化的光声、超声、光声弹性内窥成像装置及其方法
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CN116077175B (zh) * 2023-03-02 2024-02-23 哈尔滨工业大学（威海） 一种血管内四模态成像及消融一体化导管

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN101594819A (zh) * 2006-11-08 2009-12-02 光学实验室成像公司 光声成像装置和方法
CN101912250A (zh) * 2010-05-24 2010-12-15 华南师范大学 一种血管内光声超声双模成像内窥镜装置及其成像方法
US20110098572A1 (en) * 2008-10-28 2011-04-28 The Regents Of The University Of California Ultrasound guided optical coherence tomography, photoacoustic probe for biomedical imaging
US20120253180A1 (en) * 2010-10-19 2012-10-04 Stanislav Emelianov Combined ultrasound and photoacoustic imaging of metal objects
CN102743191A (zh) * 2012-06-28 2012-10-24 华南师范大学 聚焦式旋转扫描光声超声血管内窥成像装置及其成像方法
CN103385758A (zh) * 2013-07-22 2013-11-13 深圳先进技术研究院 一种血管内光声超声双模成像系统及其成像方法

Family Cites Families (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH01139081A (ja) * 1987-11-27 1989-05-31 Olympus Optical Co Ltd レーザ光照射装置
AU2002308466A1 (en) * 2001-04-24 2002-11-05 National Research Council Of Canada Method and apparatus for probing objects in motion
JP5506395B2 (ja) * 2006-12-19 2014-05-28 コーニンクレッカ フィリップス エヌ ヴェ 光音響及び超音波の結合型イメージング・システム
CA2760691A1 (en) * 2009-05-01 2010-11-04 Visualsonics Inc. System for photoacoustic imaging and related methods
CN101919686B (zh) * 2010-09-21 2011-12-14 华中科技大学 用于活动动物脑皮层功能观测的多模式成像系统
CN102512206B (zh) * 2011-12-13 2014-04-09 苏州生物医学工程技术研究所 血管内超声超声诊断与光声治疗装置及其治疗方法

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN101594819A (zh) * 2006-11-08 2009-12-02 光学实验室成像公司 光声成像装置和方法
US20110098572A1 (en) * 2008-10-28 2011-04-28 The Regents Of The University Of California Ultrasound guided optical coherence tomography, photoacoustic probe for biomedical imaging
CN101912250A (zh) * 2010-05-24 2010-12-15 华南师范大学 一种血管内光声超声双模成像内窥镜装置及其成像方法
US20120253180A1 (en) * 2010-10-19 2012-10-04 Stanislav Emelianov Combined ultrasound and photoacoustic imaging of metal objects
CN102743191A (zh) * 2012-06-28 2012-10-24 华南师范大学 聚焦式旋转扫描光声超声血管内窥成像装置及其成像方法
CN103385758A (zh) * 2013-07-22 2013-11-13 深圳先进技术研究院 一种血管内光声超声双模成像系统及其成像方法

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN116158720A (zh) * 2022-12-30 2023-05-26 深圳开立生物医疗科技股份有限公司 光学-光声-超声复合内窥镜和内窥镜系统
CN116158720B (zh) * 2022-12-30 2023-11-21 深圳开立生物医疗科技股份有限公司 光学-光声-超声复合内窥镜和内窥镜系统

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