WO2020056624A1 - 一种光声双模成像探头 - Google Patents

一种光声双模成像探头 Download PDF

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Publication number
WO2020056624A1
WO2020056624A1 PCT/CN2018/106480 CN2018106480W WO2020056624A1 WO 2020056624 A1 WO2020056624 A1 WO 2020056624A1 CN 2018106480 W CN2018106480 W CN 2018106480W WO 2020056624 A1 WO2020056624 A1 WO 2020056624A1
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WO
WIPO (PCT)
Prior art keywords
transducer
optical fiber
imaging probe
mode imaging
photoacoustic dual
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Ceased
Application number
PCT/CN2018/106480
Other languages
English (en)
French (fr)
Inventor
吴飞
唐明
柯昌星
杨芳
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Shenzhen Mindray Bio Medical Electronics Co Ltd
Shenzhen Mindray Scientific Co Ltd
Original Assignee
Shenzhen Mindray Bio Medical Electronics Co Ltd
Shenzhen Mindray Scientific Co Ltd
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Shenzhen Mindray Bio Medical Electronics Co Ltd, Shenzhen Mindray Scientific Co Ltd filed Critical Shenzhen Mindray Bio Medical Electronics Co Ltd
Priority to PCT/CN2018/106480 priority Critical patent/WO2020056624A1/zh
Priority to CN201880097179.3A priority patent/CN112672690B/zh
Priority to CN202411907541.2A priority patent/CN119732655A/zh
Publication of WO2020056624A1 publication Critical patent/WO2020056624A1/zh
Priority to US17/204,185 priority patent/US20210270780A1/en
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N29/00—Investigating or analysing materials by the use of ultrasonic, sonic or infrasonic waves; Visualisation of the interior of objects by transmitting ultrasonic or sonic waves through the object
    • G01N29/22—Details, e.g. general constructional or apparatus details
    • G01N29/24—Probes
    • G01N29/2418—Probes using optoacoustic interaction with the material, e.g. laser radiation, photoacoustics
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
    • G01N21/1702—Systems in which incident light is modified in accordance with the properties of the material investigated with opto-acoustic detection, e.g. for gases or analysing solids
    • 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, 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, 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
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B06—GENERATING OR TRANSMITTING MECHANICAL VIBRATIONS IN GENERAL
    • B06B—METHODS OR APPARATUS FOR GENERATING OR TRANSMITTING MECHANICAL VIBRATIONS OF INFRASONIC, SONIC, OR ULTRASONIC FREQUENCY, e.g. FOR PERFORMING MECHANICAL WORK IN GENERAL
    • B06B1/00—Methods or apparatus for generating mechanical vibrations of infrasonic, sonic, or ultrasonic frequency
    • B06B1/02—Methods or apparatus for generating mechanical vibrations of infrasonic, sonic, or ultrasonic frequency making use of electrical energy
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01H—MEASUREMENT OF MECHANICAL VIBRATIONS OR ULTRASONIC, SONIC OR INFRASONIC WAVES
    • G01H9/00—Measuring mechanical vibrations or ultrasonic, sonic or infrasonic waves by using radiation-sensitive means, e.g. optical means
    • G01H9/004—Measuring mechanical vibrations or ultrasonic, sonic or infrasonic waves by using radiation-sensitive means, e.g. optical means using fibre optic sensors
    • G—PHYSICS
    • G10—MUSICAL INSTRUMENTS; ACOUSTICS
    • G10K—SOUND-PRODUCING DEVICES; METHODS OR DEVICES FOR PROTECTING AGAINST, OR FOR DAMPING, NOISE OR OTHER ACOUSTIC WAVES IN GENERAL; ACOUSTICS NOT OTHERWISE PROVIDED FOR
    • G10K15/00—Acoustics not otherwise provided for
    • G10K15/04—Sound-producing devices
    • G10K15/046—Sound-producing devices using optical excitation, e.g. laser bundle
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
    • G01N21/1702—Systems in which incident light is modified in accordance with the properties of the material investigated with opto-acoustic detection, e.g. for gases or analysing solids
    • G01N2021/1706—Systems in which incident light is modified in accordance with the properties of the material investigated with opto-acoustic detection, e.g. for gases or analysing solids in solids

Definitions

  • the invention relates to a photoacoustic dual-mode imaging probe.
  • Photoacoustic dual-mode imaging is a dual-mode imaging method that combines photoacoustic imaging and ultrasound imaging. Photoacoustic imaging reflects the functional information of living organisms, while traditional ultrasound imaging reflects the structural information of living organisms and effectively combines the two. Together, photoacoustic dual-modality imaging overcomes the shortcomings of single-modality imaging and can provide more comprehensive information on tissue structure and function.
  • the photoacoustic dual-modality imaging system includes an ultrasound device, a laser, and a fiber optic beam coupled to an ultrasound probe.
  • the photoacoustic system and the ultrasonic system are relatively independent and can be disassembled. It is difficult to clean and disinfect during use, and the grip and human-computer interaction performance are poor.
  • a coupling pad needs to be used in order to concentrate the laser energy under the acoustic head and diffuse the laser spot simultaneously. The coupling pad needs to be cleaned, disinfected and replaced, which increases the use and maintenance costs.
  • the invention provides a photoacoustic dual-mode imaging probe to solve the problem that when using a photoacoustic dual-modality imaging system, the photoacoustic system and the ultrasound system of the probe are relatively independent, and it is difficult to clean and sterilize during use, the grip and the human Poor machine interaction performance and the use of coupling pads cause many inconveniences.
  • the invention provides a photoacoustic dual-mode imaging probe, which includes an optical fiber, a transducer, and a casing; the optical fiber and the transducer are at least partially wrapped inside the casing, and the optical fiber outlet and the transducer are located in the photoacoustic dual-mode imaging probe Fiber optic head for transmitting laser pulses; transducer for transmitting and receiving ultrasonic signals.
  • the photoacoustic dual-mode imaging probe provided by the invention wraps the optical fiber and the transducer in the interior through the shell, so that the three become a whole, which is convenient for cleaning and disinfection, convenient to hold, strong human-computer interaction performance, and eliminates a coupling pad. usage of.
  • FIG. 1 is a cross-sectional view of an embodiment of a photoacoustic dual-mode imaging probe
  • FIG. 2 is a partially enlarged cross-sectional view of an embodiment of a photoacoustic dual-mode imaging probe
  • FIG 3 is a cross-sectional view of an embodiment of a photoacoustic dual-mode imaging probe.
  • the photoacoustic dual-mode imaging probe includes an optical fiber 3, a transducer 2, and a housing 1; the optical fiber 3 is used for transmitting laser pulses; the transducer is used for transmitting and receiving ultrasonic signals ; The optical fiber 3 and the transducer 2 are at least partially wrapped inside the casing 1;
  • the end of the transducer 2 transmitting and receiving ultrasonic signals is designated as the front end, and the end of the photoacoustic dual-mode imaging probe used for scanning is the acoustic head, and the direction toward the acoustic head is photoacoustic dual-mode imaging.
  • the front of the probe is the front of the probe.
  • the light exit of the optical fiber 3 and the transducer 2 are both located on the acoustic head end of the photoacoustic dual-mode imaging probe, so as to realize the functions of transmitting the laser pulse and transmitting and receiving ultrasonic signals by the acoustic head end of the photoacoustic dual-mode imaging probe.
  • the optical fiber 3 and the transducer 2 are at least partially wrapped inside the casing 1, including: the optical fiber 3 and the transducer 2 are completely enclosed in the casing 1; the light outlet of the optical fiber 3 and the front end of the transducer 2 are exposed outside the casing 1, and the rest It is partially wrapped in the casing 1, that is, the acoustic head end of the photoacoustic dual-mode imaging probe is not wrapped by the casing 1; or other optical fibers 3 and the transducer 2 are at least partially wrapped inside the casing 1.
  • the optical fiber 3 When the photoacoustic dual-mode imaging probe responds to the working signal, on the one hand, the optical fiber 3 generates a laser pulse to irradiate human tissue, and the substance with strong optical absorption characteristics in the tissue absorbs light energy and causes local heating and thermal expansion, thereby generating an ultrasonic signal outward It is transmitted and received by the transducer 2.
  • the transducer 2 converts the received ultrasonic signal into an electrical signal and transmits it to the ultrasound host.
  • the ultrasound host processes the ultrasound signal to generate a photoacoustic image for diagnosis by medical staff.
  • the transducer 2 receives the working signal, it transmits an ultrasonic signal to the human tissue and receives the corresponding ultrasonic echo signal.
  • the transducer 2 converts the received ultrasonic signal into an electrical signal and transmits it to the ultrasonic host.
  • the ultrasonic host By processing this ultrasound signal, an ultrasound image is generated for diagnosis by medical staff.
  • the photoacoustic dual-mode imaging probe wraps the optical fiber 3 and the transducer 2 integrally through the housing 1. Through a photoacoustic dual-mode imaging probe, the requirements of the photoacoustic imaging and ultrasonic imaging dual-mode imaging can be achieved, which improves the probe holding It is also good for cleaning and disinfection during use.
  • the optical fiber 3 and the transducer 2 are completely wrapped in the casing 1.
  • At least the outer casing at the light exit of the optical fiber 3 is made of a light guide material, at least at the front end of the transducer 2.
  • the shell is made of sound-transmitting material, including only the shell at the light exit of the optical fiber 3 is made of light-guiding material, only the shell at the front end of the transducer 2 is made of acoustic material, and the other parts of the shell 1 are made of other materials
  • the housing at the front end of the optical fiber 3 and the front end of the transducer 2 are made of light-guiding and sound-transmitting materials, and other parts of the housing 1 are made of other materials; Other conditions that meet the conditions.
  • the laser pulse emitted by the optical fiber 3 is transmitted through the light guide portion of the housing 1 at the light exit of the optical fiber 3, and is focused on the human tissue in front of the probe's acoustic head, reducing the optical signal being converted by the transducer.
  • the laser pulse emitted by the optical fiber 3 passes through the light guide portion of the housing 1 at the light exit of the optical fiber 3 to play a role of focusing the laser pulse in front of the acoustic head and diffusing the laser spot, replacing the role of the coupling pad and avoiding
  • the probe must cooperate with the inconvenience caused by the coupling pad.
  • a substance with strong optical absorption characteristics in the tissue absorbs light energy and causes local heating and thermal expansion, thereby generating an ultrasonic signal to propagate outward and pass through the housing 1 at the front end of the transducer 2.
  • the acoustic part is received by the transducer 2, and the ultrasonic signal is converted into a photoacoustic image after conversion processing.
  • the ultrasonic signal emitted by the transducer 2 enters the human tissue through the sound-transmitting part of the housing 1 at the front end of the transducer 2, and the echo signal formed passes through the front end of the transducer 2
  • the sound-transmitting part of the casing 1 is received by the transducer 2 and the echo signal is converted into an ultrasonic image.
  • the optical fiber 3 is completely wrapped in the casing 1, the front end of the transducer 2 is exposed outside the casing 1, and the rest is wrapped inside the casing 1, at least the casing 1 at the light outlet of the optical fiber 3.
  • Made of light guide material This embodiment includes a case where the entire housing 1 is made of a light guide material, only the housing 1 at the light exit of the optical fiber 3 is made of a light guide material, and the other parts of the housing 1 are made of other materials or other conditions are met.
  • the laser pulse emitted by the optical fiber 3 passes through the light guide portion of the housing 1 at the light exit of the optical fiber 3 and is then focused on the human tissue in front of the acoustic head of the probe.
  • the role of the light guide portion of the housing 1 diffuses the laser spot emitted by the optical fiber, reduces the energy radiated on the local part of the human tissue, and prevents the laser from burning the skin.
  • the laser pulse emitted by the optical fiber 3 passes through the light guide portion of the casing 1 at the light exit of the optical fiber 3 to play a role of concentrating the optical signal under the acoustic head and diffusing the laser spot, replacing the role of the coupling pad and avoiding
  • the probe must cooperate with the inconvenience caused by the coupling pad.
  • a substance with strong optical absorption characteristics in the tissue absorbs light energy and causes local heating and thermal expansion, thereby generating an ultrasonic signal to be transmitted outward and received by the transducer 2.
  • the ultrasonic signal After conversion processing, a photoacoustic image is generated.
  • the ultrasonic signal emitted by the transducer 2 enters the human tissue, and the echo ultrasonic signal formed is received by the transducer 2, and the echo ultrasonic signal is converted to generate an ultrasonic image.
  • a head cover is further included.
  • the light exit of the optical fiber 3 and the front end of the transducer 2 are exposed outside the housing 1, that is, the head of the photoacoustic dual-mode imaging probe is not covered by the housing 1.
  • Wrapped, the acoustic hood is located at the light exit of the optical fiber 3 and the front end of the transducer 2, and is wrapped outside the acoustic head end of the photoacoustic dual-mode imaging probe and connected to the housing 1.
  • the acoustic hood is made of light-guiding and sound-transmitting material .
  • the laser pulse emitted by the optical fiber 3 is transmitted through the probe cover and focused on the human tissue in front of the probe's acoustic head, reducing the energy loss caused by the light signal being blocked by the transducer;
  • the function of the head cover diffuses the laser spot emitted by the optical fiber 3, reduces the energy irradiated on the local part of the human tissue, and prevents the laser from burning the skin.
  • the laser pulse emitted by the optical fiber 3 through the acoustic hood plays the role of focusing the laser pulse in front of the acoustic head and diffusing the laser spot, replacing the role of the coupling pad and avoiding the need for the probe in the traditional dual-mode imaging process.
  • the optical fiber 3 and the transducer 2 are completely enclosed in the casing 1, there is a filling layer 4 between the light outlet of the optical fiber 3 and the front end of the transducer 2 and the casing 1.
  • Layer 4-position light-guiding and sound-transmitting materials such as materials with good acoustic and optical transmission properties, such as liquid coupling agents, gel materials, or mixtures of the two.
  • the laser pulse emitted by the optical fiber 3 is transmitted through the filling layer 4 and the housing 1, which can better illuminate the light field energy in front of the acoustic head; on the other hand, The laser pulse emitted by the optical fiber 3 is transmitted through the filling layer 4 and the casing 1, so that the effect of the laser spot diffusion and the reduction of local energy is better; at the same time, it will not affect the transmission and reception of the ultrasonic signal.
  • the light outlet of the optical fiber 3 and the front end of the transducer 2 are exposed outside the casing 1 and wrapped in the hood, and there is a filling between the light outlet of the optical fiber and the front end of the transducer and the hood.
  • the filling layer is a light-guiding and sound-transmitting material, such as a liquid coupling agent, a gel material, or a mixture of the two, which has good acoustic and optical transmission properties.
  • the laser pulse emitted by the optical fiber 3 is transmitted through the filling layer 4 and the acoustic hood, which can better illuminate the light field energy in front of the acoustic head;
  • the laser pulse emitted by the optical fiber 3 is transmitted through the filling layer 4 and the acoustic hood, so that the diffusion of the laser spot is more effective in reducing local energy; at the same time, it will not affect the transmission and reception of ultrasonic signals.
  • the casing 1 is wrapped before the light exit of the optical fiber 3
  • the filling layer is a light guide material.
  • the laser pulse emitted by the optical fiber 3 is transmitted through the filling layer 4 and the casing 1, which can better illuminate the light field energy in front of the acoustic head.
  • the laser emitted by the optical fiber 3 The transmission of the pulse through the filling layer 4 and the casing 1 makes the laser spot diffusion more effective in reducing local energy, while not affecting the transmission and reception of ultrasonic signals.
  • the figure does not show that, in the embodiment in which the acoustic hood is wrapped with the light outlet of the optical fiber 3 and the front end of the transducer 2, there is a filling layer between the optical outlet of the optical fiber 3 and the acoustic hood, and the filling layer is a light guide material.
  • the laser pulse emitted by the optical fiber 3 is transmitted through the filling layer 4 and the acoustic head cover, which can better focus the light field energy to the front of the acoustic head, while the optical fiber 3 emits
  • the transmission of the laser pulse through the filling layer 4 and the acoustic hood makes the diffusion of the laser spot more effective in reducing local energy, while not affecting the transmission and reception of ultrasonic signals.
  • the light exit of the optical fiber 3 is spaced a predetermined distance from the front end of the transducer 2 to reduce the laser pulse emitted by the light exit of the optical fiber 3 being blocked by the transducer and affect the light.
  • the quality of the acoustic imaging can be reduced by a predetermined distance between the light exit of the optical fiber 3 and the front end of the transducer 2 to reduce the interference of the laser pulse emitted by the optical fiber 3 on the transducer.
  • the predetermined distance is determined comprehensively by the type, size and measurement requirements of the probe.
  • the front section of the optical fiber 3 is parallel to the axis where the transducer 2 is located or the front section of the optical fiber 3 is arranged at an acute angle with the axis where the transducer 2 is located.
  • the axis where the transducer 2 is located refers to a straight line perpendicular to the front surface of the transducer 2, that is, a straight line perpendicular to the surface of the transducer 2 transmitting and receiving ultrasonic signals.
  • the front section of the optical fiber 3 is that the optical fiber 3 is located in front of the photoacoustic dual-mode imaging probe. Part of the ministry.
  • the front section of the optical fiber 3 is parallel to the axis where the transducer 2 is located or the front section of the optical fiber 3 is arranged at an acute angle with the axis where the transducer 2 is located, that is, the angle between the front section of the optical fiber 3 and the transducer 2 is greater than or equal to 0 degrees and less than 90 degrees.
  • the angle is configured according to the clinical depth of detection requirements.
  • the front section of the optical fiber 3 and the transducer 2 are at an acute angle, the light exit of the inclined optical fiber 3 solves the problem that the light beam is blocked by the transducer 2, and at the same time, the laser pulse emitted by the optical fiber 3 is effectively focused on the sound of the probe Under the head.
  • the optical fiber 3 may be one or a plurality of fibers, and the plurality of optical fibers may be arranged side by side into an optical fiber bundle. In one embodiment, a plurality of optical fibers 3 are included.
  • the multiple optical fibers 3 are located on both sides of the transducer 2, on the side of the transducer 2, or around the transducer 2.
  • the surrounding of the transducer 2 may be evenly distributed on the transducer.
  • One week can also be divided into three beams, four beams surrounding the transducer 2 and other positions that are beneficial to the optical fiber 3 to emit laser pulses, and the transducer 2 to transmit and receive ultrasonic signals.
  • the plurality of optical fibers 3 may be aligned with each other to form an optical fiber bundle arranged at the above position, or may be separately arranged at the above position.
  • a fixing device 5 is further included.
  • the optical fiber 3 is wrapped in the fixing device 5, and the fixing device 5 is at least partially housed in the casing.
  • the fixing device 5 is used for fixing the optical fiber 3 and plays a role of protecting the optical fiber 3.
  • the optical fiber 3 and the transducer 2 are fixedly connected as a whole, and the relative positions of the optical fiber 3 and the transducer 2 can be fixed by glue bonding, mechanical fixing, or other fixed connection methods.
  • this embodiment further includes a sound transmitting element 6.
  • the sound transmitting element 6 is at least partially wrapped outside the transducer 2 and extends to the front surface of the transducer 2. At least a part of the optical fiber 3 and the transducer 2 are fixedly connected together through the sound-transmitting element 6, and the light exit of the optical fiber 3 is exposed outside the sound-transmitting element 6.
  • the ultrasonic signal emitted by the transducer 2 plays a focusing role through the sound transmitting element 6 located on its front surface, reducing the loss of the ultrasonic signal and improving the quality of imaging; other parts of the sound transmitting element 6 are wholly or partially wrapped in said Outside the transducer 2, the sound-transmitting element 6 pots the transducer 2 and the optical fiber 3 so that the transducer 2 and the optical fiber 3 are fixedly connected as a whole through the sound-transmitting element 6.
  • the sound-transmitting element 6 is made of a sound-transmissive and reflective material, for example, a non-absorption, high-scattering substance is added to a conventional lens material, or the sound-transmitting element 6 is made of a sound-transmitting and light-absorbing material.
  • the sound-transmitting element 6 made of a sound-transmitting reflective material or a sound-absorbing light-absorbing material completely or partially covers the transducer, so that the laser pulse emitted by the optical fiber 3 does not enter the transducer 2 and cause interference, and is located at the same time as the transducer
  • the sound transmitting element on the front surface of the transducer can focus the ultrasonic signals emitted by the transducer 2.
  • this embodiment further includes a signal cable 7.
  • the signal cable 7 includes a transducer signal line (not shown), an optical fiber extension (not shown), and an outer skin 8; the transducer signal The cable is connected to the transducer 2.
  • the transducer receives and transmits signals through the transducer signal line; the fiber extension is the part where the fiber 3 extends to the signal cable, and the laser pulse is transmitted to and from the fiber 3 through the fiber extension.
  • the light exit port emits outwards; the transducer signal line and the fiber extension are wrapped in the outer skin 8, and the fiber extension and the transducer signal line are wrapped together to make the overall structure simple and the photoacoustic dual-mode imaging probe easy to use.
  • the signal cable 7 further includes a protection device (not shown in the figure), the protection device is wrapped outside the optical fiber extension section, and the sheath 8 is wrapped outside the protection device, and the protection device protects the optical fiber with the signal inside the signal cable.
  • the cable is not easy to break when it is bent to a certain degree.
  • the signal cable 7 further includes a shielding network (not shown in the figure), the shielding network is wrapped outside the transducer signal line and the optical fiber extension, and the sheath 8 is wrapped outside the shielding network.
  • the shielding network is set so that when the electric signal and the optical signal are transmitted in the transducer signal line and the optical fiber extension section, the interference from the external environment is avoided, and the transmission efficiency is improved.
  • the transducer signal lines are all distributed around the optical fiber extension section, and the sheath 8 is wrapped around the transducer signal lines and the optical fiber extension section to form a signal cable 7 integrally.

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Abstract

本发明公开了一种光声双模成像探头，包括光纤、换能器和外壳；光纤和换能器至少部分包裹于外壳内部，光纤出光口与换能器前端均位于光声双模成像探头的声头端；光纤用于发射激光脉冲；换能器用于发射和接收超声信号。光声双模成像探头通过外壳将光纤和换能器都包裹于其内部，使三者成为一个整体，便于清洁消毒、方便握持、人机交互性能强且免去了耦合垫的使用。

Description

一种光声双模成像探头 技术领域
本发明涉及一种光声双模成像探头。
背景技术
光声双模成像为结合了光声成像和超声成像的双模式成像方式，光声成像体现了生物体的功能信息，而传统的超声成像反应了生物体的结构信息，将二者有效地结合起来，即光声双模态成像克服了单一模态成像的不足，能够提供更全面的组织结构和功能信息。
光声双模态成像系统包括超声设备、激光器、光纤束耦合至超声探头。光声系统、超声系统相对独立，可以分拆，在使用过程中清洁消毒困难，握持感和人机交互性能较差。另外，在光声双模态成像系统使用过程中，需配合使用耦合垫以使激光能量集中到声头下方同时扩散激光光斑，耦合垫需清洁消毒和更换，提高了使用和维护成本。
发明内容
本发明提供了一种光声双模成像探头，以解决在使用光声双模态成像系统时，探头的光声系统、超声系统相对独立，在使用过程中清洁消毒困难、握持感和人机交互性能差，以及使用耦合垫带来许多不便。
本发明提供了一种光声双模成像探头，包括光纤、换能器和外壳；光纤和换能器至少部分包裹于外壳内部，光纤的出光口与换能器均位于光声双模成像探头的声头端；光纤用于发射激光脉冲；换能器用于发射和接收超声信号。
本发明提供的光声双模成像探头通过外壳将光纤和换能器都包裹于其内部，使三者成为一个整体，便于清洁消毒、方便握持、人机交互性能强且免去了耦合垫的使用。
附图说明
图1为光声双模成像探头的一种实施例的剖面图；
图2为光声双模成像探头的一种实施例的剖面局部放大图；
图3为光声双模成像探头的一种实施例的剖面图。
具体实施方式
下面将结合本发明实施例中的附图，对本发明实施例中的技术方案进行清楚、完整地描述，显然，所描述的实施例仅仅是本发明一部分实施例，而不是全部的实施例。基于本发明中的实施例，本领域普通技术人员在没有做出创造性劳动前提下所获得的所有其他实施例，都属于本发明保护的范围。此外，由于已知的功能和构造会以不必要的细节模糊描述，因此将不详细地描述他们。
如图1至图2所示，实施例所述的光声双模成像探头，包括光纤3、换能器2和外壳1；光纤3用于发射激光脉冲；换能器用于发射和接收超声信号；光纤3和换能器2至少部分包裹于外壳1内部。为方便叙述，指定换能器2向外发射和接收超声信号的一端为前端，指定光声双模成像探头用于扫查的一端为声头端，朝向声头端的方向为光声双模成像探头的前方。光纤3的出光口与换能器2均位于光声双模成像探头的声头端，以实现光声双模成像探头声头端发射激光脉冲和发射、接收超声信号的功能。光纤3和换能器2至少部分包裹于外壳1内部，包括：光纤3和换能器2完全包裹于外壳1内；光纤3的出光口和换能器2的前端露于外壳1外，其余部分包裹于外壳1内，即光声双模成像探头的声头端不被外壳1所包裹；或者其他光纤3和换能器2至少部分包裹于外壳1内部的情况。当光声双模成像探头响应工作信号时，一方面，光纤3产生激光脉冲照射至人体组织，组织中具有强光学吸收特性的物质吸收光能量后引起局部升温和热膨胀，从而产生超声信号向外传播并被换能器2接收，换能器2将所接收到的超声信号转换成电信号传导至超声主机，超声主机通过处理该超声信号，生成光声图像供医护人员进行诊断；另一方面，所述换能器2在接收到工作信号时，向人体组织发射超声信号并接收相应的超声回波信号，换能器2将接收到的超声信号转换成电信号传导至超声主机，超声主机通过处理该超声信号，生成超声图像供医护人员进行诊断。光声双模成像探头通过外壳1将光纤3和换能器2一体包裹，通过一个光声双模成像探头可以达到光声成像以及超声成像双模式成像对探头的要求，提升了探头的握持感，也利于在使用过程中的清洁消毒。
如图1所示，一种实施例中，光纤3和换能器2完全包裹于外壳1内，至少光纤3的出光口处的外壳采用导光材料制成，至少换能器2的前端处的外壳采用透声材料制成，包括仅光纤3的出光口处的外壳采用导光材料制成， 仅换能器2的前端处的外壳采用声材料制成，外壳1其他部分采用其他材料制成；或者光纤3的出光口和换能器2的前端处的外壳采用导光透声材料制成，外壳1其他部分采用其他材料制成；或者外壳1整体采用导光透声材料制成以及满足条件的其他情况。在光声双模成像探头使用时，光纤3发射的激光脉冲通过光纤3的出光口处的外壳1导光部分透射后集中照射在探头声头前方的人体组织，减少了光信号被换能器遮挡而造成的能量损失；同时由于光纤3的出光口处的外壳1导光部分的作用，将光纤3发射的激光光斑扩散，降低照射在人体组织局部的能量，避免激光灼伤皮肤。本实施例中，光纤3发射的激光脉冲通过光纤3的出光口处的外壳1导光部分起到了使激光脉冲集中在声头前方以及扩散激光光斑的作用，替代了耦合垫的作用，避免了传统双模成像过程中，探头必须配合使用耦合垫带来的不便。由光纤3发射的激光脉冲进入人体组织后，组织中具有强光学吸收特性的物质吸收光能量后引起局部升温和热膨胀，从而产生超声信号向外传播并通过换能器2的前端的外壳1透声部分被换能器2接收到，该超声信号经过转化处理后生成光声图像。在光声双模成像探头使用时，换能器2发射的超声信号，通过换能器2的前端的外壳1透声部分进入人体组织，形成的回波信号通过换能器2的前端处的外壳1透声部分被换能器接2收到，该回波信号经过转化处理后生成超声图像。
如图2所示，一种实施例中，光纤3完全包裹于外壳1内，换能器2的前端露于外壳1外部，其余部分包裹于外壳1内部，至少光纤3出光口处的外壳1采用导光材料制成。本实施例包括外壳1整体采用导光材料制成、仅光纤3的出光口处的外壳1采用导光材料而其余部分外壳1采用其他材料制成或者其他满足条件的情况。在光声双模成像探头使用时，光纤3发射的激光脉冲通过光纤3的出光口处的外壳1导光部分透射后集中照射在探头声头前方的人体组织，同时由于光纤3的出光口处的外壳1导光部分的作用，将光纤发射的激光光斑扩散，降低照射在人体组织局部的能量，避免激光灼伤皮肤。本实施例中，光纤3发射的激光脉冲通过光纤3的出光口处的外壳1导光部分起到了使光信号集中在声头下方以及扩散激光光斑的作用，替代了耦合垫的作用，避免了传统双模成像过程中，探头必须配合使用耦合垫带来的不便。由光纤3发射的激光脉冲进入人体组织后，组织中具有强光学吸收特性的物质吸收光能量后引起局部升温和热膨胀，从而产生超声信号向外传 播并被换能器2接收到，该超声信号经过转化处理后生成光声图像。在光声双模成像探头使用时，换能器2发射的超声信号进入人体组织，形成的回波超声信号被换能器2接收到，该回波超声信号经过转化处理后生成超声图像。
图未示出，一种实施例中，还包括声头罩，光纤3的出光口与换能器2的前端露于外壳1外部，即光声双模成像探头的声头端不被外壳1所包裹，声头罩位于光纤3的出光口和换能器2的前端，包裹于光声双模成像探头的声头端外部并与外壳1连接，声头罩为导光透声材料制成。在光声双模成像探头使用时，光纤3发射的激光脉冲通过探头罩透射后集中照射在探头声头前方的人体组织，减少了光信号被换能器遮挡而造成的能量损失；同时由于声头罩的作用，将光纤3发射的激光光斑扩散，降低照射在人体组织局部的能量，避免激光灼伤皮肤。本实施例中，光纤3发射的激光脉冲通过声头罩起到了使激光脉冲集中在声头前方以及扩散激光光斑的作用，替代了耦合垫的作用，避免了传统双模成像过程中，探头必须配合使用耦合垫带来的不便。由光纤3发射的激光脉冲进入人体组织后，组织中具有强光学吸收特性的物质吸收光能量后引起局部升温和热膨胀，从而产生超声信号向外传播并通过声头罩被换能器2接收到，该超声信号经过转化处理后生成光声图像。在光声双模成像探头使用时，换能器2发射的超声信号，通过声头罩进入人体组织，形成的回波信号通过声头罩被换能器接2收到，该回波信号经过转化处理后生成超声图像。
如图3所示，在光纤3和换能器2完全包裹于外壳1内的一种实施例中，光纤3的出光口和换能器2的前端与外壳1之间有填充层4，填充层4位导光透声材料，例如液体耦合剂、凝胶材料或者二者的混合物等具有良好的声学和光学传导透射性能的材料。在光声双模成像探头使用时，一方面光纤3发射的激光脉冲通过填充层4和外壳1透射，可以起到更好的将光场能量集中照射到声头前方的作用；另一方面，光纤3发射的激光脉冲通过填充层4和外壳1的透射，使激光光斑扩散降低局部能量的作用更佳；同时不会影响超声信号的发送和接收。
另一种实施例中，光纤3的出光口与换能器2的前端露于外壳1外部并包裹于声头罩内，光纤的出光口和换能器的前端与声头罩之间有填充层；所述填充层为导光透声材料，例如液体耦合剂、凝胶材料或者二者的混合物等具有良好的声学和光学传导透射性能的材料。在光声双模成像探头使用时， 一方面光纤3发射的激光脉冲通过填充层4和声头罩透射，可以起到更好的将光场能量集中照射到声头前方的作用；另一方面，光纤3发射的激光脉冲通过填充层4和声头罩的透射，使激光光斑扩散降低局部能量的作用更佳；同时不会影响超声信号的发送和接收。
图未示出，在光纤3的出光口前包裹有外壳1的实施例中，在光纤3的出光口与外壳1之间有填充层，填充层为导光材料。在光声双模成像探头使用时，光纤3发射的激光脉冲通过填充层4和外壳1透射，可以起到更好的将光场能量集中照射到声头前方的作用，同时光纤3发射的激光脉冲通过填充层4和外壳1的透射，使激光光斑扩散降低局部能量的作用更佳，同时不会影响超声信号的发送和接收。
图未示出，在光纤3的出光口与换能器2的前端包裹有声头罩的实施例中，光纤3的出光口与声头罩之间有填充层，填充层为导光材料。在光声双模成像探头使用时，光纤3发射的激光脉冲通过填充层4和声头罩的透射，可以起到更好的将光场能量集中照射到声头前方的作用，同时光纤3发射的激光脉冲通过填充层4和声头罩的透射，使激光光斑扩散降低局部能量的作用更佳，同时不会影响超声信号的发送和接收。
如图1至3所示，在本实施例中，光纤3的出光口与换能器2的前端间隔预定的距离，以减少光纤3出光口发射的激光脉冲被换能器遮挡，而影响光声成像的质量，同时，通过光纤3的出光口与换能器2的前端间隔预定的距离，能够减少光纤3发射的激光脉冲对换能器的干扰。预定距离通过探头的类型、尺寸和测量的要求综合确定。
如图1至3所示，在本实施例中，光纤3的前段与换能器2所在轴线平行或光纤3的前段与换能器2所在轴线成锐角配置。换能器2所在轴线指垂直于换能器2前表面的直线，即垂直于换能器2发射和接收超声信号的表面的直线，光纤3的前段为光纤3位于光声双模成像探头前部的一部分。光纤3的前段与换能器2所在轴线平行或光纤3的前段与换能器2所在轴线成锐角配置，即光纤3的前段与换能器2所成角度大于等于0度、小于90度，其角度根据临床的探测深度需求配置。在光纤3的前段与换能器2成锐角的实施例中，倾斜配置的光纤3的出光口解决了光束被换能器2遮挡的问题，同时使得光纤3发射的激光脉冲有效集中于探头声头下方。
光纤3可以为一根也可以为多根，多根光纤可以并排为光纤束。在一种 实施例中，包括多根光纤3。
在一种实施例中，多根光纤3位于换能器2两侧、位于换能器2一侧或者环绕于换能器2，所述环绕于换能器2可以为均布于换能器2一周，也可以为分成三束、四束环绕在换能器2周围以及其他有利于光纤3发射激光脉冲、换能器2发射和接收超声信号的位置。多根光纤3可以相互排列形成光纤束排布在上述位置，也可以分开排布在上述位置。
如图3所示，在本实施例中，还包括固定装置5，光纤3包裹于固定装置5中，固定装置5至少部分收容于外壳中。固定装置5用于固定光纤3，并起到保护光纤3的作用。
一种实施例中，光纤3与换能器2固定连接为一体，可以通过胶粘接、机械固接或者其他固定连接方式，使得光纤3和换能器2的相对位置固定。
如图3所示，本实施例中还包括透声元件6，透声元件6至少部分包裹于换能器2外部，并延伸至换能器2前表面，光纤3的至少一部分与换能器2通过透声元件6固定连接在一起，光纤3的出光口露于透声元件6外。换能器2发射的超声信号透过位于其前表面的透声元件6起到了聚焦作用，减少了超声信号的损失，提高了成像的质量；透声元件6其他部分全部或部分包裹于所述换能器2外部，透声元件6将换能器2与光纤3灌接，使得换能器2与光纤3通过透声元件6固定连接为一体。
一种实施例中，透声元件6采用透声反光的材料制成，例如在传统透镜材料中加入无吸收、高散射物质，或者透声元件6采用透声吸光的材料制成。采用透声反光材料或者透声吸光材料制成的透声元件6全部或部分包裹所述换能器使得所述光纤3发出的激光脉冲不会进入换能器2而引起干扰，同时位于换能器前表面的透声元件能对换能器2发出的超声信号起到聚焦作用。
如图3所示，本实施例还包括信号线缆7，信号线缆7包括换能器信号线(图未示出)、光纤延伸段(图未示出)和外皮8；换能器信号线与换能器2连接，换能器通过换能器信号线接收和传递信号；光纤延伸段为光纤3延伸至信号线缆的部分，激光脉冲通过光纤延伸段传递至光纤3并从光纤3出光口向外发射；换能器信号线与光纤延伸段包裹于外皮8中，将光纤延伸段和换能器信号线包裹为一体，使整体结构简单，光声双模成像探头使用便捷。
一种实施例中，信号线缆7还包括保护装置(图未示出)，保护装置包裹于光纤延伸段外部,外皮8包裹于保护装置外部，该保护装置保护光纤在 信号线缆内部随信号线缆一定程度弯曲时不易折断。
一种实施例中，信号线缆7还包括屏蔽网(图未示出),屏蔽网包裹于换能器信号线与光纤延伸段外部,外皮8包裹于屏蔽网的外部。屏蔽网的设置使得电信号和光信号在换能器信号线和光纤延伸段中传递时，免于被外部环境所干扰，提高传输效率。
另一种实施例中，换能器信号线均布于光纤延伸段的周围，外皮8包裹于换能器信号线和光纤延伸段的外部，一体形成信号线缆7。
以上所述，仅为本申请的具体实施方式，但本申请的保护范围并不局限于此，任何熟悉本技术领域的技术人员在本申请揭露的技术范围内，可轻易想到变化或替换，都应涵盖在本申请的保护范围之内。因此，本申请的保护范围应以所述权利要求的保护范围为准。

Claims (20)

  1. 一种光声双模成像探头，其特征在于：包括光纤、换能器和外壳；
    所述光纤和换能器至少部分包裹于外壳内部，所述光纤的出光口与换能器均位于所述光声双模成像探头的声头端；
    所述光纤用于发射激光脉冲；
    所述换能器用于发射和接收超声信号。
  2. 如权利要求1所述的光声双模成像探头，其特征在于：所述光纤和换能器完全包裹于所述外壳内；
    至少所述光纤的出光口处的外壳采用导光材料制成；
    至少所述换能器的前端处的外壳采用透声材料制成。
  3. 如权利要求1所述的光声双模成像探头，其特征在于：所述光纤完全包裹于所述外壳内；
    所述换能器的前端露于所述外壳外部，其余部分包裹于所述外壳内部；
    至少所述光纤的出光口处的外壳采用导光材料制成。
  4. 如权利要求1所述的光声双模成像探头，其特征在于：还包括声头罩；
    所述光纤的出光口与所述换能器的前端露于所述外壳外部；
    所述声头罩包裹所述光纤的出光口和所述换能器的前端的外部，并与外壳连接；
    所述声头罩为导光透声材料制成。
  5. 如权利要求2所述的光声双模成像探头，其特征在于：所述光纤的出光口和换能器的前端与外壳之间有填充层；
    所述填充层为导光透声材料。
  6. 如权利要求4所述的光声双模成像探头，其特征在于：所述光纤的出光口和换能器的前端与声头罩之间有填充层；
    所述填充层为导光透声材料。
  7. 如权利要求2至3任一所述的光声双模成像探头，其特征在于：所述光纤的出光口与外壳之间有填充层；
    所述填充层为导光材料。
  8. 如权利要求4任一所述的光声双模成像探头，其特征在于：所述光纤的出光口与声头罩之间有填充层；
    所述填充层为导光材料。
  9. 如权利要求1所述的光声双模成像探头，其特征在于：所述光纤的出光口与所述换能器的前端间隔预定距离。
  10. 如权利要求1所述的光声双模成像探头，其特征在于：所述光纤的前段与换能器所在轴线平行或光纤的前段和换能器所在轴线成锐角。
  11. 如权利要求1所述的光声双模成像探头，其特征在于：包括多根光纤。
  12. 如权利要求11所述的光声双模成像探头，其特征在于：所述多根光纤位于换能器两侧、位于换能器一侧或者环绕于换能器。
  13. 如权利要求1所述的光声双模成像探头，其特征在于：还包括固定装置，所述光纤包裹于所述固定装置中；
    所述固定装置至少部分收容于外壳中。
  14. 如权利要求1所述的光声双模成像探头，其特征在于：所述光纤与所述换能器固定连接。
  15. 如权利要求1所述的光声双模成像探头，其特征在于：还包括透声元件，所述透声元件至少部分包裹于所述换能器外部，并延伸至换能器前表面；
    所述光纤的至少一部分与所述换能器通过所述透声元件固定连接在一起；
    所述光纤出光口露于所述透声元件外。
  16. 如权利要求15所述的光声双模成像探头，其特征在于：所述透声元件采用透声反光或者透声吸光的材料制成。
  17. 如权利要求1所述的光声双模成像探头，其特征在于：还包括信号线缆；
    所述信号线缆包括换能器信号线、光纤延伸段和外皮；
    所述换能器信号线与所述换能器连接；
    所述光纤延伸段为所述光纤从声头端延伸至信号线缆的部分；
    所述换能器信号线与所述光纤延伸段包裹于所述外皮中。
  18. 如权利要求17所述的光声双模成像探头，其特征在于：所述信号线缆还包括保护装置；
    所述保护装置包裹于所述光纤延伸段外部；
    所述外皮包裹于所述保护装置外部。
  19. 如权利要求17所述的光声双模成像探头，其特征在于：所述信号线缆还包括屏蔽网；
    所述屏蔽网包裹于所述换能器信号线与所述光纤延伸段外部；
    所述外皮包裹于所述屏蔽网的外部。
  20. 如权利要求17至19任一所述的光声双模成像探头，其特征在于：所述换能器信号线均布于所述光纤延伸段的周围。
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