An all-optical side-transmitting and receiving integrated fiber-optic ultrasound endoscope probe

Abstract

The present invention discloses an all-optical side-directed transceiver integrated fiber-optic ultrasonic endoscope probe, belonging to the field of ultrasonic technology. It comprises: an optical fiber, a first layer of wavelength-selective transmission reflectors, a second layer of wavelength-selective transmission reflectors, a heat-insulating layer, and a photoacoustic conversion layer, which sequentially cover the side of the optical fiber from the inside out. The first layer of wavelength-selective transmission reflectors and the second layer of wavelength-selective transmission reflectors are connected by a supporting structure, and the three constitute a Fabry-Perot interferometer cavity. The end of the optical fiber is an inclined end face, and a full-wavelength reflector is provided on its surface. The present invention adopts the method of photo-induced ultrasonic excitation and optical ultrasonic detection. Compared with traditional piezoelectric ultrasonic endoscopes, it has the advantages of wide bandwidth, high imaging resolution, simple preparation process, and resistance to electromagnetic interference.

Description

Technical Field

[0001] The present invention belongs to the field of ultrasound technology, and more specifically, relates to an all-optical side-transmitting and receiving integrated fiber-optic ultrasound endoscope probe. Background Art

[0002] Ultrasound plays an important role in clinical medical diagnosis due to its inherent safety, strong penetration, high imaging contrast, and rapid and real-time performance. Ultrasound endoscopy involves inserting a probe into human organs to image the digestive tract, bronchi, blood vessels, and other parts of the body. It can provide specific images of lesions and provide a strong basis for surgery and disease diagnosis. Traditional ultrasonic endoscopes use electrical transducers that utilize the piezoelectric effect to emit and detect ultrasound. However, this probe has a single frequency, and doctors need to replace probes of different frequencies according to the requirements of the examination location, which brings many inconveniences. In addition, piezoelectric ultrasonic probes have low sensitivity and large size, which have certain limitations on further improving the quality of endoscopic imaging and expanding the scope of use.

[0003] Compared with traditional piezoelectric ultrasound probes, the size of fiber-optic ultrasound endoscopy probes is mainly determined by the diameter of the optical fiber, which is only on the order of hundreds of microns. Fiber-optic ultrasound probes have the advantages of high sensitivity and wide bandwidth, and the characteristics of photo-induced ultrasound make them more extensive in the spectrum. In addition, fiber-optic ultrasound probes are not subject to electromagnetic interference, and their structure is easier to integrate. Current fiber-optic ultrasound transducers are mainly divided into two categories: ultrasonic emission type and ultrasonic detection type. Emission type transducers convert excitation light into ultrasonic waves through the photoacoustic effect; fiber-optic ultrasound detectors mainly include Fabry-Perot interferometer type, Mach-Zehnder interferometer type and fiber Bragg grating type. However, these two types of fiber-optic ultrasound transducers cannot simultaneously achieve ultrasonic excitation and detection, so additional ultrasonic transmitters or detectors need to be introduced in the imaging system, which makes the transmission and reception of the fiber-optic ultrasound transducer independent, making it difficult to reduce the size of the system.

[0004] Current fiber-optic ultrasound endoscopes primarily utilize a forward-facing mode, emitting and detecting ultrasound signals directly at the front end of the optical fiber. This design struggles to meet the requirements for lateral information acquisition during practical endoscopic imaging. Typically, lateral detection requires the introduction of acoustic reflection and acoustic wave coupling structures, which further increases the size and assembly complexity of the endoscopic probe, limiting its application. Summary of the Invention

[0005] In response to the technical defects and improvement needs in the existing technology, the purpose of the present invention is to provide an all-optical lateral transceiver integrated fiber-optic ultrasound endoscope probe, which aims to solve the technical problems of the existing ultrasound endoscopes, such as narrow bandwidth, low imaging resolution, large size, complex system, and independent transmission and reception of the existing fiber-optic ultrasound probes, and the inability to simultaneously perform lateral excitation and detection.

[0006] To achieve the above objectives, the present invention provides an all-optical side-direction transceiver integrated fiber-optic ultrasound endoscope probe, comprising: an optical fiber, a first layer of wavelength-selective transmission reflectors, a second layer of wavelength-selective transmission reflectors, a thermal insulation layer, and a photoacoustic conversion layer sequentially covering, from the inside out, the semicircular side surfaces of the optical fiber, the first layer of wavelength-selective transmission reflectors and the second layer of wavelength-selective transmission reflectors being connected by a supporting structure, the three layers forming a Fabry-Perot interferometer cavity; the end of the optical fiber is an inclined end face, the surface of which is provided with a full-wavelength reflector;

[0007] During operation, the excitation light is a pulsed laser, which is transmitted axially in the inner cladding of the optical fiber. At the end of the optical fiber, it is reflected by the full-wavelength reflector to the semi-circular side surface of the optical fiber opposite the end of the optical fiber, passes through the Fabry-Perot interferometer cavity and the thermal insulation layer, and irradiates the photoacoustic conversion layer. The photoacoustic conversion layer absorbs the energy of the excitation light, generates ultrasonic waves through thermal expansion, and emits them outward, thereby realizing the ultrasonic transmission function of the all-optical side-type integrated transceiver fiber optic ultrasonic endoscope probe. The emitted ultrasonic waves are reflected by external objects and act on the Fabry-Perot interferometer cavity.

[0008] The detection light is a continuous laser, which is transmitted axially in the core of the optical fiber. At the end of the optical fiber, it is reflected by the full-wavelength reflector to the side of the optical fiber opposite to the end of the optical fiber. The detection light interferes in the Fabry-Perot interferometer cavity, and the Fabry-Perot interferometer cavity is driven by the ultrasonic wave to produce deformation, thereby changing the intensity of the detection light, and the modulated detection light returns along the original path; by detecting the reflected detection light signal, the sound wave detection function of the lateral transceiver integrated optical fiber ultrasonic endoscope probe can be realized.

[0009] The optical fiber is a double-clad optical fiber, which consists of a core, an inner cladding, and an outer cladding, and is used to guide the transmission of excitation light and detection light; the excitation light is a pulsed laser, and the detection light is a continuous laser.

[0010] The fiber core has a large refractive index, similar to the single-mode optical fiber core, and is used for the transmission of single-mode probe light and interference light;

[0011] The transmission mode of the inner cladding at the excitation light wavelength is multimode transmission;

[0012] The outer cladding is used to confine the excitation light, the detection light, and the interference light;

[0013] The end of the optical fiber is the sensing area. The end face of the optical fiber in the sensing area is polished to a 45-degree inclination angle, and the inclination angle is covered with a full-wavelength reflector for reflecting the excitation light and the detection light.

[0014] The first layer of wavelength selective transmission reflector and the second layer of wavelength selective transmission reflector transmit almost all of the excitation light, having a transmittance greater than 95% at the excitation laser wavelength, and partially reflect the detection light, having a reflectance greater than 90% at the detection laser wavelength;

[0015] The first layer of wavelength selective transmission reflector, the second layer of wavelength selective transmission reflector, and the supporting structure constitute a Fabry-Perot interferometer cavity structure;

[0016] The prepared Fabry-Perot interferometer cavity structure is used for high-frequency and broadband photoinduced ultrasound detection;

[0017] The thermal insulation layer is a polymer waterproof structure, which mainly blocks the heat generated by the photoacoustic conversion layer from disturbing the detection structure, and has a transmittance greater than 95% at the wavelength of the excitation light;

[0018] The photoacoustic conversion layer is composed of a light absorbing material and a thermal expansion material, and is used to generate a broadband photoacoustic signal; the light absorbing material has a large light absorption coefficient, including but not limited to carbon black, graphene, and oily color essence;

[0019] The thermal expansion material has a high thermal expansion coefficient and a low specific heat capacity, including but not limited to transparent polymers such as polydimethylsiloxane (PDMS).

[0020] The principle of ultrasonic detection of the present invention is:

[0021] The optical fiber transmits excitation light and probe light. The excitation light propagates axially along the fiber's inner cladding, while the probe light propagates axially along the fiber's core. At the fiber's end, the excitation light and probe light are reflected by a full-wavelength reflector on a 45-degree inclined end face toward the side of the sensing area at the fiber's end. After interference in the Fabry-Perot (FP) interferometer cavity on the fiber's side, the probe light returns along its original path of incidence, exits the fiber's input end, and is received by a photodetector. The excitation light continues to propagate, passing through the FP interferometer cavity and the thermal insulation layer before irradiating the photoacoustic conversion layer. The photoacoustic conversion layer absorbs the laser beam energy of the excitation light, converts it into ultrasonic waves, and emits them outward, thus realizing the ultrasonic transmission function of the lateral transceiver fiber-optic ultrasound probe. Simultaneously, the photoacoustic conversion layer receives ultrasonic echoes and deforms according to the ultrasonic echoes, driving the FP interferometer cavity to deform, causing the cavity length of the FP interferometer cavity to change, thereby affecting the returned probe light signal. By detecting the reflected probe light signal, the ultrasonic detection function of the lateral transceiver fiber-optic ultrasound probe is realized.

[0022] The present invention also provides a method for preparing an all-optical side-transmitting and receiving integrated fiber-optic ultrasound endoscope probe, comprising the following steps:

[0023] S1. Select a double-clad optical fiber, strip and clean the end face coating of the optical fiber output end, wipe it with alcohol, and then polish the optical fiber end face to a 45° inclination angle;

[0024] S2. Chemically treat the sensing area at the end of the optical fiber with an organic material to improve the adhesion between the optical fiber surface and the photoresist and reflector.

[0025] S3. Protect the optical fiber side sensing area clean by sputtering a full-wavelength reflector at a 45-degree angle at the end of the optical fiber.

[0026] S4. Sputtering a first layer of wavelength selective transmission mirror on the side of the optical fiber through which the reflected light path passes in the sensing area;

[0027] S5. Deposit photoresist in the sensing area and cure it to form a support structure. Further sensitivity enhancement can be achieved by using a photolithography process to create a hollow cavity in the area where the reflected light path passes.

[0028] S6. depositing a second layer of wavelength selective transmission reflector on the outside of the support structure;

[0029] S7. Depositing a parylene film as a thermal insulation layer on the outer surface of the second wavelength selective transmission reflector;

[0030] S8. Mix the light-absorbing material and the thermal expansion material as a photoacoustic material, and coat the photoacoustic material on the side of the optical fiber as a photoacoustic transducer to generate a broadband, high-efficiency photoacoustic signal for endoscopic imaging.

[0031] Compared with the prior art, the above technical solution conceived by the present invention can achieve the following beneficial effects:

[0032] 1) The present invention uses a method of photo-ultrasound excitation and optical ultrasonic detection. Compared with traditional piezoelectric ultrasonic endoscopes, it has the advantages of wide bandwidth, high imaging resolution, simple preparation process, and resistance to electromagnetic interference;

[0033] 2) The present invention uses double-clad optical fiber to achieve the propagation of excitation light and detection light in the same optical fiber;

[0034] 3) The present invention realizes the lateral emission of excitation light and detection light through a 45-degree full-wavelength reflector on the end face of the optical fiber;

[0035] 4) The all-optical lateral photo-induced ultrasound transceiver fiber optic endoscope of the present invention is integrated into a single optical fiber and has a small size of approximately 200 microns;

[0036] 5) The present invention sequentially covers the Fabry-Perot interference structure and the photoacoustic excitation structure to form an integral structure on the side of the optical fiber, and integrates the ultrasound transmitter and detector on the same optical fiber, thereby realizing the integration of fiber-optic ultrasound transmission and reception, reducing the size of the endoscope and the difficulty of packaging;

[0037] 6) The ultrasonic emission and detection structure of the present invention is located on the side wall of the optical fiber. Unlike traditional forward detection, compared with traditional fiber optic ultrasonic endoscopes, it does not require additional acoustic-optical coupling equipment, has a compact structure and small size, and meets the needs of endoscopic imaging and side imaging. BRIEF DESCRIPTION OF THE DRAWINGS

[0038] Figure 1 This is a schematic structural diagram of the all-optical side-mounted fiber-optic ultrasound probe provided by the present invention;

[0039] Figure 2 Schematic diagrams of the principles of ultrasonic excitation and ultrasonic detection of the all-optical side-transmitting and receiving integrated fiber-optic ultrasonic probe of the present invention, wherein (a) is a schematic diagram of the principle of the fiber-optic probe generating ultrasonic waves; (b) is a schematic diagram of the principle of the fiber-optic probe detecting ultrasonic waves;

[0040] Figure 3 This is a schematic diagram of the use of the all-optical side-mounted fiber-optic ultrasound probe endoscope of the present invention;

[0041] Reference numerals:

[0042] 1- optical fiber, 2- first layer wavelength selective transmission reflector, 3- second layer wavelength selective transmission reflector, 4- full wavelength reflector, 5- Fabry-Perot interference cavity, 6- supporting structure, 7- thermal insulation layer, 8- photoacoustic conversion layer. DETAILED DESCRIPTION

[0043] In order to make the objectives, technical solutions and advantages of the present invention more clearly understood, the present invention is further described in detail below with reference to the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely for explaining the present invention and are not intended to limit the present invention. In addition, the technical features involved in the various embodiments of the present invention described below may be combined with each other as long as they do not conflict with each other.

[0044] Figure 1 This is a schematic diagram of the structure of the all-optical side-transmitting and receiving integrated fiber-optic ultrasound endoscope probe in the present invention. Figure 1 As shown, the present invention provides an all-optical side-direction transceiver integrated fiber optic ultrasound endoscope probe, comprising an optical fiber 1, a first layer of wavelength selective transmission reflector 2, a second layer of wavelength selective transmission reflector 3, a heat insulation layer 7, and a photoacoustic conversion layer 8, which sequentially cover the semicircular side surface of the optical fiber 1 from the inside out. The first layer of wavelength selective transmission reflector 2 and the second layer of wavelength selective transmission reflector 3 are connected by a support structure 6, and the three constitute a Fabry-Perot interferometer cavity 5. The end of the optical fiber 1 is an inclined end face, and a full-wavelength reflector 4 is provided on its surface.

[0045] During operation, the excitation light is a pulsed laser, which is transmitted axially in the inner cladding of the optical fiber 1. At the end of the optical fiber 1, it is reflected by the full-wavelength reflector 4 to the semi-circular side surface of the optical fiber opposite to the end of the optical fiber 1, passes through the Fabry-Perot interferometer cavity 5 and the thermal insulation layer 7, and irradiates the photoacoustic conversion layer 8. The photoacoustic conversion layer 8 absorbs the energy of the excitation light, generates ultrasonic waves through thermal expansion, and emits them outward, realizing the ultrasonic emission function of the all-optical side-type integrated optical fiber ultrasonic endoscope probe. The emitted ultrasonic waves are reflected by external objects and act on the Fabry-Perot interferometer cavity 5.

[0046] The probe light is a continuous laser beam that propagates axially within the core of optical fiber 1. At the end of optical fiber 1, it is reflected by the full-wavelength reflector 4 to the side of the fiber opposite the end. There, the probe light interferes within the Fabry-Perot interferometer cavity 5. Driven by the ultrasound, the cavity 5 deforms, altering the intensity of the probe light. The modulated probe light then returns along its original path. By detecting the reflected probe light signal, the acoustic wave detection function of the lateral transceiver fiber-optic ultrasound endoscope probe is realized.

[0047] The optical fiber 1 is a double-clad optical fiber, which consists of a core, an inner cladding, and an outer cladding, and is used to simultaneously guide the propagation of excitation light and detection light. The excitation light is transmitted in the inner cladding, the detection light is transmitted in the core, and the outer cladding is used to transmit bound light.

[0048] The excitation light can pass through the first layer of wavelength selective transmission mirror 2, the second layer of wavelength selective transmission mirror 3, and the Fabry-Perot interference cavity 5; the first layer of wavelength selective transmission mirror 2, the second layer of wavelength selective transmission mirror 3, and the supporting structure 6 cooperate with each other to form a closed Fabry-Perot interference cavity 5.

[0049] The photoacoustic conversion layer 8 can absorb the laser beam energy of the excitation light and convert it into ultrasonic waves, and emit it outward, thereby realizing the ultrasonic wave transmitting function of the lateral transceiver integrated optical fiber ultrasonic probe. At the same time, the photoacoustic conversion layer 8 can receive ultrasonic echoes and produce deformation according to the ultrasonic echoes, thereby driving the Fabry-Perot interferometer cavity 5 to deform and causing the cavity length of the Fabry-Perot interferometer cavity 5 to change, thereby further affecting the returned detection light signal. By detecting the reflected detection light signal, the sound wave receiving function of the transceiver integrated lateral ultrasonic probe can be realized.

[0050] The optical fiber 1 is used to guide the excitation light incident from its input end. The excitation light is transmitted in the inner cladding of the guiding optical fiber, propagates to the 45-degree inclined end face of the optical fiber, and is reflected to the side of the optical fiber by the full-wavelength reflector 4. The excitation light passes through the first layer of wavelength selective transmission reflector 2, the second layer of wavelength selective transmission reflector 3, the Fabry-Perot interferometer cavity 5, and the thermal insulation layer 7, and is absorbed by the photoacoustic conversion layer 8 and excites an ultrasonic signal. The ultrasonic signal is transmitted forward and reflected by the object to be measured (such as the blood vessel wall). The reflected ultrasonic wave acts on the lateral optical fiber ultrasonic probe, and the reflected ultrasonic signal is detected by detecting the Fabry-Perot interferometer cavity 5 to obtain image information of the object to be measured.

[0051] The optical fiber 1 is also used to guide the transmission of the probe light incident from its input end. The probe light is transmitted within the core of the guiding optical fiber, propagates to the 45-degree inclined interface of the optical fiber, and is reflected to the side of the optical fiber by the full-wavelength reflector 4. The probe light can be reflected by the first layer of wavelength selective reflector 2 and the second layer of wavelength selective reflector 3, and the probe light interferes in the Fabry-Perot structure. When the refractive index and the incident wavelength in the resonant cavity remain unchanged, the external ultrasonic pressure acting on the thin film structure will cause the cavity length to change, and the corresponding reflected light intensity will change. By demodulating the corresponding light intensity, the ultrasonic signal intensity and frequency information can be effectively demodulated. The interfered light beam is reflected back to the side of the optical fiber 1 by the Fabry-Perot interferometer cavity 5, and then reflected and coupled to the optical fiber core by the full-wavelength reflector 4. It is emitted from the optical fiber output end and received by the photodetector.

[0052] Figure 2 Schematic diagram of ultrasonic excitation and ultrasonic detection of the all-optical side-transmitting and receiving integrated fiber-optic ultrasonic endoscope probe in the present invention, wherein Figure 2 (a) is a schematic diagram of the principle of generating ultrasonic waves by a fiber optic probe. Figure 2 (b) is a schematic diagram of the principle of detecting ultrasonic waves using a fiber optic probe.

[0053] like Figure 2 As shown in (a), an excitation laser is coupled into optical fiber 1. The excitation light propagates through the outer cladding of optical fiber 1 toward the fiber sensing end face. When the excitation light reaches the 45-degree interface at the fiber end face, it is reflected by a full-wavelength reflector 4 toward the side of the fiber. The excitation light's optical path changes to the side of the fiber and propagates outward, further penetrating a Fabry-Perot interferometer cavity 5 transparent to the excitation light wavelength band and a transparent thermal insulation layer 7 before irradiating a photoacoustic conversion layer 8. This layer absorbs the excitation light, generating a photoacoustic ultrasound signal based on the photoacoustic effect. This signal radiates outward and propagates to the imaging sample.

[0054] like Figure 2As shown in (b), a probe laser is coupled into optical fiber 1, and the probe light is transmitted from the core of optical fiber 1 toward the optical fiber sensing end face. When the probe light reaches the 45-degree interface at the optical fiber end face, it is reflected by the full-wavelength reflector 4 toward the side of the optical fiber. The probe light first enters the first wavelength-selective transmission reflector 2, where it is partially reflected and partially projected. It then passes through the support structure 6 and is finally reflected by the second wavelength-selective transmission reflector. After the reflected light and the probe light interfere with each other in the Fabry-Perot interferometer cavity 5, they are reflected by the full-wavelength reflector 4 and return through optical fiber 1 along the original incident light path. When the ultrasonic wave generated by the photoacoustic conversion layer 8 is reflected by the sample and propagates back to the side of the optical fiber ultrasonic probe, the sensing structure deforms and displaces under the action of the ultrasonic wave. The deformation of the film changes the cavity length of the Fabry-Perot interferometer cavity 5, which in turn causes a change in the interference light intensity of the resonant cavity. The reflected light propagates in the opposite direction of the incident light path, exiting from the back of optical fiber 1 toward the end face, and is ultimately received by the photodetector. The magnitude of the ultrasonic signal is determined by demodulating the intensity of the reflected light.

[0055] Figure 3 This is a schematic diagram of the use of the all-optical side-transmitting and receiving integrated fiber-optic ultrasonic endoscope probe prepared by the present invention. Figure 3 As shown in the figure, the excitation light uses pulsed laser and the detection light uses continuous laser. The pulsed laser for exciting ultrasound and the continuous light for detecting ultrasound are coupled from the incident port of the double-clad optical fiber into the above-mentioned double-clad optical fiber. With the help of the three-dimensional rotating mobile platform and the signal processing and control system, the probe is placed into the endoscopic environment, as shown in the figure. Figure 3 As shown in the figure, inside the blood vessel, the lateral all-optical transceiver integrated ultrasound fiber optic endoscopic imaging function can be realized.

[0056] Furthermore, the present invention also proposes a method for preparing the above-mentioned all-optical side-pointing transceiver integrated fiber optic ultrasound endoscope probe, the specific steps of which include:

[0057] S1. Select a double-clad optical fiber, strip and clean the end face coating of the optical fiber output end, wipe it with alcohol, and then polish the optical fiber end face to a 45° inclination angle;

[0058] S2. Chemically treat the sensing area at the end of the optical fiber with an organic material to improve the adhesion between the optical fiber surface and the photoresist and reflector.

[0059] S3. Protect the optical fiber side sensing area clean by sputtering a full-wavelength reflector at a 45-degree angle at the end of the optical fiber.

[0060] S4. Sputtering a first layer of wavelength selective transmission mirror on the side of the optical fiber through which the reflected light path passes in the sensing area;

[0061] S5. Deposit photoresist in the sensing area and cure it to form a support structure. Further sensitivity enhancement can be achieved by using a photolithography process to create a hollow cavity in the area where the reflected light path passes.

[0062] S6. depositing a second layer of wavelength selective transmission reflector on the outside of the support structure;

[0063] S7. Depositing a parylene film as a thermal insulation layer on the outer surface of the second wavelength selective transmission reflector;

[0064] S8. Mix the light-absorbing material and the thermal expansion material as a photoacoustic material, and coat the photoacoustic material on the side of the optical fiber as a photoacoustic transducer to generate a broadband, high-efficiency photoacoustic signal for endoscopic imaging.

[0065] It will be easily understood by those skilled in the art that the above description is merely a preferred embodiment of the present invention and is not intended to limit the present invention. Any modifications, equivalent substitutions, and improvements made within the spirit and principles of the present invention should be included in the scope of protection of the present invention.

Claims

1. An all-optical side-mounted fiber-optic ultrasonic endoscope probe, characterized in that: The optical fiber (1) comprises a first layer of wavelength selective transmission reflector (2), a second layer of wavelength selective transmission reflector (3), a heat insulation layer (7) and a photoacoustic conversion layer (8) sequentially covering the semicircular side surface of the optical fiber (1) from the inside to the outside, wherein the first layer of wavelength selective transmission reflector (2) and the second layer of wavelength selective transmission reflector (3) are connected via a supporting structure (6), and the three constitute a Fabry-Perot interference cavity (5); the end of the optical fiber (1) is an inclined end face, and a full-wavelength reflector (4) is provided on the surface of the end face; During operation, the excitation light is a pulsed laser, which is transmitted axially in the inner cladding of the optical fiber (1), and is reflected by the full-wavelength reflector (4) at the end of the optical fiber (1) to the semicircular side surface, passes through the Fabry-Perot interference cavity (5) and the thermal insulation layer (7), and irradiates the photoacoustic conversion layer (8); the photoacoustic conversion layer (8) absorbs the energy of the excitation light, generates ultrasonic waves through thermal expansion, and emits them outward, thereby realizing the ultrasonic wave emission function of the all-optical side-transmitting and receiving integrated optical fiber ultrasonic endoscope probe; the emitted ultrasonic waves are reflected by external objects and act on the Fabry-Perot interference cavity (5); The detection light is a continuous laser, which is transmitted axially in the core of the optical fiber (1) and reflected by the full-wavelength reflector (4) at the end of the optical fiber (1) to the side of the optical fiber opposite to the end of the optical fiber (1). The detection light interferes in the Fabry-Perot interferometer cavity (5). The Fabry-Perot interferometer cavity (5) is driven by the ultrasonic wave to produce deformation, thereby changing the intensity of the detection light, and the modulated detection light returns along the original path; by detecting the reflected detection light signal, the detection sound wave function of the lateral transceiver integrated optical fiber ultrasonic endoscope probe can be realized.

2. The all-optical side-transmitting and receiving integrated fiber-optic ultrasound endoscope probe according to claim 1, characterized in that: The end of the optical fiber (1) is a 45-degree inclined end face.

3. The all-optical side-transmitting and receiving integrated fiber-optic ultrasound endoscope probe according to claim 1, characterized in that: The first wavelength selective transmission reflector (2) and the second wavelength selective transmission reflector (3) have a transmittance greater than 95% at the excitation light wavelength and a reflectance greater than 90% at the detection light wavelength.

4. The all-optical side-transmitting and receiving integrated fiber-optic ultrasound endoscope probe according to claim 1, characterized in that: The heat insulation layer (7) is a polymer.

5. The all-optical side-transmitting and receiving integrated fiber-optic ultrasound endoscope probe according to claim 1, characterized in that: The photoacoustic conversion layer (8) comprises a light absorbing material and a thermal expansion material.

6. The all-optical side-transmitting and receiving integrated fiber-optic ultrasound endoscope probe according to claim 1, characterized in that: The material of the support structure (6) is photoresist.

7. The all-optical side-transmitting and receiving integrated fiber-optic ultrasonic endoscopic probe according to claim 4, characterized in that: The heat-insulating layer (7) has a transmittance greater than 95% at the wavelength of the excitation light.

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