All-optical lateral transceiving integrated optical fiber ultrasonic endoscopic probe

Abstract

The invention discloses an all-optical lateral transceiving integrated optical fiber ultrasonic endoscopic probe, and belongs to the technical field of ultrasound. Comprising an optical fiber, a first-layer wavelength selective transmission reflector, a second-layer wavelength selective transmission reflector, a heat insulation layer and a photoacoustic conversion layer, the first-layer wavelength selective transmission reflector, the second-layer wavelength selective transmission reflector, the heat insulation layer and the photoacoustic conversion layer sequentially cover the side face of the optical fiber from inside to outside, and the first-layer wavelength selective transmission reflector and the second-layer wavelength selective transmission reflector are connected through a supporting structure. The three parts form a Fabry-Perot interference cavity; the tail end of the optical fiber is an inclined end face, and a full-wavelength reflector is arranged on the surface of the inclined end face. Compared with a traditional piezoelectric ultrasonic endoscope, a method of photoinduced ultrasonic excitation and optical ultrasonic detection is adopted, and the ultrasonic endoscope has the advantages of being wide in frequency band, high in imaging resolution, simple in preparation process, resistant to electromagnetic interference and the like.

Description

Technical Field

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

[0002] Ultrasound plays an important role in clinical medical diagnosis because of its inherent safety, strong penetration, high imaging contrast, fast and real-time advantages. Ultrasonic endoscopy is to insert the probe into the human organs to image the digestive tract, bronchi, blood vessels and other parts. It can provide specific lesion images and provide a strong basis for surgery and disease diagnosis. Traditional ultrasonic endoscopes use electrical transducers to emit and detect ultrasound using the piezoelectric effect. However, this probe has a single frequency, and doctors need to replace probes of different frequencies according to the requirements of the inspection position, 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 usage scenarios.

[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 in 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 structures are 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 interference type, Mach-Zehnder interference type, and fiber grating type. However, these two types of fiber-optic ultrasound transducers cannot simultaneously achieve ultrasound excitation and detection, so additional ultrasound 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] The existing fiber-optic ultrasonic endoscopes mainly adopt the forward mode, emitting and detecting ultrasonic signals at the front end of the optical fiber. This design is difficult to meet the needs of lateral information collection during actual endoscopic imaging. Usually, in order to achieve lateral detection, it is necessary to introduce acoustic reflection structures and acoustic wave coupling structures, which further increases the size and assembly difficulty of the endoscope probe, thereby limiting the application scope of the fiber-optic ultrasonic probe. Summary of the invention

[0005] In view of the technical defects and improvement needs existing in the prior art, the purpose of the present invention is to provide an all-optical lateral-transmitting and receiving integrated fiber-optic ultrasonic endoscope probe, aiming to solve the technical problems that the existing ultrasonic endoscope probes have narrow bandwidth, low imaging resolution, large size, complex system, and independent transmission and reception of the existing fiber-optic ultrasonic probes, and cannot simultaneously perform lateral excitation and detection.

[0006] To achieve the above-mentioned object, 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 reflector, a second layer of wavelength selective transmission reflector, a heat insulation layer and a photoacoustic conversion layer sequentially covering the semicircular side surface of the optical fiber from the inside to the outside, the first layer of wavelength selective transmission reflector and the second layer of wavelength selective transmission reflector are connected by a supporting structure, and the three constitute a Fabry-Perot interference cavity; the end of the optical fiber is an inclined end face, and a full-wavelength reflector is arranged on its surface;

[0007] When working, the excitation light is a pulsed laser, which is transmitted axially in the inner cladding of the optical fiber, and is reflected by the full-wavelength reflector at the end of the optical fiber to the semicircular side of the optical fiber opposite to the end of the optical fiber, and passes through the Fabry-Perot interference cavity and the thermal insulation layer to irradiate 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, realizing the ultrasonic 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;

[0008] The detection light is a continuous laser, which is transmitted axially in the core of the optical fiber, and is reflected by the full-wavelength reflector at the end of the optical fiber 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 deformed by the drive of the ultrasonic wave, thereby changing the light intensity of the detection light, and the modulated detection light returns from 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 like the single-mode optical fiber core and is used for the transmission of single-mode detection light and interference light;

[0011] The transmission mode of the inner cladding at the excitation light wavelength is multi-mode 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 slope 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 photo-induced ultrasound detection;

[0017] The heat 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 the excitation light and the detection light, the excitation light is transmitted axially in the inner cladding of the optical fiber, and the detection light is transmitted axially in the core of the optical fiber. At the end of the optical fiber, the excitation light and the detection light are reflected by the full-wavelength reflector on the 45-degree inclined end face to the side of the sensing area at the end of the optical fiber. After the detection light forms interference in the Fabry-Perot interference cavity on the side of the optical fiber, it returns along the original path of the incident light path, emerges from the input end of the optical fiber, and is received by the photodetector; the excitation light continues to transmit, passes through the Fabry-Perot interference cavity and the thermal insulation layer, and irradiates the photoacoustic conversion layer; the photoacoustic conversion layer can absorb the laser beam energy of the excitation light, convert it into ultrasonic waves and emit it outward, realizing the ultrasonic transmission function of the lateral transceiver integrated optical fiber ultrasonic probe. At the same time, the photoacoustic conversion layer can receive ultrasonic echoes, deform according to the ultrasonic echoes, drive the Fabry-Perot interference cavity to deform, change the cavity length of the Fabry-Perot interference cavity, and then affect the returned detection light signal. By detecting the reflected detection light signal, the ultrasonic detection function of the lateral transceiver integrated optical fiber ultrasonic endoscope probe can be realized.

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

[0023] S1. Select a double-clad optical fiber, remove and clean the end 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 organic materials to improve the adhesion between the optical fiber surface and the photoresist and reflector;

[0025] S3. Protect the optical fiber side sensing area clean and sputter 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 reflector on the side of the optical fiber through which the sensing region and the reflected light path pass;

[0027] S5. Deposit photoresist in the sensing area and solidify it to form a support structure. To further enhance sensitivity, a hollow cavity can be made in the area where the reflected light path passes by using a photolithography process;

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

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

[0030] S8. Mix the light absorbing material and the heat expanding 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 adopts the method of photo-ultrasound excitation and optical ultrasonic detection. Compared with the traditional piezoelectric ultrasonic endoscope, it has the advantages of wide bandwidth, high imaging resolution, simple preparation process, and anti-electromagnetic interference;

[0033] 2) The present invention adopts 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 the excitation light and the detection light through the 45-degree full-wavelength reflector at the end face of the optical fiber;

[0035] 4) The all-optical lateral photo-induced ultrasound transceiver fiber endoscope of the present invention is integrated into a single optical fiber and has a small size of about 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, integrates the ultrasound transmitter and the detector on the same optical fiber, realizes the integration of fiber-optic ultrasound transmission and reception, and reduces 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. Different from the traditional forward detection, compared with the traditional fiber-optic ultrasonic endoscope, it does not require additional acoustic-optical coupling equipment, has a compact structure and small size, and meets the needs of lateral imaging of endoscopic imaging. BRIEF DESCRIPTION OF THE DRAWINGS

[0038] Figure 1 A schematic diagram of the structure of the all-optical side-direction transceiver integrated optical fiber ultrasound probe provided by the present invention;

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

[0040] Figure 3 It is a schematic diagram of the use of the all-optical side-direction transceiver integrated 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-support structure, 7-thermal insulation layer, 8-photoacoustic conversion layer. DETAILED DESCRIPTION

[0043] In order to make the purpose, technical solutions and advantages of the present invention more clearly understood, the present invention is further described in detail below in conjunction with the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are only used to explain 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 can be combined with each other as long as they do not conflict with each other.

[0044] Figure 1 FIG. 1 is a schematic diagram of the structure of the all-optical side-transmitting and receiving integrated fiber-optic ultrasound endoscope probe of the present invention. Figure 1 As shown, the present invention provides an all-optical side-direction transceiver integrated fiber optic ultrasonic 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 sequentially covering the semicircular side surface of the optical fiber 1 from the inside to the outside, the first layer of wavelength selective transmission reflector 2 and the second layer of wavelength selective transmission reflector 3 are connected by 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 arranged on its surface;

[0045] When working, 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 of the optical fiber opposite to the end of the optical fiber 1, and passes through the Fabry-Perot interference cavity 5 and the thermal insulation layer 7 to irradiate 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-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;

[0046] The detection light is a continuous laser, which is transmitted axially in the core of the optical fiber 1, and is 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, which is driven by the ultrasonic wave to deform, thereby changing the intensity of the detection light, and the modulated detection light returns from 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. .

[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 reflector 2, the second layer of wavelength selective transmission reflector 3, and the Fabry-Perot interference cavity 5; the first layer of wavelength selective transmission reflector 2, the second layer of wavelength selective transmission reflector 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 emission function of the lateral transceiver integrated optical fiber ultrasonic probe. At the same time, the photoacoustic conversion layer 8 can receive ultrasonic echoes and deform according to the ultrasonic echoes, thereby driving the Fabry-Perot interference cavity 5 to deform and changing the cavity length of the Fabry-Perot interference cavity 5, thereby further affecting the returned detection light signal. By detecting the reflected detection light signal, the function of receiving sound waves 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 wavelength selective transmission reflector 2, the second-layer wavelength selective transmission reflector 3, the Fabry-Perot interference 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 interference 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 detection light incident from its input end. The detection light is transmitted in 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 detection light can be reflected by the first layer of wavelength selective transmission reflector 2 and the second layer of wavelength selective transmission reflector 3, and the detection 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 acts on the thin film structure to change the cavity length, and the corresponding reflected light intensity changes. 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 interference cavity 5, and then reflected and coupled to the optical fiber core by the full-wavelength reflector 4, and emitted from the optical fiber output end to be received by the photodetector.

[0052] Figure 2 Schematic diagram of ultrasonic excitation and ultrasonic detection of the all-optical side-transmitting and receiving integrated optical fiber 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), the excitation laser is coupled into the optical fiber 1, and the excitation light is transmitted from the outer cladding of the optical fiber 1 to the optical fiber sensing end face. When the excitation light is transmitted to the 45-degree interface of the optical fiber end face, it is reflected to the side of the optical fiber by the full-wavelength reflector 4. The optical path of the excitation light changes to the side of the optical fiber and transmits outward, further penetrating the Fabry-Perot interference cavity 5 transparent to the excitation light band, the transparent insulation layer 7, and irradiating the photoacoustic conversion layer 8; the photoacoustic conversion layer 8 absorbs the excitation light, generates a photoacoustic ultrasound signal based on the photoacoustic effect, and radiates it outward, propagating to the imaging sample.

[0054] like Figure 2As shown in (b), the detection laser is coupled into the optical fiber 1, and the detection light is transmitted from the core of the optical fiber 1 to the optical fiber sensing end face. When the detection light is transmitted to the 45-degree interface of the optical fiber end face, it is reflected by the full-wavelength reflector 4 to the side of the optical fiber. The detection light first enters the first layer of wavelength selective transmission reflector 2, is partially reflected and partially projected, passes through the support structure 6, and is finally reflected by the second layer of wavelength selective transmission reflector; after the reflected light and the detection light interfere with each other in the Fabry-Perot interferometer cavity 5, they are reflected by the full-wavelength reflector 4 and return along the original path of the incident light through the optical fiber 1; 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 is deformed and displaced under the action of the ultrasonic wave, and the deformation of the film changes the cavity length of the Fabry-Perot interferometer cavity 5, which in turn causes the interference light intensity of the resonant cavity to change, and the reflected light propagates in the opposite direction along the incident light path, and is emitted from the rear end face of the optical fiber 1, and is finally received by the photodetector; the magnitude of the ultrasonic signal is obtained by demodulating the intensity of the reflected light.

[0055] Figure 3 Schematic diagram of the use of the all-optical side-transmitting and receiving integrated fiber-optic ultrasound endoscope probe prepared by the present invention. Figure 3 As shown, the excitation light uses a pulsed laser, and the detection light uses a 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 three-dimensional rotating mobile platform and the signal processing and control system, the probe is placed into the endoscopic environment, as shown in FIG. 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 all-optical side-transmitting and receiving integrated optical fiber ultrasound endoscope probe, the specific steps of which include:

[0057] S1. Select a double-clad optical fiber, remove and clean the end 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 organic materials to improve the adhesion between the optical fiber surface and the photoresist and reflector;

[0059] S3. Protect the optical fiber side sensing area clean and sputter 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 reflector on the side of the optical fiber through which the sensing region and the reflected light path pass;

[0061] S5. Deposit photoresist in the sensing area and solidify it to form a support structure. To further enhance sensitivity, a hollow cavity can be made in the area where the reflected light path passes by using a photolithography process;

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

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

[0064] S8. Mix the light absorbing material and the heat expanding 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 only 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 protection scope of the present invention.

Claims

1. An all-optical lateral transceiver integrated fiber optic ultrasound 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) which sequentially cover 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 support 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 arranged on the surface of the end face; When working, the excitation light is a pulsed laser, which is transmitted axially in the inner cladding of the optical fiber (1), 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 heat 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-direction transceiver 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 is 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), and the Fabry-Perot interferometer cavity (5) is deformed by the drive of the ultrasonic wave, thereby changing the light intensity of the detection light, and the modulated detection light returns from 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.

2. The all-optical side-direction transceiver 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-direction transceiver 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-direction transceiver 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-direction transceiver 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-direction transceiver 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-direction transceiver integrated fiber-optic ultrasound endoscope 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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