CN116158720B

CN116158720B - Optical-photoacoustic-ultrasonic composite endoscope and endoscope system

Info

Publication number: CN116158720B
Application number: CN202211734438.3A
Authority: CN
Inventors: 邱建军; 龚鹏程; 叶驰竣
Original assignee: Sonoscape Medical Corp
Current assignee: Sonoscape Medical Corp
Priority date: 2022-12-30
Filing date: 2022-12-30
Publication date: 2023-11-21
Anticipated expiration: 2042-12-30
Also published as: CN116158720A

Abstract

The invention provides an optical-photoacoustic-ultrasonic composite endoscope and an endoscope system. The optical-photoacoustic-ultrasonic composite endoscope includes an insertion portion including a head end portion including: a head end seat; the convex array ultrasonic probe is arranged at the front end of the head end seat; the photoacoustic excitation light window is arranged on the head end seat and positioned on the side surface of the convex array ultrasonic probe; an optical imaging assembly disposed on the head end mount, the optical imaging assembly being closer to the proximal end of the insertion portion than the convex array ultrasonic probe, the optical imaging assembly having an illumination light window; and the light guide piece penetrates through the insertion part and extends into the head end seat, and the light guide piece is aligned with the photoacoustic excitation light window and the illumination light window and respectively conducts the photoacoustic excitation light and the illumination light. The optical-photoacoustic-ultrasonic composite endoscope can simultaneously realize optical, ultrasonic, photoacoustic and ultrasonic-photoacoustic imaging, and does not interfere with each other. The imaging modes can be independently presented, or two or three imaging modes can be presented simultaneously.

Description

Optical-photoacoustic-ultrasonic composite endoscope and endoscope system

Technical Field

The invention relates to the technical field of medical instruments, in particular to an optical-photoacoustic-ultrasonic composite endoscope and an endoscope system.

Background

The endoscopic imaging is used as a noninvasive imaging method, can effectively prolong the human sight, is widely applied to image diagnosis and image-guided treatment in various fields such as digestive tracts, cardiovascular and cerebrovascular systems, urinary systems, respiratory systems and the like, and greatly promotes the examination precision of diseases.

In recent years, multi-modal endoscopic imaging techniques, such as optical imaging techniques, ultrasonic endoscopic techniques, and photoacoustic imaging techniques, have been rapidly developed. The optical imaging technology has the characteristic of high resolution, but because tissues have strong scattering property on light, the imaging depth of the electronic endoscope is limited to be within 1 millimeter, and the deep lesions cannot be accurately detected. The ultrasonic endoscope is an endoscopic imaging device which fuses ultrasonic and electronic endoscopes together, and can solve the problem that a conventional electronic endoscope does not have depth resolution capability. However, ultrasonic endoscopy detects ultrasonic echo signals reflected by different layered structures, resulting in lower image contrast and lower detailed viewing capabilities for tissue. Photoacoustic imaging technology is to introduce photoacoustic excitation light into a biological lumen through an endoscope probe to excite ultrasonic waves (photoacoustic signals), and then to image tissues by receiving the generated ultrasonic signals through a miniature ultrasonic transducer placed in an endoscope catheter. The photoacoustic imaging technology can make up for the defect of shallow detection depth in pure optical imaging.

As described above, the optical imaging technique and the ultrasonic endoscope technique have respective disadvantages, and the ultrasonic endoscope technique and the photoacoustic imaging technique can compensate for the problem of shallow detection depth in the optical imaging technique, and the optical imaging technique can compensate for the problem of low contrast of the image obtained in the ultrasonic endoscope technique. Therefore, development of an endoscopic imaging apparatus having optical imaging technology, ultrasonic endoscope technology, and photoacoustic imaging technology at the same time has become clinically demanded.

Disclosure of Invention

In order to at least partially solve the problems in the prior art, according to one aspect of the present invention, there is provided an optical-photoacoustic-ultrasonic composite endoscope including an insertion portion including a head end portion including: a head end seat; the convex array ultrasonic probe is arranged at the front end of the head end seat; the photoacoustic excitation light window is arranged on the head end seat and positioned on the side surface of the convex array ultrasonic probe; an optical imaging assembly disposed on the head end mount, the optical imaging assembly being closer to the proximal end of the insertion portion than the convex array ultrasonic probe, the optical imaging assembly having an illumination light window; and the light guide piece penetrates through the insertion part and extends into the head end seat, and the light guide piece is aligned with the photoacoustic excitation light window and the illumination light window and respectively conducts the photoacoustic excitation light and the illumination light.

The optical-photoacoustic-ultrasonic composite endoscope provided by the application can realize optical, ultrasonic, photoacoustic and ultrasonic-photoacoustic imaging simultaneously, and can not interfere with each other, so that the accuracy of in-vivo diagnosis is greatly improved. The optical imaging mode and other imaging modes are not mutually influenced, and the ultrasonic imaging mode, the photoacoustic imaging mode and the ultrasonic-photoacoustic fusion imaging mode can be switched in real time, can be independently presented in a single imaging mode, and can be simultaneously presented in two or three imaging modes. Moreover, the optical-photoacoustic-ultrasonic composite endoscope provided by the application can be similar to a conventional ultrasonic endoscope in appearance, does not change the operation habit of a user, is friendly to the user operation, and is also beneficial to inserting or withdrawing from a body cavity.

Illustratively, the optical imaging assembly includes an objective imaging module having a filter disposed therein for filtering near infrared light.

Illustratively, the objective imaging module includes a lens holder and a lens barrel, an optical lens group is disposed in the lens barrel, the lens barrel is connected to the lens holder, the optical imaging module further includes a photoelectric sensor disposed on the lens holder, and the filter is disposed in the lens holder and between the lens barrel and the photoelectric sensor.

The optical-photoacoustic-ultrasonic composite endoscope further includes a light guide portion and an operation portion connected between the light guide portion and the insertion portion, the light guide including a bundle of optical fibers, the bundle of optical fibers being bifurcated such that the bundle of optical fibers includes a trunk bundle section connected proximally to the light guide portion, and first and second bundle sections extending distally to a head end, wherein a distal end of the first bundle section is aligned with the illumination light window and a distal end of the second bundle section is aligned with the photoacoustic excitation light window.

Illustratively, the optical fiber bundle is bifurcated within the handle portion.

Illustratively, a fixing ring is sleeved at the branching position of any two sections of the optical fiber bundles, and protective covers are sleeved on the two optical fiber bundle sections at two sides of the branching position and are fixed to the fixing ring.

Illustratively, the light guide portion has a light guide interface disposed thereon, the proximal end of the fiber optic bundle being connected to the light guide interface.

The photoacoustic excitation light window includes a first photoacoustic excitation light window and a second photoacoustic excitation light window, the second fiber bundle section being bifurcated within the head end and forming a first sub-fiber bundle section and a second sub-fiber bundle section, the first sub-fiber bundle section being aligned with the first photoacoustic excitation light window, the second sub-fiber bundle section being aligned with the second photoacoustic excitation light window.

The light guide member includes a first sub-optical fiber bundle section and a second sub-optical fiber bundle section, the photoacoustic excitation light window includes a first photoacoustic excitation light window and a second photoacoustic excitation light window, a distal end of the first sub-optical fiber bundle section is aligned with the first photoacoustic excitation light window, a distal end of the second sub-optical fiber bundle section is aligned with the second photoacoustic excitation light window, and the first photoacoustic excitation light window and the second photoacoustic excitation light window are located on two sides of the convex array ultrasonic probe, respectively.

Illustratively, the first photoacoustic excitation light window and the second photoacoustic excitation light window are arc-shaped and are matched with the acoustic window of the convex array ultrasonic probe, and the outer surfaces of the first photoacoustic excitation light window and the second photoacoustic excitation light window do not protrude out of the acoustic window.

The first and second photoacoustic excitation light windows are illustratively configured to refract photoacoustic excitation light conducted by the first and second sub-fiber bundle segments, respectively, toward the middle of the convex array ultrasound probe.

Illustratively, the inner surface of the first photoacoustic excitation light window has a first inclined surface that is inclined toward the proximal end in a direction approaching the convex array ultrasound probe, the distal end of the first sub-fiber bundle section being aligned with the first inclined surface; and/or the inner surface of the second photoacoustic excitation light window is provided with a second inclined surface, the second inclined surface is inclined towards the proximal end along the direction approaching the convex array ultrasonic probe, and the distal end of the second sub-optical fiber bundle section is aligned with the second inclined surface.

Illustratively, the distal ends of the first and second sub-fiber bundle segments are inclined toward the convex array ultrasound probe.

Illustratively, the distal ends of the plurality of first optical fibers included in the first sub-fiber bundle segment are separated from one another and form a first fan-shaped structure, and the distal ends of the plurality of second optical fibers included in the second sub-fiber bundle segment are separated from one another and form a second fan-shaped structure.

Illustratively, the head end portion further includes a first optical fiber fixing member, wherein a plurality of first through holes corresponding to distal ends of the plurality of first optical fibers are provided on the first optical fiber fixing member, axes of the plurality of first through holes pass through a center of the first fan-shaped structure, and the distal ends of the plurality of first optical fibers are respectively fixed in the corresponding first through holes; the head end part further comprises a second optical fiber fixing piece, a plurality of second through holes corresponding to the distal ends of the second optical fibers one by one are arranged on the second optical fiber fixing piece, the axes of the second through holes pass through the center of the second fan-shaped structure, and the distal ends of the second optical fibers are respectively fixed in the corresponding second through holes.

Illustratively, the distal end of the head end mount is provided with a recess recessed toward the proximal end of the insertion portion, and the male array ultrasonic probe, the first optical fiber mount, and the second optical fiber mount are all disposed within the recess, the first optical fiber mount being bonded to the side walls of the male array ultrasonic probe and the recess, and the second optical fiber mount being bonded to the side walls of the male array ultrasonic probe and the recess.

Illustratively, glue overflow grooves are arranged on the sides of the first optical fiber fixing piece and the second optical fiber fixing piece, which face the convex array ultrasonic probe.

Illustratively, a first photoacoustic excitation light window is bonded to an outer surface of the first fiber optic mount and a second photoacoustic excitation light window is bonded to an outer surface of the second fiber optic mount.

The front surface of the first optical fiber fixing piece comprises a first light-emitting surface and a first bonding surface, a plurality of first through holes penetrate through to the first light-emitting surface, a first glue overflow groove is formed in the first bonding surface, the front surface of the second optical fiber fixing piece comprises a second light-emitting surface and a second bonding surface, a plurality of second through holes penetrate through to the second light-emitting surface, a second glue overflow groove is formed in the second bonding surface, and an included angle is formed between the first light-emitting surface and the first bonding surface; and/or an included angle is formed between the second light-emitting surface and the second bonding surface.

Illustratively, the first fiber optic mount has an arcuate shape extending along an arcuate edge of the first fan-shaped structure; and/or the second fiber fixing piece is arc-shaped extending along the arc edge of the second fan-shaped structure.

Illustratively, distal ends of the plurality of first optical fibers are respectively provided with first hard cured sections, and the first hard cured sections are fixed to the plurality of first through holes in a one-to-one correspondence; and/or the distal ends of the plurality of second optical fibers are respectively provided with a second hard curing section, and the second hard curing sections are fixed to the plurality of second through holes in a one-to-one correspondence manner.

According to another aspect of the present invention, an endoscope system is provided. The endoscope system comprises any of the optical-photoacoustic-ultrasonic composite endoscopes described above.

In the summary, a series of concepts in a simplified form are introduced, which will be further described in detail in the detailed description section. This summary is not intended to identify key features or essential features of the claimed subject matter, nor is it intended to be used as an aid in determining the scope of the claimed subject matter.

Advantages and features of the invention are described in detail below with reference to the accompanying drawings.

Drawings

The following drawings are included to provide an understanding of the invention and are incorporated in and constitute a part of this specification. Embodiments of the present invention and their description are shown in the drawings to explain the principles of the invention. In the drawings of which there are shown,

FIG. 1 is a schematic view of an endoscope system according to an exemplary embodiment of the present invention;

FIG. 2 is a schematic view of an optical-photoacoustic-ultrasonic composite endoscope according to an exemplary embodiment of the present invention;

fig. 3 is a perspective view of a head end portion of an insertion portion of an optical-photoacoustic-ultrasonic composite endoscope according to an exemplary embodiment of the present invention;

FIG. 4 is another angular perspective view of the head end shown in FIG. 3;

FIG. 5 is a side view of the head end shown in FIG. 3;

FIG. 6 is a partial cross-sectional view of the head end shown in FIG. 3;

FIG. 7 is an optical property diagram of the filter of FIG. 6;

FIG. 8 is a side cross-sectional view of the head end shown in FIG. 3;

FIG. 9 is a cross-sectional view of the head end portion shown in FIG. 3 perpendicular to the axial direction of the insertion portion;

fig. 10 is an enlarged view of a portion of the head end shown in fig. 9;

FIG. 11 is a schematic view of a light guide according to an exemplary embodiment of the present invention; and

fig. 12 is a schematic view of an optical fiber bundle according to an exemplary embodiment of the present invention.

Wherein the above figures include the following reference numerals:

10. an optical-photoacoustic-ultrasonic composite endoscope; 12. an insertion section; 121. an insertion tube; 122. a bending portion; 13. a head end portion; 15. a light guide section; 151. a light guide interface; 16. an operation unit; 20. a light source device; 21. a processing device; 22. a display; 23. an ultrasonic connector; 30. an endoscope system; 100. a head end seat; 200. a convex array ultrasonic probe; 210. an acoustic window; 300. a photoacoustic excitation light window; 310. a first photoacoustic excitation light window; 311. a first inclined surface; 320. a second photoacoustic excitation light window; 321. a second inclined surface; 400. a light guide; 402. a trunk fiber optic bundle section; 403. a first fiber optic bundle segment; 404. a second fiber optic bundle segment; 410. a first sub-fiber bundle segment; 411. a distal end of the first optical fiber; 412. a first hard cure section; 420. a second sub-fiber bundle segment; 421. a distal end of a second optical fiber; 422. a second hard cure section; 440. a fixing ring; 500. an optical imaging assembly; 501. an illumination light window; 502. a camera; 510. an objective imaging module; 511. a light filter; 512. a lens base; 513. a lens barrel; 514. an optical lens group; 520. a photoelectric sensor; 600. a first optical fiber fixing member; 610. a first through hole; 620. a first light-emitting surface; 630. a first adhesive surface; 631. a first glue overflow groove; 640. a glue overflow groove; 700. a second optical fiber fixing member; 710. and a second through hole.

Detailed Description

In the following description, numerous details are provided to provide a thorough understanding of the invention. However, it will be understood by those skilled in the art that the following description illustrates preferred embodiments of the invention by way of example only and that the invention may be practiced without one or more of these details. Furthermore, some technical features that are known in the art have not been described in detail in order to avoid obscuring the invention.

According to one aspect of the present invention, as shown in fig. 2, an optical-photoacoustic-ultrasonic composite endoscope 10 is provided. The optical-photoacoustic-ultrasonic composite endoscope 10 has rich imaging modes, can support an optical imaging mode, an ultrasonic imaging mode, a photoacoustic imaging mode and an ultrasonic-photoacoustic fusion imaging mode, and is beneficial to improving the accuracy of disease diagnosis. In accordance with another aspect of the present invention, as shown in FIG. 1, an endoscope system 30 is provided. Endoscope system 30 may include any of the optical-photoacoustic-ultrasonic composite endoscopes 10 described below. Illustratively, the endoscope system 30 may further include a light source device 20, a processing device 21, a display 22, an ultrasonic connector 23, and an ultrasonic host (not shown in the figures).

The optical-photoacoustic-ultrasonic composite endoscope 10 provided by the present invention may include an insertion portion 12. The insertion portion 12 may be inserted into the body of the observed subject, and the insertion portion 12 may include a head end portion 13 at a distal end thereof. The head end 13 may be provided with an optical imaging device, and illumination light and/or photoacoustic excitation light generated by the light source device 20 may be conducted to the distal end of the optical-photoacoustic-ultrasonic composite endoscope 10 for imaging, and the processing device 21 processes and displays an image signal acquired by the optical imaging device at the distal end of the optical-photoacoustic-ultrasonic composite endoscope 10 on the display 22. The optical-photoacoustic-ultrasonic composite endoscope 10 may transmit an ultrasonic signal to an ultrasonic host through the ultrasonic connector 23, the ultrasonic host may process the ultrasonic signal, and the processed result may be displayed on the display 22. For the optical-photoacoustic-ultrasonic composite endoscope 10, an ultrasonic transducer, a photoacoustic excitation light window, and the like may also be provided on the head end portion 13, which will be described in detail later. Typically, the head end 13 is rigid. In addition to the head end 13, the insertion part 12 may also comprise an insertion tube 121 with graduations and a bending part 122 enabling different direction swinging.

For convenience of description, the distal end mentioned below refers to an end of the optical-photoacoustic-ultrasonic composite endoscope 10 that is closer to an object to be observed when the optical-photoacoustic-ultrasonic composite endoscope 10 is used by an operator; the proximal end referred to hereinafter refers to an end of the optical-photoacoustic-ultrasonic composite endoscope 10 that is closer to the operator when the operator uses the optical-photoacoustic-ultrasonic composite endoscope 10.

The insertion portion 12 may include a head end portion 13. The head end 13 may be located at the distal end of the insertion portion 12. As shown in fig. 3-6 and 8-9, the head end 13 may include a head end mount 100, a convex array ultrasound probe 200, a photoacoustic excitation light window 300, a light guide 400, and an optical imaging assembly 500. Typically, the head end 13 may further include a water-air delivery line and an instrument channel, such that the head end 13 may integrate functions such as illumination, camera shooting, water-air delivery, ultrasonic imaging, photoacoustic imaging, and forceps instrument manipulation. It should be noted that the relative positions of the head end 100, the convex ultrasonic probe 200, the photoacoustic excitation light window 300, the light guide 400, and the optical imaging assembly 500 on the head end 13 may be arbitrary, and are not particularly limited herein. Preferably, the head end 13 may have a similar profile to that of a conventional ultrasonic endoscope.

The head end seat 100 can be designed into various shapes according to the requirement, the head end seat 100 can be used for bearing the internal components of the head end 13, and the head end seat 100 can be used as a carrier for multifunctional integration of the head end 13. Preferably, the head end socket 100 may be made of a plastic material, and such a head end socket 100 may have a good insulation effect.

The male array ultrasonic probe 200 may be disposed at the front end of the head end mount 100. The front end refers to an end of the optical-photoacoustic-ultrasonic composite endoscope 10 that is closer to the object to be observed on the head end 13 when in use. The convex ultrasonic probe 200 and the head end seat 100 can be fixedly connected, and the convex ultrasonic probe 200 can be arranged at the front end of the head end seat 100 in various forms such as welding, threaded connection or clamping connection. The male array ultrasound probe 200 may include an ultrasound transducer that may transmit and receive ultrasound waves to form an ultrasound image. The term "convex ultrasonic probe 200" as used herein means that the convex ultrasonic probe 200 can receive not only ultrasonic echoes formed by ultrasonic waves emitted by itself but also ultrasonic echoes generated by irradiation of photoacoustic excitation light on an object to be observed, and the photoacoustic excitation light may be emitted from the head end 13 through the photoacoustic excitation light window 300. The convex-array ultrasonic probe 200 may be connected with an external ultrasonic-photoacoustic host, the convex-array ultrasonic probe 200 may transmit the received ultrasonic wave to the external ultrasonic-photoacoustic host, and through the ultrasonic-photoacoustic host processing, an imaging mode such as ultrasonic imaging, photoacoustic imaging or ultrasonic-photoacoustic fusion imaging may be realized.

Photoacoustic excitation light window 300 may be disposed on head-end mount 100. As shown in fig. 3, the photoacoustic excitation light window 300 may have various shapes as needed, the photoacoustic excitation light window 300 may be provided on the head end 100 by various forms of welding, screwing or clamping, etc., and the photoacoustic excitation light window 300 may form a part of the housing of the head end 13 on the head end 100.

Preferably, the photoacoustic excitation light window 300 may be fully transparent, and the photoacoustic excitation light window 300 may be made of a non-metallic material, i.e. the photoacoustic excitation light window 300 may comprise the form of a fully transparent non-metallic material light window. Preferably, the outer surface of the photoacoustic excitation light window 300 may also be of a hydrophobic design, so that food waste, mucus, etc. adhering to the surface of the photoacoustic excitation light window 300 may be reduced from the body cavity mucosal surface of the observed object. The photoacoustic excitation light window 300 may change the emission path of the photoacoustic excitation light beam to form a better photoacoustic excitation light field, and the photoacoustic excitation light window 300 may be an outlet from which the photoacoustic excitation light is emitted by the head end 13. Preferably, the photoacoustic excitation light window 300 may include a light refracting means such that the photoacoustic excitation light may be emitted from the photoacoustic excitation light window 300 at a preset emission angle. The light refracting means may be a prism (e.g. a trapezoidal prism). Photoacoustic excitation light window 300 may also include light reflecting means, which may be a prism, a planar mirror, a concave mirror, a convex mirror, or the like.

The photoacoustic excitation light window 300 may be located at a side of the convex array ultrasound probe 200. In this way, the photoacoustic excitation light window 300 guides the emission of photoacoustic excitation light, and the convex array ultrasonic probe 200 emits and receives ultrasonic waves, which may not interfere with each other. As shown in fig. 3, photoacoustic excitation light windows 300 may be located on both sides of the convex array ultrasound probe 200. In other embodiments not shown, the photoacoustic excitation light window 300 may surround the convex array ultrasound probe 200, and the photoacoustic excitation light window 300 may also be located at one side of the convex array ultrasound probe 200, and the photoacoustic excitation light window 300 may have various different shapes according to different needs, which is not particularly limited herein.

The light guide 400 may be disposed through the insertion portion 12 and extend into the head end socket 100. As shown in fig. 2, the optical-photoacoustic-ultrasonic composite endoscope 10 may include a light guide portion 15, an operation portion 16, and an insertion portion 12. The operation portion 16 may be connected between the light guide portion 15 and the insertion portion 12. The light guide 400 may include an optical fiber, which may be a single mode optical fiber or a multimode optical fiber. The light guide 400 may be provided to penetrate the light guide portion 15, the operation portion 16, and the insertion portion 12. The light guide 400 may be aligned with the photoacoustic excitation light window 300 and conduct photoacoustic excitation light to the photoacoustic excitation light window 300. The distal end of the light guide 400 may be aligned with the photoacoustic excitation light window 300. In the embodiment shown in fig. 1, the proximal end of the light guide 15 may be connected to the light source device 20, and photoacoustic excitation light generated by an external photoacoustic excitation light source may reach the head end socket 100 through the light guide 400. The distal end of the light guide 400 may have a form matching the shape of the photoacoustic excitation light window 300, as in the embodiment shown in fig. 8, the photoacoustic excitation light window 300 has a cambered shape, and correspondingly, the distal end of the light guide 400 may be bifurcated into a fan shape, so that the distal end of the light guide 400 is better aligned with the photoacoustic excitation light window 300. After the photoacoustic excitation light generated by the external photoacoustic excitation light source reaches the head end seat 100 through the conduction of the light guide 400, the photoacoustic excitation light may be emitted outwards through the photoacoustic excitation light window 300.

The optical imaging assembly 500 may be disposed on the head end mount 100. The optical imaging assembly 500 may include an illumination light window 501, a camera 502, etc., and the optical imaging assembly 500 may be used for optical imaging. The light guide 400 may also be used to conduct illumination light. The distal end of the light guide 400 is aligned with the illumination light window 501.

The optical fiber that conducts illumination light and the optical fiber that conducts photoacoustic excitation light may be the same optical fiber bundle. In this case, the optical fiber bundle may be branched at a position in the middle, and two optical fiber bundle segments from the branching to the distal end may be aligned with the illumination light window 501 and the photoacoustic excitation light window 300, respectively. The fiber bundle from the branching position to the near end is a main fiber bundle section, and the main fiber bundle section can transmit illumination light and photoacoustic excitation light. In this case, only one light guide interface may be provided on the light guide portion 15. Which will be described in more detail later. In another set of embodiments, the light guide 400 may include two optical fiber bundles independent of each other, transmitting illumination light and photoacoustic excitation light, respectively. In this case, two light guide interfaces may be provided on the light guide portion 15, and optically coupled to an external photoacoustic excitation light source and an illumination light source, respectively.

The illumination light transmitted from the light guide 400 is irradiated to the observed object through the illumination light window 501, the observed object can reflect the illumination light, and the camera 502 can receive the reflected illumination light. When the camera 502 can be connected to an external image processing apparatus, the received reflected illumination light can be transmitted to the external image processing apparatus, and optical imaging can be realized based thereon. The optical imaging assembly 500 may be closer to the proximal end of the insertion portion 12 than the male array ultrasound probe 200. The ultrasonic probe 200 needs to receive ultrasonic echoes generated from the observed object, so the ultrasonic probe 200 can be closer to the distal end of the insertion part 12 than the optical imaging assembly 500, so that the ultrasonic probe 200 receives ultrasonic waves more effectively. Also, the optical imaging assembly 500 and the male array ultrasonic probe 200 are spaced apart on the axis P-P of the optical-photoacoustic-ultrasonic composite endoscope 10, and interference of the optical imaging assembly 500 and the male array ultrasonic probe 200 with each other can be reduced.

As shown in fig. 4, the light guide 400 may be bifurcated at any position in the light guide portion 15, the operation portion 16, or the insertion portion 12, one of which may transmit illumination light to the optical imaging assembly 500 and the other of which may transmit photoacoustic excitation light to the photoacoustic excitation light window 300.

In the optical imaging mode, the light guide 400 may guide illumination light generated from an external illumination light source to the optical imaging assembly 500, and the optical imaging assembly 500 may irradiate illumination light to an object to be observed, thereby enabling optical imaging.

In the photoacoustic imaging mode, the light guide 400 may conduct photoacoustic excitation light generated by an external photoacoustic excitation light source to the photoacoustic excitation light window 300, the photoacoustic excitation light is refracted by the photoacoustic excitation light window 300 and then irradiates to an observed object, and after the observed object is irradiated with the photoacoustic excitation light, a photoacoustic signal (essentially ultrasonic wave) is generated and received by the convex-array ultrasonic probe 200, so that photoacoustic imaging may be realized.

In the ultrasonic imaging mode, the convex ultrasonic probe 200 can transmit ultrasonic waves to an observed object, and each layer structure in the observed object reflects the ultrasonic waves to different degrees to form ultrasonic echoes and receive the ultrasonic echoes by the convex ultrasonic probe 200, so that ultrasonic imaging can be realized.

In ultrasound-photoacoustic fusion imaging, the male array ultrasound probe 200 and the external photoacoustic excitation light source operate at preset time intervals, for example, the male array ultrasound probe 200 first emits ultrasound to an observed object

The wave, then interval time T, the photoacoustic excitation light source emits photoacoustic excitation light, the photoacoustic excitation light is conducted by the light guide 5 pieces 400 to reach the photoacoustic excitation light window 300, and then is refracted by the photoacoustic excitation light window 300 and irradiates

An object under observation. In this way, the convex ultrasonic probe 200 acquires the ultrasonic echo signal reflected from the observed object first, and then acquires the photoacoustic signal emitted from the observed object over the time interval T. The male array ultrasonic probe 200 can connect the male array ultrasonic probe 200 to an external ultrasonic-photoacoustic host

The ultrasonic echo signal and the photoacoustic signal are transmitted to an ultrasonic-photoacoustic host, and the ultrasonic-photoacoustic host respectively processes the ultrasonic echo signal and the photoacoustic signal according to a time interval T of 0, so that ultrasonic-photoacoustic fusion can be realized

Imaging. The optical-photoacoustic-ultrasonic composite endoscope 10 thus has an ultrasonic-photoacoustic imaging mode. Preferably, the time interval T may be between 1 μs and 100 μs, which is not perceived by the human eye, so that the visual ultrasound imaging and the photoacoustic imaging may be regarded as simultaneous moment imaging without motion artifacts.

5 in some embodiments, the optical imaging mode of the optical-photoacoustic-ultrasound composite endoscope 10 is primarily

The auxiliary insertion part is used for inserting into and exiting from the digestive tract, and is enabled in the whole course during operation, and is independent from the other imaging modes and is not influenced by the other imaging modes.

The optical-photoacoustic-ultrasonic composite endoscope 10 provided by the application can realize optical, ultrasonic, photoacoustic and ultrasonic-photoacoustic imaging simultaneously, and can not interfere with each other, so that the accuracy of in-vivo diagnosis is greatly improved. 0, wherein the optical imaging mode and other imaging modes are not mutually influenced, and the ultrasonic imaging mode and the photoacoustic imaging mode

The mode and the ultrasonic-photoacoustic fusion imaging mode can be switched in real time, and can be independently presented in a single imaging mode or can be presented in two or three imaging modes at the same time. Moreover, the optical-photoacoustic-ultrasonic composite endoscope 10 provided by the application can be similar to a conventional ultrasonic endoscope in appearance, can not change the operation habit of a user, is friendly to the user operation, and is also beneficial to the insertion or withdrawal of the endoscope into or from a body cavity.

5 illustratively, as shown in fig. 6, the optical imaging assembly 500 may include an objective imaging module 510,

the objective imaging module 510 may be provided therein with a filter 511, and the filter 511 may be used to filter near infrared light. The wavelength range of the photoacoustic excitation light conducted by the light guide 400 is generally located in the near infrared light band. Optical properties of the filter 511 as shown in FIG. 7, the filter 511 has a wavelength in the near infrared band

The light transmittance in the light source is very low, and the light transmittance for visible light can basically reach 100%. The filter 5110 can comprise various materials that conform to the optical properties shown in fig. 7. By providing the filter 511

So as to avoid that the photoacoustic excitation light reflected by the observed object influences the observation effect of the optical imaging mode, the possible interference of the photoacoustic imaging mode or the ultrasonic-photoacoustic imaging mode to the optical imaging mode can be further reduced.

Further, the objective imaging module 510 may include a lens holder 512 and a lens barrel 513, an optical lens group 514 may be disposed in the lens barrel 513, and the lens barrel 513 may be connected to the lens holder 512. The optical imaging assembly 500 may further include a photosensor 520, the photosensor 520 may be disposed on the lens mount 512, and the filter 511 may be disposed within the lens mount 512 and may be located between the lens barrel 513 and the photosensor 520. The lens barrel 513 may be coupled to the lens mount 512 by various forms of adhesive coupling, screw coupling, welding or clamping. The optical lens group 514 may form an optical information transmission system. The lens barrel 513 can protect the optical lens group 514, so that the optical lens group 514 is not easy to collide and break, the optical lens group 514 is more stable, and the optical imaging effect of the whole device can be improved. The photoelectric sensor 520 may convert the optical signal into an electrical signal, and may further transmit the electrical signal to the processing device 21 for processing. Preferably, the photosensor 520 may include a CMOS chip. The mounting groove of the optical filter 511 may be preset on the lens base 512, and the optical filter 511 may be disposed in the mounting groove on the lens base 512 in an adhesive manner. The lens holder 512 is disposed to limit the optical filter 511, so as to enhance the effect of the optical filter 511 for filtering near infrared light and stability of the whole device. In the embodiment shown in fig. 6, the filter 511 is located between the photosensor 520 and the optical lens set 514. In other not-shown embodiments, the filter 511 may be provided at the front end of the lens barrel 513 (i.e., the end facing the object to be observed), or at an arbitrary position within the lens barrel 513.

Illustratively, referring to fig. 2 and 12 in combination, the light guide 400 may include a fiber bundle that may be bifurcated such that the fiber bundle may include a main fiber bundle section 402 connected proximally to the light guide portion 15, and first and second fiber bundle sections 403 and 404 extending distally to the head end portion 13. The fiber bundle may be bifurcated at any location in the light guide portion 15, the handling portion 16, or the insertion portion 12, with the proximal end of the fiber bundle terminating at a furcation with a trunk fiber bundle segment 402. The proximal end of the fiber bundle, i.e., the proximal end of the main fiber bundle section 402, may be connected to the light guide 15. After the illumination light or the photoacoustic excitation light generated by the light source device 20 is transmitted to the light guide portion 15, the illumination light or the photoacoustic excitation light may be further transmitted from the light guide portion 15 to the trunk fiber bundle section 402, and both the illumination light and the photoacoustic excitation light may be transmitted to the trunk fiber bundle section 402.

Wherein the distal end of the first fiber bundle segment 403 may be aligned with the illumination light window 501 and the distal end of the second fiber bundle segment 404 may be aligned with the photoacoustic excitation light window 300. After the fiber bundle is split into two strands, one strand is a first fiber bundle section 403, and the first fiber bundle section 403 can transmit illumination light to the illumination light window 501; the other strand is a second fiber bundle section 404, and the second fiber bundle section 404 may transmit photoacoustic excitation light to the photoacoustic excitation light window 300. The illumination light emitted through the distal end of the first fiber bundle section 403 can be irradiated onto the object to be observed through the illumination light window 501, and the photoacoustic excitation light emitted through the distal end of the second fiber bundle section 404 can be irradiated onto the object to be observed through the photoacoustic excitation light window 300.

The optical fiber bundle may be bifurcated at any position in the light guide portion 15, the operating portion 16, or the insertion portion 12. There are typically many harnesses in the insertion tube 121 of the insertion portion 12, for example, in order to provide the head end portion 13 with a function of handling a forceps instrument, an instrument channel may be provided in the insertion tube 121, and a wire rope may be provided in the instrument channel, which may be used to pull a medical instrument. The optical fiber bundle is split into two in the insertion portion 12, because the number of the wires in the insertion portion 12 is large, the wires inside the insertion portion 12 will move along with the bending of the bending portion 122, and if the optical fiber bundle is split in the insertion portion 12, the wires inside the insertion portion 12 are easily stirred into a cluster, which affects the reliability of the endoscope. The light guide portion 15 is generally far away from the head end portion 13, and the optical fiber bundle is split into two bundles in the light guide portion 15, so that the split first optical fiber bundle section 403 and second optical fiber bundle section 404 have longer lengths, waste of internal materials can be caused, stability of the whole device is not facilitated, and repair difficulty can be improved.

Therefore, preferably, the optical fiber bundle can be branched in the operation portion 16. When the optical fiber bundle needs to be disassembled for maintenance or replacement, the branching part of the optical fiber bundle can be more conveniently taken out from the operation part 16; the operation part 16 and the light guide part 15 are a whole bundle of optical fibers, so that the optical fibers are easy to be pulled out during maintenance; at the same time, the operating portion is closer to the head end 13, and the lengths of the first fiber bundle section 403 and the second fiber bundle section 404 can be shorter, so that the internal structure of the overall apparatus is simpler.

Illustratively, as shown in FIG. 12, a securing ring 440 may be provided around the bifurcation of any two segments of the fiber bundle. The bifurcation may be where the main fiber bundle section 402 is split into a first fiber bundle section 403 and a second fiber bundle section 404. Alternatively, the furcation may be a furcation where the second fiber bundle section 404 is split into a first sub-fiber bundle section 410 and a second sub-fiber bundle section 420. Two fiber bundle segments on both sides of the crotch may be sleeved with a protective sheath, which may be secured to the securing ring 440. The protective cover can be made of plastic materials, can protect the optical fiber bundle and can reduce external interference to the optical fiber bundle. The retaining ring 440 may be made of metal or plastic material. The fixing ring 440 is sleeved at the branching position of the optical fiber bundle, so that the branching position of the optical fiber bundle can be protected from being damaged by external interference. The protective sheath may be connected to the fixing ring 440 by welding or fusing, etc., so that the stability of the branching portion of the optical fiber bundle may be further improved, thereby improving the stability of the overall device.

Illustratively, as shown in fig. 2, a light guide interface 151 may be provided on the light guide 15, and the proximal end of the optical fiber bundle may be connected to the light guide interface 151. The light source device 20 may switchably supply illumination light or photoacoustic excitation light, but cannot supply illumination light and photoacoustic excitation light at the same time, and the light guide portion 15 of the optical-photoacoustic-ultrasonic composite endoscope 10 is connected to the light source device 20. The light source device 20 may comprise two parts of an illumination light source and a photoacoustic excitation light source, wherein the two parts of the illumination light source and the photoacoustic excitation light source can be freely switched but cannot be simultaneously turned on, and preferably, the switching of the illumination light source and the photoacoustic excitation light source can be prompted by a buzzer to avoid false touch. When an operator turns on the diagnosis and treatment, the light source device 20 can be switched to an illumination light source, and optical illumination can be provided, so that the optical-photoacoustic-ultrasonic composite endoscope 10 can capture an optical image to obtain surface layer information of an observed object. Meanwhile, an operator can transmit and receive ultrasonic signals by using the convex array ultrasonic probe so as to obtain deep information of an observed object. When an operator has the requirements of high-resolution, high-contrast and high-sensitivity structural imaging and functional imaging, the light source device 20 can be switched to a photoacoustic excitation light source, so that photoacoustic imaging can be performed, and diagnosis and treatment can be performed more accurately. In this case, only one light guide interface 151 may be provided on the light guide 15, and the light guide 15 may be connected to the light source device 20 through the light guide interface 151. The proximal end of the optical fiber bundle may be connected to the light guide 15, and preferably, the proximal end of the optical fiber bundle and the light guide 15 may be connected at the light guide interface 151, so that the light guide 15 may also achieve the purpose of transmitting illumination light and photoacoustic excitation light using the optical fiber bundle.

Of course, in other embodiments not shown, the illumination light and photoacoustic excitation light may not be provided using a bifurcated fiber optic bundle. But the illumination light and the photoacoustic excitation light are provided by two independent fiber bundles, respectively. In this way, optical imaging and photoacoustic imaging can be performed simultaneously. In this case, two light guide interfaces may be provided on the light guide portion 15, respectively connected to the two interfaces on the light source device, to receive the illumination light and the photoacoustic excitation light, respectively.

Illustratively, the photoacoustic excitation light window 300 may include a first photoacoustic excitation light window 310 and a second photoacoustic excitation light window 320, the second fiber bundle section 404 may be bifurcated within the head end 13 and form a first sub-fiber bundle section 410 and a second sub-fiber bundle section 420, the first sub-fiber bundle section 410 may be aligned with the first photoacoustic excitation light window 310, and the second sub-fiber bundle section may be aligned with the second photoacoustic excitation light window 320. The first sub-fiber bundle segment 410 may conduct photoacoustic excitation light to the first photoacoustic excitation light window 310 and the second sub-fiber bundle segment 420 may conduct photoacoustic excitation light to the second photoacoustic excitation light window 320. The first photoacoustic excitation light window 310 and the second photoacoustic excitation light window 320 may have different relative positional relationships by different designs. Alternatively, the first photoacoustic excitation light window 310 and the second photoacoustic excitation light window 320 may guide refraction of the photoacoustic excitation light, respectively, thereby changing the emission paths of the photoacoustic excitation light beams to form better photoacoustic excitation light fields, respectively. In this way, by the cooperation of the first sub-fiber bundle section 410 and the second sub-fiber bundle section 420 with the first photoacoustic excitation light window 310 and the second photoacoustic excitation light window 320, the divergence angle, the exit angle, and the irradiation area of the photoacoustic excitation light exiting from the photoacoustic excitation light window 300 can be designed as needed, and thus the sensitivity of photoacoustic imaging can be improved and the imaging area can be enlarged as needed.

Illustratively, as shown in fig. 3, 5 and 9, the first photoacoustic excitation light window 310 and the second photoacoustic excitation light window 320 may be located on opposite sides of the convex array ultrasonic probe 200 or may be located on adjacent sides of the convex array ultrasonic probe 200. The convex array ultrasound probe 200 may have an acoustic window 210 as shown in fig. 9. The convex array ultrasound probe 200 typically has a circular arc-shaped acoustic window 210. As shown in fig. 5, the acoustic window 210 may extend about an axis L. The axis L is perpendicular to the axis P-P of the insertion portion 12, which is the point L in fig. 5 and is perpendicular to the axis P-P. The acoustic window 210 may be in the form of an acoustic lens or other various acoustic elements that may converge or diverge acoustic waves. Preferably, the acoustic window 210 may include a portion made of a nonmetallic material, for example, the acoustic window 210 may include a portion made of an opaque silica gel material, so that photoacoustic excitation light may be prevented from being refracted through the acoustic window to the inside of the head end portion 13.

The first and second photoacoustic excitation light windows 310 and 320 may be located at both sides of the convex array ultrasonic probe 200, respectively. Such irradiation regions respectively formed by the first photoacoustic excitation light window 310 and the second photoacoustic excitation light window 320 may cover the detection regions of the convex array ultrasound probe 200 from different directions from both sides, respectively, that is, such first photoacoustic excitation light window 310 and second photoacoustic excitation light window 320 may form a good photoacoustic excitation light field.

Illustratively, each of the first photoacoustic excitation light window 310 and the second photoacoustic excitation light window 320 may be arc-shaped to fit the acoustic window 210, and such a design may enable the outgoing light path of the photoacoustic excitation light to be coaxial with the acoustic path of the ultrasonic probe of the convex array ultrasonic probe 200. The outer surfaces of the first photoacoustic excitation light window 310 and the second photoacoustic excitation light window 320 may not protrude from the acoustic window 210, so that the head end portion 13 can be ensured to be similar to the head end portion of a conventional ultrasonic endoscope in appearance, an operator may not need to change the operation habit when using the ultrasonic endoscope, and irregular shapes of the head end portion 13 can be avoided, which is beneficial for the insertion portion 12 to be inserted into or withdrawn from the body cavity of the observed object.

Illustratively, as shown in fig. 9, the inner surface of the first photoacoustic excitation light window 310 may have a first inclined surface 311, the first inclined surface 311 may be inclined toward the proximal end in a direction approaching the convex array ultrasound probe 200, and the distal end of the first sub-fiber bundle section 410 may be aligned with the first inclined surface 311. The inner surface of the second photoacoustic excitation light window 320 may have a second inclined surface 321, the second inclined surface 321 may be inclined toward the proximal end in a direction approaching the convex array ultrasonic probe 200, and the distal end of the second sub-optical fiber bundle section 420 may be aligned with the second inclined surface 321. Thus, the first and second photoacoustic excitation light windows 310 and 320 may refract the photoacoustic excitation light conducted by the first and second sub-fiber bundle sections 410 and 420, respectively, toward the middle of the convex array ultrasound probe 200, as shown in fig. 9, toward the central axis M-M. Fig. 9 shows a schematic diagram of a photoacoustic excitation light field, which is more powerful near the imaging plane of the convex ultrasound probe 200, so that the imaging effect of the convex ultrasound probe 200 can be better.

In addition to the first inclined plane 311 and the second inclined plane 321, there may be other various manners to make the first photoacoustic excitation light window 310 and the second photoacoustic excitation light window 320 respectively refract the photoacoustic excitation light toward the central axis M-M of the convex array ultrasonic probe 200, which will not be described herein.

Illustratively, the distal end of the first sub-fiber bundle segment 410 and the distal end of the second sub-fiber bundle segment 420 may be inclined toward the convex array ultrasound probe 200. As shown in fig. 9, the first photoacoustic excitation light window 310 has a first inclined surface 311, the second photoacoustic excitation light window 320 has a second inclined surface 321, the distal end of the first sub-fiber bundle section 410 may be aligned approximately perpendicularly to the first inclined surface 311, and the distal end of the second sub-fiber bundle section 420 may be aligned approximately perpendicularly to the second inclined surface 321, so that the photoacoustic excitation light window 300 guides the photoacoustic excitation light to be refracted more effectively, and the alignment relationship between the first sub-fiber bundle section 410 and the second sub-fiber bundle section 420 and the photoacoustic excitation light window 300 is more stable.

Illustratively, as shown in fig. 11, the distal ends 411 of the plurality of first optical fibers included in the first sub-fiber bundle section 410 may be separated from each other and may form a first fan-shaped structure, and the distal ends 421 of the plurality of second optical fibers included in the second sub-fiber bundle section 420 may be separated from each other and may form a second fan-shaped structure. The distal ends 411 of the plurality of first optical fibers may have the same shape or may have different shapes, and preferably the distal ends 411 of the plurality of first optical fibers may be in the form of a plurality of thin cylinders. The distal ends 411 of the plurality of first optical fibers may be uniformly distributed at an angle therebetween after being separated from each other, and in the first fan-shaped structure formed by the distal ends 411 of the plurality of first optical fibers, an outermost positioning angle α as shown in the drawing may be greater than or equal to a scanning angle of the convex ultrasonic probe 200. The distal ends 421 of the second plurality of optical fibers may be similar to the distal ends 411 of the first plurality of optical fibers, and will not be described again. It is noted that the first fan-shaped structure formed by the distal ends 411 of the plurality of first optical fibers and the second fan-shaped structure formed by the distal ends 421 of the plurality of second optical fibers may be the same or different, and are not particularly limited herein.

Further, as shown in fig. 9 to 10, the head end 13 may further include a first optical fiber fixing member 600, where the first optical fiber fixing member 600 may be provided with a plurality of first through holes 610 corresponding to the distal ends 411 of the plurality of first optical fibers one by one, and axes of the plurality of first through holes 610 pass through the center of the first fan-shaped structure, and the distal ends 411 of the plurality of first optical fibers may be fixed in the corresponding first through holes 610, respectively; the head end 13 may further include a second optical fiber fixing member 700, and the second optical fiber fixing member 700 may be provided with a plurality of second through holes 710 in one-to-one correspondence with distal ends 421 of the plurality of second optical fibers, and axes of the plurality of second through holes 710 may pass through a center of the second fan-shaped structure, and the distal ends 421 of the plurality of second optical fibers may be respectively fixed in the corresponding second through holes 710.

The first through holes 610 may be matched with the shape of the distal ends 411 of the plurality of first optical fibers, the distal ends 411 of the plurality of first optical fibers may be fixedly connected with the plurality of first through holes 610 by means of gluing, and the distal ends 411 of each of the thin branched first optical fibers may correspond to one of the first through holes 610. The second optical fiber fixing member 700 may be similar to the first optical fiber fixing member 600, and will not be described herein.

The plurality of first through holes 610 of the first optical fiber fixing member 600 and the plurality of second through holes 710 of the second optical fiber fixing member 700 can fix the distal ends 411 and 421 of the plurality of first optical fibers, respectively, so that the fixing manner is simple in structure, and the distal ends 411 and 421 of the plurality of first optical fibers and the plurality of second optical fibers can be protected by the first optical fiber fixing member 600 and the second optical fiber fixing member 700, so that the positions of the plurality of first optical fibers and the plurality of second optical fibers are not easily changed due to external reasons such as collision, and the stability of the whole device is improved.

Illustratively, the first photoacoustic excitation light window 310 may be bonded to an outer surface of the first optical fiber mount 600 and the second photoacoustic excitation light window 320 may be bonded to an outer surface of the second optical fiber mount 700. The first optical fiber fixing member 600 may have a shape matching that of the first photoacoustic excitation light window 310, and an outer surface of a distal end of the first optical fiber fixing member 600 may be fixedly coupled to the first photoacoustic excitation light window 310 by various forms such as adhesive coupling, screw coupling, or welding. The second optical fiber fixing member 700 may have a shape matching that of the second photoacoustic excitation light window 320, and an outer surface of a distal end of the second optical fiber fixing member 700 may be fixedly coupled to the second photoacoustic excitation light window 320 by various forms such as adhesive coupling, screw coupling, or welding.

Illustratively, as shown in fig. 10, the front surface of the first optical fiber fixing member 600 may include a first light-exiting surface 620 and a first adhesive surface 630. The front surface of the first optical fiber fixing member 600 refers to an outer side surface of the distal end of the first optical fiber fixing member 600, and one side of the front surface of the first optical fiber fixing member 600 closer to the convex array ultrasonic probe 200 may be the first light-emitting surface 620, and the other side may be the first adhesive surface 630. The first light emitting surface 620 and the first bonding surface 630 may have an included angle therebetween, that is, the front surface of the first optical fiber fixing member 600 may not be a plane. The plurality of first through holes 610 may penetrate through to the first light emitting surface 620, and the first adhesive surface 630 may be provided with a first glue overflow groove 631. The first adhesive surface 630 may be thick and glued to ensure fixation, and the first light-emitting surface 620 may be thin and glued to avoid excessive thickness and non-uniformity of the glue layer affecting refraction of the photoacoustic excitation light. Since an included angle may be formed between the first light-emitting surface 620 and the first bonding surface 630, the glue at the first bonding surface 630 does not easily run onto the first light-emitting surface 620.

Illustratively, the front surface of the second optical fiber mount 700 may include a second light exit surface and a second adhesive surface. The front surface of the second fiber mount 700 refers to the outer side of the distal end of the second fiber mount 700. The second through holes 710 may penetrate through to the second light emitting surface, and the second adhesive surface may be provided with a second glue overflow groove, and an included angle is formed between the second light emitting surface and the second adhesive surface. The second optical fiber fixing member 700 may be similar to the first optical fiber fixing member 600, and will not be described herein.

Illustratively, the distal end of the head end mount 100 may be provided with a recess recessed toward the proximal end of the insertion portion 12, which may provide a receiving space for the arrangement of the male array ultrasonic probe 200, the first optical fiber mount 600, and the second optical fiber mount 700, and the male array ultrasonic probe 200, the first optical fiber mount 600, and the second optical fiber mount 700 may all be disposed within the recess. As shown in fig. 9, both sides of the first optical fiber fixing member 600 may be bonded to the side walls of the male array ultrasonic probe 200 and the groove, respectively. So that the first fiber fixing member 600 is more stable. The both sides of the second optical fiber mount 700 may be bonded to the sidewalls of the male array ultrasonic probe 200 and the groove, respectively. So that the second fiber fixing member 700 is more stable.

In combination with the above, the outer surface of the distal end of the first optical fiber fixing member 600 and the outer surface of the distal end of the second optical fiber fixing member 700 can be fixedly connected to the photoacoustic excitation optical window 300, the first optical fiber fixing member 600 and the second optical fiber fixing member 700 can be stably disposed in the head end portion 13, the position is not easily changed due to external collision or the like, and further the distal ends 411 of the plurality of first optical fibers connected inside the first optical fiber fixing member 600 can be more stable, the distal ends 421 of the plurality of second optical fibers connected inside the second optical fiber fixing member 700 can also be more stable, and thus the overall device is more stable.

Illustratively, the sides of the first and second optical fiber fixtures 600 and 700 facing the male array ultrasonic probe 200 may be provided with glue overflow grooves. As shown in fig. 10, a glue overflow groove 640 may be provided on a side of the first optical fiber fixing member 600 facing the convex array ultrasonic probe 200, and the glue overflow groove 640 may increase reliability of adhesive connection between the first optical fiber fixing member 600 and the convex array ultrasonic probe 200.

Illustratively, the first fiber optic mount 600 may have an arcuate shape extending along the arcuate edge of the first fan-shaped structure. The shape of the first fiber fixing member 600 can be matched with the first fan-shaped structure formed by the distal ends 411 of the plurality of first optical fibers, so that the installation is easy, the material can be saved, and the shape consistency of the whole device is better.

Illustratively, the second fiber optic mount 700 may be arcuate extending along the arcuate edge of the second fan-shaped structure. The second fiber holder 700 may be shaped to match the second fan-shaped configuration formed by the distal ends 421 of the plurality of second fibers, which may be easier to install, and may save material, and may also provide better overall device profile uniformity.

Illustratively, as shown in fig. 11, the distal ends 411 of the plurality of first optical fibers may be provided with first hard-cured sections 412, respectively, and the first hard-cured sections 412 may be fixed to the plurality of first through holes 610 in a one-to-one correspondence. Illustratively, the distal ends 421 of the plurality of second optical fibers may be provided with second hard-cured segments 422, respectively, and the second hard-cured segments 422 may be secured to the plurality of second through-holes 710 in a one-to-one correspondence. Alternatively, the first and second hard segments 412, 422 may be formed from fiber stubs that fit over the optical fibers, which may serve as support structures for the optical fibers. Alternatively, the first hard-cured section 412 and the second hard-cured section 422 may also be hard sections formed using various curing methods. The distal ends 411 of the plurality of first optical fibers are connected to the plurality of first through holes 610 by the first hard cured section 412, which can provide both effective protection for the distal ends 411 of the plurality of first optical fibers and facilitate securing the distal ends of the first sub-fiber bundle sections 410 to the first fiber mount 600. The distal ends 421 of the plurality of second optical fibers are connected to the plurality of second through holes 710 by the second hard cured section 422, which both provides effective protection for the distal ends 421 of the plurality of second optical fibers and facilitates securing the distal ends of the second sub-fiber bundle sections 420 to the second fiber mount 700.

In the description of the present invention, it should be understood that the azimuth or positional relationships indicated by the azimuth terms such as "front", "rear", "upper", "lower", "left", "right", "transverse", "vertical", "horizontal", and "top", "bottom", etc., are generally based on the azimuth or positional relationships shown in the drawings, merely for convenience of describing the present invention and simplifying the description, and these azimuth terms do not indicate and imply that the apparatus or elements referred to must have a specific azimuth or be constructed and operated in a specific azimuth, without limiting the scope of protection of the present invention; the orientation terms "inner" and "outer" refer to the inner and outer relative to the outline of the components themselves.

For ease of description, regional relative terms, such as "above … …," "above … …," "upper surface at … …," "above," and the like, may be used herein to describe regional positional relationships of one or more components or features to other components or features illustrated in the figures. It will be understood that the relative terms of regions include not only the orientation of the components illustrated in the figures, but also different orientations in use or operation. For example, if the element in the figures is turned over entirely, elements "over" or "on" other elements or features would then be included in cases where the element is "under" or "beneath" the other elements or features. Thus, the exemplary term "above … …" may include both orientations of "above … …" and "below … …". Moreover, these components or features may also be positioned at other different angles (e.g., rotated 90 degrees or other angles), and all such cases are intended to be encompassed herein.

It is noted that the terminology used herein is for the purpose of describing particular embodiments only and is not intended to be limiting of exemplary embodiments according to the present application. As used herein, the singular is also intended to include the plural unless the context clearly indicates otherwise, and furthermore, it is to be understood that the terms "comprises" and/or "comprising" when used in this specification are taken to specify the presence of stated features, steps, operations, components, assemblies, and/or combinations thereof.

It should be noted that the terms "first," "second," and the like in the description and the claims of the present application and the above figures are used for distinguishing between similar objects and not necessarily for describing a particular sequential or chronological order. It is to be understood that the data so used may be interchanged where appropriate such that embodiments of the application described herein may be implemented in sequences other than those illustrated or otherwise described herein.

The present application has been illustrated by the above-described embodiments, but it should be understood that the above-described embodiments are for purposes of illustration and description only and are not intended to limit the application to the embodiments described. In addition, it will be understood by those skilled in the art that the present application is not limited to the embodiments described above, and that many variations and modifications are possible in light of the teachings of the application, which variations and modifications are within the scope of the application as claimed. The scope of the application is defined by the appended claims and equivalents thereof.

Claims

1. An optical-photoacoustic-ultrasonic composite endoscope comprising an insertion portion including a head end portion, characterized in that the head end portion comprises:

a head end seat;

a convex array ultrasonic probe arranged at the front end of the head end seat;

the photoacoustic excitation light window is arranged on the head end seat and positioned on the side surface of the convex array ultrasonic probe;

an optical imaging assembly disposed on the head end mount, the optical imaging assembly being closer to the proximal end of the insertion portion than the male array ultrasound probe, the optical imaging assembly having an illumination light window; and

the light guide piece penetrates through the insertion part and extends into the head end seat, and is aligned with the photoacoustic excitation light window and the illumination light window and used for respectively conducting photoacoustic excitation light and illumination light;

the outer surface of the optical-photoacoustic-ultrasonic composite endoscope is observed from the side surface of the axis of the insertion part of the optical-photoacoustic-ultrasonic composite endoscope, and the convex array ultrasonic probe, the photoacoustic excitation light window and the optical imaging assembly are distributed on the same side of the optical-photoacoustic-ultrasonic composite endoscope.

2. The optical-photoacoustic-ultrasonic composite endoscope of claim 1, wherein the optical imaging assembly comprises an objective imaging module having a filter disposed therein for filtering near infrared light.

3. The optical-photoacoustic-ultrasonic composite endoscope of claim 2, wherein the objective imaging module comprises a lens mount and a lens barrel with an optical lens set disposed therein, the lens barrel being connected to the lens mount, the optical imaging assembly further comprising a photosensor disposed on the lens mount, the filter being disposed within the lens mount between the lens barrel and the photosensor.

4. The optical-photoacoustic-ultrasonic composite endoscope of claim 1, further comprising a light guide portion and an operating portion connected between the light guide portion and the insertion portion,

the light guide includes a fiber bundle that is bifurcated such that the fiber bundle includes a main fiber bundle section connected at a proximal end to the light guide portion, and first and second fiber bundle sections extending distally to the head end,

wherein the distal end of the first fiber bundle segment is aligned with the illumination light window and the distal end of the second fiber bundle segment is aligned with the photoacoustic excitation light window.

5. The optical-photoacoustic-ultrasonic composite endoscope of claim 4, wherein the optical fiber bundle is bifurcated within the operation portion.

6. The optical-photoacoustic-ultrasonic composite endoscope of claim 4, wherein a fixing ring is sleeved at a branching position of any two sections of the optical fiber bundles, and protective skins are sleeved on two optical fiber bundle sections on two sides of the branching position, and the protective skins are fixed to the fixing ring.

7. The optical-photoacoustic-ultrasonic composite endoscope of claim 4 wherein the light guide is provided with a light guide interface to which the proximal end of the optical fiber bundle is connected.

8. The optical-photoacoustic-ultrasonic composite endoscope of claim 4, wherein the photoacoustic excitation light window comprises a first photoacoustic excitation light window and a second photoacoustic excitation light window, the second fiber optic bundle section being bifurcated within the head end and forming a first sub-fiber optic bundle section and a second sub-fiber optic bundle section, the first sub-fiber optic bundle section being aligned with the first photoacoustic excitation light window and the second sub-fiber optic bundle section being aligned with the second photoacoustic excitation light window.

9. The optical-photoacoustic-ultrasonic composite endoscope of claim 1, wherein the light guide comprises a first sub-fiber bundle section and a second sub-fiber bundle section, the photoacoustic excitation light window comprising a first photoacoustic excitation light window and a second photoacoustic excitation light window, the distal end of the first sub-fiber bundle section being aligned with the first photoacoustic excitation light window, the distal end of the second sub-fiber bundle section being aligned with the second photoacoustic excitation light window, the first photoacoustic excitation light window and the second photoacoustic excitation light window being located on either side of the convex array ultrasonic probe, respectively.

10. The optical-photoacoustic-ultrasonic composite endoscope of claim 9, wherein the first and second photoacoustic excitation light windows are each arc-shaped to fit the acoustic window of the convex array ultrasonic probe, and the outer surfaces of the first and second photoacoustic excitation light windows do not protrude from the acoustic window.

11. The optical-photoacoustic-ultrasonic composite endoscope of claim 9, wherein the first and second photoacoustic excitation light windows are configured to refract photoacoustic excitation light conducted by the first and second sub-fiber bundle segments, respectively, toward a middle of the convex array ultrasonic probe.

12. The optical-photoacoustic-ultrasonic composite endoscope of claim 11, wherein,

the inner surface of the first photoacoustic excitation light window is provided with a first inclined surface which is inclined towards the proximal end along the direction of approaching the convex array ultrasonic probe, and the distal end of the first sub-optical fiber bundle section is aligned with the first inclined surface; and/or

The inner surface of the second photoacoustic excitation light window is provided with a second inclined plane, the second inclined plane is inclined towards the proximal end along the direction approaching to the convex array ultrasonic probe, and the distal end of the second sub-optical fiber bundle section is aligned with the second inclined plane.

13. The optical-photoacoustic-ultrasonic composite endoscope of claim 9 wherein the distal ends of the first and second sub-fiber bundle segments are inclined toward the convex array ultrasonic probe.

14. The optical-photoacoustic-ultrasonic composite endoscope of claim 9 wherein the distal ends of the plurality of first optical fibers comprised by the first sub-fiber bundle section are separated from each other and form a first fan-shaped structure and the distal ends of the plurality of second optical fibers comprised by the second sub-fiber bundle section are separated from each other and form a second fan-shaped structure.

15. The optical-photoacoustic-ultrasonic composite endoscope of claim 14, wherein,

the head end part further comprises a first optical fiber fixing piece, a plurality of first through holes which are in one-to-one correspondence with the distal ends of the plurality of first optical fibers are arranged on the first optical fiber fixing piece, the axes of the plurality of first through holes pass through the center of the first fan-shaped structure, and the distal ends of the plurality of first optical fibers are respectively fixed in the corresponding first through holes;

the head end part further comprises a second optical fiber fixing piece, a plurality of second through holes which are in one-to-one correspondence with the distal ends of the second optical fibers are arranged on the second optical fiber fixing piece, the axes of the second through holes pass through the center of the second fan-shaped structure, and the distal ends of the second optical fibers are respectively fixed in the corresponding second through holes.

16. The optical-photoacoustic-ultrasonic composite endoscope of claim 15, wherein the distal end of the head end mount is provided with a groove recessed toward the proximal end of the insertion portion, the male ultrasonic probe, the first optical fiber mount and the second optical fiber mount each being disposed within the groove, the first optical fiber mount being bonded to the side walls of the male ultrasonic probe and the groove, the second optical fiber mount being bonded to the side walls of the male ultrasonic probe and the groove.

17. The optical-photoacoustic-ultrasonic composite endoscope of claim 16, wherein glue overflow grooves are provided on sides of the first and second optical fiber fixtures facing the convex array ultrasonic probe.

18. The optical-photoacoustic-ultrasonic composite endoscope of claim 15, wherein the first photoacoustic excitation light window is bonded to an outer surface of the first fiber optic mount and the second photoacoustic excitation light window is bonded to an outer surface of the second fiber optic mount.

19. The optical-photoacoustic-ultrasonic composite endoscope of claim 18, wherein the front surface of the first optical fiber fixing member includes a first light-emitting surface and a first adhesive surface, the plurality of first through holes penetrate to the first light-emitting surface, the first adhesive surface is provided with a first glue overflow groove, the front surface of the second optical fiber fixing member includes a second light-emitting surface and a second adhesive surface, the plurality of second through holes penetrate to the second light-emitting surface, the second adhesive surface is provided with a second glue overflow groove, wherein

An included angle is formed between the first light-emitting surface and the first bonding surface; and/or

An included angle is formed between the second light-emitting surface and the second bonding surface.

20. The optical-photoacoustic-ultrasonic composite endoscope of claim 15, wherein the first optical fiber fixing member is in an arc shape extending along an arc edge of the first fan-shaped structure; and/or the second optical fiber fixing piece is in an arc shape extending along the arc edge of the second fan-shaped structure.

21. The optical-photoacoustic-ultrasonic composite endoscope of claim 15, wherein distal ends of the plurality of first optical fibers are respectively provided with first hard-cured sections, the first hard-cured sections being fixed to the plurality of first through holes in one-to-one correspondence; and/or distal ends of the plurality of second optical fibers are respectively provided with second hard curing sections, and the second hard curing sections are fixed to the plurality of second through holes in a one-to-one correspondence.

22. An endoscope system comprising the optical-photoacoustic-ultrasonic composite endoscope of any one of claims 1-21.