An endoscope device capable of eliminating OCT speckle noise in real time

Abstract

The present application provides an endoscope device capable of eliminating OCT speckle noise in real time, which comprises an OCT imaging system and an endoscope probe; the endoscope probe is driven by a stepping drive assembly, the OCT imaging system comprises an OCT imaging catheter and an optical chopper arranged in the OCT imaging catheter; a single-mode optical fiber is arranged in the OCT imaging catheter, the single-mode optical fiber is connected with a self-focusing lens through a sleeve, and the optical chopper is arranged behind the self-focusing lens; a rotating device is connected with the optical chopper, and a micro-reflection prism is arranged behind the optical chopper; after the light beam of the single-mode optical fiber passes through the self-focusing lens, the light beam is modulated by the optical chopper and then turned to a detection area through the micro-reflection prism; the spatial distribution of the light beam is changed by using the chopper, the modulation of speckle noise is realized, and the image quality is significantly improved without reducing the spatial resolution.

Description

Technical Field

[0001] This invention relates to the field of endoscopy, and more particularly to an endoscopic device capable of eliminating OCT speckle noise in real time. Background Technology

[0002] Optical coherence tomography (OCT) is a non-invasive imaging technique based on the principle of low-coherence optical interference. It is widely used in medical imaging, particularly excelling in ophthalmology, dermatology, and cardiovascular imaging. OCT technology utilizes a combination of low-coherence light sources and interferometers to achieve high-resolution tomographic imaging of biological tissues, providing micron-level detail observation and offering advantages such as non-contact, non-invasiveness, and rapid imaging. However, OCT imaging also faces several challenges, such as speckle noise affecting image quality, reducing contrast, and limiting the accuracy of quantitative analysis.

[0003] Speckle noise is primarily caused by random scattering from the sample's internal microstructure. When a coherent light beam illuminates the sample, the irregular structure within the sample causes light scattering, generating different coherent light signals. These signals superimpose on the detector, forming random interference patterns, which manifest as speckle noise in the image. Speckle noise has a significant impact on images, specifically by reducing image contrast, interfering with the identification of details in target structures, affecting the accuracy of quantitative data extracted from images, and increasing the risk of misdiagnosis in medical procedures.

[0004] An optical chopper is a key device for beam modulation, widely used in lasers, spectrometers, photoelectric detection systems, and other fields. Its basic principle involves periodically modulating a light beam through mechanical or acousto-optic means to generate pulsed beams or AC signals. Optical choppers have multiple important functions in optical systems, such as beam modulation, signal enhancement, synchronous detection, and light source control, effectively improving the system's signal-to-noise ratio and measurement accuracy. In terms of applications, optical choppers are widely used in laser modulation, spectral measurement, biomedical imaging, and photoelectric detection. As an indispensable component of modern optical technology, the application of optical choppers significantly improves the performance and reliability of various optical systems.

[0005] In OCT systems, optical choppers can be used to modulate sample light beams, effectively controlling and reducing speckle noise during real-time imaging. By periodically interrupting or modulating the sample beam, the optical chopper can induce changes in the spatial distribution of the sample beam, thereby breaking the coherence of speckle noise and reducing its formation. This method not only helps improve the contrast and sharpness of OCT images but also achieves higher-quality real-time imaging without sacrificing spatial resolution.

[0006] However, there are still some limitations to integrating optical choppers into endoscope OCT systems. Therefore, how to integrate optical choppers into endoscope OCT systems in clinical applications and how to effectively reduce or suppress speckle noise have become key issues for improving image quality and diagnostic accuracy. Summary of the Invention

[0007] The purpose of this invention is to provide an endoscopic device capable of eliminating OCT speckle noise in real time, so as to solve the problems of image quality degradation and reduced diagnostic accuracy caused by speckle noise in traditional endoscopic OCT imaging.

[0008] To address the aforementioned technical problems, the present invention provides an endoscope capable of eliminating OCT speckle noise in real time. The endoscope includes an OCT imaging system and an endoscope probe. The endoscope probe is driven by a stepper drive assembly, and the OCT imaging system includes an OCT imaging conduit and an optical chopper disposed within the OCT imaging conduit.

[0009] The OCT imaging conduit is equipped with a single-mode optical fiber, which is connected to a self-focusing lens via a sleeve, and the optical chopper is located behind the self-focusing lens.

[0010] The optical chopper is equipped with a rotating device, and a micro-reflection prism is placed staggered behind the optical chopper to avoid beam obstruction; the beam of the single-mode fiber passes through the self-focusing lens, is modulated by the optical chopper, and is then deflected by the micro-reflection prism to the area to be detected.

[0011] In a preferred embodiment, the optical chopper is configured as a circular metal mesh, the thickness of the optical chopper is set to 0.5mm-0.7mm, and the diameter is 6mm;

[0012] The optical chopper has a rhomboid shape with a mesh structure of 0.01mm × 0.01mm.

[0013] In a preferred embodiment, the rotating device is a micro motor, and the chopper has a circular hole in the middle. The circular hole is adapted to the rotating motor shaft of the micro motor and is used to modulate the sample beam in real time, thereby effectively reducing the speckle noise caused by the microstructure inside the sample and realizing the periodic modulation of the beam.

[0014] In a preferred embodiment, the OCT imaging catheter includes a rigid shell, and the front end of the rigid shell has a first opening and a second opening;

[0015] The first opening is used for focusing the light beam and receiving the light scattering signal; the second opening is used to place the miniature horse.

[0016] In a preferred embodiment, the micro-reflective prism is fixed to the rear end of the rigid housing; the micro-reflective prism is fixed with 9005 epoxy resin AB glue.

[0017] In a preferred embodiment, the OCT imaging catheter further includes a tubular sheath that encapsulates the entire OCT imaging catheter.

[0018] In a preferred embodiment, the upper part of the rigid housing is provided with a third opening, which is used to observe the distance between the sleeve and the self-focusing lens.

[0019] In a preferred embodiment, the stepper drive assembly includes a stepper motor, a synchronous rotary motor, a synchronous belt, and an optoelectronic slip ring;

[0020] The synchronous rotary motor is connected to the synchronous belt, and the stepper motor drives the synchronous rotary motor to rotate through the synchronous belt.

[0021] In a preferred embodiment, the photoelectric slip ring employs a rotary photoelectric coupling method.

[0022] Compared with the prior art, the technical solution of the present invention has the following beneficial effects:

[0023] 1. A novel speckle noise modulation technique was achieved by modifying the spatial distribution of the sample beam using a special chopper. This technique significantly improves image quality without reducing spatial resolution, and its low cost, simple structure, and compact integration provide important advantages for the design of endoscopic probes in clinical applications.

[0024] 2. By setting up staggered optical choppers and micro-reflection prisms, the optical choppers can rotate and effectively suppress speckle noise by periodically modulating the light beam entering the imaging unit, significantly improving the contrast and clarity of the image, thus providing doctors with more accurate diagnostic information, and is suitable for a variety of medical imaging applications. Attached Figure Description

[0025] Figure 1 This is a schematic diagram of the endoscopic device catheter structure in a preferred embodiment of the present invention;

[0026] Figure 2 This is a schematic diagram of the internal distribution structure of the endoscopic device catheter in a preferred embodiment of the present invention;

[0027] Figure 3 This is a schematic diagram of the optical chopper of the endoscopic device in a preferred embodiment of the present invention;

[0028] Figure 4 This is a schematic diagram of the stepping device of the endoscope in a preferred embodiment of the present invention.

[0029] Explanation of reference numerals in the attached drawings: 01, fixed position; 02, rigid shell; 03, first opening; 04, second opening; 05, positive wire; 06, negative wire; 07, optical chopper; 11, micro-reflection prism; 12, detection area; 13, self-focusing lens; 14, sleeve; 15, third opening; 16, single-mode optical fiber; 17, micro motor; 21, stepper motor; 22, synchronous rotary motor; 23, synchronous belt; 24, photoelectric slip ring. Detailed Implementation

[0030] The technical solutions of the present invention will be clearly and completely described below with reference to the accompanying drawings of the embodiments of the present invention. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. All other embodiments obtained by those skilled in the art based on the embodiments of the present invention without creative effort are within the scope of protection of the present invention.

[0031] In the description of this invention, it should be noted that the terms "upper," "lower," "inner," "outer," "top / bottom," etc., indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings. They are used only for the convenience of describing the invention and for simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation. Therefore, they should not be construed as limitations on the invention. Furthermore, the terms "first" and "second" are used for descriptive purposes only and should not be construed as indicating or implying relative importance.

[0032] In the description of this invention, it should be noted that, unless otherwise explicitly specified and limited, the terms "installed", "equipped", "sleeved / connected", "connected", etc., should be interpreted broadly. For example, "connection" can be a wall-mounted connection, a detachable connection, or an integral connection; it can be a mechanical connection or an electrical connection; it can be a direct connection or an indirect connection through an intermediate medium; it can be a connection within two components. For those skilled in the art, the specific meaning of the above terms in this invention can be understood according to the specific circumstances.

[0033] refer to Figures 1-4 This embodiment provides an endoscope capable of eliminating OCT speckle noise in real time. The endoscope includes an OCT imaging system and an endoscope probe. The endoscope probe is driven by a stepper drive assembly. The OCT imaging system includes an OCT imaging conduit and an optical chopper 07 disposed inside the OCT imaging conduit.

[0034] like Figure 1The OCT imaging catheter described herein is constructed using a sophisticated combination of optical elements. This imaging catheter includes several key components connected sequentially in a specific order to ensure stable transmission of optical signals and accurate imaging during the imaging process. Specifically, a single-mode fiber 16 is first installed inside the catheter to transmit a coherent beam from the light source. The single-mode fiber 16 has high light transmission efficiency, effectively transmitting the light signal to the target area. The single-mode fiber 16 is connected to a self-focusing lens 13 via a sleeve 14. The use of the self-focusing lens 13 significantly improves the beam resolution, enabling the OCT imaging system to capture minute structural details within the tissue.

[0035] An optical chopper 07 is disposed behind the self-focusing lens 13. The function of the optical chopper 07 is to periodically interrupt or modulate the beam during its transmission. This modulation can effectively suppress the formation of speckle noise, thereby improving the contrast and sharpness of the image.

[0036] like Figure 3 The optical chopper 07 employs a specially designed optical chopper. This optical chopper 07 is a circular metal mesh with a thickness of approximately 0.6 mm and a diameter of 6 mm, its mesh structure exhibiting a rhomboid shape of 0.01 × 0.01 mm. The sample beam passing through the chopper has a diameter of approximately 0.1 mm, and regardless of the incident angle of the sample beam, the optical chopper 07 always partially obstructs the sample beam. When the optical chopper 07 rotates at a uniform speed, it continuously alters the spatial distribution of the beam entering the sample through the self-focusing lens 13. This modulation process causes changes in the amplitude of backscattered light from scatterers in each resolvable volume element within the sample, resulting in random and continuous variations in the speckle pattern. Ultimately, by averaging these images with different speckle patterns, images with significantly suppressed speckle noise can be obtained, thereby improving the clarity and contrast of OCT imaging and enhancing the diagnostic accuracy of the endoscope in clinical applications.

[0037] A rotating device, a miniature motor 17, is installed inside the OCT imaging guide tube to drive the optical chopper 07 to rotate at a constant speed. The chopper has a circular hole in the middle, which is adapted to the rotating shaft of the miniature motor 17. Through precise control, the miniature motor 17 can drive the chopper fixed on it to rotate at high speed.

[0038] A micro-reflection prism 11 is disposed after the optical chopper 07. The beam of the single-mode fiber 16, after passing through the self-focusing lens 13, is modulated by the optical chopper 07 and then refracted by the micro-reflection prism 11 to the area to be detected 12. The micro motor 17 drives the optical chopper 07 to rotate 360° to acquire one frame of image. The endoscope probe is stepped with a precision of 50µm through a customized stepping drive component to acquire a settable step x distance and a three-dimensional raw data set consisting of N high-resolution images. The rotation of the optical chopper 07 can realize multi-angle reflection of the beam, thereby covering a wider imaging range and improving the overall image quality.

[0039] like Figure 2 In the design of the endoscopic device, to avoid beam obstruction during transmission, a staggered arrangement of the optical chopper 07 and the micro-reflective prism 11 is specifically adopted. The positions of the optical chopper 07 and the micro-reflective prism 11 are precisely calculated and optimized so that the beam falls on the center of the micro-reflective prism after passing two-thirds of the distance from the center of the optical chopper 07. This structural design fully considers the synergistic effect between the various optical components, ensuring that they do not interfere with each other's beam propagation path during operation, thus guaranteeing smooth beam transmission during the imaging process.

[0040] The OCT imaging catheter includes a rigid housing 02, which not only protects the distal end of the catheter but also ensures the stability of the endoscopic probe when in contact with tissue. The rigid housing 02 is designed with compatibility with human tissue in mind, effectively reducing tissue damage during clinical procedures while providing a robust platform to support the entire catheter operation.

[0041] A first opening 03 and a second opening 04 are formed at the front end of the rigid housing 02. The first opening 03 is a small opening, and the second opening 04 is a large opening. The first opening 03 is used for focusing the light beam and receiving light scattering signals. The second opening 04 is used to house a micro motor 17, which includes a positive wire 0505 and a negative wire 0606 for power supply. A fixing position 01 is provided at the rear end of the rigid housing 02 for fixing a micro-reflecting prism 11, which is fixed with 9005 epoxy resin AB glue. A third opening 15 is provided at the upper part of the rigid housing 02 for observing the distance between the sleeve 14 and the self-focusing lens 13.

[0042] To protect the optical fiber and other optical components, the OCT imaging catheter also includes a flexible sheath. This sheath encapsulates the entire catheter, providing necessary mechanical protection and maintaining its stability. The sheath is made of a soft yet strong material, capable of resisting the effects of the external environment, while its high light transmittance will not adversely affect light transmission. It also protects the internal optical components of the probe from contamination by mucus, which could degrade image quality. Food-grade white oil can be added between the flexible sheath and the catheter for lubrication to prevent adhesion and facilitate catheter insertion or removal.

[0043] Overall, this OCT imaging catheter, through its carefully designed optical and mechanical components, enables efficient and accurate tissue imaging, providing reliable image support for clinical diagnosis.

[0044] Following general anesthesia induction, the imaging process acquires information about the target tissue under endoscopic guidance. The distance for three-dimensional imaging can be determined by setting the parameters of the stepping device. This embodiment involves a stepping drive component for endoscopic OCT three-dimensional imaging. Through precise mechanical design and motor control, this component achieves accurate positioning and efficient scanning of the imaging probe, providing crucial support for acquiring high-quality three-dimensional images. The following is a detailed description of the stepping drive component:

[0045] like Figure 4 The stepper drive assembly includes a stepper motor 21, a synchronous rotary motor 22, a synchronous belt 23, and a photoelectric slip ring 24. These components work together to form a highly integrated drive system, enabling the imaging probe to perform multi-angle and multi-directional scanning actions under precise control, thereby generating three-dimensional tissue images.

[0046] The photoelectric slip ring 24 is a key component in the stepper drive assembly, designed to transmit optical and electrical signals between the imaging device and the OCT imaging catheter.

[0047] The photoelectric slip ring 24 employs a rotary photoelectric coupling method, enabling seamless transmission of electrical and optical signals during rotation, achieving efficient photoelectric conversion. This design ensures that the imaging probe does not experience signal distortion or quality degradation due to rotation during scanning, thus guaranteeing the accuracy and reliability of 3D imaging.

[0048] The synchronous rotary motor 22 is interconnected with the synchronous belt 23, and the stepper motor 21 drives the synchronous rotary motor 22 to rotate via the synchronous belt 23. This forms the transmission mechanism in the stepper drive assembly. Through precise stepping control, the synchronous rotary motor 22 drives the stepper motor 21 to drive the synchronous pulley, which in turn drives the synchronous belt 23, enabling the imaging probe to move smoothly and precisely along a designated path. The selection and design of the synchronous belt 23 take into account its durability and transmission efficiency, ensuring stable performance during long-term use.

[0049] The stepper motor 21 in the stepper drive assembly is responsible for precisely controlling the operation of the synchronous rotary motor 22. The stepper drive assembly receives commands from the control system and adjusts the motor's speed, direction, and step angle to meet the needs of different imaging tasks. Through precise motor control, the stepper drive assembly enables the imaging probe to perform detailed scanning along complex three-dimensional paths, thereby acquiring high-resolution tissue images.

[0050] Through the coordinated operation of the aforementioned components, the stepper drive assembly provides highly stable scanning motion in endoscopic OCT 3D imaging. This stepper drive assembly not only improves the spatial resolution of the image but also ensures reliability and stability during long-term operation. The design of this stepper drive assembly also simplifies and streamlines system maintenance and upgrades, making it suitable for a variety of complex clinical imaging needs.

[0051] The above description is merely a preferred embodiment of the present invention, but the design concept of the present invention is not limited thereto. Any non-substantial modifications made to the present invention by those skilled in the art within the scope of the technology disclosed in the present invention using this concept shall be deemed as an infringement of the protection scope of the present invention.

Claims

1. An endoscopic device capable of real-time elimination of OCT speckle noise, characterized in that: The endoscopic device includes an OCT imaging system and an endoscopic probe; the endoscopic probe is driven by a stepper drive assembly, and the OCT imaging system includes an OCT imaging catheter and an optical chopper disposed inside the OCT imaging catheter. The OCT imaging conduit is equipped with a single-mode optical fiber, which is connected to a self-focusing lens via a sleeve, and the optical chopper is located behind the self-focusing lens. The optical chopper is equipped with a rotating device, and a micro-reflection prism is placed offset behind the optical chopper; the beam of the single-mode fiber passes through the self-focusing lens, is modulated by the optical chopper, and is then deflected by the micro-reflection prism to the area to be detected.

2. An endoscopic device capable of real-time elimination of OCT speckle noise according to claim 1, characterized in that: The optical chopper is configured as a circular metal mesh, with a thickness of 0.5mm-0.7mm and a diameter of 6mm. The optical chopper has a rhomboid shape with a mesh structure of 0.01mm × 0.01mm.

3. An endoscopic device capable of real-time elimination of OCT speckle noise according to claim 2, characterized in that: The rotating device is a micro motor, and the chopper has a circular hole in the middle, which is adapted to the rotating motor shaft of the micro motor.

4. An endoscopic device capable of real-time elimination of OCT speckle noise according to claim 3, characterized in that: The OCT imaging catheter includes a rigid shell, and the front end of the rigid shell has a first opening and a second opening; The first opening is used for focusing the light beam and receiving the light scattering signal; the second opening is used to place the miniature horse.

5. An endoscopic device capable of real-time elimination of OCT speckle noise according to claim 4, characterized in that: The micro-reflective prism is fixed to the rear end of the rigid shell; the micro-reflective prism is fixed with 9005 epoxy resin AB glue.

6. An endoscopic device capable of real-time elimination of OCT speckle noise according to claim 5, characterized in that: The OCT imaging catheter also includes a tubular sheath that encapsulates the entire OCT imaging catheter.

7. An endoscopic device capable of real-time elimination of OCT speckle noise according to claim 4, characterized in that: The upper part of the rigid housing is provided with a third opening, which is used to observe the distance between the sleeve and the self-focusing lens.

8. An endoscopic device capable of real-time elimination of OCT speckle noise according to claim 1, characterized in that: The stepper drive assembly includes a stepper motor, a synchronous rotary motor, a synchronous belt, and an optoelectronic slip ring. The synchronous rotary motor is connected to the synchronous belt, and the stepper motor drives the synchronous rotary motor to rotate through the synchronous belt.

9. An endoscopic device capable of real-time elimination of OCT speckle noise according to claim 8, characterized in that: The photoelectric slip ring employs a rotary photoelectric coupling method.

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