Endoscopic device capable of eliminating OCT speckle noise in real time

Abstract

The invention provides an endoscopic device capable of eliminating OCT speckle noise in real time. The endoscopic device comprises an OCT imaging system and an endoscopic probe. The endoscopic probe is driven by a stepping driving assembly, and 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 micro-reflecting prisms are arranged behind the optical chopper in a staggered manner; after passing through the self-focusing lens, a light beam of the single-mode optical fiber is modulated by the optical chopper and then is reflected to a to-be-detected area through the micro-reflecting prism; spatial distribution of light beams is changed through the chopper, speckle noise modulation is achieved, and the image quality is remarkably improved under the condition that the spatial resolution is not reduced.

Description

Technical Field

[0001] The present invention relates to the field of endoscopes, and in particular to an endoscope device capable of eliminating OCT speckle noise in real time. Background Art

[0002] Optical Coherence Tomography (OCT) is a non-invasive imaging technology based on the principle of low-coherence light interference. It is widely used in the field of medical imaging, especially in ophthalmology, dermatology and cardiovascular imaging. OCT technology combines low-coherence light sources with interferometers to achieve high-resolution tomographic imaging of biological tissues, which can provide micron-level detail observation and has the advantages of non-contact, non-invasive and fast imaging. However, OCT imaging also faces many challenges. For example, the presence of speckle noise will affect image quality, reduce contrast, and limit the accuracy of quantitative analysis.

[0003] Speckle noise is mainly caused by random scattering of tiny structures inside the sample. When a coherent light beam is irradiated onto the sample, the irregular structure inside the sample causes light scattering, generating different coherent light signals, which are superimposed on the detector to form a random interference pattern, thus appearing as speckle noise in the image. Speckle noise has a significant impact on the image, specifically by reducing image contrast, interfering with the recognition of target structure details, affecting the accuracy of quantitative data extracted from the image, and increasing the risk of misjudgment in medical diagnosis.

[0004] Optical chopper is a key device for beam modulation and is widely used in lasers, spectrometers, photoelectric detection systems and other fields. Its basic principle includes periodically modulating the light beam by mechanical or acousto-optic means to generate a pulsed light beam or an AC signal. Optical choppers have many important functions in optical systems, such as beam modulation, signal enhancement, synchronous detection and light source control, which can effectively improve the signal-to-noise ratio and measurement accuracy of the system. In terms of application, optical choppers are widely used in laser modulation, spectral measurement, biomedical imaging and photoelectric detection. As an indispensable part of modern optical technology, the application of optical choppers has significantly improved the performance and reliability of various optical systems.

[0005] In OCT systems, optical choppers can be used to modulate the sample light beam in order to effectively regulate and reduce 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 the speckle noise and weakening the formation of speckles. This method not only helps to improve the contrast and clarity of OCT images, but also achieves higher quality real-time imaging without sacrificing spatial resolution.

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

[0007] The object of the present 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] In order to solve the above technical problems, the present invention provides an endoscopic device capable of eliminating OCT speckle noise in real time, the endoscopic device comprising an OCT imaging system and an endoscopic probe; the endoscopic probe is driven by a stepper drive assembly, the OCT imaging system comprises an OCT imaging catheter and an optical chopper disposed in the OCT imaging catheter;

[0009] The OCT imaging catheter is provided with a single-mode optical fiber, the single-mode optical fiber is connected to a self-focusing lens through a sleeve, and the optical chopper is arranged behind the self-focusing lens;

[0010] A rotating device is connected to the optical chopper, and micro-reflection prisms are staggered behind the optical chopper to avoid light beam obstruction; after the light beam of the single-mode optical fiber passes through the self-focusing lens, it is modulated by the optical chopper and then deflected to the area to be detected through the micro-reflection prism.

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

[0012] The grid structure of the optical chopper has a rhombus shape of 0.01 mm×0.01 mm.

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

[0014] In a preferred embodiment, the OCT imaging catheter comprises a rigid shell, and a first opening and a second opening are formed at a front end of the rigid shell;

[0015] The first opening is used for focusing the light beam and receiving the light scattering signal; the second opening is used for placing the micro-horse.

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

[0017] In a preferred embodiment, the OCT imaging catheter further comprises a hose sheath, which encapsulates the entire OCT imaging catheter.

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

[0019] In a preferred embodiment, the stepping drive assembly includes a stepping motor, a synchronous rotating motor, a synchronous belt and a photoelectric slip ring;

[0020] The synchronous rotating motor is connected to a synchronous belt, and the stepping motor drives the synchronous rotating motor to rotate through the synchronous belt.

[0021] In a preferred embodiment, the optoelectronic slip ring adopts a rotary optoelectronic 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 is realized by setting a special chopper to change the spatial distribution of the sample beam. This technique significantly improves the image quality without reducing the spatial resolution. Its low cost, simple structure and compact integration provide important advantages for the design of endoscope probes in clinical applications.

[0024] 2. By setting staggered optical choppers and micro-reflection prisms, the optical chopper can rotate, and the light beam entering the imaging unit is periodically modulated to effectively suppress the formation of speckle noise, significantly improve the contrast and clarity of the image, thereby providing doctors with more accurate diagnostic basis, and is suitable for a variety of medical imaging applications. BRIEF DESCRIPTION OF THE DRAWINGS

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

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

[0027] Figure 3 A schematic diagram of an optical chopper of an endoscope device in a preferred embodiment of the present invention;

[0028] Figure 4 Schematic diagram of a stepping device of an endoscope device in a preferred embodiment of the present invention.

[0029] Explanation of the accompanying drawings: 01, fixed position; 02, rigid shell; 03, first opening; 04, second opening; 05, positive line; 06, negative line; 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, stepping motor; 22, synchronous rotating motor; 23, synchronous belt; 24, photoelectric slip ring. DETAILED DESCRIPTION

[0030] The technical solutions in the embodiments of the present invention will be clearly and completely described below in conjunction with the drawings in the embodiments of the present invention; it is obvious that the described embodiments are only part of the embodiments of the present invention, rather than all the embodiments, and all other embodiments obtained by ordinary technicians in this field based on the embodiments of the present invention without making creative work are within the scope of protection of the present invention.

[0031] In the description of the present invention, it should be noted that the terms "upper", "lower", "inner", "outer", "top / bottom" and the like indicate positions or positional relationships based on the positions or positional relationships shown in the drawings, and are only for the convenience of describing the present invention and simplifying the description, rather than indicating or implying that the device or element referred to must have a specific position, be constructed and operated in a specific position, and therefore cannot be understood as limiting the present invention. In addition, the terms "first" and "second" are used for descriptive purposes only and cannot be understood as indicating or implying relative importance.

[0032] In the description of the present invention, it should be noted that, unless otherwise clearly stipulated and limited, the terms "installed", "provided with", "mounted / connected", "connected", etc. should be understood in a broad sense. 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 the internal connection of two components. For ordinary technicians in this field, the specific meanings of the above terms in the present invention can be understood according to specific circumstances.

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

[0034] like Figure 1, the OCT imaging catheter is composed of fine optical elements. The imaging catheter includes a plurality of key components, which are connected in sequence in a specific order to ensure stable transmission and precise imaging of optical signals during the imaging process. Specifically, a single-mode optical fiber 16 is first configured inside the catheter to transmit a coherent light beam from a light source. The single-mode optical fiber 16 has a high light transmission efficiency and can effectively transmit the light signal to the target area. The single-mode optical fiber 16 is connected to the self-focusing lens 13 through the sleeve 14. The use of the self-focusing lens 13 greatly improves the resolution of the light beam, enabling the OCT imaging system to capture tiny structural details inside the tissue.

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

[0036] like Figure 3 , the optical chopper 07 adopts a specially designed optical chopper 07. The optical chopper 07 is a circular metal mesh with a thickness of about 0.6 mm and a diameter of 6 mm, and its mesh structure presents a rhombus shape of 0.01×0.01 mm. The diameter of the sample beam passing through the chopper is about 0.1 mm. Regardless of the incident angle of the sample beam, the optical chopper 07 will always partially block the sample beam. When the optical chopper 07 rotates at a uniform speed, it will continuously change the spatial distribution of the light beam passing through the self-focusing lens 13 and entering the sample. This modulation process causes the amplitude of the backscattered light of the scatterer in each resolvable volume element inside the sample to change, so that the speckle pattern changes randomly and continuously. Finally, by averaging these images with different speckle patterns, an image with significantly suppressed speckle noise can be obtained, thereby improving the clarity and contrast of OCT imaging and improving the diagnostic accuracy of endoscopic devices in clinical applications.

[0037] A rotating device for driving the optical chopper 07 to rotate at a constant speed is arranged in the OCT imaging catheter. The rotating device is a micro motor 17. A circular hole is arranged in the middle of the chopper, and the circular hole is adapted to the rotating motor shaft of the micro motor 17. The micro motor 17 can drive the chopper fixed thereon to rotate at a high speed through precise control.

[0038] A micro-reflection prism 11 is arranged behind the optical chopper 07. After the light beam of the single-mode optical fiber 16 passes through the self-focusing lens 13, it is modulated by the optical chopper 07 and then deflected to the detection area 12 through the micro-reflection prism 11. The micro-motor 17 drives the optical chopper 07 to rotate 360° once to obtain a frame of image. The endoscope probe is stepped with an accuracy of 50um through a customized stepping drive component to obtain a three-dimensional raw data group consisting of a settable step x distance and N frames of high-resolution images; the rotation of the optical chopper 07 can realize multi-angle reflection of the light beam, thereby covering a wider imaging range and improving the overall quality of the image.

[0039] like Figure 2 In the design of the endoscope device, in order to avoid the light beam being blocked during transmission, a structural layout in which the optical chopper 07 and the micro-reflection prism 11 are staggered is specially adopted. The positions of the optical chopper 07 and the micro-reflection prism 11 are precisely calculated and optimized, so that the light beam falls on the center of the micro-reflection prism after passing through two-thirds of the distance from the center of the optical chopper 07. This structural design fully considers the synergy between the various optical components, so that the two will not interfere with the propagation path of the light beam when working, ensuring the smooth transmission of the light beam during the imaging process.

[0040] The OCT imaging catheter includes a rigid shell 02, which is not only used to protect the end portion of the catheter, but also ensures the stability of the endoscope probe when it contacts the tissue. The design of the rigid shell 02 takes into account the compatibility with human tissue, which can effectively reduce the damage to the tissue during clinical operation, and at the same time provides a solid platform to support the operation of the entire catheter.

[0041] A first opening 03 and a second opening 04 are provided at the front end of the rigid shell 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 the light scattering signal. The second opening 04 is used for placing the micro motor 17. The micro motor 17 includes a positive line 0505 and a negative line 0606 for power supply. A fixed position 01 is provided at the rear end of the rigid shell 02. The fixed position 01 is used to fix the micro reflective prism 11. The micro reflective prism 11 is fixed by 9005 epoxy resin AB glue. A third opening 15 is provided at the upper part of the rigid shell 02. The third opening 15 is used to observe the distance between the sleeve 14 and the self-focusing lens 13.

[0042] In order to protect the optical fiber and other optical components, the OCT imaging catheter also includes a hose sheath, which is used to encapsulate the entire catheter, provide necessary mechanical protection, and maintain the stability of the catheter. The sheath material is soft, but has sufficient strength to resist the influence of the external environment. At the same time, the high light transmittance will not have an adverse effect on light transmission, and protect the optical components inside the probe from being contaminated by mucus, resulting in a decrease in imaging quality. To facilitate the insertion or withdrawal of the catheter, food-grade white oil can be added between the hose sheath and the catheter for lubrication to prevent adhesion.

[0043] Overall, the OCT imaging catheter can achieve efficient and precise tissue imaging through carefully designed optical and mechanical components, providing reliable image support for clinical diagnosis.

[0044] After general anesthesia is induced, the imaging process acquires information about the target tissue under the guidance of an existing endoscope, and the distance of the three-dimensional imaging can be acquired by setting the parameters of the stepper device. This embodiment involves a stepper drive assembly for endoscopic OCT three-dimensional imaging. The stepper drive assembly achieves precise positioning and efficient scanning of the imaging probe through precise mechanical design and motor control, providing important support for obtaining high-quality three-dimensional images. The following is a detailed description of the stepper drive assembly:

[0045] like Figure 4 The stepping drive assembly includes a stepping motor 21, a synchronous rotating motor 22, a synchronous belt 23 and a photoelectric slip ring 24. These components cooperate with each other to form a highly integrated drive system, so that the imaging probe can perform multi-angle and multi-directional scanning actions under precise control, thereby generating a three-dimensional tissue image.

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

[0047] The photoelectric slip ring 24 adopts a rotary photoelectric coupling method, which can seamlessly transmit electrical signals and optical signals during the rotation process to achieve efficient photoelectric conversion. This design ensures that the imaging probe will not cause signal distortion or quality degradation due to rotation during the scanning process, thereby ensuring the accuracy and reliability of three-dimensional imaging.

[0048] The synchronous rotating motor 22 is connected to the synchronous belt 23, and the stepping motor 21 drives the synchronous rotating motor 22 to rotate through the synchronous belt 23. A transmission mechanism in the stepping drive assembly is formed. The synchronous rotating motor 22 drives the synchronous wheel to drive the synchronous belt 23 through precise stepping control, so that the imaging probe moves smoothly and accurately on the specified path. The selection and design of the synchronous belt 23 take into account its durability and transmission efficiency, and can maintain 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 rotating motor 22. The stepper drive assembly receives instructions from the control system to adjust the motor 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 on a complex three-dimensional path, thereby obtaining high-resolution tissue images.

[0050] Through the coordinated work of the above components, the stepper drive assembly can provide highly stable scanning motion in endoscopic OCT three-dimensional imaging. This stepper drive assembly not only improves the spatial resolution of the image, but also ensures reliability and stability during long-term work. The design of this stepper drive assembly also makes the maintenance and upgrade of the system simpler and more efficient, and is suitable for a variety of complex clinical imaging needs.

[0051] The above is only a preferred specific implementation of the present invention, but the design concept of the present invention is not limited to this. Any technician familiar with the technical field who uses this concept to make non-substantial changes to the present invention within the technical scope disclosed by the present invention shall be deemed to infringe the protection scope of the present invention.

Claims

1. An endoscope device capable of eliminating OCT speckle noise in real time, characterized in that: The endoscope device comprises an OCT imaging system and an endoscope probe; the endoscope probe is driven by a stepper drive assembly, and the OCT imaging system comprises an OCT imaging catheter and an optical chopper arranged in the OCT imaging catheter; The OCT imaging catheter is provided with a single-mode optical fiber, the single-mode optical fiber is connected to a self-focusing lens through a sleeve, and the optical chopper is arranged behind the self-focusing lens; A rotating device is connected to the optical chopper, and micro-reflection prisms are staggered behind the optical chopper; after the light beam of the single-mode optical fiber passes through the self-focusing lens, it is modulated by the optical chopper and then folded to the area to be detected through the micro-reflection prism.

2. The endoscopic device capable of eliminating OCT speckle noise in real time according to claim 1, characterized in that: The optical chopper is set to a circular metal mesh, the thickness of the optical chopper is set to 0.5mm-0.7mm, and the diameter is 6mm; The grid structure of the optical chopper has a rhombus shape of 0.01 mm×0.01 mm.

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

4. The endoscopic device capable of eliminating OCT speckle noise in real time according to claim 3, characterized in that: The OCT imaging catheter comprises a rigid shell, and a first opening and a second opening are formed at the front end of the rigid shell; The first opening is used for focusing the light beam and receiving the light scattering signal; the second opening is used for placing the micro-horse.

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

6. The endoscopic device capable of eliminating OCT speckle noise in real time according to claim 5, characterized in that: The OCT imaging catheter further comprises a hose sheath, which encapsulates the entire OCT imaging catheter.

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

8. The endoscopic device capable of eliminating OCT speckle noise in real time according to claim 1, characterized in that: The stepping drive assembly includes a stepping motor, a synchronous rotating motor, a synchronous belt and a photoelectric slip ring; The synchronous rotating motor is connected to a synchronous belt, and the stepping motor drives the synchronous rotating motor to rotate through the synchronous belt.

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

Images