CN117045204A - Wind-driven far-end lateral scanning device of optical endoscopic probe - Google Patents
Wind-driven far-end lateral scanning device of optical endoscopic probe Download PDFInfo
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- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
- A61B5/0062—Arrangements for scanning
- A61B5/0066—Optical coherence imaging
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
- A61B1/00002—Operational features of endoscopes
- A61B1/00004—Operational features of endoscopes characterised by electronic signal processing
- A61B1/00009—Operational features of endoscopes characterised by electronic signal processing of image signals during a use of endoscope
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
- A61B1/06—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor with illuminating arrangements
- A61B1/07—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor with illuminating arrangements using light-conductive means, e.g. optical fibres
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
- A61B5/0082—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes
- A61B5/0084—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes for introduction into the body, e.g. by catheters
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Abstract
The invention discloses an optical endoscopic probe wind-driven far-end lateral scanning device which comprises an air pump, a three-way valve, a catheter and an optical fiber microprobe, wherein the air pump is connected with the catheter through the three-way valve, the optical fiber microprobe passes through the three-way valve and enters the catheter, and the optical fiber microprobe is configured to rotate around the central axis of the catheter under the driving of air flow injected by the air pump at the tail end in the catheter, so that far-end lateral scanning is realized. Compared with the prior lateral scanning scheme driven by the near end and the far end, the invention adopts the far-end wind power driving, and is safer, more efficient and more stable; negative effects of non-uniform rotation distortion and wire shielding problems in the prior art on acquired images are avoided, and imaging quality is improved; the whole probe and the device have low cost, and can reduce the medical expense of patients; the volume is small, the operation is simple, and the operation burden of doctors is reduced.
Description
Technical Field
The invention relates to the technical field of photoelectric information, in particular to an optical endoscopic probe wind-driven far-end lateral scanning device.
Background
The optical endoscopic probe is used as a tool for in-situ optical imaging and treatment of internal organs, cavities or tissues of a human body, has multiple advantages of accuracy, real-time, miniaturization, no radiation, biocompatibility and the like, and plays a key role in medical diagnosis and treatment. Is commonly used for various imaging means such as optical coherence tomography (Optical Coherence Tomography, OCT), fluorescence, optoacoustic, multispectral and the like, and is helpful for providing accurate medical diagnosis and treatment guidance for doctors. In addition, the method can be used for precise treatment methods such as photo-thermal treatment, photodynamic treatment and the like, and can be used for treating lesions in a targeted manner.
The structure of the optical fiber endoscope probe mainly comprises an optical fiber waveguide for light beam transmission, a micro optical device for light beam focusing and deflection and a light beam scanning device for point-by-point scanning. The transmitted beam can be divided into a sideways scan and a forward scan, depending on the axial direction of the transmitted beam relative to the probe. Compared with forward scanning, lateral scanning through 360-degree circumferential rotation of the light beam is more suitable for imaging and treatment of lumen structures (such as blood vessels, airways, digestive tracts and the like). By matching with the axial position linear translation (pullback), three-dimensional scanning information can be obtained.
Typically, the beam rotating scanning device is placed outside the body, driven by a motor, and torque is transmitted to the distal end through a torque coil wrapped by an optical fiber waveguide to drive the probe to rotate laterally, which is called proximal scanning. Therefore, the design structure of the probe for proximal scanning is compact, so that the miniaturized probe can smoothly pass through a tiny cavity channel such as a coronary artery blood vessel. However, friction is generated between the rotating torque coil and the protective catheter, and part of loss in the torque transmission process causes non-uniform rotation disturbance of the acquired signals, so that artifacts are generated by image distortion. In order to suppress the influence of non-uniform rotation disturbance inherent to near-end scanning, with the development of micro-electromechanical system (Microelectromechanical Systems, MEMS) technology, researchers mount miniaturized motors at the end of an optical probe to drive micro-optical devices for beam deflection to realize far-end lateral scanning, thereby alleviating the disturbance of non-uniform rotation disturbance and greatly improving the rotation scanning speed (Optics Express 20.22 (2012): 24132-24138). However, the miniature motor has the disadvantages of high cost, complex probe design, large size compared with a near-end scanning probe, electric shock risk and the like, and limits the clinical application of the miniature motor. In addition, because the motor is arranged at the end part of the probe, the power supply lead shields the light beam transmission of a part of the area, so that a part of shadow area appears in the scanning area, and clinical imaging and treatment are affected.
In recent years, other solutions have been developed to replace the micro-motor drive to achieve distal lateral scanning. Pang et al (Biomedical Optics Express 6.6.6.6 (2015): 2231-2236) designed a magnetic drive based distal scanning probe. The small cylindrical magnet integrated with the right-angle prism is arranged at the tail end of the probe, and the generated external magnetic field drives the small magnet inside the probe to rotate, so that the light beam can realize lateral scanning on the blood vessel wall. The probe is small in size and low in cost, and the connection wire is not needed, so that the shielding of the visual field is avoided. The disadvantage is that the circumferential scanning speed is too slow, the required external magnetic field strength is limited by the distance between the magnet and the small magnet, the magnetic field is easily interfered by clinical environment, and the in-situ scanning is limited. Lu et al (Scientific Reports 8.1.8.1 (2018): 5150) developed a liquid-driven distal passive scanning optical probe. The right-angle prism is arranged on the micro propeller, the micro propeller is arranged at the tail end of the probe, and the micro propeller is driven to rotate by the kinetic energy of the fluid to realize the lateral circumference scanning of the light beam. The design cost is lower, the rotating speed is high, and electric scanning equipment is not needed. However, in the working process of adopting far-end liquid driving, liquid is required to be continuously discharged to the cavity channel at the end part of the probe, and the application range is limited. Flushing with saline, for example, in a blood vessel, can avoid imaging effects from blood, and is not applicable in other lumens, such as the airways.
Accordingly, those skilled in the art have focused their efforts on developing an optical endoscopic head wind-driven distal lateral scanning device that overcomes the problems of the prior art.
Disclosure of Invention
In view of the above-mentioned drawbacks of the prior art, the technical problems to be solved by the present invention are:
for the proximal drive lateral scanning scheme: the external motor drives the whole endoscopic probe to rotate, and the image distortion is caused by non-uniform rotation distortion due to friction force and torque transmission loss, and in addition, the rotation scanning speed is limited.
For a distal drive lateral scanning scheme: (1) the remote miniature motor is adopted for driving: the miniature motor has the disadvantages of high cost, complex probe design, large size compared with a near-end scanning probe, electric shock risk and the like, and the clinical application of the miniature motor is limited. In addition, because the motor is arranged at the end part of the probe, the power supply lead shields the light beam transmission of a part of the area, so that a part of shadow area appears in the scanning area, and clinical imaging and treatment are affected. (2) The remote magnetic drive is adopted: the circumferential scanning speed is too slow, the required external magnetic field intensity is limited by the distance between the magnetic field and the small magnet, the magnetic field is easily interfered by clinical environment, and in-situ in-vivo scanning is limited. (3) Using a remote fluid drive: in the working process, liquid is required to be continuously discharged to the cavity at the end part of the probe, and the application range is limited, for example, the liquid can not be used in the air passage.
In order to achieve the above purpose, the invention provides an optical endoscopic probe wind-driven distal lateral scanning device, which comprises an air pump, a three-way valve, a catheter and an optical fiber micro probe, wherein the air pump is connected with the catheter through the three-way valve, the optical fiber micro probe penetrates through the three-way valve to enter the catheter, and the optical fiber micro probe is configured to rotate around the central axis of the catheter at the tail end in the catheter by the air flow injected by the air pump, so as to realize distal lateral scanning.
Further, the catheter comprises an inner catheter and an outer catheter, the three-way valve is provided with a first hole, a second hole and a third hole, the first hole and the second hole are oppositely arranged, a channel formed by the first hole and the second hole is obliquely arranged, the air pump outlet is connected with the first hole, the second hole is connected with the inner catheter, the inner catheter is inserted into the outer catheter and is sealed and fixed at the intersection of the tail ends of the inner catheter and the outer catheter, the side wall of the tail end of the inner catheter is provided with a plurality of exhaust holes, and the optical fiber microprobe penetrates through the third hole and enters the inner catheter.
Further, the optical fiber microprobe comprises an optical fiber connector, an optical fiber, a protective sleeve, an optical beam expanding element, an optical focusing element, an optical reflecting element, a micro turbine, a T-shaped cylinder and a limiting part, wherein the optical fiber penetrates through the third hole to enter the inner catheter, one end of the optical fiber is connected with a light source through the optical fiber connector, the other end of the optical fiber in the inner catheter is connected with one end of the protective sleeve, the other end of the optical fiber is connected with the optical beam expanding element and the optical focusing element, the other end of the protective sleeve is connected with the limiting part, one side of the limiting part is connected with the T-shaped cylinder and the optical reflecting element, the optical reflecting element and the optical focusing element are oppositely arranged, and the other side of the limiting part is connected with the micro turbine.
Further, the T-shaped cylinder is fixedly connected with the light reflecting element at the center of the large-diameter end, and the T-shaped cylinder is fixedly connected with the center of the micro turbine after penetrating into the limiting part matched with the small-diameter end in size.
Further, the dimensions of the protective sleeve, the inner conduit and the outer conduit are designed to ensure that a certain clearance exists between the inner conduit and the protective sleeve and between the inner conduit and the outer conduit to allow normal flow of gas.
Further, the diameter of the micro turbine is larger than the outer diameter of the protective sleeve and smaller than the inner diameter of the inner conduit, so that the micro turbine can be driven to rotate when gas flows through the micro turbine.
Further, the inner diameter of the limiting part is consistent with the small diameter end of the T-shaped cylinder, and the outer diameter of the limiting part is consistent with the inner diameter of the protection sleeve.
Further, the inner diameter of the protective sleeve is larger than or equal to the maximum diameter of the optical fiber, the optical beam expanding element and the optical focusing element, so that the optical fiber, the optical beam expanding element and the optical focusing element can normally enter the protective sleeve and keep coaxial with the protective sleeve.
Further, the optical fiber end, the light beam expanding element, the light focusing element, the light reflecting element, the T-shaped cylinder, the limiting component and the micro turbine are coaxial in the protective sleeve and simultaneously coaxial with the protective sleeve shaft so as to enable the light beam to be transmitted to the side direction correctly.
Further, when the optical fiber micro probe works, the air pump continuously injects air in the inner guide pipe at a constant speed, generates air flow at a constant speed, passes through the inner guide pipe, drives the micro turbine at the tail end of the optical fiber micro probe in the inner guide pipe to rotate, drives the light reflecting element to coaxially and synchronously rotate, and the light beam penetrates through the protective sleeve, the inner guide pipe and the outer guide pipe through focusing and deflection and is emitted to the inner wall of a target to realize lateral uniform speed rotation scanning, and the air flowing through the micro turbine reaches a gap between the inner guide pipe and the outer guide pipe through the exhaust hole at the tail end of the inner guide pipe to be finally and safely discharged.
Compared with the prior art, the invention has the following advantages:
(1) The invention adopts the far-end wind power driving, and compared with the prior near-end and far-end driving lateral scanning scheme, the invention is safer, more efficient and more stable.
(2) The negative influence of the non-uniform rotation distortion and the wire shielding problem in the prior art on the acquired image is avoided, and the imaging quality is improved.
(3) The whole probe and the device have low cost, and can reduce the medical expense of patients; the volume is small, the operation is simple, and the operation burden of doctors is reduced.
The conception, specific structure, and technical effects of the present invention will be further described with reference to the accompanying drawings to fully understand the objects, features, and effects of the present invention.
Drawings
FIG. 1 is a schematic diagram of a preferred embodiment of the present invention;
FIG. 2 is a three-dimensional block diagram of the light reflecting element, T-cylinder, spacing member, micro turbine section of a preferred embodiment of the present invention;
FIG. 3 is a two-dimensional side view of a light reflecting element, T-cylinder, stop member, micro turbine section of a preferred embodiment of the present invention.
The device comprises a 1-air pump, a 2-optical fiber connector, a 3-three-way valve, a 4-optical fiber, a 5-inner conduit, a 6-outer conduit, a 7-light beam expanding element, an 8-light focusing element, a 9-light reflecting element, a 10-limiting component, an 11-inner conduit air hole, a 12-protective sleeve, a 13-T-shaped cylinder and a 14-micro turbine.
Detailed Description
The following description of the preferred embodiments of the present invention refers to the accompanying drawings, which make the technical contents thereof more clear and easier to understand. The present invention may be embodied in many different forms of embodiments and the scope of the present invention is not limited to only the embodiments described herein.
In the drawings, like structural elements are referred to by like reference numerals and components having similar structure or function are referred to by like reference numerals. The dimensions and thickness of each component shown in the drawings are arbitrarily shown, and the present invention is not limited to the dimensions and thickness of each component. The thickness of the components is exaggerated in some places in the drawings for clarity of illustration.
Examples
As shown in fig. 1-3, the present embodiment provides an optical endo-probe wind-driven distal side scanning device, which comprises an air pump 1, an optical fiber connector 2, a three-way valve 3, an optical fiber 4, an inner catheter 5, an outer catheter 6, a light beam expanding element 7, a light focusing element 8, a light reflecting element 9, a limiting component 10, an inner catheter air hole 11, a protective sleeve 12, a t-shaped cylinder 13 and a micro turbine 14.
The connection relation of the components is as follows:
the air pump 1 and the inner conduit 5 are respectively connected with two holes of the three-way valve 3, the optical fiber 4 enters the inner conduit 5 from the third hole of the three-way valve 3, and the inner conduit 5 is inserted into the outer conduit 6 and is sealed and fixed at the intersection of the tail ends of the two. The optical fiber 4 is connected with a light source at one end outside the catheter by an optical fiber connector 2. The end of the optical fiber 4 in the inner guide pipe 5 is connected with a protective sleeve 12, light beams in the protective sleeve 12 are emitted from the end part of the optical fiber 4, transmitted to a light reflecting element 9 fixed with a micro turbine 14 and a T-shaped cylinder 13 through a light beam expanding element 7 and a light focusing element 8, and the focused light is emitted to the inner wall of a target through an inclined reflecting surface of 90 degrees.
When in operation, the air pump 1 continuously injects air into the inner guide pipe 5 at a constant speed, a wind (air flow) with a constant flow rate is formed in the inner guide pipe 5, passes through the micro turbine 14 at the tail end of the optical fiber micro probe, drives the micro turbine 14 and the light reflecting element 9 to rotate together at a constant speed, and realizes the lateral uniform speed 360-degree scanning of the focused light beam on the inner wall of the target. The air flow passing through the microturbine 14 enters the gap between the inner conduit 5 and the outer conduit 6 through a stack of exhaust holes 11 at the end of the inner conduit 5 and finally exits at the end of the outer conduit 6 near the three-way valve 3. The direction of the air flow is shown by the dashed arrow.
The T-shaped cylinder 13 is fixed with glue to the light reflecting element 9 at the center of the large diameter end. The T-shaped cylinder 13 penetrates into the limit part 10 matched with the small diameter end in size and then is fixed with the center of the micro turbine 14 by glue. In this way it is achieved that the light-reflecting element 9 rotates coaxially with the microturbine 14 within the protective sleeve 12.
The protecting sleeve 12, the inner conduit 5 and the outer conduit 6 should be selected to have proper dimensions, so that a certain clearance exists between the inner conduit 5 and the protecting sleeve 12 and between the inner conduit 5 and the outer conduit 6 to allow the normal flow of gas. The inner conduit 5 is provided with a sufficient size and number of air holes 11 at its end to allow the internal air to escape between the inner conduit 5 and the outer conduit 6.
The micro turbine 14 is intended to convert the kinetic energy of the gas into rotational kinetic energy of the gas itself, driving the light reflecting element 9 to rotate coaxially and synchronously. The diameter of the micro turbine 14 is larger than the outer diameter of the protective sleeve 12 and smaller than the inner diameter of the inner conduit 5, so that the micro turbine 14 can be driven to rotate when air flows through the inner conduit.
The inner diameter of the limiting member 10 should be equal to or slightly larger than the small diameter end of the T-shaped cylinder 13 to ensure penetration. The outer diameter of the limiting member 10 should be equal to or slightly smaller than the inner diameter of the protective sleeve 12, and the outer side of the limiting member 10 and the inner side of the protective sleeve 12 are fixed by glue.
The inner diameter of the protective sleeve 12 is larger than or equal to the maximum diameter of the optical fiber 4, the light beam expanding element 7 and the light focusing element 8, and the end of the optical fiber 4 and the end of the protective sleeve 12 are fixed by glue so as to ensure that the three can normally enter the protective sleeve 12 and keep coaxial with the protective sleeve 12.
The intersection of the tail ends of the inner guide pipe 5 and the outer guide pipe 6 is sealed and fixed by glue, so that the isolation between the inside of the guide pipe and the target cavity is ensured.
The end of the optical fiber 4, the light beam expanding element 7, the light focusing element 8, the light reflecting element 9, the T-shaped cylinder 13, the limiting component 10 and the micro turbine 14 are coaxial in the protective sleeve 12, and are coaxial with the protective sleeve 12 at the same time, so that the light beam is correctly transmitted laterally.
The micro turbine 14 can be designed into different appearance structures, and can rotate at a high speed under reasonable airflow driving. Suitable materials (specifically, resins, glass, plastics, etc.) and processing modes (specifically, 3D printing additive processing, multiphoton micro-nano processing based on femtosecond laser, etc.) are selected according to the design dimensions of the microturbine 14.
The protective sleeve 12 is intended to protect the probe tip from contamination and damage, and is made of a material having a certain transparency, such as quartz, an optically transparent polymer, or the like, in consideration of light beam propagation.
The optical fiber 4 may employ various types of optical fibers, such as a single mode optical fiber, a multimode optical fiber, a double clad optical fiber, a photonic crystal optical fiber, a fluoride optical fiber, and the like, depending on the characteristics and use of the transmitted light.
The light beam expander 7 is used to expand the angle of the light beam emitted from the optical fiber, and may be specifically a coreless optical fiber with a suitable refractive index, a solid glass rod, or the like.
The light focusing element 8 focuses the light beam to achieve high resolution imaging or accurate treatment positioning, and may specifically be a microlens, graded index lens (or optical fiber), ball lens, or the like.
The light reflecting element 9 deflects the light by 90 ° (from forward to sideways propagation), and may be embodied by a reflecting prism coated with a metal or dielectric reflecting film, an optical fiber inclined reflecting surface, or the like.
Compared with various problems caused by the prior near-end and far-end driving lateral scanning schemes, the invention adopts a far-end wind power driving lateral rotation scanning mode, and can make up the defects of the prior art.
The invention adopts an air pump to continuously inject air at a constant speed in the inner guide pipe, generates wind (air flow) at a constant speed, passes through the inner guide pipe, drives the micro turbine element positioned at the tail end of the inner probe of the inner guide pipe to rotate, is rigidly fixed between the micro turbine and the light reflecting element, and the rotating micro turbine drives the light reflecting element to coaxially and synchronously rotate, so that light beams penetrate through the protective sleeve and the inner guide pipe and the outer guide pipe through focusing and deflection, and are emitted to the wall of a cavity to realize lateral uniform rotation scanning. Air flowing through the turbine reaches the gap between the inner conduit and the outer conduit through the air holes at the end part of the inner conduit and is finally and safely discharged. Compared with other technical schemes, the wind power driving device has no risk factors such as electric shock, magnetic field interference, liquid injection and the like, and the use safety of patients is improved. In addition, stable high-speed rotation can be realized through accurate control of wind speed.
The invention does not adopt a near-end beam rotary scanning motor device, does not need a torque coil to wrap an optical fiber to transmit torque so as to enable the probe to laterally rotate, and does not have non-uniform rotation distortion; the light reflecting element used for deflecting the light beam and arranged at the tail end of the probe is not driven by a micro motor, so that the shielding of the view of a wire supplied by the motor is avoided.
The main micro turbine structure of the invention has small size and simple design, can be obtained by using the existing mature micro processing technology, and has low processing and assembling cost. In the application process, the probe can be driven to rotate laterally only by setting constant air flow speed by an air pump and injecting air into the inner sleeve, the operation process is relatively simple, and an additional motor and an electromagnetic device are not required to be configured.
The foregoing describes in detail preferred embodiments of the present invention. It should be understood that numerous modifications and variations can be made in accordance with the concepts of the invention without requiring creative effort by one of ordinary skill in the art. Therefore, all technical solutions which can be obtained by logic analysis, reasoning or limited experiments based on the prior art by the person skilled in the art according to the inventive concept shall be within the scope of protection defined by the claims.
Claims (10)
1. The wind-driven far-end lateral scanning device for the optical endoscopic probe is characterized by comprising an air pump, a three-way valve, a catheter and an optical fiber microprobe, wherein the air pump is connected with the catheter through the three-way valve, the optical fiber microprobe penetrates through the three-way valve and enters the catheter, and the optical fiber microprobe is configured to rotate around the central axis of the catheter at the tail end in the catheter by the air flow injected by the air pump, so that the far-end lateral scanning is realized.
2. The optical endo-probe wind-driven distal side scanning device according to claim 1, wherein the catheter comprises an inner catheter and an outer catheter, the three-way valve is provided with a first hole, a second hole and a third hole, the first hole and the second hole are oppositely arranged, the channel formed by the first hole and the second hole is obliquely arranged, the air pump outlet is connected with the first hole, the second hole is connected with the inner catheter, the inner catheter is inserted into the outer catheter and is sealed and fixed at the intersection of the tail ends of the inner catheter, a plurality of exhaust holes are formed in the side wall of the tail end of the inner catheter, and the optical fiber microprobe passes through the third hole and enters the inner catheter.
3. The optical endo-probe wind-driven distal side scanning device according to claim 2, wherein the optical fiber micro-probe comprises an optical fiber connector, an optical fiber, a protective sleeve, an optical beam expanding element, an optical focusing element, an optical reflecting element, a micro turbine, a T-shaped cylinder and a limiting component, wherein the optical fiber penetrates through the third hole to enter the inner catheter, one end of the optical fiber is connected with a light source through the optical fiber connector, the other end of the optical fiber in the inner catheter is connected with one end of the protective sleeve, the other end of the optical fiber is connected with the optical beam expanding element and the optical focusing element, the other end of the protective sleeve is connected with the limiting component, one side of the limiting component is connected with the T-shaped cylinder and the optical reflecting element, the optical reflecting element and the optical focusing element are oppositely arranged, and the other side of the limiting component is connected with the micro turbine.
4. The optical endo-endoscopic head wind driven distal side scanning device according to claim 3, wherein said T-shaped cylinder is fixedly connected to said light reflecting element at the center of the large diameter end, said T-shaped cylinder being fixedly connected to the center of said micro turbine after the small diameter end penetrates into said limiting member matching the size thereof.
5. The optical endo-endoscopic wind powered distal side scanning device according to claim 3, wherein said protective sleeve, inner conduit, outer conduit are sized to ensure that there is a gap between said inner conduit and protective sleeve, between said inner conduit and outer conduit allowing normal gas flow.
6. The optical endo-probe wind driven distal side scanning device according to claim 3, wherein said microturbine has a diameter greater than an outer diameter of said protective sleeve and less than an inner diameter of said inner conduit to ensure that gas flow therethrough causes said microturbine to rotate.
7. The optical endo-endoscopic head wind driven distal side scanning device according to claim 4, wherein said limiting member has an inner diameter corresponding to the small diameter end of said T-shaped cylinder and an outer diameter corresponding to the inner diameter of said protective sleeve.
8. The optical endo-endoscopic head wind driven distal side scanning device according to claim 3, wherein said protective sleeve has an inner diameter greater than or equal to the largest diameter of said optical fiber, light beam expanding element and light focusing element to ensure that said optical fiber, light beam expanding element and light focusing element can normally enter said protective sleeve and remain coaxial with said protective sleeve.
9. The optical endo-probe wind driven distal side scanning device according to claim 3, wherein said fiber tip, light expanding element, light focusing element, light reflecting element, T-cylinder, stop member, micro turbine remain coaxial within said protective sleeve and simultaneously with said protective sleeve axis for proper lateral propagation of the light beam.
10. The wind-driven far-end lateral scanning device of the optical endoscopic probe according to claim 4, wherein in operation, the air pump continuously injects air in the inner conduit at a constant speed, generates air flow with a constant speed through the inner conduit, drives the micro turbine at the tail end of the optical fiber micro probe in the inner conduit to rotate, drives the light reflecting element to coaxially and synchronously rotate, and the light beam passes through the protective sleeve, the inner conduit and the outer conduit through focusing and deflection and is emitted to the inner wall of a target to realize lateral uniform speed rotation scanning, and the air flowing through the micro turbine reaches a gap between the inner conduit and the outer conduit through the exhaust hole at the tail end of the inner conduit to be finally and safely discharged.
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| CN202311254019.4A CN117045204A (en) | 2023-09-26 | 2023-09-26 | Wind-driven far-end lateral scanning device of optical endoscopic probe |
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| CN202311254019.4A CN117045204A (en) | 2023-09-26 | 2023-09-26 | Wind-driven far-end lateral scanning device of optical endoscopic probe |
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Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1780584A (en) * | 2003-04-28 | 2006-05-31 | 德州系统大学董事会 | Catheter imaging probe and method |
| CN107854114A (en) * | 2017-10-12 | 2018-03-30 | 中国科学院上海光学精密机械研究所 | Passive drive rotation sweep optic probe |
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Patent Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1780584A (en) * | 2003-04-28 | 2006-05-31 | 德州系统大学董事会 | Catheter imaging probe and method |
| CN107854114A (en) * | 2017-10-12 | 2018-03-30 | 中国科学院上海光学精密机械研究所 | Passive drive rotation sweep optic probe |
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