CN108670177B - Imaging probe of breast duct endoscope - Google Patents
Imaging probe of breast duct endoscope Download PDFInfo
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- CN108670177B CN108670177B CN201810524691.3A CN201810524691A CN108670177B CN 108670177 B CN108670177 B CN 108670177B CN 201810524691 A CN201810524691 A CN 201810524691A CN 108670177 B CN108670177 B CN 108670177B
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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
- A61B1/04—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 combined with photographic or television appliances
- A61B1/05—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 combined with photographic or television appliances characterised by the image sensor, e.g. camera, being in the distal end portion
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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
- A61B1/00064—Constructional details of the endoscope body
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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
- A61B1/00131—Accessories for endoscopes
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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
- A61B1/00163—Optical arrangements
- A61B1/00165—Optical arrangements with light-conductive means, e.g. fibre optics
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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
- A61B5/0033—Features or image-related aspects of imaging apparatus classified in A61B5/00, e.g. for MRI, optical tomography or impedance tomography apparatus; arrangements of imaging apparatus in a room
- A61B5/004—Features or image-related aspects of imaging apparatus classified in A61B5/00, e.g. for MRI, optical tomography or impedance tomography apparatus; arrangements of imaging apparatus in a room adapted for image acquisition of a particular organ or body part
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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
- A61B5/0091—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes for mammography
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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
- A61B5/0093—Detecting, measuring or recording by applying one single type of energy and measuring its conversion into another type of energy
- A61B5/0097—Detecting, measuring or recording by applying one single type of energy and measuring its conversion into another type of energy by applying acoustic waves and detecting light, i.e. acoustooptic measurements
Abstract
The invention provides a breast duct endoscope imaging probe.A pulse laser is coupled into one end of an excitation optical fiber, is focused and irradiated to a reflecting element at the other end of the excitation optical fiber through a collimation converging element and then reflected, is focused under the inner surface of an organism through a capsule, generates an ultrasonic signal due to an acousto-optic effect, and reflects the ultrasonic signal to an optical resonance element after being irradiated to the reflecting element through the capsule, so that the resonance frequency of the optical resonance element is changed; the detection light is coupled into one end of the receiving optical fiber, the other end of the receiving optical fiber is coupled into the optical resonance element, the detection light with the changed resonance frequency is reflected back from the receiving optical fiber, and three-dimensional imaging is carried out through the optical detector and the imaging unit. The invention has higher integration level and miniaturization of devices, realizes the full-light acousto-optic signal acquisition with low cost, miniaturization, optical transparency and high bandwidth, and greatly improves the prior clinical mastoscopy technology.
Description
Technical Field
The invention belongs to the technical field of endoscope imaging, and particularly relates to a breast duct endoscope imaging probe.
Background
Pathological nipple discharge is one of the common manifestations of breast lesions. Common causes include papillary tumors in the mammary duct, dilated mammary duct, breast cancer, plasma cell mastitis, etc. Before the invention and application of the breast endoscopy technology, the examination means including ultrasound, magnetic resonance, molybdenum target and the like can not obtain more accurate diagnosis results. The breast duct endoscope is an endoscope camera light source system, can be used for visually observing the appearance of pathological changes in the breast duct, can be used for carrying out focus biopsy and can also be used for carrying out lavage treatment of medicines. However, the existing breast duct endoscope has the following defects: first, the imaging depth of the breast tube scope is limited. The depth of the breast duct endoscope is limited by the diameter, length and bending degree of the endoscope body, and the breast duct at the end which is smaller than the diameter of the endoscope body can not be reached. Studies have shown that intramammary papillary tumors often occur in the epithelial cells and interstitium of the small and terminal ducts, which often do not dilate significantly, resulting in missed diagnosis. Secondly, the breast endoscopy can not scan lesion and surrounding tissues in the lesion in a multi-slice manner, and all levels of catheters need to be checked step by step, and only two-dimensional images can be obtained, so that the diagnosis information provided for clinicians is limited. Meanwhile, the examination has low diagnosis confirming efficiency, and the pain of the patient is great when the examination is used as invasive examination. Thirdly, the resolution of the mammoscope is limited, and the elasticity and the functional state of the focal tissue are not judged.
The acousto-optic endoscope is a novel hybrid imaging technology which can be used for combining optical imaging and ultrasonic imaging in a non-invasive hollow organ, is concerned by people in the fields of blood vessel and gastrointestinal diseases and the like, and mainly has the following advantages: firstly, the medicine is harmless to human body. Acousto-optic imaging does not generate any ionizing radiation, does not require the use of any biomarkers, and does not destroy or alter any tissue properties. Secondly, the imaging depth is deep, the contrast is strong and the resolution is high. The acousto-optic imaging utilizes the strong penetration characteristic of ultrasonic waves and the absorption difference of tissues to laser, and realizes the imaging with high resolution and high contrast at a deeper position of the tissues. And thirdly, the tissue function imaging capability is provided. Acousto-optic imaging can also measure the absorption coefficients of different parts of the tissue and correlate with corresponding molecular structures or physiological states, monitor the functional state of the tissue, such as hemoglobin content in blood vessels, oxygen metabolism, tumor progression, and the like.
The basic principle of the acousto-optic endoscope imaging technology mainly comprises three steps: firstly, pulse laser is irradiated to biological tissues through an optical element in a probe; secondly, the biological tissue body absorbs the pulse laser to generate heat, generates a photoacoustic effect and radiates ultrasonic waves outwards; thirdly, an ultrasonic detector in the probe receives ultrasonic waves, converts the ultrasonic waves into corresponding electric signals and transmits the electric signals to a computer, and an image is output by adopting an image reconstruction algorithm. The sensors and optics in the probe are therefore one of the core technologies for acousto-optic imaging. Most probes in the existing acousto-optic endoscope imaging system adopt an ultrasonic sensor based on piezoelectric sensing. Such sensors are typically bulky, miniaturized and then placed in an endoscopic probe resulting in limited sensitivity and detection bandwidth performance, and are not easily integrated into arrays of multiple sensors, thus limiting the resolution, signal-to-noise ratio, and speed of imaging, making such real-time high resolution imaging applications difficult to achieve. In addition, the optical opacity of the piezoelectric ultrasonic sensor increases the difficulty in designing the optical elements of the endoscope. To address this problem, various acousto-optic imaging probes have been proposed that incorporate more compact, higher resolution ultrasonic sensors. The goal of the use of acousto-optic imaging probes is to increase their resolution and miniaturization and to obtain higher quality images.
The current endoscope probe design based on the acousto-optic imaging technology mainly comprises the following two types:
the first design is shown in FIG. 1 and is from the document "A minor all-optical photosynthetically probing probe" Proc. of SPIE Vol.7899,78991F (2011). The acousto-optic endoscope imaging probe comprises: 1-1 casing, 1-2 single-mode optical fiber, 1-3 acousto-optic signal detection sensor and 1-4 capsule. One end of the single-mode optical fiber 1-2 is fixed in the sleeve 1-1, coupled with the excitation light source and can rotate around the optical fiber axis. The other end of the single-mode fiber 1-2 is polished to form a reflecting surface with an included angle of 45 degrees with the fiber axis and is arranged in the capsule 1-4. An acousto-optic signal detection sensor 1-3 based on the Fabry-Perot polymer film principle is prepared on a coating layer at the other end of the single-mode optical fiber 1-2 through a multilayer coating process, and air is filled in a capsule 1-4. When the probe works, an excitation light signal is coupled from one end of the single-mode optical fiber 1-2, total reflection is carried out on a 45-degree reflecting surface at the other end, a part of the excitation light signal after penetrating through the acousto-optic signal detection sensor 1-3 is focused at a certain point in biological tissues, and the other part of the excitation light signal is reflected back to enter the single-mode optical fiber 1-2 again. The point in the biological tissue absorbs the energy of the exciting light, generates an ultrasonic signal and radiates the ultrasonic signal to the acousto-optic signal detection sensor 1-3, the intensity or the phase of a reflected light signal is changed by changing the film shape, the reflected light signal is transmitted back to the computer, and image display is realized through an image reconstruction algorithm. This solution has three disadvantages: first, although the cylindrical fiber side wall can focus the excitation light in the direction perpendicular to the fiber axis, the excitation density is low, and therefore the required power consumption is large. Secondly, the ultrasonic signals do not have special convergence elements, so the collection efficiency is low and the signal loss is large. Thirdly, due to the low quality factor of the fabry-perot microcavity, the detection sensitivity of the acousto-optic signal is low, and the resolution of the image is limited.
The second design is shown in fig. 2 and is derived from the literature, "an intravascular imaging system and method", chinese patent CN 104545811B. The acousto-optic endoscope imaging probe comprises: the device comprises a multimode optical fiber 2-1, a flexible spring coil 2-2, a matching pipe 2-3, a converging element 2-4, a reflecting element 2-5, an ultrasonic transducer 2-6, a supporting element 2-7 and a protective sleeve 2-8. The matching tube 2-3, the converging element 2-4, the reflecting element 2-5, the ultrasonic transducer 2-6 and the support element 2-7 are arranged within a protective sleeve 2-8. One end of the flexible spring coil 2-2 is fixed on the inner wall of the protective sleeve 2-8, and the other end is connected with the excitation light source. One end of the multimode optical fiber 2-1 passes through the inside of the matching tube 2-3 and is fixed at one end of the converging element 2-4, and the reflecting element 2-5 is fixed between the other end of the converging element 2-4 and the ultrasonic transducer 2-6. The ultrasonic transducers 2-6 are arranged on the support elements 2-7. When the probe works, an excitation light signal is coupled from one end of the multimode optical fiber 2-1, converged by the converging element 2-4, reflected by the reflecting element 2-5 and focused at a certain point in the biological tissue. The point in the biological tissue absorbs the energy of the exciting light, generates an ultrasonic signal, is received by the ultrasonic transducers 2-6 and is transmitted back to the computer, and image display is realized through an image reconstruction algorithm. The disadvantage of this approach is that with ultrasonic transducers, the optics is opaque, resulting in a complex optical design, low integration, and limited resolution and signal-to-noise ratio by the volume of the piezoelectric material.
Disclosure of Invention
The technical problem to be solved by the invention is as follows: provided is a breast duct endoscope imaging probe which can simplify the optical design, and can make the device integration higher and miniaturized.
The technical scheme adopted by the invention for solving the technical problems is as follows: a breast duct endoscope imaging probe comprises an optical fiber, a collimation converging element, a reflecting element and a capsule, and is characterized in that: the optical fiber comprises an excitation optical fiber and a receiving optical fiber, and the probe also comprises an optical resonance element for changing the resonance frequency under the returned ultrasonic wave;
the position relation among the excitation optical fiber, the receiving optical fiber, the collimation converging element, the reflecting element, the capsule and the optical resonance element meets the following optical path: the pulse laser is coupled into one end of the excitation optical fiber, is focused and irradiated to the reflecting element at the other end of the excitation optical fiber through the collimation converging element and then is reflected, is focused below the inner surface of the organism through the capsule, generates an ultrasonic signal due to an acousto-optic effect, and reflects and focuses the reflected ultrasonic signal to the optical resonance element after being irradiated to the reflecting element through the capsule, so that the resonance frequency of the optical resonance element is changed; the detection light is coupled into one end of the receiving optical fiber, the other end of the receiving optical fiber is coupled into the optical resonance element, the detection light with the changed resonance frequency is reflected back from the receiving optical fiber, and three-dimensional imaging is carried out through the optical detector and the imaging unit.
According to the scheme, the excitation optical fiber, the receiving optical fiber, the collimation converging element, the reflecting element and the optical resonance element are all arranged in the capsule, and the excitation optical fiber and the receiving optical fiber are positioned on the same side of the reflecting element.
According to the scheme, the excitation optical fiber, the receiving optical fiber, the collimation converging element, the reflecting element and the optical resonance element form a whole body capable of rotating around the axial direction of the capsule.
According to the scheme, the optical resonance element comprises a planar integrated waveguide device with an elasto-optical effect, wherein the planar integrated waveguide device consists of a grating coupler, a connecting waveguide and a micro-ring resonant cavity; the planar integrated waveguide device is integrally manufactured on the end face of the receiving optical fiber, and the grating coupler is aligned with the core of the receiving optical fiber.
According to the scheme, the planar integrated waveguide device is made of polymer materials and is manufactured on the end face of the receiving optical fiber by adopting a semiconductor nano-imprinting process.
According to the scheme, two ends of the grating coupler are connected with the connecting waveguide end to end, a certain gap is formed between the micro-ring resonant cavity and the connecting waveguide, and the micro-ring resonant cavity is arranged right above the grating coupler.
According to the scheme, the reflecting element comprises 2 independent reflecting mirrors, wherein the first reflecting mirror is used for reflecting or converging the laser output by the collimation converging element, and the second reflecting mirror is used for reflecting or converging the reflected ultrasonic signals.
According to the scheme, the first reflecting mirror is provided with an optical reflecting surface, and the second reflecting mirror is provided with a stainless steel reflecting surface.
According to the scheme, the reflecting element comprises an independent reflecting mirror and an independent reflecting surface, wherein the reflecting surface is used for reflecting or converging the laser output by the collimation converging element, and the reflecting mirror is used for reflecting or converging the reflected ultrasonic signal.
According to the scheme, the reflecting surface is the end surface or the polished surface of the excitation optical fiber at a certain angle, and the reflecting mirror is provided with a stainless steel reflecting surface.
According to the scheme, the optical resonant element comprises an optical resonant cavity with a Fano resonance effect.
According to the scheme, the optical resonant cavity is a metal surface plasmon polariton photonic crystal or a reflection grating.
The invention has the beneficial effects that:
1. the endoscope adopts 2 optical fibers and two optical paths, adopts a compact and high-sensitivity optical resonance element, and utilizes the characteristic that the ultrasonic wave changes the resonance frequency of the optical resonance element, thereby realizing the acquisition of signals, having simple integral structure, simplifying optical design, having higher integration level and miniaturization of devices, realizing the full-light acousto-optic signal acquisition with low cost, miniaturization, optical transparency and high bandwidth, and greatly improving the existing clinical endoscope technology.
2. The optical resonance element is manufactured on one end face of the receiving optical fiber by adopting a semiconductor nano-imprinting process, and the fiber core of the receiving optical fiber is directly coupled with the optical resonance element through the grating coupler, so that the optical design difficulty and the optical coupling process cost in the probe are reduced.
3. Compared with the Fabry-Perot poly-film cavity in the prior art, the optical resonant element based on the micro-ring resonant cavity has higher quality factor, thus having higher detection sensitivity and image resolution. In addition, by optimizing the waveguide parameters in the optical resonance element, an optical Fano resonance effect can be generated, a steeper resonance spectral line is formed, and the detection sensitivity and the image resolution are further improved.
4. When the receiving optical fiber, the optical resonance element, the reflecting element, the collimation converging element and the light-emitting fiber rotate around the axis of the capsule at a high speed as a whole, the detection signal can scan the appearance of the inner wall of the biological tissue by 360 degrees, so that high-speed real-time imaging is realized.
Drawings
Fig. 1 is a schematic structural diagram of a first design of the prior art.
Fig. 2 is a schematic diagram of a second design of the prior art.
Fig. 3 is a schematic structural diagram according to an embodiment of the present invention.
Fig. 4 is a schematic structural diagram of an optical resonant element according to an embodiment of the present invention.
FIG. 5A is a resonance spectrum of a prior art optical resonator element.
FIG. 5B is a resonance spectrum diagram of an optical resonator element according to an embodiment of the invention.
Fig. 6 is a schematic structural diagram of another embodiment of the present invention.
Fig. 7 is a schematic structural diagram of another embodiment of the present invention.
In the figure: 1-1 parts of a sleeve, 1-2 parts of a single-mode fiber, 1-3 parts of an acoustic-optical signal detection sensor and 1-4 parts of a capsule;
the device comprises a multimode optical fiber 2-1, a flexible spring coil 2-2, a matching pipe 2-3, a converging element 2-4, a reflecting element 2-5, an ultrasonic transducer 2-6, a supporting element 2-7 and a protective sleeve 2-8;
a receiving optical fiber 10, an optical resonance element 20, a reflection element 30, a collimation convergence element 40, an excitation optical fiber 50, and a capsule 60; a micro-ring resonant cavity 21 connecting the waveguide 22 and the grating coupler 23; a first reflecting surface 31, a second reflecting surface 32, a first reflecting mirror 33, a second reflecting mirror 34, a third reflecting surface 35, and a third reflecting mirror 36.
Detailed Description
The invention is further illustrated by the following specific examples and figures.
The first embodiment is as follows:
the invention provides a breast duct endoscope imaging probe, based on the acousto-optic imaging principle, as shown in fig. 3, comprising an optical fiber, a collimation converging element 40, a reflecting element 30 and a capsule 60, wherein the optical fiber comprises an excitation optical fiber 50 and a receiving optical fiber 10, and the probe further comprises an optical resonance element 20 for changing the resonance frequency under the returned ultrasonic wave. The position relationship among the excitation fiber 50, the receiving fiber 10, the collimation converging element 40, the reflecting element 30, the capsule 60 and the optical resonant element 20 satisfies the following optical paths: the pulse laser is coupled into one end of the excitation fiber 50, is focused on and irradiated on the first reflecting surface 31 of the reflecting element 30 through the collimation converging element 40 at the other end of the excitation fiber 50, is reflected, is focused under the inner surface of a living body through the capsule 60, generates an ultrasonic signal due to an acousto-optic effect, and is reflected and focused to the optical resonance element 20 after being irradiated on the second reflecting surface 32 of the reflecting element 30 through the capsule 60, so that the resonance frequency of the optical resonance element 20 is changed; the detection light is coupled into one end of the receiving fiber 10, coupled into the optical resonance element 20 at the other end of the receiving fiber 10, and the detection light with the changed resonance frequency is reflected from the receiving fiber 10 and subjected to three-dimensional imaging through the optical detector and the imaging unit. The invention changes the detection principle of the probe only, and does not relate to the improvement of the imaging method, and the imaging method can adopt the image reconstruction algorithm in the prior art.
In this embodiment, the excitation fiber 50, the receiving fiber 10, the collimating and converging element 40, the reflecting element 30 and the optical resonant element 20 are all disposed in the capsule 60, and the excitation fiber 50 and the receiving fiber 10 are located on the same side of the reflecting element 30.
Further, the excitation fiber 50, the receiving fiber 10, the collimating and condensing element 40, the reflecting element 30 and the optical resonance element 20 form a whole body capable of rotating around the axial direction of the capsule 60. When the receiving optical fiber 10, the optical resonance element 20, the reflection element 30, the collimation convergence element 40 and the excitation optical fiber 50 rotate around the axis of the capsule 60 at a high speed as a whole, the detection signal can scan the appearance of the inner wall of the biological tissue by 360 degrees, thereby realizing high-speed real-time imaging.
Further, as shown in fig. 4, the optical resonant element 20 includes a planar integrated waveguide device with an elasto-optical effect, and the planar integrated waveguide device is composed of a grating coupler 23, a connecting waveguide 22 and a micro-ring resonant cavity 21; the planar integrated waveguide device is integrally manufactured on the end face of the receiving optical fiber 10, and the grating coupler 23 is aligned with the core of the receiving optical fiber 10. The planar integrated waveguide device is made of polymer material and is manufactured on the end face of the receiving optical fiber 10 by adopting a semiconductor nano-imprinting process. Two ends of the grating coupler 23 are connected with the connecting waveguide 22 end to end, a certain gap is arranged between the micro-ring resonant cavity 21 and the connecting waveguide 22, and the micro-ring resonant cavity 21 is arranged right above the grating coupler 23. When the probe light is coupled from the other end of the receiving fiber 10 into the connecting waveguide 22 and the micro-ring resonator 21 on the end face of the fiber through the grating coupler 23, the probe light is reflected back and coupled into the receiving fiber 10 again through the grating coupler 23. Compared with the Fabry-Perot poly-film cavity in the prior art, the optical resonant element 20 based on the micro-ring resonant cavity 21 has a higher quality factor, and therefore has higher detection sensitivity and image resolution. In addition, by optimizing the waveguide parameters in the optical resonance element 20, an optical fano resonance effect can be generated, a steeper resonance spectral line is formed, and the detection sensitivity and the image resolution are further improved.
Fig. 5A is a resonance line and a probe light wavelength of the optical resonance element of the related art, and fig. 5B is a resonance line of the optical resonance element of the present invention. The wavelength of the detected light in the prior art is lambda1The detection wavelength of the technology of the invention is lambda2. It can be seen from the figure that when the ultrasonic signal causes the resonance line of the optical resonance element to move the same distance, the resonance line of the micro-ring resonant cavity of the invention generated by the fanno resonance effect is steeper, so the detection light signal has larger change amplitude, and the detection sensitivity and the image resolution are higher.
Example two:
the principle and structure of the present embodiment are the same as those of the first embodiment, and the difference is that: as shown in fig. 6, the reflective element 30 includes 2 independent mirrors; the first reflecting mirror 33 is used for reflecting or converging the laser output from the collimation and convergence element and has an optical reflecting surface; the second reflecting mirror 34 is used for reflecting or collecting the reflected ultrasonic signals and has a stainless steel reflecting surface.
Example three:
the principle and structure of the present embodiment are the same as those of the first embodiment, and the difference is that: as shown in fig. 7, the reflecting element 30 includes a third reflecting mirror 36 and a third reflecting surface 35, wherein the third reflecting surface 35 is used for reflecting or condensing the laser output from the collimating and condensing element 40, and may be an angled (e.g. 45 degrees) end surface or a polished surface of the excitation fiber 50; the third reflector 36 is used for reflecting or collecting the reflected ultrasonic signals and has a stainless steel reflecting surface.
The reflecting surface or mirror of the reflecting element 30 is processed by a surface coating process.
The optical resonant element 20 may also be other optical resonant cavities with fanuo resonance effect, such as a metal surface plasmon photonic crystal or a reflection grating.
The above embodiments are only used for illustrating the design idea and features of the present invention, and the purpose of the present invention is to enable those skilled in the art to understand the content of the present invention and implement the present invention accordingly, and the protection scope of the present invention is not limited to the above embodiments. Therefore, all equivalent changes and modifications made in accordance with the principles and concepts disclosed herein are intended to be included within the scope of the present invention.
Claims (7)
1. A breast duct endoscope imaging probe comprises an optical fiber, a collimation converging element, a reflecting element and a capsule, and is characterized in that: the optical fiber comprises an excitation optical fiber and a receiving optical fiber, and the probe also comprises an optical resonance element for changing the resonance frequency under the returned ultrasonic wave;
the position relation among the excitation optical fiber, the receiving optical fiber, the collimation converging element, the reflecting element, the capsule and the optical resonance element meets the following optical path: the pulse laser is coupled into one end of the excitation optical fiber, is focused and irradiated to the reflecting element at the other end of the excitation optical fiber through the collimation converging element and then is reflected, is focused below the inner surface of the organism through the capsule, generates an ultrasonic signal due to an acousto-optic effect, and reflects and focuses the reflected ultrasonic signal to the optical resonance element after being irradiated to the reflecting element through the capsule, so that the resonance frequency of the optical resonance element is changed; the detection light is coupled into one end of the receiving optical fiber, the other end of the receiving optical fiber is coupled into the optical resonance element, the detection light with the changed resonance frequency is reflected back from the receiving optical fiber, and three-dimensional imaging is carried out through the optical detector and the imaging unit;
the optical resonance element comprises a planar integrated waveguide device with an elasto-optical effect, and the planar integrated waveguide device consists of a grating coupler, a connecting waveguide and a micro-ring resonant cavity; the planar integrated waveguide device is integrally manufactured on the end face of the receiving optical fiber, and the grating coupler is aligned with the core of the receiving optical fiber;
the planar integrated waveguide device is made of polymer materials and is manufactured on the end face of the receiving optical fiber by adopting a semiconductor nano-imprinting process;
two ends of the grating coupler are connected with the connecting waveguide end to end, a certain gap is arranged between the micro-ring resonant cavity and the connecting waveguide, and the micro-ring resonant cavity is arranged right above the grating coupler;
the excitation optical fiber, the receiving optical fiber, the collimation converging element, the reflecting element and the optical resonance element are all arranged in the capsule, and the excitation optical fiber and the receiving optical fiber are positioned on the same side of the reflecting element;
the excitation optical fiber, the receiving optical fiber, the collimation converging element, the reflecting element and the optical resonance element form a whole body which can rotate around the axial direction of the capsule;
the reflecting element comprises 2 independent reflecting mirrors, wherein the first reflecting mirror is used for reflecting or converging the laser output by the collimation converging element, and the second reflecting mirror is used for reflecting or converging the reflected ultrasonic signal.
2. The breast endoscope imaging probe of claim 1, wherein: the first reflector has an optical reflective surface and the second reflector has a stainless steel reflective surface.
3. A breast duct endoscope imaging probe comprises an optical fiber, a collimation converging element, a reflecting element and a capsule, and is characterized in that: the optical fiber comprises an excitation optical fiber and a receiving optical fiber, and the probe also comprises an optical resonance element for changing the resonance frequency under the returned ultrasonic wave;
the position relation among the excitation optical fiber, the receiving optical fiber, the collimation converging element, the reflecting element, the capsule and the optical resonance element meets the following optical path: the pulse laser is coupled into one end of the excitation optical fiber, is focused and irradiated to the reflecting element at the other end of the excitation optical fiber through the collimation converging element and then is reflected, is focused below the inner surface of the organism through the capsule, generates an ultrasonic signal due to an acousto-optic effect, and reflects and focuses the reflected ultrasonic signal to the optical resonance element after being irradiated to the reflecting element through the capsule, so that the resonance frequency of the optical resonance element is changed; the detection light is coupled into one end of the receiving optical fiber, the other end of the receiving optical fiber is coupled into the optical resonance element, the detection light with the changed resonance frequency is reflected back from the receiving optical fiber, and three-dimensional imaging is carried out through the optical detector and the imaging unit;
the optical resonance element comprises a planar integrated waveguide device with an elasto-optical effect, and the planar integrated waveguide device consists of a grating coupler, a connecting waveguide and a micro-ring resonant cavity; the planar integrated waveguide device is integrally manufactured on the end face of the receiving optical fiber, and the grating coupler is aligned with the core of the receiving optical fiber;
the planar integrated waveguide device is made of polymer materials and is manufactured on the end face of the receiving optical fiber by adopting a semiconductor nano-imprinting process;
two ends of the grating coupler are connected with the connecting waveguide end to end, a certain gap is arranged between the micro-ring resonant cavity and the connecting waveguide, and the micro-ring resonant cavity is arranged right above the grating coupler;
the excitation optical fiber, the receiving optical fiber, the collimation converging element, the reflecting element and the optical resonance element are all arranged in the capsule, and the excitation optical fiber and the receiving optical fiber are positioned on the same side of the reflecting element;
the excitation optical fiber, the receiving optical fiber, the collimation converging element, the reflecting element and the optical resonance element form a whole body which can rotate around the axial direction of the capsule;
the reflecting element comprises an independent reflecting mirror and an independent reflecting surface, wherein the reflecting surface is used for reflecting or converging the laser output by the collimation converging element, and the reflecting mirror is used for reflecting or converging the reflected ultrasonic signal.
4. The breast endoscope imaging probe of claim 3, wherein: the reflecting surface is the end surface of the excitation optical fiber with a certain angle, and the reflecting mirror is provided with a stainless steel reflecting surface.
5. The breast endoscope imaging probe of claim 1, wherein: the optical resonant element comprises an optical resonant cavity with a Fano resonance effect.
6. The breast endoscope imaging probe of claim 5, wherein: the optical resonant cavity is a metal surface plasmon polariton photonic crystal or a reflection grating.
7. The breast endoscope imaging probe of claim 4, wherein: the end face is a polished face.
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| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201810524691.3A CN108670177B (en) | 2018-05-28 | 2018-05-28 | Imaging probe of breast duct endoscope |
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| CN201810524691.3A CN108670177B (en) | 2018-05-28 | 2018-05-28 | Imaging probe of breast duct endoscope |
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| CN108670177A CN108670177A (en) | 2018-10-19 |
| CN108670177B true CN108670177B (en) | 2020-09-01 |
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| CN110251053B (en) * | 2019-07-24 | 2021-05-28 | 文曼科技(深圳)有限公司 | Endoscope special for breast duct |
| CN110584570B (en) * | 2019-10-12 | 2022-11-08 | 深圳大学 | All-optical detection endoscopic photoacoustic imaging system |
| CN110859601B (en) * | 2019-12-20 | 2023-05-05 | 暨南大学 | Photoacoustic imaging probe and photoacoustic imaging system |
| CN111134591B (en) * | 2019-12-27 | 2022-09-06 | 华南师范大学 | Photoacoustic microscopic imaging pen and imaging method |
| CN114994842A (en) * | 2022-08-01 | 2022-09-02 | 成都开必拓科技有限公司 | Medical laser optical fiber interconnecting device and medical laser optical fiber system formed by same |
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| WO2014197899A2 (en) * | 2013-06-07 | 2014-12-11 | Northwestern University | Methods, systems and apparatus of an all-optics ultrasound sensor |
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