CN109349982A - Multi-modal Cholangiopancreatogrinhy system - Google Patents
Multi-modal Cholangiopancreatogrinhy system Download PDFInfo
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
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- A61B1/00002—Operational features of endoscopes
- A61B1/00004—Operational features of endoscopes characterised by electronic signal processing
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- A61B1/00131—Accessories for endoscopes
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- A—HUMAN NECESSITIES
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- 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
- 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
- A61B1/043—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 for fluorescence imaging
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
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- 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
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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
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- A61B8/5261—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data for combining image data of patient, e.g. merging several images from different acquisition modes into one image combining images from different diagnostic modalities, e.g. ultrasound and X-ray
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Abstract
The invention discloses a kind of multi-modal Cholangiopancreatogrinhy systems, comprising: image processing system, the first optical imaging system, ultrasonic image-forming system；Interior snooping head, with optic probe component and ultrasonic transducer；The photoelectricity slip ring assembly of snooping head rotation in driving；Photoelectricity slip ring assembly includes the rotation drive device of rotary photoelectric coupling unit and driving rotary photoelectric coupling unit rotation, has photoelectricity slip ring in rotary photoelectric coupling unit；Connect first optical fiber of one end of the first optical imaging system and photoelectricity slip ring；Connect the other end of photoelectricity slip ring and the second optical fiber of optic probe component；Connect first electrical signal line of one end of ultrasonic image-forming system and photoelectricity slip ring；Connect the other end of photoelectricity slip ring and the second electrical signal line of optic probe component.Above-mentioned multi-modal Cholangiopancreatogrinhy system is imaged by the common cooperation of multi-modal (optics and ultrasound), improves the resolution ratio and imaging depth of imaging, is suitable for Cholangiopancreatogrinhy.
Description
Technical field
The present invention relates to based endoscopic imaging equipment technical field, in particular to a kind of multi-modal Cholangiopancreatogrinhy system.
Background technique
Pancreatic duct malignant change often originates from the endothelial cell of ductus pancreaticus or bile duct.It is generally formed a dynamic process:
It is manifested initially by pancreatic duct epithelial cell dysplasia, further infiltrates and grows to pancreatic duct basilar memebrane, is sent out after breaking through basilar memebrane
Exhibition is adenocarcinoma infiltrating.In this course, the change of pancreatic duct epithelium typical tectology is mainly reflected in structure and thin
It is abnormal that born of the same parents learn both sides.Criticized extremely in structure normal pancreatic duct epithelium by marshalling simple cuboidal or low columnar epithelium by
Gradually is replaced rich in the high column cell of mucus cytoplasm, occurs that epithelial cell is disorganized and the forfeiture of normal cell polarity；Carefully
Born of the same parents learn refers to that nucleus is irregular extremely, and chromatin contaminates deeply, and nucleus is not of uniform size, and nuclear proportion increases to be increased with nuclear fission activity
Add.When the cell of dysplasia continues to increase, breakthrough basilar memebrane, into parenchymatous disease, just development is with deep invasion for infiltration
Duct adenocarcinoma.Great the choosing that accurate judgement is pancreatic duct malignant tumour clinic diagnosis is carried out to the morphological abnormalities in this stage
War.
Pancreas is the big body of gland that liver is only second in human body, and position is deeper.Malignant change once occurs for pancreas gallbladder, often with there is morbidity
Concealment, progress is fast, high recurrence rate, shifts early feature.Since pancreas gallbladder position is deeper, the early diagnosis of such lesion is early controlled at present
It is extremely difficult.Currently, lacking efficient method of early diagnosis and effective molecular marking technique, the pancreas disorder of gallbladder to pancreas gallbladder malignant tumour
Become mechanism to be still not clear.The majority clinically made a definite diagnosis has been middle and advanced stage patient, poor prognosis, 5 years survival rates of patient after treatment
It is below 5%.Cancer of pancreas is more known as " king of cancer ".Therefore, there is highly sensitive, high specific and clinic to be applicable in for research and development
The instrument of the early stage diagnosis and treatment of property, is the prospective need of pancreatic duct cancer diagnosis and treatment.
Through abdomen B ultrasound (working frequency is in 5MHz) due to its simplicity, economy, hurtless measure, repeatable check and relatively accurate etc.
Advantage becomes the preferred iconography means for pancreas gallbladder cancer people at highest risk and clinically suspecting pancreas gallbladder carninomatosis people progress screening.But
Since ultrasonic echo decaying and intestinal gas interference cause image resolution ratio lower, the pancreatic neoplasm diagnosis to < 2cm is only
21.0%~64.5%, also pancreatic duct can not be effectively imaged.CT and MRI is current clinical most-often used diagnosis pancreas
The standard method of gallbladder malignant tumour can show that pancreas gallbladder lump or part increase, pancreatic duct continuity by directly or indirectly sign
Interruption, but 75% or so is also only reached to the diagnosis of lesser tumour (diameter≤2cm).Since most pancreas gallbladders are pernicious
Tumour originates from corresponding vessel intimae, therefore the anatomic passageway of ductus pancreaticus and bile duct is that the interior development for peeping intervention imaging technique mentions
Having supplied may.Inside peep intervention imaging technique can form in both macro and micro level to pancreas gallbladder and structure carry out it is more careful
Observation and accurate analysis.Wherein, EUS combines endoscope and laparoscopic technique on the basis of ultrasound, realizes that guidance fine needle is worn
Biopsy pancreas gallbladder occupying lesion is pierced, sensibility, specificity and the accuracy of diagnosing primary Yu secondary pancreas gallbladder tumour are improved,
Goldstandard as surgical operation.But since the working frequency of EUS is equally relatively low with Transabdominal Ultrasound, this equally limits it
For the imaging capability of pancreatic duct structure and minimal disease.Ultrasonic in pancreatic duct (IntraductalUltrasonography,
IDUS) medium-high frequency Ultrasonic microprobe can be directly placed in pancreatic duct through endoscopic forceps channel and carries out real time imagery, diameter is less than
The parenchymal tumor of 2cm has higher sensibility, but its placed-depth is limited, it is difficult to pass through the distal end of pancreatic duct.Further, since its
Working frequency is lower, and lack of resolution is to be clearly imaged pancreatic duct internal membranous structure.Diameter is less than the ductus pancreaticus mirror energy of 1mm
It is inserted directly into pancreatic duct direct imaging, is played an important role to diagnosis early stage pancreas gallbladder cancer, but the surface of pancreatic duct inner wall can only be provided
Information.
Come in recent years, many new imaging techniques continue to develop, and new means are brought to pancreatic duct tumor imaging.Packet
Ultrasonic imaging, optical coherent chromatographic imaging, fluorescence imaging, photoacoustic imaging and co-focusing imaging are peeped in including.
Ultrasonic imaging is inside peeped, may be implemented to carry out tomography to ductus pancreaticus inner membrance.Utilize deeper excellent of supersonic sounding depth
Gesture, to the comprehensive assessment of lesion more than OCT detection range, especially to the invasive depth of tumour carry out deeper identification and
Identification, the effective of the two combine the biological property for reflecting pancreas gallbladder tumour comprehensively, have also carried out more in detail to progression of disease situation
Most.
Optical coherent chromatographic imaging (OpticalCoherence tomography, OCT) has in body, tomographic imaging, high
Differentiate and imaging depth deeply several aspects the characteristics of.Endoscopic OCT (Endoscopic OCT, E-OCT) is as the important of OCT technology
Branch is directed light at organ-tissue to be measured by probe, can overcome the limited weakness of light penetration depth, is obtained in human body
The high-resolution tomographic map of organ depth passes through tissue morphology to carry out high-resolution imaging to clinical diagnosis region of interest
Research is learned, realizes the early diagnosis of disease.
On the basis of fluorescence imaging, is illuminated point by point by laser beam and pin hole modulation in space is flat to remove sample non-focus
The scattering light in face can form a kind of new imaging technique, confocal microscopic image (Confocalmicroscopy, CM).Altogether
It focuses microendoscopic and makees scanning light source using laser, after high power objective focuses, be scanned into point by point, line by line, to sample tissue
Picture, the phosphor collection that laser excitation goes out share an object lens, the focus, that is, scanning laser focus point and instantaneous imaging of object lens
Object point.System is once focused, and scanning is limited in a plane of sample.When focusing depth is different, so that it may obtain
The image of sample different depth level, these image informations are all stored in computer, are analyzed and are simulated by computer, can shown
The stereochemical structure of sample product.
Photoacoustic imaging (Photoacoustic Imaging, PAI) is the new bio of a kind of non-invasive and unionized formula
Medical imaging procedure.Laser beam injects sample tissue, and biological tissue can absorb the energy of laser beam.The light beam of the accumulation point of light beam
Energy causes the expansion and contraction in tissue local region, to issue ultrasonic signal, this signal is referred to as photoacoustic signal.No
It is different with absorption of the structural constituent to light, thus photoacoustic signal carries the characteristic of tissue light absorption.Pass through ultrasonic transducer
(10-5) detects this signal, so that it may obtain the image information of tissue.Photoacoustic imaging has optical imagery high-resolution
Feature also has the high imaging depth advantage of ultrasonic imaging simultaneously.
In above-mentioned four kinds of optical imageries (optical coherent chromatographic imaging, fluorescence imaging, photoacoustic imaging and co-focusing imaging) side
In formula, OCT image and photoacoustic imaging are relative to larger imaging depth, and resolution ratio is lower.Corresponding fluorescence imaging and
Co-focusing imaging has higher resolution ratio and imaging depth is very shallow.
In conclusion be tomography to be realized for the key of early stage pancreatic duct cancer imaging, it is comprehensive body, tomography at
Picture, the clinical requirement of high-resolution and the several aspects of imaging depth.And if it is desired to obtain high-resolution method, current mainstream side
Method has high frequency ultrasound, optical coherence tomography (OCT), fluorescence imaging and co-focusing imaging etc..And the imaging of these imaging techniques is deep
Degree is all relatively shallower, so pancreaticobiliary duct disease position must be thrown into imaging capability by the interior method peeped.
Therefore, a kind of system suitable for Cholangiopancreatogrinhy how is provided, it has also become those skilled in the art are urgently to be resolved
The problem of.
Summary of the invention
In view of this, the present invention provides a kind of multi-modal Cholangiopancreatogrinhy system, in order to be suitable for Cholangiopancreatogrinhy.
To achieve the above object, the invention provides the following technical scheme:
A kind of multi-modal Cholangiopancreatogrinhy system, comprising:
Image processing system；
The first optical imaging system being connected to described image processing system；
The ultrasonic image-forming system being connected to described image processing system；
Interior snooping head, the interior snooping head have the optic probe component for being able to carry out optical imagery detection and are able to carry out
The ultrasonic transducer of ultrasonic imaging detection；
Drive the photoelectricity slip ring assembly of the interior snooping head rotation；The photoelectricity slip ring assembly includes rotary photoelectric coupling
Unit and the rotation drive device of the driving rotary photoelectric coupling unit rotation, the interior tool of the rotary photoelectric coupling unit
There is photoelectricity slip ring；
Connect first optical fiber of one end of first optical imaging system and the photoelectricity slip ring；
Connect the other end of the photoelectricity slip ring and the second optical fiber of the optic probe component；
Connect first electrical signal line of one end of the ultrasonic image-forming system and the photoelectricity slip ring；
Connect the other end of the photoelectricity slip ring and the second electrical signal line of the optic probe component.
Preferably, in above-mentioned multi-modal Cholangiopancreatogrinhy system, the photoelectricity slip ring includes smooth ring structure
With electric slip ring structure；
The smooth ring structure includes two mutually independent optical collimators, and two optical collimators can be in free sky
Between in mutually transmit, two optical collimators are connect with first optical fiber and second optical fiber respectively；
The electric slip ring structure includes two point slip rings for contacting with each other and being relatively rotatable to each other, two described slip rings minute
It is not connect with first electrical signal line and second electrical signal line.
Preferably, in above-mentioned multi-modal Cholangiopancreatogrinhy system, further includes:
The second optical imaging system being connected to described image processing system, second optical imaging system are that copolymerization is burnt
Endoscope system or fluoroscopic imaging systems；First optical imaging system is optical coherence tomography system or photoacoustic imaging system
System；
Wavelength division multiplexer, the wavelength division multiplexer is by second optical imaging system and first optical imaging system
It is multiplexed together and is connect with first optical fiber.
Preferably, in above-mentioned multi-modal Cholangiopancreatogrinhy system, second optical imaging system is fluoroscopic imaging systems,
First optical imaging system is optical coherence tomography system；
The wavelength division multiplexer is by the OCT sample arm of the fluoroscopic imaging systems and the optical coherence tomography system
It is multiplexed together and is connect with first optical fiber.
Preferably, in above-mentioned multi-modal Cholangiopancreatogrinhy system, further include synchronize the ultrasonic image-forming system ultrasound and
The master flip-flop of the fluorescence imaging of the fluoroscopic imaging systems.
Preferably, in above-mentioned multi-modal Cholangiopancreatogrinhy system, the fluoroscopic imaging systems further include for collecting transmitting
Fluorescence doubly clad optical fiber coupler.
Preferably, in above-mentioned multi-modal Cholangiopancreatogrinhy system, the excitation light source of the fluoroscopic imaging systems is semiconductor
Laser；
The light source of the optical coherence tomography system is VCSEL light source.
It preferably, further include the interior snooping headgear of the connection interior snooping head in above-mentioned multi-modal Cholangiopancreatogrinhy system
Pipe, second optical fiber and second electrical signal line are located in the interior snooping head casing tube.
Preferably, in above-mentioned multi-modal Cholangiopancreatogrinhy system, the interior snooping head further include:
Accommodate the anti-torsion casing of the optic probe component and the ultrasonic transducer；
The Marking ring being set in the anti-torsion casing.
Preferably, in above-mentioned multi-modal Cholangiopancreatogrinhy system, the optic probe component is globe lens.
Preferably, in above-mentioned multi-modal Cholangiopancreatogrinhy system, centre frequency >=50MHz of the ultrasonic transducer；
The full-size of the ultrasonic transducer is not more than 0.6mm.
Preferably, in above-mentioned multi-modal Cholangiopancreatogrinhy system, the optic probe component issues direction and the institute of light beam
It states ultrasonic transducer and issues the contrary of acoustic beam.
It can be seen from the above technical scheme that multi-modal Cholangiopancreatogrinhy system provided by the invention, has the first light
Imaging system and ultrasonic image-forming system are learned, also, also there is the optic probe for being able to carry out optical imagery detection in interior snooping head
Component and the ultrasonic transducer for being able to carry out ultrasonic imaging detection, the first optical fiber are coupled with the second optical fiber by rotary photoelectric single
Member rotation connection, the first electrical signal line are connected to the second electrical signal line by the rotation of rotary photoelectric coupling unit, the second optical fiber
Light beam transfer and projects to sample tissue by the optical focusing unit in interior snooping head, the second electrical signal line can drive interior peep
Ultrasonic transducer in probe issues high frequency ultrasound and also directive sample tissue, under the driving of rotation drive device, interior snooping
Head makees uniform rotation, to realize the imaging to pancreatic duct.The optical signal of directive sample tissue can pass through optics in interior snooping head
Focusing unit, the second optical fiber, photoelectricity slip ring and the first optical fiber (backtracking) are to the first optical imaging system, and by image
It is shown after the processing of reason system.It also can be by the ultrasonic transduction in interior snooping head from ultrasonic signal reflected in sample tissue
Device is received and converted into electric signal, passes through the second electrical signal line, photoelectricity slip ring and the first electrical signal line (backtracking) to ultrasound
It in imaging system, and is shown after being handled by image processing system, to complete the based endoscopic imaging process to pancreatic duct.?
, can be using ultrasonic image-forming system as standing imaging in entire imaging system, the first optical imaging system is as aid imaging
Mode, and shown after being handled by image processing system, to complete the based endoscopic imaging process to pancreatic duct.The present invention mentions
On the one hand the multi-modal Cholangiopancreatogrinhy system supplied utilizes the higher advantage of optical imagery resolution ratio, provide high-resolution chromatography letter
Breath；On the other hand the advantage deeper using ultrasonic imaging investigation depth, to the detection range more than the first optical imaging system
The comprehensive assessment of lesion, especially carries out deeper identification and identification to the invasive depth of tumour, and the effective of the two combines entirely
Face reflects the biological property of pancreas gallbladder tumour, has also carried out more explaination in detail to progression of disease situation.Therefore, pass through multimode
The common cooperation of state (optics and ultrasound) is imaged, and improves the resolution ratio and imaging depth of imaging, can effectively identify lesion morning
The variation of phase pancreatic duct epithelial cell is suitable for Cholangiopancreatogrinhy.
Detailed description of the invention
In order to more clearly explain the embodiment of the invention or the technical proposal in the existing technology, to embodiment or will show below
There is attached drawing needed in technical description to be briefly described, it should be apparent that, the accompanying drawings in the following description is only this
Some embodiments of invention for those of ordinary skill in the art without creative efforts, can be with
It obtains other drawings based on these drawings.
Fig. 1 is the first structural schematic diagram of multi-modal Cholangiopancreatogrinhy system provided in an embodiment of the present invention；
Fig. 2 is second of structural schematic diagram of multi-modal Cholangiopancreatogrinhy system provided in an embodiment of the present invention；
Fig. 3 is the structural schematic diagram of interior snooping head provided in an embodiment of the present invention.
Specific embodiment
The invention discloses a kind of multi-modal Cholangiopancreatogrinhy systems, in order to be suitable for Cholangiopancreatogrinhy.
Following will be combined with the drawings in the embodiments of the present invention, and technical solution in the embodiment of the present invention carries out clear, complete
Site preparation description, it is clear that described embodiments are only a part of the embodiments of the present invention, instead of all the embodiments.It is based on
Embodiment in the present invention, it is obtained by those of ordinary skill in the art without making creative efforts every other
Embodiment shall fall within the protection scope of the present invention.
Fig. 1, Fig. 2 and Fig. 3 are please referred to, Fig. 1 is the first of multi-modal Cholangiopancreatogrinhy system provided in an embodiment of the present invention
Kind structural schematic diagram；Fig. 2 is second of structural schematic diagram of multi-modal Cholangiopancreatogrinhy system provided in an embodiment of the present invention；Figure
3 be the interior structural schematic diagram for spying upon head provided in an embodiment of the present invention.
The embodiment of the invention provides a kind of multi-modal Cholangiopancreatogrinhy systems, comprising: image processing system 1 and image
The first optical imaging system 2 that processing system 1 is connected to；The ultrasonic image-forming system 3 being connected to image processing system 1；Interior snooping head
10, interior snooping head 10 has the optic probe component 10-3 for being able to carry out optical imagery detection and is able to carry out ultrasonic imaging detection
Ultrasonic transducer 10-5；The photoelectricity slip ring assembly 6 that snooping head 10 rotates in driving；Photoelectricity slip ring assembly 6 includes rotary light
It is electrically coupled unit 7 and drives the rotation drive device 8 of the rotation of rotary photoelectric coupling unit 7, in rotary photoelectric coupling unit 7
With photoelectricity slip ring；Connect the first optical fiber 4 of the first optical imaging system 2 and one end of photoelectricity slip ring；Connect photoelectricity slip ring
Second optical fiber 10-1 of the other end and optic probe component 10-3；Connect the of one end of ultrasonic image-forming system 3 and photoelectricity slip ring
One electrical signal line 5；Connect the other end of photoelectricity slip ring and the second electrical signal line 10-2 of optic probe component 10-3.
Multi-modal Cholangiopancreatogrinhy system provided in an embodiment of the present invention, have the first optical imaging system 2 and ultrasound at
Also there is the optic probe component 10-3 for being able to carry out optical imagery detection as system 3, also, in interior snooping head 10 and can be into
The ultrasonic transducer 10-5 of row ultrasonic imaging detection, the first optical fiber 4 and the second optical fiber 10-1 pass through rotary photoelectric coupling unit 7
Rotation connection, the first electrical signal line 5 are connected to the second electrical signal line 10-2 by the rotation of rotary photoelectric coupling unit 7, and second
The light beam of optical fiber 10-1 is transferred and is projected to sample tissue, the second electrical signal line by the optical focusing unit in interior snooping head 10
10-2 can drive the ultrasonic transducer in interior snooping head 10 to issue high frequency ultrasound and also directive sample tissue, in rotation drive device
Under 8 driving, interior snooping head 10 makees uniform rotation, to realize the imaging to pancreatic duct.The optical signal meeting of directive sample tissue
Pass through optical focusing unit, the second optical fiber 10-1, photoelectricity slip ring and the first optical fiber 4 (backtracking) in interior snooping head 10 to first
Optical imaging system 2, and shown after the processing of image processing system 1.The reflected ultrasound letter from sample tissue
Number also electric signal can be received and converted by the ultrasonic transducer 10-5 in interior snooping head 10, by the second electrical signal line 10-2,
Photoelectricity slip ring and the first electrical signal line 5 (backtracking) into ultrasonic image-forming system 4, and by image processing system 1 handle after
It shows, to complete the based endoscopic imaging process to pancreatic duct.It, can be by ultrasonic image-forming system 3 in entire imaging system
As standing imaging, the first optical imaging system 2 is used as aid imaging mode, and shows after being handled by image processing system 1
It shows and, to complete the based endoscopic imaging process to pancreatic duct.Multi-modal Cholangiopancreatogrinhy system provided in an embodiment of the present invention,
On the one hand the higher advantage of optical imagery resolution ratio is utilized, high-resolution chromatography information is provided；On the other hand it is visited using ultrasonic imaging
The deeper advantage of depth measurement degree, to the comprehensive assessment of the lesion of the detection range more than the first optical imaging system 2, especially to tumour
Invasive depth carry out deeper identification and identification, the effective of the two combines the biological characteristics for reflecting pancreas gallbladder tumour comprehensively
Sign has also carried out more explaination in detail to progression of disease situation.Therefore, by multi-modal (optics and ultrasound) it is common cooperation at
Picture improves the resolution ratio and imaging depth of imaging, can effectively identify the variation of lesion early stage pancreatic duct epithelial cell, is applicable in
In Cholangiopancreatogrinhy.
Preferably, in multi-modal Cholangiopancreatogrinhy system provided in an embodiment of the present invention, image processing system 1 includes calculating
Machine and display.
In the present embodiment, photoelectricity slip ring includes smooth ring structure and electric slip ring structure；Smooth ring structure includes two mutual
Independent optical collimator, two optical collimators can be transmitted mutually in free space, two optical collimators respectively with the first light
Fibre 4 and the second optical fiber 10-1 connection；Electric slip ring structure includes two point slip rings for contacting with each other and being relatively rotatable to each other, two points
Slip ring is connect with the first electrical signal line 5 and the second electrical signal line 10-2 respectively.
As shown in Figures 1 and 3, in the first embodiment, the sample arm 2-1 of the first optical imaging system 2, which can be exported, to be swept
Frequency light beam, light beam are imported into rotary photoelectric coupling unit 7 by the first optical fiber 4.Meanwhile ultrasonic image-forming system 3 issues and surpasses
Acoustically-driven signal is also introduced into rotary photoelectric coupling unit 7 by the first electrical signal line 5.In rotary photoelectric coupling unit 7
Smooth ring structure include space optical transmission system that two optical collimators are constituted, the light in the first optical fiber 4 is collimated by a light
It is transferred to another optical collimator in free space after device collimation, is transferred into the second optical fiber 10- again after overcoupling
1.This two optical collimators are spatially separating in mechanical structure.Therefore two optical collimators can be made in relative rotation
In the case of, keep the transmission of optical signal.And the electric slip ring structure in rotary photoelectric coupling unit 7 includes to contact with each other and can phase
To the point slip ring of rotation.Electric signal transmission is kept while can relatively rotating.
As shown in Figure 1, the present embodiment is two mode Cholangiopancreatogrinhy systems.With single mode Cholangiopancreatogrinhy system phase
Than effectively increasing the resolution ratio and imaging depth of imaging.
As shown in Fig. 2, the present embodiment is three mode Cholangiopancreatogrinhy systems, multi-modal Cholangiopancreatogrinhy system further include:
The second optical imaging system 11 being connected to image processing system 1, the second optical imaging system 11 be copolymerized burnt endoscope system or
Fluoroscopic imaging systems；First optical imaging system 2 is optical coherence tomography system or photoacoustic imaging system；Wavelength division multiplexer
12, wavelength division multiplexer 12 by the second optical imaging system 11 and the first optical imaging system 2 be multiplexed together and with the first optical fiber 4
Connection.It is understood that OCT image and photoacoustic imaging be relative to larger imaging depth, and resolution ratio is lower.Fluorescence at
Picture and co-focusing imaging have higher resolution ratio and imaging depth is very shallow.By wavelength division multiplexer 12 by the second optical imagery system
System 11 and first optical imaging system 2 be multiplexed together and connect with the first optical fiber 4, further improve imaging resolution and at
As depth.
Further, in the present embodiment, the second optical imaging system 11 is fluoroscopic imaging systems, the first optical imagery system
System 2 is optical coherence tomography system；Wavelength division multiplexer 12 is by fluoroscopic imaging systems and optical coherence tomography system
OCT sample arm 2-1 is multiplexed together and connect with the first optical fiber 4.
It is exported after the sample arm 2-1 light beam output of optical coherence tomography system with the sample arm of fluoroscopic imaging systems
Light couples in a wavelength division multiplexer 12.Then rotary photoelectric coupling unit 7 is output to by the first optical fiber 4 (multimode fibre)
In.Ultrasound control electric signal in ultrasonic image-forming system 3 also enters into rotary photoelectric coupling unit also by the first electrical signal line 5
In 7.Photoelectricity slip ring in rotary photoelectric coupling unit 7 includes smooth ring structure and electric slip ring structure；Both ends can be allowed to have relatively
In the case where rotation, synchronous transfer optical signal and electric signal.
Wherein, rotation drive device 8 is rotation motor.The rotation of rotary photoelectric coupling unit 7 is by rotation drive device 8
Power is provided.
As shown in Fig. 2, in the present embodiment, the sample arm of optical coherence tomography system (the first optical imaging system 2)
After the output of 2-1 light beam and the light of the sample arm output of fluoroscopic imaging systems (the second optical imaging system 11) is in a wavelength-division multiplex
It is coupled in device (WDM) 12.Then it is output in rotary photoelectric coupling unit 7 by the first optical fiber (multimode fibre) 4.Ultrasonic imaging
Ultrasound control electric signal in system 3 also enters into rotary photoelectric coupling unit 7 also by the first electrical signal line 5.Rotate light
In the case where being electrically coupled unit 7 and both ends being allowed to have relative rotation, synchronous transfer optical signal and electric signal.And rotary photoelectric couples
The rotation of unit 7 is to provide power by rotation motor (rotation drive device 8).Rotary photoelectric coupling unit 7 and rotation motor group
Conjunction constitutes photoelectricity slip ring assembly 6.It is interior snooping head casing tube 9 in contain transmission OCT and fluorescence signal the second optical fiber 10-1 with
And the second electrical signal line 10-2 of transmission ultrasonic signal, interior spy upon are integrated with optical system (the optics spy of focus on light beam in head 10
Head part 10-3) and a ultrasonic transducer 10-5.The light beam of the second optical fiber 10-1 in interior snooping head casing tube 9 passes through interior snooping
Optic probe component 10-3 (optical focus module) in first 10 transfers and projects to sample tissue, transmits the second of ultrasonic signal
Electrical signal line 10-2 can drive the ultrasonic transducer 10-5 of interior snooping head 10 to issue high frequency ultrasound and also directive sample tissue.Inside peep
Probe sleeve 9 and snooping head 10 make uniform rotation under the driving of rotary photoelectric coupling unit 7, to realize to pancreatic duct
Imaging.
The middle optical signal of directive sample tissue understands backtracking to optical coherence tomography system (the first optical imagery system
It unites 2) and in fluoroscopic imaging systems (the second optical imaging system 11), and by optical coherence tomography system and fluorescence imaging system
Photodetector detection in system, forms digital signal, shows after the processing of image processing system 1.From sample sets
It knits reflected ultrasonic signal and electric signal is received and converted by the ultrasonic transducer 10-5 in interior snooping head 10, former road is returned
It is back in ultrasonic image-forming system 3, and is shown after being handled by image processing system 1.To complete to being peeped in pancreatic duct
Imaging process.
It further include the ultrasound and fluoroscopic imaging systems of synchronizing ultrasound imaging system 3 in multi-modal Cholangiopancreatogrinhy system
The master flip-flop of fluorescence imaging.Further, the trigger signal of scanning source laser device is used to carry out synchronizing ultrasound as master flip-flop
And fluorescence imaging.Optical coherence tomography system and fluoroscopic imaging systems are combined using wavelength division multiplexer 12.
Further, fluoroscopic imaging systems further include the doubly clad optical fiber coupler for collecting the fluorescence of transmitting.It adopts
The light of transmitting is collected, with doubly clad optical fiber (DCF) coupler to guarantee the compact of three modal systems and stablize.
The excitation light source of fluoroscopic imaging systems is semiconductor laser.For specific marker M2 type macrophage in pancreas gallbladder cancer
Surface antigen CD206, constructing function nir dye indocyanine green marks M2 type macrophage as novel fluorescence probe,
Specific recognition CD206 passes through PMT using the 680-750nm wave band of semiconductor laser adjustable laser as excitation light source
(photomultiplier tube, photomultiplier tube) collection >=800nm fluorescence is realized to CD206+-M2 type macrophage
Fluorescent molecules imaging.To the integrated then multiple according to the selection wavelength-division of OCT/ fluorescing system different wave length situation of bimodal light path part
OCT sample arm 2-1 light source and fluorescent excitation light source are integrated into same single mode broadband optical fiber optical path with device 12；For fluorescence imaging
The semiconductor laser and doubly clad optical fiber coupler of excitation light source are included into excitation light and transmitting optical transport is collected；It is this complete
Optic fibre light path design ensure that bimodal light path system is compact and stablizes.
The light source of optical coherence tomography system is VCSEL (VerticalCavity Surface
EmittingLaser, vertical cavity surface lase) light source.
In pancreatic duct based endoscopic imaging, bile duct diameter is 6-8mm, main pancreatic duct diameter about 2-3mm, and secondary branch is then more
Carefully.In this multi-modal Cholangiopancreatogrinhy system, the SS-OCT of big range Imaging ensure that the pipeline blur-free imaging to different depth.
Long range SS-OCT system is used in order to solve the above problem, and wherein swept light source selects VCSEL swept light source, and coherence length is super
10mm is crossed, covering common bile duct or ductus pancreaticus is more than 6mm.
Further, in transmission process, composite light beam passes through one-site model core from input port to output port, single mode
The minor diameter of core generates high energy density to surface texture, to realize efficient excitation.Emit light through doubly clad optical fiber
The ability for collecting transmitting light can be improved in the major diameter that coupler is output to multimode fibre, and the corresponding filtering of progress obtains glimmering in PMT
Optical information.Ultrasonic imaging then passes through acoustic generator/receiver and generates and detect ultrasonic signal.
As shown in figure 3, multi-modal Cholangiopancreatogrinhy system provided in an embodiment of the present invention, further includes connecting interior snooping head 10
Interior snooping head casing tube 9, the second optical fiber 10-1 and the second electrical signal line 10-2 are located in interior snooping head casing tube 9.
The second optical fiber 10-1 and the second electrical signal line 10-2 is contained in interior snooping head casing tube 9, is integrated in interior snooping head 10
It is able to carry out the optic probe component 10-3 of optical imagery detection and is able to carry out the ultrasonic transducer 10- of ultrasonic imaging detection
The light beam of 5, the second optical fiber 10-1 of interior snooping head casing tube 9 by the optic probe component 10-3 in interior snooping head 10, (visit by optics
Head part is referred to as optical focus module) it transfers and projects to sample tissue, transmit the second electrical signal line of ultrasonic signal
10-2 can drive the ultrasonic transducer 10-5 in interior snooping head 10 to issue high frequency ultrasound and also directive sample tissue.Interior snooping headgear
Pipe 9 and snooping head 10 make uniform rotation under the driving of rotary photoelectric coupling unit 7, to realize the imaging to pancreatic duct.
The optical signal of directive sample tissue can by optic probe component 10-3, the second optical fiber 10-1 in interior snooping head 10 and
First optical fiber, 4 backtracking passes through image processing system to the first optical imaging system 2 (optical coherence tomography system)
It is shown after 1 processing.It also can be by the ultrasonic transducer in interior snooping head 10 from ultrasonic signal reflected in sample tissue
10-5 is received and converted into electric signal, passes through the second electrical signal line 10-2 and 5 backtracking of the first electrical signal line to ultrasonic imaging
In system 3, and shown after being handled by image processing system 1.To complete the based endoscopic imaging process to pancreatic duct.
In the present embodiment, the second electrical signal line 10-2 is a kind of coaxial cable, so as to shield extraneous electromagnetic signal,
Obtain higher signal transmission quality.Ultrasonic excitation signal excitation high-frequency transducer 10-5 inspires ultrasound, and passes through tune
System forms high-frequency ultrasonic beam 10-9.High-frequency ultrasonic beam 10-9 directive sample tissue is simultaneously received back using high-frequency transducer 10-5
Wave signal.The signal is passed back to by the second electrical signal line 10-2 is obtained with the super of sample tissue in ultrasonic image-forming system 3
Acoustic image.
In the present embodiment, interior snooping head 10 further include: accommodate the anti-of optic probe component 10-3 and ultrasonic transducer 10-5
Reverse casing 10-7；The Marking ring 10-6 being set in anti-torsion casing 10-7.Marking ring 10-6 is for marking interior snooping head 10
Position in space, to correct the spatial relation of imaging.Preferably, anti-torsion casing 10-7 is with higher just
Property, thus in vivo rotate during will not wide-angle torsion.
In order to improve resolution ratio, optic probe component 10-3 is globe lens.
Light can form the light beam 10-8 of focusing after globe lens modulation reshaping in second optical fiber 10-1.Under globe lens
Surface is processed to the gold-plated tapered plane 10-4 for having certain angle, which can be 90 ° by light beam steering, thus directive sample
Product tissue.Since light beam is focused, it is hereby achieved that higher lateral resolution.Globe lens can disappear by special design
Except pseudomorphism, more high imaging quality is obtained.
Further, centre frequency >=50MHz of ultrasonic transducer 10-5；The full-size of ultrasonic transducer 10-5 is little
In 0.6mm.By above-mentioned setting, to improve the longitudinal resolution of ultrasound image.It, will in the hardware aspect of ultrasonic image-forming system 3
It is excited using wide bandwidth (> 200MHz) sinusoidal impulse, and cooperates low noise variable gain amplifier, it is super to further increase high frequency
The picture quality of sound.
Further, the present invention is to novel piezoelectric material, such as MEMS monocrystalline/epoxy resin 1-3PIN-PMN-PT relaxation iron
Electric monocrystalline etc. and its performance are deeply developed, and the parameters such as its high-temperature dielectric peak, coercive electric field and residual polarization are analyzed, by mixing
Miscellaneous remodeling improves its mechanical performance and temperature stability.
In order to improve structural compactness, optic probe component 10-3 issues direction and the ultrasonic transducer 10-5 of light beam 10-8
Issue the contrary of acoustic beam 10-9.
By above-mentioned setting, so that ultrasonic transducer 10-5 and optic probe component 10-3 take back-to-back topology.And
And using loud absorbent properties material as the back lining materials of ultrasonic transducer 10-5, further decrease ultrasonic transducer 10-5's
Thickness is effectively utilized the space of anti-torsion casing 10-7.Effectively reduce the size of interior snooping head 10.
Also, the devices such as high frequency ultrasound pulse clawback transmitting-receiving instrument, ultrasonic amplifier are further comprised in ultrasonic image-forming system 3.
Building precise electric control scanning platform can integrate smooth ring and electric slip ring, the behaviour being connected for imaging catheter with host
Unit is controlled, the low-loss transmission of optical signal and electric signal between rotatable parts and stationary parts is realized, realizes the rotation of imaging catheter
Turn, withdraw scanning, obtains mechanical movement needed for three-dimensional imaging in pancreatic duct and withdrawn for imaging catheter.
The foregoing description of the disclosed embodiments enables those skilled in the art to implement or use the present invention.
Various modifications to these embodiments will be readily apparent to those skilled in the art, as defined herein
General Principle can be realized in other embodiments without departing from the spirit or scope of the present invention.Therefore, of the invention
It is not intended to be limited to the embodiments shown herein, and is to fit to and the principles and novel features disclosed herein phase one
The widest scope of cause.
Claims (12)
1. a kind of multi-modal Cholangiopancreatogrinhy system characterized by comprising
Image processing system (1)；
The first optical imaging system (2) being connected to described image processing system (1)；
The ultrasonic image-forming system (3) being connected to described image processing system (1)；
Interior snooping head (10), interior snooping head (10) have the optic probe component (10-3) for being able to carry out optical imagery detection
And it is able to carry out the ultrasonic transducer (10-5) of ultrasonic imaging detection；
Drive the photoelectricity slip ring assembly (6) of interior snooping head (10) rotation；The photoelectricity slip ring assembly (6) includes rotary light
It is electrically coupled the rotation drive device (8) of unit (7) and driving rotary photoelectric coupling unit (7) rotation, it is described rotary
There is photoelectricity slip ring in photoelectric coupling unit for promoting inhibition (7)；
Connect first optical fiber (4) of one end of first optical imaging system (2) and the photoelectricity slip ring；
Connect the other end of the photoelectricity slip ring and the second optical fiber (10-1) of the optic probe component (10-3)；
Connect first electrical signal line (5) of one end of the ultrasonic image-forming system (3) and the photoelectricity slip ring；
Connect the other end of the photoelectricity slip ring and the second electrical signal line (10-2) of the optic probe component (10-3).
2. multi-modal Cholangiopancreatogrinhy system as described in claim 1, which is characterized in that the photoelectricity slip ring includes smooth ring
Structure and electric slip ring structure；
The smooth ring structure includes two mutually independent optical collimators, and two optical collimators can be in free space
Mutually transmission, two optical collimators are connect with first optical fiber (4) and second optical fiber (10-1) respectively；
The electric slip ring structure includes two point slip rings for contacting with each other and being relatively rotatable to each other, two described slip rings respectively with
First electrical signal line (5) and second electrical signal line (10-2) connection.
3. multi-modal Cholangiopancreatogrinhy system as described in claim 1, which is characterized in that further include:
The second optical imaging system (11) being connected to described image processing system (1), second optical imaging system (11)
To be copolymerized burnt endoscope system or fluoroscopic imaging systems；First optical imaging system (2) is optical coherence tomography system
Or photoacoustic imaging system；
Wavelength division multiplexer (12), the wavelength division multiplexer (12) is by second optical imaging system (11) and first optics
Imaging system (2) is multiplexed together and connect with first optical fiber (4).
4. multi-modal Cholangiopancreatogrinhy system as claimed in claim 3, which is characterized in that second optical imaging system
It (11) is fluoroscopic imaging systems, first optical imaging system (2) is optical coherence tomography system；
The wavelength division multiplexer (12) is by the OCT sample arm of the fluoroscopic imaging systems and the optical coherence tomography system
(2-1) is multiplexed together and connect with first optical fiber (4).
5. multi-modal Cholangiopancreatogrinhy system as claimed in claim 4, which is characterized in that further include synchronizing the ultrasonic imaging
The master flip-flop of the fluorescence imaging of the ultrasonic and described fluoroscopic imaging systems of system (3).
6. multi-modal Cholangiopancreatogrinhy system as claimed in claim 4, which is characterized in that the fluoroscopic imaging systems further include
For collecting the doubly clad optical fiber coupler of the fluorescence of transmitting.
7. multi-modal Cholangiopancreatogrinhy system as claimed in claim 4, which is characterized in that
The excitation light source of the fluoroscopic imaging systems is semiconductor laser；
The light source of the optical coherence tomography system is VCSEL light source.
8. multi-modal Cholangiopancreatogrinhy system as described in claim 1, which is characterized in that further include the connection interior snooping head
(10) interior snooping head casing tube (9), second optical fiber (10-1) and second electrical signal line (10-2), which are located in described, to be peeped
In probe sleeve (9).
9. multi-modal Cholangiopancreatogrinhy system as described in claim 1, which is characterized in that the interior snooping head (10) is also wrapped
It includes:
Accommodate the anti-torsion casing (10-7) of the optic probe component (10-3) and the ultrasonic transducer (10-5)；
The Marking ring (10-6) being set in the anti-torsion casing (10-7).
10. multi-modal Cholangiopancreatogrinhy system as described in claim 1, which is characterized in that the optic probe component (10-
It 3) is globe lens.
11. multi-modal Cholangiopancreatogrinhy system as described in claim 1, which is characterized in that the ultrasonic transducer (10-5)
Centre frequency >=50MHz；
The full-size of the ultrasonic transducer (10-5) is not more than 0.6mm.
12. such as the described in any item multi-modal Cholangiopancreatogrinhy systems of claim 1-11, which is characterized in that the optic probe
Component (10-3) issues the direction of light beam (10-8) and the ultrasonic transducer (10-5) issues the contrary of acoustic beam (10-9).
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Cited By (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN110464309A (en) * | 2019-08-27 | 2019-11-19 | 深圳大学 | A kind of fluorescent endoscopic imgaing system across scale |
| CN111387947A (en) * | 2020-04-07 | 2020-07-10 | 中国科学院苏州生物医学工程技术研究所 | Multi-mode microscopic endoscopic imaging device and method |
| CN111419149A (en) * | 2020-03-13 | 2020-07-17 | 上海应用技术大学 | Multi-mode endoscope and endoscopic imaging system |
| CN113080870A (en) * | 2021-04-12 | 2021-07-09 | 北京航空航天大学 | Imaging system |
| CN114159029A (en) * | 2021-11-30 | 2022-03-11 | 深圳先进技术研究院 | Optical coherence tomography system and imaging catheter thereof |
| CN115919372A (en) * | 2023-01-28 | 2023-04-07 | 深圳先进技术研究院 | Multimode endoscopic imaging system based on short wave near-infrared fluorescence |
| CN115989989A (en) * | 2023-02-15 | 2023-04-21 | 暨南大学 | Omnibearing rotary scanning endoscopic imaging device based on optical fiber sensor |
Citations (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101147669A (en) * | 2007-10-25 | 2008-03-26 | 浙江大学 | Integrated optical coherence chromatographic imaging and laser inducing fluorescent-spectrum single optical fiber endoscopy system |
| CN103385758A (en) * | 2013-07-22 | 2013-11-13 | 深圳先进技术研究院 | Intravascular opto-acoustic and ultrasonic dual-mode imaging system and imaging method thereof |
| CN103462644A (en) * | 2012-06-07 | 2013-12-25 | 中国科学院深圳先进技术研究院 | Photoacoustic endoscope |
| CN204274504U (en) * | 2014-10-21 | 2015-04-22 | 白晓苓 | Ultrasonic/optics double-mode imaging the probe of a kind of based endoscopic imaging |
| US20160242737A1 (en) * | 2013-10-07 | 2016-08-25 | The Regents Of The University Of California | Integrated Ultrasound, OCT, PA and/or Florescence Imaging Endoscope for Diagnosing Cancers in Gastrointestinal, Respiratory, and Urogenital Tracts |
| CN106691396A (en) * | 2017-02-28 | 2017-05-24 | 华南师范大学 | Intravascular fluorescent-photoacoustic-ultrasonic multi-mode imaging device and method |
| CN108618758A (en) * | 2018-04-27 | 2018-10-09 | 华南师范大学 | Intravascular photoacoustic-optical coherence tomography-near infrared light multi-modality imaging apparatus and method |
-
2018
- 2018-12-07 CN CN201811496842.5A patent/CN109349982A/en active Pending
Patent Citations (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101147669A (en) * | 2007-10-25 | 2008-03-26 | 浙江大学 | Integrated optical coherence chromatographic imaging and laser inducing fluorescent-spectrum single optical fiber endoscopy system |
| CN103462644A (en) * | 2012-06-07 | 2013-12-25 | 中国科学院深圳先进技术研究院 | Photoacoustic endoscope |
| CN103385758A (en) * | 2013-07-22 | 2013-11-13 | 深圳先进技术研究院 | Intravascular opto-acoustic and ultrasonic dual-mode imaging system and imaging method thereof |
| US20160242737A1 (en) * | 2013-10-07 | 2016-08-25 | The Regents Of The University Of California | Integrated Ultrasound, OCT, PA and/or Florescence Imaging Endoscope for Diagnosing Cancers in Gastrointestinal, Respiratory, and Urogenital Tracts |
| CN204274504U (en) * | 2014-10-21 | 2015-04-22 | 白晓苓 | Ultrasonic/optics double-mode imaging the probe of a kind of based endoscopic imaging |
| CN106691396A (en) * | 2017-02-28 | 2017-05-24 | 华南师范大学 | Intravascular fluorescent-photoacoustic-ultrasonic multi-mode imaging device and method |
| CN108618758A (en) * | 2018-04-27 | 2018-10-09 | 华南师范大学 | Intravascular photoacoustic-optical coherence tomography-near infrared light multi-modality imaging apparatus and method |
Cited By (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN110464309A (en) * | 2019-08-27 | 2019-11-19 | 深圳大学 | A kind of fluorescent endoscopic imgaing system across scale |
| CN111419149A (en) * | 2020-03-13 | 2020-07-17 | 上海应用技术大学 | Multi-mode endoscope and endoscopic imaging system |
| CN111387947A (en) * | 2020-04-07 | 2020-07-10 | 中国科学院苏州生物医学工程技术研究所 | Multi-mode microscopic endoscopic imaging device and method |
| CN113080870A (en) * | 2021-04-12 | 2021-07-09 | 北京航空航天大学 | Imaging system |
| CN114159029A (en) * | 2021-11-30 | 2022-03-11 | 深圳先进技术研究院 | Optical coherence tomography system and imaging catheter thereof |
| CN115919372A (en) * | 2023-01-28 | 2023-04-07 | 深圳先进技术研究院 | Multimode endoscopic imaging system based on short wave near-infrared fluorescence |
| CN115989989A (en) * | 2023-02-15 | 2023-04-21 | 暨南大学 | Omnibearing rotary scanning endoscopic imaging device based on optical fiber sensor |
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