WO2020113570A1

WO2020113570A1 - Multi-mode cholangiopancreatography system

Info

Publication number: WO2020113570A1
Application number: PCT/CN2018/119871
Authority: WO
Inventors: 马腾; 王丛知; 胡德红; 盛宗海; 肖杨; 郑海荣
Original assignee: 深圳先进技术研究院
Priority date: 2018-12-07
Filing date: 2018-12-07
Publication date: 2020-06-11

Abstract

A multi-mode cholangiopancreatography system, comprising: an image processing system (1); a first optical imaging system (2); an ultrasonic imaging system (3); an endoscope probe (10) which is provided with an optical probe component (10-3) and an ultrasonic transducer (10-5); a photoelectric slip ring component (6) driving the endoscope probe (10) to rotate, the photoelectric slip ring component (6) comprising a rotary photoelectric coupling unit (7) and a rotation driving device (8) for driving the rotary photoelectric coupling unit (7) to rotate, and a photoelectric slip ring being provided in the rotary photoelectric coupling unit (7); a first optical fiber (4) connecting the first optical imaging system (1) to one end of the photoelectric slip ring; a second optical fiber (10-1) connecting the other end of the photoelectric slip ring to the optical probe component (10-3); a first electric signal line (5) connecting the ultrasonic imaging system (3) to one end of the photoelectric slip ring; and a second electric signal line (10-2) connecting the other end of the photoelectric slip ring to the ultrasonic transducer (10-5). According to the multi-mode cholangiopancreatography system, by means of optical and ultrasonic cooperative imaging, the resolution ratio of imaging and an imaging depth are increased, and the system is applicable to cholangiopancreatography.

Description

Multimodal pancreaticobiliary imaging system

Technical field

The invention relates to the technical field of endoscopic imaging equipment, in particular to a multimodal pancreaticobiliary imaging system.

Background technique

Malignant lesions of the pancreaticobiliary duct often originate from endothelial cells of the pancreatic duct or bile duct. Its formation is usually a dynamic process: initially manifested as dysplasia of pancreatic bile duct epithelial cells, which further infiltrated and grown into the pancreatic bile duct basement membrane, and developed into invasive adenocarcinoma after breaking through the basement membrane. In this process, the typical histomorphological changes of the pancreaticobiliary duct epithelium are mainly reflected in the abnormalities in both structure and cytology. Structural abnormality means that the normal pancreatic bile duct epithelium is gradually replaced by neatly arranged single-layer cubic or low columnar epithelium, which is replaced by high columnar cells rich in mucous cytoplasm. Epithelial cell arrangement disorder and normal cell polarity loss occur; cytological abnormality refers to the nucleus Irregular, deep staining of chromatin, the size of the nucleus is different, the proportion of nucleus and cytoplasm is increased and the activity of mitosis is increased. When the dysplastic cells continue to grow, breaking through the basement membrane and infiltrating into the organ parenchyma, they develop into ductal adenocarcinoma with deep infiltration. Accurate judgment of morphological abnormalities at this stage is a major challenge for clinical diagnosis and treatment of pancreaticobiliary malignant tumors.

The pancreas is the largest gland in the human body after the liver, and is deeper. Once malignant lesions occur in the pancreas and gallbladder, they often have the characteristics of hidden disease, rapid progress, high recurrence rate and early metastasis. Due to the deep location of the pancreas and gallbladder, it is extremely difficult to diagnose and treat such lesions early. At present, there is a lack of efficient early diagnosis methods and effective molecular labeling techniques for pancreaticobiliary malignant tumors, and the mechanism of pancreaticobiliary lesions is still unclear. Most of the clinically diagnosed patients are already in the advanced stage, and the prognosis is extremely poor. The 5-year survival rate of patients after treatment is less than 5%. Pancreatic cancer is also known as "the king of cancer." Therefore, the development of early diagnosis and treatment equipment with high sensitivity, high specificity and clinical applicability is a prospective demand for the diagnosis and treatment of pancreaticobiliary duct cancer.

Transabdominal ultrasound (operating frequency is 5MHz) is the first choice for imaging of high-risk pancreatobiliary cancer patients and clinically suspected pancreatobiliary cancer patients because of its advantages of simplicity, economy, non-invasive, repeatable examination and relatively accurate. means. However, due to ultrasound echo attenuation and intestinal gas interference, the image resolution is low, and the diagnosis rate of pancreatic tumors less than 2 cm is only 21.0% to 64.5%, and the pancreaticobiliary duct cannot be effectively imaged. CT and MRI are currently the most commonly used standard methods for diagnosing pancreaticobiliary malignant tumors in the clinic. Direct and indirect signs can show pancreaticobiliary masses or local enlargement, continuous interruption of pancreaticobiliary duct, but for smaller tumors (diameter ≤ The diagnosis rate of 2cm) is only about 75%. Since the vast majority of pancreaticobiliary malignant tumors originate from the corresponding duct intima, the anatomical channels of the pancreatic duct and bile duct provide the possibility for the development of endoscopic interventional imaging technology. Endoscopic interventional imaging technology can make more detailed observation and accurate analysis of pancreatic gallbladder morphology and structure at the macro and micro levels. Among them, EUS combines endoscopy and laparoscopy on the basis of ultrasound to achieve guided fine needle aspiration biopsy of pancreaticobiliary space-occupying lesions, which improves the sensitivity, specificity and specificity of the diagnosis of primary and secondary pancreaticobiliary tumors. Accuracy has become the gold standard for surgical operations. However, because the operating frequency of EUS is as low as that of transabdominal ultrasound, this also limits its ability to image pancreaticobiliary duct structures and small lesions. Intraductal ultrasonography (IDUS) can be directly placed into the pancreaticobiliary duct for real-time imaging through the endoscopic clamp channel. The high-frequency micro-ultrasound probe can be directly placed into the pancreaticobiliary duct for real-time imaging. The depth is limited and it is difficult to pass the distal end of the pancreaticobiliary duct. In addition, due to its low operating frequency, the resolution is not sufficient for clear imaging of the pancreaticobiliary duct intima structure. Pancreatoscopy with a diameter of less than 1mm can be directly inserted into the pancreaticobiliary duct and directly imaged. It is important for the diagnosis of early pancreaticobiliary carcinoma, but it can only provide surface information on the inner wall of the pancreaticobiliary duct.

In recent years, many new imaging technologies have been continuously developed, which has brought new methods to pancreaticobiliary duct tumor imaging. Including endoscopic ultrasound imaging, optical coherence tomography, fluorescence imaging, photoacoustic imaging and confocal imaging.

Endoscopic ultrasound imaging can achieve tomographic imaging of pancreatic duct intima. Taking advantage of the deeper depth of ultrasound detection, comprehensive evaluation of the lesions beyond the OCT detection range, especially the deeper identification and identification of the depth of tumor invasion, the effective combination of the two fully reflects the biological characteristics of pancreaticobiliary tumors, The progress of the disease is also more detailed.

Optical coherence tomography (Optical Coherence tomography, OCT) has the characteristics of volume and tomography, high resolution and deep imaging depth. Endoscopic OCT (Endoscopic OCT, E-OCT), as an important branch of OCT technology, guides the light to the organ and tissue to be tested through the probe, which can overcome the weak point of limited light penetration depth and obtain high-resolution tomography of organ depth in the human body Images, so as to carry out high-resolution imaging of the parts of interest in clinical diagnosis, and realize the early diagnosis of diseases through histomorphological research.

On the basis of fluorescence imaging, a point-by-point illumination of the laser beam and spatial pinhole modulation to remove scattered light from the non-focus plane of the sample can form a new imaging technology, confocal microscopy (CM). Confocal microscopy uses a laser as the scanning light source. After focusing through a high-power objective lens, the sample tissue is scanned and imaged point by line, line by line, and the fluorescence collected by the laser shares an objective lens. The focus of the objective lens is the focus point of the scanning laser. It is also the object point of instantaneous imaging. After the system is focused once, the scan is limited to one plane of the sample. When the depth of focus is not the same, you can obtain images of different depth levels of the sample. These image information are stored in the computer. Through computer analysis and simulation, the three-dimensional structure of the sample can be displayed.

Photoacoustic imaging (PAI) is a new non-invasive and non-ionizing biomedical imaging method. The laser beam enters the sample tissue, and the biological tissue absorbs the energy of the laser beam. The beam energy at the focal point of the beam causes expansion and contraction of the local area of the tissue, thereby sending out an ultrasonic signal, which is called a photoacoustic signal. Different tissue components absorb light differently, so the photoacoustic signal carries the characteristics of tissue light absorption. By detecting this signal through the ultrasonic transducer (10-5), image information of the tissue can be obtained. Photoacoustic imaging has the characteristics of higher resolution of optical imaging and also has the advantage of high imaging depth of ultrasound imaging.

Among the above four optical imaging (optical coherence tomography, fluorescence imaging, photoacoustic imaging, and confocal imaging) methods, OCT imaging and photoacoustic imaging have a larger imaging depth and lower resolution. The corresponding fluorescence imaging and confocal imaging have higher resolution and the imaging depth is very shallow.

To sum up, the key to early pancreaticobiliary duct cancer imaging is to achieve tomography imaging, comprehensive in-vivo and tomographic imaging, high resolution and imaging depth in several aspects of clinical requirements. If you want to obtain high-resolution methods, the current mainstream methods are high-frequency ultrasound, optical coherence tomography (OCT), fluorescence imaging and confocal imaging. The imaging depth of these imaging technologies is relatively shallow, so the imaging ability must be thrown to the location of pancreaticobiliary duct lesions through endoscopic methods.

Therefore, how to provide a system suitable for pancreaticobiliary duct imaging has become an urgent problem for those skilled in the art.

Summary of the invention

In view of this, the present invention provides a multimodal pancreaticobiliary duct imaging system, so as to be suitable for pancreaticobiliary duct imaging.

To achieve the above objectives, the present invention provides the following technical solutions:

A multi-modal pancreaticobiliary imaging system, including:

Image processing system;

A first optical imaging system in communication with the image processing system;

An ultrasound imaging system connected to the image processing system;

An endoscopic probe, which has an optical probe component capable of performing optical imaging detection and an ultrasonic transducer capable of performing ultrasonic imaging detection;

A photoelectric slip ring assembly that drives the endoscope probe to rotate; the photoelectric slip ring assembly includes a rotary photoelectric coupling unit and a rotary drive device that drives the rotary photoelectric coupling unit to rotate, and the rotary photoelectric coupling unit has a photoelectric Slip ring

A first optical fiber connecting the first optical imaging system and one end of the photoelectric slip ring;

Connecting the other end of the photoelectric slip ring to the second optical fiber of the optical probe component;

A first electrical signal line connecting the ultrasonic imaging system and one end of the photoelectric slip ring;

Connect the other end of the photoelectric slip ring to the second electrical signal line of the optical probe component.

Preferably, in the above multi-modal pancreaticobiliary duct imaging system, the photoelectric slip ring includes a smooth ring structure and

Electric slip ring structure;

The smooth ring structure includes two independent optical collimators. The two optical collimators can transmit to each other in free space. The two optical collimators are respectively connected to the first optical fiber and the optical fiber. Second fiber connection;

The electric slip ring structure includes two point slip rings that are in contact with each other and can rotate relatively, and the two point slip rings are respectively connected to the first electrical signal line and the second electrical signal line.

Preferably, the above multi-modal pancreaticobiliary duct imaging system further includes:

A second optical imaging system connected to the image processing system, the second optical imaging system is a confocal endoscope system or a fluorescence imaging system; the first optical imaging system is an optical coherence tomography system or photoacoustic imaging system;

A wavelength division multiplexer that multiplexes the second optical imaging system and the first optical imaging system together and connects to the first optical fiber.

Preferably, in the above multi-modal pancreaticobiliary duct imaging system, the second optical imaging system is a fluorescence imaging system, and the first optical imaging system is an optical coherence tomography imaging system;

The wavelength division multiplexer multiplexes the fluorescence imaging system and the OCT sample arm of the optical coherence tomography system together and is connected to the first optical fiber.

Preferably, the above multi-modal pancreaticobiliary duct imaging system further includes a main trigger for synchronizing the ultrasound of the ultrasound imaging system and the fluorescence imaging of the fluorescence imaging system.

Preferably, in the above multimodal pancreaticobiliary duct imaging system, the fluorescence imaging system further includes a double-clad fiber coupler for collecting emitted fluorescence.

Preferably, in the above multi-modal pancreaticobiliary duct imaging system, the excitation light source of the fluorescence imaging system is a semiconductor laser;

The light source of the optical coherence tomography system is a VCSEL light source.

Preferably, the above multimodal pancreaticobiliary duct imaging system further includes an endoscopic probe sleeve connected to the endoscopic probe, and the second optical fiber and the second electrical signal line are located in the endoscopic probe sleeve.

Preferably, in the above multi-modal pancreaticobiliary duct imaging system, the endoscopic probe further includes:

An anti-twist sleeve that accommodates the optical probe component and the ultrasonic transducer;

A marking ring provided in the anti-rotation sleeve.

Preferably, in the above multi-modal pancreaticobiliary duct imaging system, the optical probe component is a ball lens.

Preferably, in the above multi-modal pancreaticobiliary duct imaging system, the center frequency of the ultrasonic transducer is ≥50MHz;

The maximum size of the ultrasonic transducer is not greater than 0.6mm.

Preferably, in the above multimodal pancreaticobiliary duct imaging system, the direction of the light beam emitted by the optical probe component is opposite to the direction of the sound beam emitted by the ultrasonic transducer.

It can be seen from the above technical solutions that the multi-modal pancreaticobiliary duct imaging system provided by the present invention has a first optical imaging system and an ultrasound imaging system, and the endoscope probe also has an optical probe component capable of optical imaging detection and An ultrasonic transducer capable of ultrasonic imaging detection, the first optical fiber and the second optical fiber are rotationally connected by a rotary photoelectric coupling unit, the first electrical signal line and the second electrical signal line are rotationally connected by a rotary photoelectric coupling unit, and the second optical fiber The light beam is turned through the optical focusing unit in the endoscopic probe and emitted to the sample tissue. The second electrical signal line will drive the ultrasonic transducer in the endoscopic probe to emit high-frequency ultrasound and also shoot at the sample tissue. Under the driving, the endoscopic probe rotates at a uniform speed, thereby realizing the imaging of the pancreaticobiliary duct. The optical signal incident on the sample tissue will be sent to the first optical imaging system through the optical focusing unit, the second optical fiber, the photoelectric slip ring and the first optical fiber (the original path returns) in the endoscopic probe, and is displayed after being processed by the image processing system. The ultrasonic signal reflected from the sample tissue will also be received by the ultrasonic transducer in the endoscopic probe and converted into an electrical signal, through the second electrical signal line, the photoelectric slip ring and the first electrical signal line (the original return) to It is displayed in the ultrasound imaging system and processed by the image processing system, thus completing the endoscopic imaging process of the pancreaticobiliary duct. In the entire imaging system, the ultrasound imaging system can be used as a standing imaging, and the first optical imaging system can be used as an auxiliary imaging method and displayed after being processed by the image processing system, thereby completing the endoscopic imaging process of the pancreaticobiliary duct. The multi-modal pancreaticobiliary duct imaging system provided by the present invention, on the one hand, takes advantage of the higher resolution of optical imaging to provide high-resolution tomographic information; on the other hand, it takes advantage of the deeper depth of ultrasound imaging to detect more than the first optical imaging The comprehensive detection of the lesions in the system's detection range, especially the deeper identification and recognition of the depth of tumor infiltration, the effective combination of the two fully reflects the biological characteristics of pancreaticobiliary tumors, and also provides a more detailed description of the disease progression Interpretation. Therefore, through multi-modality (optical and ultrasound) collaborative imaging, the resolution and depth of imaging are improved, which can effectively identify the changes of pancreatic and bile duct epithelial cells in the early stage of the lesion, and is suitable for pancreatic and bile duct imaging.

BRIEF DESCRIPTION

In order to more clearly explain the embodiments of the present invention or the technical solutions in the prior art, the following will briefly introduce the drawings required in the embodiments or the description of the prior art. Obviously, the drawings in the following description are only These are some embodiments of the present invention. For those of ordinary skill in the art, without paying any creative work, other drawings can be obtained based on these drawings.

FIG. 1 is a first structural schematic diagram of a multi-modal pancreaticobiliary duct imaging system provided by an embodiment of the present invention;

2 is a schematic diagram of a second structure of a multi-modal pancreaticobiliary duct imaging system provided by an embodiment of the present invention;

3 is a schematic structural diagram of an endoscope probe provided by an embodiment of the present invention.

detailed description

The invention discloses a multi-modal pancreaticobiliary duct imaging system, which is suitable for pancreaticobiliary duct imaging.

The technical solutions in the embodiments of the present invention will be described clearly and completely in conjunction with the drawings in the embodiments of the present invention. Obviously, the described embodiments are only a part of the embodiments of the present invention, but not all the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by a person of ordinary skill in the art without making creative efforts fall within the protection scope of the present invention.

Please refer to FIG. 1, FIG. 2 and FIG. 3, FIG. 1 is a schematic diagram of a first structure of a multimodal pancreaticobiliary duct imaging system provided by an embodiment of the present invention; FIG. 2 is a multimodal pancreaticobiliary duct imaging system provided by an embodiment of the present invention FIG. 3 is a schematic structural diagram of an endoscopic probe provided by an embodiment of the present invention.

An embodiment of the present invention provides a multimodal pancreaticobiliary duct imaging system, including: an image processing system 1, a first optical imaging system 2 connected to the image processing system 1; an ultrasonic imaging system 3 connected to the image processing system 1; Spy probe 10, endoscopic probe 10 has an optical probe part 10-3 capable of optical imaging detection and an ultrasonic transducer 10-5 capable of ultrasonic imaging detection; a photoelectric slip ring assembly 6 that drives the rotation of the endoscopic probe 10; photoelectric The slip ring assembly 6 includes a rotary photoelectric coupling unit 7 and a rotary drive device 8 that drives the rotary photoelectric coupling unit 7 to rotate. The rotary photoelectric coupling unit 7 has a photoelectric slip ring; the one connecting the first optical imaging system 2 and the photoelectric slip ring First optical fiber 4 at one end; connect the other end of the photoelectric slip ring to the second optical fiber 10-1 of the optical probe part 10-3; connect the ultrasonic imaging system 3 to the first electrical signal line 5 at one end of the photoelectric slip ring; connect the photoelectric The other end of the slip ring is connected to the second electrical signal line 10-2 of the optical probe part 10-3.

The multimodal pancreaticobiliary duct imaging system provided by an embodiment of the present invention has a first optical imaging system 2 and an ultrasound imaging system 3, and an endoscopic probe 10 also has an optical probe component 10-3 capable of optical imaging detection and capable For the ultrasonic transducer 10-5 for ultrasonic imaging detection, the first optical fiber 4 and the second optical fiber 10-1 are rotationally connected by the rotary photoelectric coupling unit 7, and the first electrical signal line 5 and the second electrical signal line 10-2 pass The rotating photoelectric coupling unit 7 rotates and communicates. The light beam of the second optical fiber 10-1 is turned and emitted to the sample tissue by the optical focusing unit in the endoscope probe 10. The second electrical signal line 10-2 will drive the light in the endoscope probe 10. The ultrasonic transducer emits high-frequency ultrasound and also shoots at the sample tissue. Under the drive of the rotary drive device 8, the endoscopic probe 10 rotates at a uniform speed, thereby realizing imaging of the pancreaticobiliary duct. The optical signal incident on the sample tissue will pass through the optical focusing unit in the endoscopic probe 10, the second optical fiber 10-1, the photoelectric slip ring and the first optical fiber 4 (original return) to the first optical imaging system 2 and undergo image processing Displayed after system 1 is processed. The ultrasonic signal reflected from the sample tissue will also be received by the ultrasonic transducer 10-5 in the endoscopic probe 10 and converted into an electrical signal through the second electrical signal line 10-2, the photoelectric slip ring and the first electrical signal Line 5 (return to the original path) is sent to the ultrasound imaging system 4 and processed by the image processing system 1 to be displayed, thereby completing the endoscopic imaging process of the pancreaticobiliary duct. In the entire imaging system, the ultrasound imaging system 3 can be used as a standing imaging, and the first optical imaging system 2 can be used as an auxiliary imaging method and displayed after being processed by the image processing system 1, thereby completing the endoscopic imaging process of the pancreaticobiliary duct. The multi-modal pancreaticobiliary duct imaging system provided by the embodiment of the present invention, on the one hand, takes advantage of the higher resolution of optical imaging to provide high-resolution tomographic information; on the other hand, the advantage of using ultrasound imaging to detect deeper depths is better than the first The comprehensive evaluation of the lesions of the detection range of the optical imaging system 2, especially the deeper identification and identification of the depth of tumor invasion, the effective combination of the two fully reflects the biological characteristics of pancreaticobiliary tumors, and also the disease progression More detailed explanation. Therefore, through multi-modality (optical and ultrasound) collaborative imaging, the resolution and depth of imaging are improved, which can effectively identify the changes of pancreatic and bile duct epithelial cells in the early stage of the lesion, and is suitable for pancreatic and bile duct imaging.

Preferably, in the multimodal pancreaticobiliary duct imaging system provided by the embodiment of the present invention, the image processing system 1 includes a computer and a display.

In this embodiment, the photoelectric slip ring includes a smooth ring structure and an electric slip ring structure; the smooth ring structure includes two independent optical collimators. The two optical collimators can transmit to each other in free space. The two optical collimators The straightener is connected to the first optical fiber 4 and the second optical fiber 10-1 respectively; the electric slip ring structure includes two point slip rings that are in contact with each other and can rotate relatively, and the two point slip rings are respectively connected to the first electrical signal line 5 and the first The second electrical signal line 10-2 is connected.

As shown in FIGS. 1 and 3, in the first embodiment, the sample arm 2-1 of the first optical imaging system 2 outputs a swept light beam, and the light beam is introduced into the rotary photoelectric coupling unit 7 through the first optical fiber 4 . At the same time, the ultrasound imaging system 3 sends out an ultrasound excitation signal to the rotary photoelectric coupling unit 7 through the first electrical signal line 5. The smooth ring structure in the rotating photoelectric coupling unit 7 includes a spatial light transmission system composed of two optical collimators. The light in the first optical fiber 4 is collimated by one optical collimator and then transmitted to another optical collimator in free space. The straightener, after being coupled, retransmits into the second optical fiber 10-1. The two optical collimators are spatially separated in mechanical structure. Therefore, the two optical collimators can maintain the transmission of optical signals under the condition of relative rotation. The electric slip ring structure in the rotating photoelectric coupling unit 7 includes point slip rings that are in contact with each other and can rotate relatively. Can be relatively rotated while maintaining electrical signal transmission.

As shown in FIG. 1, this embodiment is a two-mode pancreaticobiliary duct imaging system. Compared with a single modal pancreaticobiliary duct imaging system, the imaging resolution and imaging depth are effectively improved.

As shown in FIG. 2, this embodiment is a three-mode pancreaticobiliary duct imaging system. The multi-modal pancreaticobiliary duct imaging system further includes: a second optical imaging system 11 in communication with the image processing system 1. The second optical imaging system 11 is a common Focusing endoscope system or fluorescence imaging system; the first optical imaging system 2 is an optical coherence tomography system or a photoacoustic imaging system; the wavelength division multiplexer 12, the wavelength division multiplexer 12 converts the second optical imaging system 11 and the first An optical imaging system 2 is multiplexed and connected to the first optical fiber 4. It can be understood that, OCT imaging and photoacoustic imaging have a larger imaging depth and lower resolution. Fluorescence imaging and confocal imaging have higher resolution and the imaging depth is very shallow. The second optical imaging system 11 and the first optical imaging system 2 are multiplexed together by the wavelength division multiplexer 12 and connected to the first optical fiber 4, which further improves the imaging resolution and imaging depth.

Further, in this embodiment, the second optical imaging system 11 is a fluorescence imaging system, and the first optical imaging system 2 is an optical coherence tomography system; the wavelength division multiplexer 12 converts the fluorescence imaging system and the optical coherence tomography The OCT sample arm 2-1 of the system is multiplexed and connected to the first optical fiber 4.

The light output from the sample arm 2-1 of the optical coherence tomography system and the light output from the sample arm of the fluorescence imaging system are coupled in a wavelength division multiplexer 12. It is then output into the rotating photoelectric coupling unit 7 through the first optical fiber 4 (multimode optical fiber). The ultrasound control electrical signal in the ultrasound imaging system 3 is also input into the rotating photoelectric coupling unit 7 through the first electrical signal line 5. The photoelectric slip ring in the rotating photoelectric coupling unit 7 includes a smooth ring structure and an electric slip ring structure; it can transmit optical signals and electrical signals synchronously with relative rotation at both ends.

Among them, the rotation drive device 8 is a rotation motor. The rotation of the rotating photoelectric coupling unit 7 is powered by the rotation driving device 8.

As shown in FIG. 2, in this embodiment, the output of the sample arm 2-1 of the optical coherence tomography system (first optical imaging system 2) and the output of the sample arm of the fluorescence imaging system (second optical imaging system 11) The light is coupled in a wavelength division multiplexer (WDM) 12. Then it is output to the rotating photoelectric coupling unit 7 through the first optical fiber (multimode optical fiber) 4. The ultrasound control electrical signal in the ultrasound imaging system 3 is also input into the rotating photoelectric coupling unit 7 through the first electrical signal line 5. The rotating photoelectric coupling unit 7 can transmit the optical signal and the electrical signal synchronously when the two ends are relatively rotated. The rotation of the rotary photoelectric coupling unit 7 is powered by a rotary motor (rotation drive 8). The combination of the rotating photoelectric coupling unit 7 and the rotating motor constitutes the photoelectric slip ring assembly 6. The endoscopic probe tube 9 contains a second optical fiber 10-1 for transmitting OCT and fluorescent signals and a second electrical signal line 10-2 for transmitting ultrasonic signals. The endoscopic probe 10 integrates an optical system for focusing the light beam (optical probe part) 10-3) and an ultrasonic transducer 10-5. The light beam of the second optical fiber 10-1 in the endoscopic probe sleeve 9 is turned by the optical probe part 10-3 (optical focusing module) in the endoscopic probe 10 and emitted to the sample tissue, and the second electrical signal line 10 that transmits the ultrasonic signal -2 will drive the ultrasound transducer 10-5 of the endoprobe 10 to emit high frequency ultrasound and also shoot at the sample tissue. The endoscopic probe cannula 9 and the speculum probe 10 are driven by the rotating photoelectric coupling unit 7 to rotate at a uniform speed, thereby realizing imaging of the pancreaticobiliary duct.

The mid-light signal incident on the sample tissue will be returned to the optical coherence tomography system (first optical imaging system 2) and the fluorescence imaging system (second optical imaging system 11) in the same way, and is used by the optical coherence tomography system and The photodetector in the fluorescence imaging system detects and forms a digital signal, which is displayed after being processed by the image processing system 1. The ultrasound signal reflected from the sample tissue is received by the ultrasound transducer 10-5 in the endoscopic probe 10 and converted into an electrical signal, and the original path is returned to the ultrasound imaging system 3, which is processed by the image processing system 1 and displayed . Thus completing the endoscopic imaging process of the pancreaticobiliary duct.

The multi-modal pancreaticobiliary duct imaging system also includes a main trigger for the ultrasound imaging of the synchronous ultrasound imaging system 3 and the fluorescence imaging of the fluorescence imaging system. Further, the trigger signal of the scanning source laser is used as the main trigger to synchronize ultrasound and fluorescence imaging. The wavelength-division multiplexer 12 is used to combine the optical coherence tomography system and the fluorescence imaging system.

Furthermore, the fluorescence imaging system further includes a double-clad fiber coupler for collecting emitted fluorescence. A double-clad fiber (DCF) coupler is used to collect the emitted light to ensure the compactness and stability of the three-mode system.

The excitation light source of the fluorescence imaging system is a semiconductor laser. Aimed at the surface antigen CD206 of M2 macrophages specifically labeled in pancreaticobiliary carcinoma, a functional near-infrared dye indocyanine green labeled M2 macrophages was constructed as a new fluorescent probe, which specifically recognizes CD206 and is adjustable by a semiconductor laser The 680-750nm wavelength band of the laser is used as the excitation light source, and the fluorescence ≥800nm is collected by PMT (photomultiplier tube) to realize the fluorescent molecular imaging of CD206+-M2 macrophages. For the integration of the dual-mode optical path part, the wavelength division multiplexer 12 is selected according to the different wavelength conditions of the OCT/fluorescence system. The OCT sample arm 2-1 light source and the fluorescent excitation light source are integrated into the same single-mode broadband fiber optical path; used for fluorescence imaging excitation The semiconductor laser of the light source, and the double-clad fiber coupler are incorporated into the excitation and emission light transmission collection; this all-fiber optical path design ensures that the dual-mode optical path system is compact and stable.

The light source of the optical coherence tomography system is a VCSEL (Vertical Cavity, Surface, Emitting Laser, vertical resonant cavity surface emitting laser) light source.

In endoscopic imaging of the pancreaticobiliary duct, the bile duct diameter is 6-8 mm, the main pancreatic duct diameter is about 2-3 mm, and the secondary branches are thinner. In this multi-modal pancreaticobiliary duct imaging system, the SS-OCT for long-range imaging ensures clear imaging of pipes of different depths. In order to solve the above problems, a long-distance SS-OCT system is adopted, in which the VCSEL frequency scanning light source is selected as the scanning frequency light source, and its coherence length exceeds 10 mm, covering a common bile duct or pancreatic duct exceeding 6 mm.

Further, in the transmission process, the composite beam passes through the single-point mode core from the input port to the output port, and the small diameter of the single-mode core generates high energy density on the surface tissue, thereby achieving high-efficiency excitation. The large diameter of the emitted light output through the double-clad fiber coupler to the multimode fiber can improve the ability to collect the emitted light, and the corresponding filtering can be used to obtain fluorescence information in the PMT. Ultrasound imaging generates and detects ultrasound signals through a sound generator/receiver.

As shown in FIG. 3, the multimodal pancreaticobiliary duct imaging system provided by an embodiment of the present invention further includes an endoscopic probe sleeve 9 connected to an endoscopic probe 10, and a second optical fiber 10-1 and a second electrical signal line 10-2 are located Inside the endoscopic probe cannula 9.

The endoscopic probe tube 9 contains a second optical fiber 10-1 and a second electrical signal line 10-2. The endoscopic probe 10 integrates an optical probe component 10-3 capable of optical imaging detection and an ultrasonic imaging detection The ultrasonic transducer 10-5, the light beam of the second optical fiber 10-1 of the endoscope probe tube 9 is turned and emitted by the optical probe part 10-3 (the optical probe part may also be called an optical focusing module) in the endoscope probe 10 To the sample tissue, the second electrical signal line 10-2 transmitting the ultrasound signal will drive the ultrasound transducer 10-5 in the endoscopic probe 10 to emit high-frequency ultrasound and also shoot the sample tissue. The endoscopic probe cannula 9 and the speculum probe 10 are driven by the rotating photoelectric coupling unit 7 to rotate at a uniform speed, thereby realizing imaging of the pancreaticobiliary duct.

The optical signal incident on the sample tissue will return to the first optical imaging system 2 (optical coherence tomography system) through the optical probe part 10-3, the second optical fiber 10-1 and the first optical fiber 4 in the endoscopic probe 10 And displayed after being processed by the image processing system 1. The ultrasound signal reflected from the sample tissue will also be received by the ultrasound transducer 10-5 in the endoscopic probe 10 and converted into an electrical signal, passing through the second electrical signal line 10-2 and the first electrical signal line 5 Return to the ultrasound imaging system 3, and display it after processing by the image processing system 1. Thus completing the endoscopic imaging process of the pancreaticobiliary duct.

In this embodiment, the second electrical signal line 10-2 is a coaxial cable, which can shield external electromagnetic signals and obtain higher signal transmission quality. The ultrasonic excitation signal excites the high-frequency ultrasonic transducer 10-5 to excite ultrasound, and forms a high-frequency ultrasonic beam 10-9 by modulation. The high-frequency ultrasonic beam 10-9 is directed to the sample tissue and receives the echo signal using the high-frequency ultrasonic transducer 10-5. This signal is transmitted back to the ultrasound imaging system 3 through the second electrical signal line 10-2 to obtain an ultrasound image of the sample tissue.

In this embodiment, the endoscopic probe 10 further includes: an anti-twist sleeve 10-7 that accommodates the optical probe part 10-3 and the ultrasonic transducer 10-5; a marking ring 10 provided in the anti-twist sleeve 10-7 -6. The marking ring 10-6 is used to mark the position of the endoscopic probe 10 in space, thereby correcting the spatial position relationship of imaging. Preferably, the anti-twist sleeve 10-7 has a relatively high rigidity so that it does not twist at a large angle during rotation in the body.

In order to improve the resolution, the optical probe part 10-3 is a spherical lens.

The light in the second optical fiber 10-1 is modulated and shaped by a ball lens to form a focused beam 10-8. The lower surface of the ball lens is processed into an angled gold-plated oblique plane 10-4, which can turn the light beam 90°, so as to be directed toward the sample tissue. Since the beam is focused, a higher lateral resolution can be obtained. The ball lens is specially designed to eliminate artifacts and achieve higher imaging quality.

Further, the center frequency of the ultrasonic transducer 10-5 is ≥50MHz; the maximum size of the ultrasonic transducer 10-5 is not more than 0.6mm. Through the above settings, to improve the longitudinal resolution of the ultrasound image. In terms of the hardware of the ultrasound imaging system 3, a wide-band (>200MHz) sinusoidal pulse excitation will be used in conjunction with a low-noise adjustable gain amplifier to further improve the image quality of high-frequency ultrasound.

Further, the present invention further develops new piezoelectric materials, such as MEMS single crystal/epoxy resin 1-3PIN-PMN-PT relaxation ferroelectric single crystal, etc. and their properties, and analyzes their high-temperature dielectric peak and coercive electric field And the remaining polarization and other parameters, through doping modification to improve its mechanical properties and temperature stability.

In order to improve the compactness of the structure, the direction of the light beam 10-8 emitted by the optical probe part 10-3 is opposite to the direction of the sound beam 10-9 emitted by the ultrasonic transducer 10-5.

With the above arrangement, the ultrasound transducer 10-5 and the optical probe part 10-3 adopt a back-to-back structure. And the use of high sound absorption performance material as the backing material of the ultrasonic transducer 10-5 further reduces the thickness of the ultrasonic transducer 10-5 and effectively uses the space of the anti-twist sleeve 10-7. The size of the endoscopic probe 10 is effectively reduced.

In addition, the ultrasound imaging system 3 also includes high-frequency ultrasound pulse callback transceivers, ultrasound amplifiers and other devices.

The precision electronically controlled scanning platform can be integrated with a smooth ring and an electric slip ring, which are used for the control unit connecting the imaging catheter and the host, to achieve low-loss transmission of optical and electrical signals between the rotating part and the stationary part, and to realize the rotation of the imaging catheter. Withdraw the scan to obtain the mechanical motion required for three-dimensional imaging of the pancreaticobiliary duct for the withdrawal of the imaging catheter.

The above 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 apparent to those skilled in the art, and the general principles defined herein can be implemented in other embodiments without departing from the spirit or scope of the present invention. Therefore, the present invention will not be limited to the embodiments shown in this document, but should conform to the widest scope consistent with the principles and novel features disclosed in this document.

Claims

A multi-modal pancreaticobiliary imaging system, which is characterized by:

Image processing system (1);

A first optical imaging system (2) in communication with the image processing system (1);

An ultrasound imaging system (3) connected to the image processing system (1);

An endoscopic probe (10) having an optical probe part (10-3) capable of performing optical imaging detection and an ultrasonic transducer (10-5) capable of performing ultrasonic imaging detection;

A photoelectric slip ring assembly (6) driving the endoscope probe (10) to rotate; the photoelectric slip ring assembly (6) includes a rotating photoelectric coupling unit (7) and driving the rotating photoelectric coupling unit (7) to rotate The rotary drive device (8), the rotary photoelectric coupling unit (7) has a photoelectric slip ring;

Connecting the first optical imaging system (2) and the first optical fiber (4) at one end of the photoelectric slip ring;

Connect the other end of the photoelectric slip ring to the second optical fiber (10-1) of the optical probe component (10-3);

A first electrical signal line (5) connecting the ultrasonic imaging system (3) and one end of the photoelectric slip ring;

Connect the other end of the photoelectric slip ring to the second electrical signal line (10-2) of the optical probe component (10-3).
The multi-modal pancreaticobiliary duct imaging system of claim 1, wherein the photoelectric slip ring includes a smooth ring structure and an electric slip ring structure;

The smooth ring structure includes two independent optical collimators, the two optical collimators can transmit to each other in free space, and the two optical collimators are respectively connected to the first optical fiber (4) And the second optical fiber (10-1) connection;

The electric slip ring structure includes two point slip rings that are in contact with each other and can rotate relatively, and the two point slip rings are respectively connected to the first electrical signal line (5) and the second electrical signal line (10- 2) Connect.
The multimodal pancreaticobiliary duct imaging system of claim 1, further comprising:

A second optical imaging system (11) in communication with the image processing system (1), the second optical imaging system (11) is a confocal endoscope system or a fluorescence imaging system; the first optical imaging system (2 ) Is an optical coherence tomography system or a photoacoustic imaging system;

A wavelength division multiplexer (12) which multiplexes the second optical imaging system (11) and the first optical imaging system (2) together with the first An optical fiber (4) is connected.
The multi-modal pancreaticobiliary duct imaging system according to claim 3, wherein the second optical imaging system (11) is a fluorescence imaging system, and the first optical imaging system (2) is optical coherence tomography system;

The wavelength division multiplexer (12) multiplexes the fluorescence imaging system and the OCT sample arm (2-1) of the optical coherence tomography system together and is connected to the first optical fiber (4).
The multi-modal pancreaticobiliary duct imaging system according to claim 4, further comprising a main trigger for synchronizing the ultrasound of the ultrasound imaging system (3) and the fluorescence imaging of the fluorescence imaging system.
The multi-modal pancreaticobiliary duct imaging system according to claim 4, wherein the fluorescence imaging system further comprises a double-clad fiber coupler for collecting emitted fluorescence.
The multimodal pancreaticobiliary duct imaging system according to claim 4, wherein:

The excitation light source of the fluorescence imaging system is a semiconductor laser;

The light source of the optical coherence tomography system is a VCSEL light source.
The multimodal pancreaticobiliary duct imaging system according to claim 1, further comprising an endoscope probe sleeve (9) connected to the endoscope probe (10), the second optical fiber (10-1) and The second electrical signal line (10-2) is located in the endoscopic probe sleeve (9).
The multi-modal pancreaticobiliary duct imaging system according to claim 1, wherein the endoscopic probe (10) further comprises:

An anti-twist sleeve (10-7) that accommodates the optical probe component (10-3) and the ultrasonic transducer (10-5);

A marking ring (10-6) provided in the anti-rotation sleeve (10-7).
The multi-modal pancreaticobiliary duct imaging system according to claim 1, wherein the optical probe component (10-3) is a ball lens.
The multimodal pancreaticobiliary duct imaging system according to claim 1, wherein the center frequency of the ultrasonic transducer (10-5) is ≥50MHz;

The maximum size of the ultrasonic transducer (10-5) is not more than 0.6mm.
The multimodal pancreaticobiliary imaging system according to any one of claims 1-11, characterized in that the direction of the light beam (10-8) emitted by the optical probe component (10-3) and the ultrasound transducer (10-5) The sound beam (10-9) emits in the opposite direction.