CN111436908A - Optical coherence tomography endoscopic probe and imaging system - Google Patents

Optical coherence tomography endoscopic probe and imaging system Download PDF

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Publication number
CN111436908A
CN111436908A CN202010306685.8A CN202010306685A CN111436908A CN 111436908 A CN111436908 A CN 111436908A CN 202010306685 A CN202010306685 A CN 202010306685A CN 111436908 A CN111436908 A CN 111436908A
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coherence tomography
optical coherence
probe
light
optical
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李奕
孙平
刘红宇
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Daichuan Medical Shenzhen Co ltd
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Daichuan Medical Shenzhen Co ltd
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0062—Arrangements for scanning
    • A61B5/0066—Optical coherence imaging
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/00163—Optical arrangements
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/06—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor with illuminating arrangements
    • A61B1/07—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor with illuminating arrangements using light-conductive means, e.g. optical fibres
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0082—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes
    • A61B5/0084—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes for introduction into the body, e.g. by catheters

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Surgery (AREA)
  • Medical Informatics (AREA)
  • Biophysics (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Physics & Mathematics (AREA)
  • Molecular Biology (AREA)
  • Pathology (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Radiology & Medical Imaging (AREA)
  • Optics & Photonics (AREA)
  • Investigating Or Analysing Materials By Optical Means (AREA)

Abstract

The invention provides an optical coherence tomography endoscopic probe and an imaging system. An optical coherence tomography endoscopic probe comprises a protective sleeve, an optical fiber, a gradient refractive index lens group and a spectroscope. One end of the protective sleeve is a closed end, and the end surface of the inner side of the closed end is a reflecting surface. The gradient refractive index lens group is accommodated in the protective sleeve. The spectroscope is arranged at one end of the gradient refractive index lens group far away from the optical fiber, the spectroscope is used for dividing the detection light into a first detection light and a second detection light, the first detection light is reflected out from one side of the protective sleeve through the spectroscope, and the second detection light is transmitted to the reflecting surface and is reflected through the reflecting surface. The upper optical coherence tomography endoscopic probe and the imaging system can improve the imaging quality.

Description

Optical coherence tomography endoscopic probe and imaging system
Technical Field
The invention relates to an endoscope component, in particular to an optical coherence tomography endoscopic probe and an imaging system.
Background
An endoscope is a medical detection instrument which can be inserted into a body cavity or viscera of a human body to perform direct observation, diagnosis and treatment.
Optical Coherence Tomography (OCT) is a non-invasive, high-resolution, in vivo measurable biomedical imaging technique that can achieve three-dimensional imaging of structures of biological tissue at depths of 1-2 mm. OCT is an optical imaging technique, and has higher image resolution than imaging techniques such as magnetic resonance and ultrasound imaging. The resolution can reach submicron to tens of microns. However, the OCT imaging depth is limited to the penetration depth of light in biological tissues, which is only in the order of millimeters lower than that of imaging techniques such as ultrasound.
In order to overcome the problem of shallow imaging depth of OCT, researchers combine OCT with endoscopic imaging to form endoscopic OCT. Endoscopic OCT is to use endoscopic probe to make the probe light go deep into the tissue to be tested, thus realizing the detection of the body vessel, stomach intestine, trachea and other lumens, and playing an important role in assisting doctors to carry out blood vessel support, vulnerable plaque detection, early cancer diagnosis and other aspects.
In a conventional OCT system, when an OCT probe is rotated at a high speed, the distortion of an optical fiber may cause a real-time change in the polarization state of sample light, while the polarization state of reference light is unchanged, resulting in a change in the intensity of an interference signal with a polarization difference, thereby affecting the imaging quality.
Disclosure of Invention
The invention aims to provide an optical coherence tomography endoscopic probe and an imaging system which can improve imaging quality.
An optical coherence tomography endoscopic probe, comprising:
one end of the protective sleeve is a closed end, and the end surface of the inner side of the closed end is a reflecting surface;
the optical fiber is used for incidence of the detection light and is accommodated in the protective sleeve;
the gradient refractive index lens group is accommodated in the protective sleeve and arranged at one end of the optical fiber and used for receiving and converging the probe light; and
the spectroscope is arranged at one end, far away from the optical fiber, of the gradient refractive index lens group and used for dividing the detection light into first detection light and second detection light, the first detection light is reflected out of one side of the protective sleeve through the spectroscope, and the second detection light is transmitted to the reflecting surface and is reflected by the reflecting surface.
In one embodiment, the reflective surface is provided with a high reflective film layer.
In one embodiment, the beam splitter is a beam splitter prism.
In one embodiment, the light splitting prism includes a first side surface, a second side surface and a third side surface, the first side surface is opposite to the gradient refractive index lens group, light enters the light splitting prism from the first side surface, is reflected by the second side surface, exits the light splitting prism from the third side surface, and exits through the side wall of the protective sleeve.
In one embodiment, the side wall of the protection sleeve is provided with a transmission part, and the transmission part is a plane.
In one embodiment, the third side is parallel to the transmissive portion of the protective sleeve.
In one embodiment, the third side face and the transmission part of the protection sleeve are connected through an optical glue layer in an adhering mode.
In one embodiment, the optical path between the inner axis of the reflecting surface and the central point of the second side of the beam splitter prism is equal to the optical path between the focal point of the first detection light and the central point of the second side of the beam splitter prism.
An optical coherence tomography imaging system comprises a circulator, a coupler, a balanced detector, a host and an optical coherence tomography endoscopic probe, wherein light enters the optical coherence tomography endoscopic probe through the circulator and the coupler, is reflected by the optical coherence tomography endoscopic probe and is transmitted to the host through the balanced detector.
In one embodiment, the probe light irradiates the optical coherence tomography endoscope probe through the circulator and the coupler, an interference signal returned from the optical coherence tomography endoscope probe is divided into two paths through the coupler, one path of the interference signal reaches the balanced detector, the other path of the interference signal reaches the balanced detector through the circulator, and a signal collected by the balanced detector is transmitted into the host.
In the optical coherence tomography imaging system, the reference arm optical path and the sample arm optical path of the optical coherence tomography endoscopic probe are both positioned in the protective sleeve. When the endoscopic probe rotates at a high speed, the polarization states of the reference arm light path and the sample arm light path are changed in real time, and the polarization states cannot be different. Therefore, the intensity of the interference signal can not be changed, and the imaging quality of the imaging system is ensured. And the reference arm and the sample arm do not cause dispersion mismatch, so that the longitudinal resolution of the optical coherence tomography system is reduced, and the imaging quality is improved.
In addition, in the optical coherence tomography endoscopic probe, the sample arm and the reference arm both pass through the optical fiber, and the length difference of the optical fiber does not cause the optical path difference between the sample light and the reference light, so that in the endoscopic probe, the sample arm and the reference arm do not generate difference due to different optical fibers, and therefore, when the probe is replaced every time, an operator does not need to debug the optical path size of the sample arm, the operation is convenient, and the operation is convenient.
Drawings
Fig. 1 is a schematic configuration diagram of an optical coherence tomography system of the present embodiment;
fig. 2 is a schematic structural diagram of the optical coherence tomography endoscopic probe shown in fig. 1.
The reference numbers indicate that 10, an optical coherence tomography imaging system, 11, a circulator, 12, a coupler, 13, a balanced detector, 14, a host computer, 100, an optical coherence tomography endoscopic probe, 110, a protective sleeve, 111, a closed end, 112, a transmission part, 113, a reflection surface, 120, an optical fiber, 130, a gradient index mirror group, 140, a spectroscope, 141, a first side surface, 142, a second side surface, 143, a third side surface, 20, a tested tissue, L, probe light, L1, first probe light, L2 and second probe light.
Detailed Description
While this invention is susceptible of embodiment in different forms, there is shown in the drawings and will herein be described in detail, specific embodiments thereof with the understanding that the present description is to be considered as an exemplification of the principles of the invention and is not intended to limit the invention to that as illustrated.
Thus, a feature indicated in this specification will serve to explain one of the features of one embodiment of the invention, and does not imply that every embodiment of the invention must have the stated feature. Further, it should be noted that this specification describes many features. Although some features may be combined to show a possible system design, these features may also be used in other combinations not explicitly described. Thus, the combinations illustrated are not intended to be limiting unless otherwise specified.
In the embodiments shown in the drawings, directional references (such as upper, lower, left, right, front and rear) are used to explain the structure and movement of the various elements of the invention not absolutely, but relatively. These descriptions are appropriate when the elements are in the positions shown in the drawings. If the description of the positions of these elements changes, the indication of these directions changes accordingly.
The preferred embodiments of the present invention will be further described in detail below with reference to the accompanying drawings.
Referring to fig. 1, the present application provides an optical coherence tomography system. The optical coherence tomography imaging system 10 of the present embodiment includes a circulator 11, a coupler 12, a balanced detector 13, a host 14, and an optical coherence tomography endoscopic probe 100. The detection light enters the optical coherence tomography endoscopic probe 100 through the circulator 11 and the coupler 12, is reflected by the optical coherence tomography endoscopic probe 100, and is transmitted to the host 14 through the balance detector 13. The detected image generated by the detected light is finally displayed after being processed by the host 14.
In the optical coherence tomography imaging system 10, the detection light emitted by the light source 15 irradiates the optical coherence tomography endoscopic probe 100 through the circulator 11 and the coupler 12, the interference signal returned from the optical coherence tomography endoscopic probe 100 is divided into two paths through the coupler 12, one path is transmitted to the balance detector 13, the other path is transmitted to the balance detector 13 through the circulator 11, the signal collected by the balance detector 13 is transmitted to the host 14, and the tomographic structure image of the detected tissue 20 is obtained through OCT data processing.
The detection light emitted by the detection light is divided into a reference arm light path and a sample arm light path through the circulator 11 and the coupler 12, and respective return lights are converged through the coupler 12 to form an interference signal and are received by the balance detector 13. In the optical coherence tomography system 10, polarization differences and dispersion mismatches introduced when the reference arm and the sample arm are branched can be eliminated, and the imaging quality can be improved. And the optical coherence tomography imaging system 10 can avoid the problem that the reference arm needs to be adjusted, thereby being convenient for the operation of doctors.
Referring to fig. 1 and fig. 2, an optical coherence tomography endoscopic probe 100 includes a protective sleeve 110, an optical fiber 120, a gradient refractive index lens assembly 130 and a beam splitter 140. The optical fiber 120, the gradient index lens assembly 130 and the beam splitter 140 are disposed in the protective sleeve 110.
The protective sleeve 110 may be used to provide a cylindrical receiving space for receiving the optical fiber 120, the gradient index lens assembly 130 and the beam splitter 140. The protection sleeve 110 may be cylindrical or other shape. And the protection sleeve 110 may be a glass tube or a rubber tube, etc.
One end of the protection sleeve 110 is a closed end 111. The closed end 111 is the front end of the protection sleeve 110. The protective sleeve 110 is closed at the front end to protect the endoscopic probe 100 and prevent liquid from entering the endoscopic probe 100, and also prevent the probe-falling part from entering the body cavity.
The optical fiber 120 is used for inputting light. In the optical coherence tomography endoscopic probe according to the present embodiment, the optical fiber 120 is used to input probe light. The optical fiber 120 is accommodated in the protective sleeve 110. Also, the optical fiber 120 is a single mode optical fiber 120.
The gradient index lens assembly 130 is an optical imaging element designed and manufactured using a medium having a gradient refractive index, the gradient index lens assembly 130 is disposed at one end of the optical fiber 120 for receiving the probe light emitted from the optical fiber 120, the gradient index lens assembly 130 is for converging the probe light L, an optical axis of the gradient index lens assembly 130 coincides with an optical axis of the light, and the probe light converges by the gradient index lens assembly 130.
The beam splitter 140 is disposed at an end of the gradient index lens assembly 130 away from the optical fiber 120, the beam splitter 140 is configured to split the probe light L into two parts, i.e., a first probe light L1 and a second probe light L2, most of the probe light is reflected by the beam splitter 140 to become a first probe light L1, and the other part of the probe light is transmitted through the beam splitter 140 to become a second probe light L2.
The protective sleeve 110 is provided with a transmission portion 112, the transmission portion 112 is used for transmitting light, when the protective sleeve 110 is a transparent tube, all positions of the protective sleeve 110 can transmit light, it is understood that in other embodiments, the protective sleeve 110 can also be a non-transparent tube, when the protective sleeve 110 is a non-transparent tube, the transmission portion 112 is a local area on the side wall of the protective sleeve 110, the transmission portion 112 is a transparent area and can transmit a first probe light L1, the first probe light L1 transmits the protective sleeve 110 from the transmission portion 112, the first probe light L1 is reflected out of the protective sleeve 110 and irradiates on the detected tissue 20, and the first probe light L1 is scattered by the detected tissue 20 and returns to the optical fiber 120 to form sample light.
Specifically, in the present embodiment, the transmission portion 112 of the protection sleeve 110 is a square region. The transmissive portion 112 may have other shapes. The shape and area of the transmission part 112 can be designed according to the shape and size of the transmission light spot, so as to meet the transmission requirement of all light rays.
The transmission portion 112 is planar, the first detection light L1 exits through the planar transmission portion 112, so as to avoid astigmatism of the first detection light L1 after exiting, the protection sleeve 110 is provided with steps at two sides of the transmission portion 112, and the steps connect the transmission portion 112 and the cylindrical surface of the protection sleeve 110.
The inner end surface of the closed end 111 of the protection sleeve 110 is a reflecting surface 113. Specifically, the reflecting surface 113 is a highly reflecting surface. The reflecting surface 113 is for reflecting the reference light.
The second detection light L2 transmits through the beam splitter 140, travels to the closed end 111 of the protective sleeve 110, is reflected by the reflective surface 113 back to the optical fiber 120 as the reference light, the sample light scattered back by the measured tissue 20 and the reference light are coupled into an interference signal, and the interference signal is received by the balanced detector and transmitted to the host for processing.
The beam splitter 140 is disposed opposite to the transmission portion of the protection sleeve 110, so that the first detection light L1 is emitted through the transmission portion, specifically, in the present embodiment, the beam splitter 140 is a beam splitter prism.
On the one hand, the beam splitter prism turns the light beam direction from the direction along the optical axis of the protection sleeve 110 to the direction nearly perpendicular to the optical axis to irradiate the lateral tissue 20 to be detected, and on the other hand, the second side 142 of the beam splitter prism is not coated with a film or a partial reflection film to transmit the second probe light L2 and split the first probe light L1 and the second probe light L2.
The beam splitter prism includes a first side 141, a second side 142, and a third side 143. The first side 141 is disposed opposite the optical fiber 120. The first side surface 141 may be connected to the gradient index lens assembly 130 through an optical adhesive layer. The optical adhesive layer can minimize the scattering of the detection light between the gradient refractive index lens assembly 130 and the beam splitter 140. It is understood that the optical glue layer may be a UV glue layer.
The detection light L enters the beam splitter prism from the first side 141, the first detection light L1 is reflected from the second side 142 to the third side 143, and exits through the third side 143, the third side 143 is disposed opposite to the transmission portion 112, and the beam splitter prism is adhesively connected to the transmission portion 112 through an optical adhesive layer.
Moreover, the optical path between the inner axis of the reflecting surface 113 and the center point of the second side 142 of the beam splitter is equal to the optical path between the focus of the first detecting light L1 and the center point of the second side 142 of the beam splitter, or the optical path between the inner axis of the reflecting surface 113 and the center point of the second side 142 of the beam splitter is slightly smaller than the optical path between the focus of the first detecting light L1 and the center point of the second side 142 of the beam splitter.
Because the difference between the refractive indexes of the two media is small due to the transmission part 112 of the protective sleeve 110 and the beam splitter prism, the two interfaces are adhered together by the optical adhesive layer, so that the reflection noise of the detection light at the interfaces can be reduced, and the imaging quality is improved.
Specifically, in the present embodiment, the transmission portion 112 of the protection sleeve 110 is a plane, so that the detection light is transmitted through the transmission portion 112 and does not radially diverge in the protection sleeve 110, so as to prevent the detection light from diverging in the transmission portion 112, and ensure that the light spot of the detection light maintains the original shape. When the spot of the detection light is circular, the spot of the emergent detection light is still circular. Also, the surface of the transmission part 112 may be provided with a high transmission film layer. The high-transmission film layer can be used for increasing the transmissivity of the detection light and improving the imaging quality.
The third side 143 of the beam splitter prism is parallel to the plane of the transmissive portion 112. the first probe light L1 is not divergent, the size and shape of the first probe light L1 are not changed, the accuracy of the first probe light L1 line is ensured, and the imaging quality is improved.
In summary, the optical coherence tomography system has at least the following advantages over the conventional optical coherence tomography system:
first, in the optical coherence tomography system 10, the reference arm optical path and the sample arm optical path of the endoscopic probe 100 are both located in the endoscopic probe. When the endoscopic probe rotates at a high speed, the polarization states of the reference arm light path and the sample arm light path are changed in real time, and the polarization states cannot be different. Therefore, the intensity of the interference signal can not be changed, and the imaging quality of the imaging system is ensured. And the reference arm and the sample arm do not cause dispersion mismatch, so that the longitudinal resolution of the optical coherence tomography system is reduced, and the imaging quality is improved.
Moreover, in the optical coherence tomography endoscopic probe 100, the sample arm and the reference arm both pass through the optical fiber 120, and the difference in length of the optical fiber 120 does not cause the optical path difference between the sample arm and the reference arm, so that in the endoscopic probe, the sample arm and the reference arm do not generate difference due to different optical fibers 120, and therefore, when the probe is replaced each time, an operator does not need to debug the optical path size of the sample arm, and the operation is convenient and convenient.
In addition, in the endoscopic probe, the beam splitter prism can perform the functions of deflecting and splitting the optical path without adding extra devices, the endoscopic probe has a simple and compact structure and a reduced volume, the first probe light L1 is emitted through the planar transmission part 112, the phenomenon of astigmatism after the first probe light L1 is emitted is avoided, the accuracy of the first probe light L1 line is ensured, and the imaging quality is improved.
While the present invention has been described with reference to several exemplary embodiments, it is understood that the terminology used is intended to be in the nature of words of description and illustration, rather than of limitation. As the present invention may be embodied in several forms without departing from the spirit or essential characteristics thereof, it should also be understood that the above-described embodiments are not limited by any of the details of the foregoing description, but rather should be construed broadly within its spirit and scope as defined in the appended claims, and therefore all changes and modifications that fall within the meets and bounds of the claims, or equivalences of such meets and bounds are therefore intended to be embraced by the appended claims.

Claims (10)

1. An optical coherence tomography endoscopic probe, comprising:
one end of the protective sleeve is a closed end, and the end surface of the inner side of the closed end is a reflecting surface;
the optical fiber is used for incidence of the detection light and is accommodated in the protective sleeve;
the gradient refractive index lens group is accommodated in the protective sleeve and arranged at one end of the optical fiber and used for receiving and converging the probe light; and
the spectroscope is arranged at one end, far away from the optical fiber, of the gradient refractive index lens group and used for dividing the detection light into first detection light and second detection light, the first detection light is reflected out of one side of the protective sleeve through the spectroscope, and the second detection light is transmitted to the reflecting surface and is reflected by the reflecting surface.
2. The optical coherence tomography endoscopic probe of claim 1, wherein said reflective surface is provided with a highly reflective film layer.
3. The optical coherence tomography endoscopic probe of claim 1, wherein the beam splitter is a beam splitter prism.
4. The endoscopic probe according to claim 2, wherein the beam splitter prism comprises a first side, a second side, and a third side, the first side is disposed opposite to the gradient index lens set, light enters the beam splitter prism from the first side, is reflected by the second side, exits the beam splitter prism from the third side, and exits through the sidewall of the protective sleeve.
5. The optical coherence tomography endoscopic probe of claim 4, wherein the side wall of the protective sleeve is provided with a transmissive portion, the transmissive portion being planar.
6. The optical coherence tomography endoscopic probe of claim 5, wherein said third side is parallel to the transmissive portion of the protective sleeve.
7. The optical coherence tomography endoscopic probe of claim 5, wherein said third side and said transmissive portion of said protective sleeve are adhesively connected by an optical glue layer.
8. The optical coherence tomography endoscopic probe of claim 1, wherein the optical path between the inner axis of the reflection surface and the center point of the second side of the beam splitter prism is equal to the optical path between the focal point of the first probe light and the center point of the second side of the beam splitter prism.
9. An optical coherence tomography system, comprising a circulator, a coupler, a balanced detector, a host and the optical coherence tomography endoscopic probe of any one of claims 1-8, wherein light enters the optical coherence tomography endoscopic probe through the circulator and the coupler, is reflected by the optical coherence tomography endoscopic probe, and propagates to the host through the balanced detector.
10. The optical coherence tomography system of claim 9, wherein the probe light is irradiated into the optical coherence tomography endoscope probe through the circulator and the coupler, an interference signal returned from the optical coherence tomography endoscope probe is divided into two paths through the coupler, one path is connected to the balanced detector, the other path is connected to the balanced detector through the circulator, and a signal collected by the balanced detector is transmitted to the host.
CN202010306685.8A 2020-04-17 2020-04-17 Optical coherence tomography endoscopic probe and imaging system Pending CN111436908A (en)

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Application Number Priority Date Filing Date Title
CN202010306685.8A CN111436908A (en) 2020-04-17 2020-04-17 Optical coherence tomography endoscopic probe and imaging system

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Application Number Priority Date Filing Date Title
CN202010306685.8A CN111436908A (en) 2020-04-17 2020-04-17 Optical coherence tomography endoscopic probe and imaging system

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CN111436908A true CN111436908A (en) 2020-07-24

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