CN220695244U

CN220695244U - Endoscopic optical coherence tomography scanning detection device for skin tissue

Info

Publication number: CN220695244U
Application number: CN202321720384.5U
Authority: CN
Inventors: 李抄; 田智柯; 杨金硕
Original assignee: Individual
Current assignee: Individual
Priority date: 2023-07-03
Filing date: 2023-07-03
Publication date: 2024-04-02
Anticipated expiration: 2033-07-03

Abstract

The utility model relates to an endoscopic optical coherence tomography scanning detection device for skin tissues, which comprises a scanning probe, wherein an optical scanning structure is arranged in the scanning probe; the optical scanning structure comprises a scanning optical fiber, a collimating lens, a wedge-shaped mirror and a scanning lens; the measuring beam is led into the scanning optical fiber from the second optical fiber port, is collimated by the collimating lens after being emitted from the first optical fiber port positioned at the focus of the collimating lens, is projected onto the wedge-shaped mirror, is deflected by the wedge-shaped mirror in an angle, and is focused by the scanning lens and at the working face of the scanning lens. The utility model can simplify the structure of the optical scanning structure.

Description

Endoscopic optical coherence tomography scanning detection device for skin tissue

Technical Field

The utility model relates to the technical field of optical device structures of endoscopes, in particular to an endoscopic optical coherence tomography scanning detection device for skin tissues.

Background

Optical coherence tomography (Opitical Coherence Tomography, OCT for short) is a high resolution, non-invasive medical imaging technique developed over the last 90 years of the 20 th century. By using the basic principle of a weak coherent light interferometer, the back reflection signal detection of different depth layers of biological tissues can be realized, two-dimensional or three-dimensional structural images can be obtained through scanning, the imaging effect is similar to ultrasonic detection, but the imaging resolution is improved relatively to ultrasound. The resolution of ultrasound is generally in the mm level, while the resolution of μm level can be obtained by optical OCT detection, so that the skin cell outline can be clearly distinguished. Therefore, the optical OCT technology has been widely used for the first time in the field of ophthalmology. In addition, near infrared laser confocal microscopy can also realize imaging of skin cell structures, but the imaging depth of confocal microscopy is generally only 0.2-0.3mm, and the imaging speed of layer-by-layer scanning is low, and the imaging depth of 2-3mm can be obtained by OCT relatively, so that the OCT technology has very good practicability for disease detection in the aspect of skin.

OCT techniques have found some applications in skin detection, for example, for surface skin tissue detection, for optical coherence tomography devices for burned skin, and for non-invasive detection of endocervical skin lesions. When the device is used for noninvasive detection of cervical endothelial lesions, endoscopic detection is needed, a two-dimensional scanning galvanometer is usually used as a light beam scanning driving unit, a multi-lens structure and an elongated optical scanning system are needed to be designed, and the device has the advantages of complex structure, high cost and poor long-term reliability.

Disclosure of Invention

First, the technical problem to be solved

In view of the above-mentioned drawbacks and shortcomings of the prior art, the present utility model provides an endoscopic optical coherence tomography device for skin tissue, which solves the technical problem that the structure is too complex when the existing optical OCT detection is used for endoscopic detection.

(II) technical scheme

In order to achieve the above purpose, the main technical scheme adopted by the utility model comprises the following steps:

in a first aspect, an embodiment of the present utility model provides an endoscopic optical coherence tomography apparatus for skin tissue, including a scanning probe, wherein an optical scanning structure is disposed inside the scanning probe; the optical scanning structure comprises a scanning optical fiber, a collimating lens, a wedge-shaped mirror and a scanning lens;

the measuring beam is led into the scanning optical fiber from the second optical fiber port, is collimated by the collimating lens after being emitted from the first optical fiber port positioned at the focus of the collimating lens, is projected onto the wedge-shaped mirror, is deflected by the wedge-shaped mirror in an angle, and is focused by the scanning lens and at the working face of the scanning lens.

The endoscopic type skin tissue optical coherence tomography detection device provided by the embodiment of the utility model uses the wedge-shaped mirror as the angle deflection, the focusing position of the measuring beam at the working face can be adjusted through the angle and the position of the wedge-shaped mirror, and the structure of the optical scanning structure can be simplified.

Optionally, the optical scanning structure further comprises a hollow motor; the hollow motor is a hollow motor, the outer wall of the hollow motor is a stator, and the center of the hollow motor is a hollow rotor; the wedge-shaped mirror is fixed on the rotor at the center of the hollow motor and rotates along with the driving of the rotor of the hollow motor, so that the direction of angle deflection of the measuring beam rotates along with the rotation of the wedge-shaped mirror, and a circular scanning track is formed on the working surface of the scanning lens. The hollow motor is used for rotating the wedge-shaped mirror to serve as a light beam scanning driving unit, a two-dimensional scanning galvanometer and a multi-lens structure are not required to be arranged, the optical structure of the probe is greatly simplified, the cost is low, and the reliability is good.

Optionally, the scanning probe further comprises a fixed sleeve, a replaceable protective sleeve and a window sheet, wherein the window sheet is fastened at the front end of the replaceable protective sleeve, and the rear end of the replaceable protective sleeve is detachably connected to the interface of the fixed sleeve;

the optical scanning structure is arranged in the replaceable protective sleeve pipe, the scanning lens faces the window sheet, and the scanning optical fiber extends out of the rear end of the fixed sleeve pipe.

Optionally, the angle between the front surface and the rear surface of the wedge mirror is 3-6 °.

Optionally, the scanning detection apparatus further includes an optical coherence tomography module, the optical coherence tomography module including: the device comprises a light source, a detector, a lens, an optical fiber coupling assembly and a reference mirror;

the light beam emitted by the light source is split into a measuring light beam and a reference light beam by the optical fiber coupling assembly;

the measuring beam is emitted to a second optical fiber port to reach the optical scanning structure; the sample to be tested is scanned and returned through the reflection original path of the sample to be tested, and then sequentially passes through the second optical fiber port and the optical fiber coupling assembly to reach the detector;

the reference beam is emitted to the reference mirror through the lens, reflected by the reference mirror, formed into a parallel beam through the lens, returned in an original path, and reaches the detector after passing through the optical fiber coupling assembly;

the return beam of the measuring beam and the return beam of the reference beam form an interference signal in the detector.

Optionally, the optical fiber coupling assembly is respectively connected with the sample arm port, the reference arm port, the light source port, the reference arm port and the detection port through optical fibers;

the sample arm port is connected with the second optical fiber port; the reference arm port is arranged at the focus of the lens and is used for coupling the reference beam to enter and exit the lens; the light source port is arranged on the light source and used for coupling and transmitting light beams emitted by the light source into the optical fiber coupling assembly; the detection port is provided at an input end of the detector and is used for coupling a return beam of the measuring beam and a return beam of the reference beam into the detector.

Optionally, the light source is an SLD light source with a center wavelength of 810-1060 nm.

Optionally, the detector is a spectral detector, the wavelength detection range of which corresponds to the wavelength range of the emitted light beam of the light source.

Optionally, the scanning detection device further comprises a central control unit and a man-machine interaction unit; the hollow motor, the light source, the detector and the man-machine interaction unit are all in electrical signal communication with the central control unit.

Optionally, the window sheet is transparent and round, and an opaque straight line is printed on at least one angle on the transparent surface; one end of the opaque straight line is arranged at the center of the circle, and the other end extends to the outer edge of the circle; the width of the opaque straight line is less than 0.5mm.

(III) beneficial effects

The beneficial effects of the utility model are as follows: the endoscopic type skin tissue optical coherence tomography detection device adopts the wedge-shaped mirror structure, and the measuring light beam is focused on the working surface of the scanning lens through the scanning lens after being subjected to angle deflection by the wedge-shaped mirror.

In the preferred embodiment, the endoscopic optical coherence tomography detection device for the skin tissue uses the hollow motor rotary wedge-shaped mirror as the light beam scanning driving unit, a two-dimensional scanning galvanometer and a multi-lens structure are not required to be arranged, the optical structure of the probe is greatly simplified, the cost is low, and the reliability is good.

Drawings

Fig. 1 is a schematic structural diagram of an endoscopic optical coherence tomography device for skin tissue in the present utility model.

[ reference numerals description ]

1. A handle; 2. a connecting seat; 3. fixing the sleeve; 4. an optical fiber; 5. a replaceable sheath tube; 6. a collimating lens; 7. a hollow motor; 8. a wedge mirror; 9. a scanning lens; 10. a window sheet; 11. a sample to be tested; 12. a central control unit; 13. a man-machine interaction unit;

20. a light source; 21. a detector; 22. a lens; 23. a reference mirror;

101. an optical fiber coupling assembly; 102. a sample arm port; 103. a light source port; 104. a reference arm port; 105. a probe port;

4a, a first fiber port; 4b, second fiber port.

Detailed Description

The utility model will be better explained by the following detailed description of the embodiments with reference to the drawings.

In order that the above-described aspects may be better understood, exemplary embodiments of the present utility model will be described in more detail below with reference to the accompanying drawings. While exemplary embodiments of the present utility model are shown in the drawings, it should be understood that the present utility model may be embodied in various forms and should not be limited to the embodiments set forth herein. Rather, these embodiments are provided so that this disclosure will be thorough and complete, and will fully convey the scope of the utility model to those skilled in the art.

Referring to fig. 1, the endoscopic optical coherence tomography detection device for skin tissue comprises a scanning probe, wherein an optical scanning structure is arranged in the scanning probe; the optical scanning structure comprises a scanning optical fiber 4, a collimating lens 6, a wedge-shaped mirror 8 and a scanning lens 9; the measuring beam is guided into the scanning optical fiber 4 from the second optical fiber port 4b, is collimated by the collimating lens 6 after being emitted from the first optical fiber port 4a positioned at the focal point of the collimating lens 6, is projected onto the wedge-shaped mirror 8, is angularly deflected by the wedge-shaped mirror 8, and is focused by the scanning lens 9 and at the working surface of the scanning lens 9. The wedge-shaped mirror is used as angle deflection, the focusing position of the measuring beam at the working surface can be adjusted through the angle and the position of the wedge-shaped mirror, and the structure of the optical scanning structure can be simplified.

In practice, the optical scanning structure further comprises a hollow motor 7; the hollow motor 7 is a hollow motor, the outer wall of the hollow motor is a stator, and the center of the hollow motor is a hollow rotor; the wedge mirror 8 is fixed to the rotor at the center of the hollow motor 7 and rotates with the rotor drive of the hollow motor 7 so that the direction of angular deflection of the measuring beam follows the rotation of the wedge mirror 8 to rotate, forming a circular scanning locus on the working surface of the scanning lens 9. The hollow motor is used for rotating the wedge-shaped mirror 8 to serve as a light beam scanning driving unit, a two-dimensional scanning galvanometer (high-speed galvanometer) and a multi-lens structure are not required to be arranged, the optical structure of the probe is greatly simplified, the cost is low, and the reliability is good.

In practice, the scanning probe further comprises a handle 1, a connecting seat 2, a fixed sleeve 3, a replaceable protective sleeve 5 and a window sheet 10. The fixed sleeve 3 is fixed on the handle 1 through the connecting seat 2, the fixed sleeve 3, the fixed sleeve 2 and the window sheet 10 are in fastening connection, the window sheet 10 is fastened at the front end of the replaceable protective sleeve 5, and the rear end of the replaceable protective sleeve 5 is detachably connected at the joint of the fixed sleeve 3. The optical scanning structure is disposed within the interchangeable sheath tube 5 with the scanning lens 9 facing the window sheet 10 and the scanning optical fiber 4 protruding from the rear end of the stationary sheath tube 3. The replaceable protective sleeve 5 can be conveniently disassembled from the fixed sleeve 3, and the replaceable protective sleeve 5 and the window sheet 10 can be reused after being sterilized after being used once. When skin tissue is detected, a couplant is smeared on the outer surface of the window sheet 10, the couplant is colloidal liquid, the direct air gap between the window sheet and the skin is eliminated, and the interference of high-intensity reflected light brought by the air gap on signals is reduced.

In implementation, the included angle between the front surface and the rear surface of the wedge-shaped mirror 8 is determined by the size of the required scanning detection annular area, and in general, the included angle between the front surface and the rear surface of the wedge-shaped mirror 8 is 3-6 degrees, so that the size of the window meets the size requirement of the gynecological endoscope.

In practice, the measuring beam deflection direction will rotate and rotate along with the wedge-shaped mirror 8 to form a circular scanning track, and finally, the scanning detection is finished on the sample 11 (such as skin tissue) to be detected, and the detection area is also circular. The window sheet 10 is also round and transparent, and can be printed with a black straight line at a certain angle, one end of the straight line is used as a center of a circle, the other end of the straight line is used to reach the outer edge, the width of the straight line is smaller than 0.5mm, the straight line is opaque to the measuring light, and the straight line can also be printed with other colors for determining the initial position in the scanning process.

In practice, the scanning detection device further comprises an optical coherence tomography module, and the optical coherence tomography module comprises: light source 20, detector 21, lens 22, fiber optic coupling assembly 101, and reference mirror 23. The fiber coupling assembly 101 is coupled to the sample arm port 102, the reference arm port 104, the light source port 103, the reference arm port 104, and the probe port 105, respectively, by optical fibers. The sample arm port 102 is connected to the second fiber port 4 b.

When the embodiment is used, the following steps are adopted: the light beam emitted by the light source 20 is coupled into the optical fiber through the light source port 103, and is split into a measuring beam and a reference beam after reaching the optical fiber coupling assembly 101.

The measuring beam exits through the sample arm port 102 and the second optical fiber port 4b to reach the optical scanning structure; the sample 11 to be tested is scanned, reflected by the sample 11 to be tested and returned in the original path, and sequentially passes through the second optical fiber port 4b, the sample arm port 102 and the optical fiber coupling assembly 101 to reach the detector 21;

the reference beam is emitted to the lens 22 through the reference arm port 104 and then to the reference mirror 23, reflected by the reference mirror 23 and formed into a parallel beam through the lens 22, and returned in the original path, and reaches the detector 21 after passing through the reference arm port 104 and the optical fiber coupling assembly 101. The reference arm port 104 is disposed at the focal point of the lens 22.

The detection port 105 is provided at the input of the detector 21 and is used to couple the return beam of the measuring beam and the return beam of the reference beam into the detector 21, which form an interference signal in the detector 21.

In this embodiment, the light source 20 is an SLD (superluminescent diode) light source with a center wavelength of 810-1060 nm. The detector 21 is a spectral detector whose wavelength detection range coincides with the wavelength range of the emitted light beam of the light source 20.

In practice, the scanning detection apparatus may further include a central control unit 12 and a man-machine interaction unit 13; the hollow motor 7, the light source 20, the detector 21 and the man-machine interaction unit 13 are all in electrical signal communication with the central control unit 12. The central control unit 12 controls on/off of the light source 20, rotation/stop of the air motor 7, that is, rotation speed, acquisition of photoelectric signals of the detector 21, and the like, and completes conversion processing of the acquired photoelectric signals, and the like. The central control unit 12 is in communication with the man-machine interaction unit 13, and is capable of changing the operation mode according to the operation of the user and outputting the detection result.

The endoscopic type skin tissue optical coherence tomography scanning detection device adopts the wedge-shaped mirror as angle deflection and the hollow motor to rotate the wedge-shaped mirror as a light beam scanning driving unit, and a high-speed vibrating mirror is not required to be arranged, so that the optical structure is greatly simplified, and the endoscopic type skin tissue optical coherence tomography scanning detection device has the advantages of low cost and good reliability compared with the prior art, and is beneficial to popularization and application.

In the description of the present utility model, it should be understood that the terms "first," "second," and the like are used for descriptive purposes only and are not to be construed as indicating or implying a relative importance or number of technical features indicated. Thus, a feature defining "a first" or "a second" may explicitly or implicitly include one or more such feature. In the description of the present utility model, the meaning of "a plurality" is two or more, unless explicitly defined otherwise.

In the present utility model, unless explicitly specified and limited otherwise, the terms "mounted," "connected," "secured," and the like are to be construed broadly, and may be, for example, fixedly connected, detachably connected, or integrally formed; can be mechanically or electrically connected; can be directly connected or indirectly connected through an intermediate medium; may be a communication between two elements or an interaction between two elements. The specific meaning of the above terms in the present utility model can be understood by those of ordinary skill in the art according to the specific circumstances.

In the present utility model, unless expressly stated or limited otherwise, a first feature is "on" or "under" a second feature, which may be in direct contact with the first and second features, or in indirect contact with the first and second features via an intervening medium. Moreover, a first feature "above," "over" and "on" a second feature may be a first feature directly above or obliquely above the second feature, or simply indicate that the first feature is higher in level than the second feature. The first feature being "under", "below" and "beneath" the second feature may be the first feature being directly under or obliquely below the second feature, or simply indicating that the first feature is level lower than the second feature.

In the description of the present specification, the terms "one embodiment," "some embodiments," "examples," "particular examples," or "some examples," etc., refer to particular features, structures, materials, or characteristics described in connection with the embodiment or example as being included in at least one embodiment or example of the present utility model. In this specification, schematic representations of the above terms are not necessarily directed to the same embodiment or example. Furthermore, the particular features, structures, materials, or characteristics described may be combined in any suitable manner in any one or more embodiments or examples. Furthermore, the different embodiments or examples described in this specification and the features of the different embodiments or examples may be combined and combined by those skilled in the art without contradiction.

While embodiments of the present utility model have been shown and described above, it will be understood that the above embodiments are illustrative and not to be construed as limiting the utility model, and that alterations, modifications, substitutions and variations may be made in the above embodiments by those skilled in the art within the scope of the utility model.

Claims

1. An endoscopic optical coherence tomography detection device for skin tissue, comprising: the scanning probe is internally provided with an optical scanning structure; the optical scanning structure comprises a scanning optical fiber (4), a collimating lens (6), a wedge-shaped mirror (8) and a scanning lens (9);

the measuring beam is guided into the scanning optical fiber (4) from the second optical fiber port (4 b), is collimated by the collimating lens (6) after being emitted from the first optical fiber port (4 a) positioned at the focal point of the collimating lens (6), is projected onto the wedge-shaped mirror (8), is deflected by the wedge-shaped mirror (8) in an angle, passes through the scanning lens (9) and is focused at the working surface of the scanning lens (9).

2. The endoscopic skin tissue optical coherence tomography instrument of claim 1, wherein said optical scanning structure further comprises a hollow motor (7); the hollow motor (7) is a hollow motor, the outer wall of the hollow motor is a stator, and the center of the hollow motor is a hollow rotor;

the wedge-shaped mirror (8) is fixed on a rotor at the center of the hollow motor (7) and rotates along with the driving of the rotor of the hollow motor (7), so that the direction of angle deflection of the measuring beam rotates along with the rotation of the wedge-shaped mirror (8), and a circular scanning track is formed on the working surface of the scanning lens (9).

3. The endoscopic skin tissue optical coherence tomography instrument according to claim 1 or 2, wherein the scanning probe further comprises a fixed sleeve (3), a replaceable sheath (5) and a window sheet (10), wherein the window sheet (10) is fastened to the front end of the replaceable sheath (5), and the rear end of the replaceable sheath (5) is detachably connected to the interface of the fixed sleeve (3);

the optical scanning structure is arranged in the replaceable protective sleeve (5) and the scanning lens (9) faces the window sheet (10), and the scanning optical fiber (4) extends out of the rear end of the fixed sleeve (3).

4. The endoscopic skin tissue optical coherence tomography instrument according to claim 1 or 2, wherein the angle between the front surface and the back surface of the wedge-shaped mirror (8) is 3-6 °.

5. The endoscopic skin tissue optical coherence tomography instrument of claim 2, wherein said instrument further comprises an optical coherence tomography module comprising: a light source (20), a detector (21), a lens (22), a fiber coupling assembly (101) and a reference mirror (23);

the light beam emitted by the light source (20) is split into a measuring light beam and a reference light beam through the optical fiber coupling assembly (101);

the measuring beam exits to a second optical fiber port (4 b) to reach the optical scanning structure; the sample (11) to be detected is scanned and returned through a reflection original path of the sample (11) to be detected, and the sample passes through the second optical fiber port (4 b) and the optical fiber coupling assembly (101) to reach the detector (21);

the reference beam is emitted to a reference mirror (23) through a lens (22), reflected by the reference mirror (23) and returned in an original path after being formed into a parallel beam through the lens (22), and reaches the detector (21) after passing through the optical fiber coupling assembly (101);

the return beam of the measuring beam and the return beam of the reference beam form an interference signal in the detector (21).

6. The endoscopic skin tissue optical coherence tomography instrument of claim 5, wherein said fiber optic coupling assembly (101) is coupled to a sample arm port (102), a reference arm port (104), a light source port (103), a reference arm port (104) and a probe port (105) via optical fibers, respectively;

-the sample arm port (102) is connected to the second fiber port (4 b); the reference arm port (104) is disposed at a focal point of the lens (22) and is used to couple the reference beam into and out of the lens (22); the light source port (103) is arranged on the light source (20) and is used for coupling and transmitting light beams emitted by the light source (20) into the optical fiber coupling assembly (101); the detection port (105) is arranged at an input end of the detector (21) and is used for coupling a return beam of the measuring beam and a return beam of the reference beam into the detector (21).

7. The endoscopic skin tissue optical coherence tomography instrument of claim 5, wherein said light source (20) is an SLD light source with a center wavelength of 810-1060 nm.

8. The endoscopic skin tissue optical coherence tomography instrument according to claim 7, wherein the detector (21) is a spectral type detector having a wavelength detection range consistent with the wavelength range of the emitted light beam of the light source (20).

9. The endoscopic skin tissue optical coherence tomography detection device according to claim 5, wherein the scanning detection device further comprises a central control unit (12) and a human-computer interaction unit (13);

the hollow motor (7), the light source (20), the detector (21) and the man-machine interaction unit (13) are all in electrical signal communication with the central control unit (12).

10. An endoscopic skin tissue optical coherence tomography instrument according to claim 3, wherein said window (10) is transparent and circular and has an opaque straight line printed on at least one angle of the transparent surface; one end of the opaque straight line is arranged at the center of the circle, and the other end extends to the outer edge of the circle; the width of the opaque straight line is less than 0.5mm.