CN107411720B - Intravascular photoacoustic/ultrasonic imaging endoscopic probe excited by high-efficiency collimated light - Google Patents
Intravascular photoacoustic/ultrasonic imaging endoscopic probe excited by high-efficiency collimated light Download PDFInfo
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Abstract
The invention discloses an intravascular photoacoustic/ultrasonic imaging endoscopic probe excited by high-efficiency collimated light, which comprises: C-Lens, concave reflector, ultrasonic transducer, optical fiber, probe shell, and torsion coil; the C-Lens is used for collimating the pulse laser transmitted by the optical fiber, the concave reflector is used for optimizing the collimated pulse laser and reflecting the pulse laser to a sample to excite an ultrasonic signal, the ultrasonic signal is converted into an electric signal through the ultrasonic transducer and is transmitted to the acquisition system through a coaxial line, and the ultrasonic transducer can independently complete ultrasonic imaging through sending or receiving. The invention utilizes the matching use of the C-Lens and the concave reflector, and can efficiently collimate the pulse laser, thereby solving the problem that the probe deviates from the center of the blood vessel and further causes image distortion due to the laser is gathered at one point, and improving the imaging quality of the blood vessel endoscope.
Description
Technical Field
The invention relates to the research field of blood vessel endoscopy, in particular to an intravascular photoacoustic/ultrasonic imaging endoscopic probe excited by high-efficiency collimated light.
Background
In the 21 st century, cardiovascular and cerebrovascular diseases become the first killers affecting human health, and rupture of atherosclerotic plaques is the main cause of acute heart disease vascular events, and although magnetic resonance vascular imaging, angiography imaging and intravascular ultrasound imaging exist at present, the imaging modes can better present the external form or the internal contour of a blood vessel, but cannot provide local detail information of the blood vessel wall. Intravascular photoacoustic imaging is a non-invasive and non-ionizing novel biomedical imaging mode developed in recent years, has the advantages of pure photoacoustic imaging and pure ultrasonic imaging, and has the advantages of high contrast of pure optical imaging, high penetrability of pure acoustic imaging and the like. By combining the intravascular photoacoustic imaging and the intravascular ultrasonic imaging, the defect of a single imaging mode can be overcome, multi-dimensional and multi-parameter information can be provided, and the intravascular plaque condition can be diagnosed;
at present, the main devices influencing the development of the photoacoustic ultrasonic imaging in blood vessels are endoscopic probes, and the current endoscopic probe schemes mainly comprise the following two types: firstly, pulse laser is output from an optical fiber and then irradiates on a tissue through a reflector, or the pulse laser is measured by the optical fiber and directly irradiates on the tissue; secondly, after being output from the optical fiber, the pulse laser irradiates on tissues after passing through an optical element and a reflector with a converging function, such as a self-focusing lens/ball lens and other lenses; the first type of endoscopic probe has the disadvantages that pulse laser is not converged, so that the resolution of a photoacoustic image is poor; the light rate density of laser irradiated on the tissue is low due to the fact that the laser is not converged, and in order to improve imaging quality, laser energy is increased, so that the tissue receives more accumulated laser energy, and the tissue is damaged; the second type of endoscopic probe has the disadvantages that pulse laser is focused at a certain point through an optical device with a convergence function, the area of a light spot near the convergence point is greatly changed, an optimal imaging picture can be obtained on a tissue at the convergence point, but in a general experimental environment, the endoscopic probe is not generally overlapped with the center of a blood vessel, the cross section of the blood vessel is not in a standard circle, the focus point of the pulse laser is not positioned on the tissue, so that the light intensity of the laser irradiated on the tissue is obviously changed, and the obtained image is distorted. At present, the scheme of the photoacoustic ultrasonic imaging endoscopic probe at abroad mainly takes a first type of probe, and the scheme of the photoacoustic ultrasonic imaging endoscopic probe at home mainly takes a second type of probe. The patent application No. 201310309340.8 discloses an intravascular photoacoustic and ultrasonic dual-mode imaging system and an imaging method thereof, and the patent application No. 201410829245.5 discloses an intravascular imaging system and an intravascular imaging method, and the patent application No. 201210220399.5 discloses a focusing rotary scanning photoacoustic and ultrasonic intravascular endoscopic imaging device and an imaging method thereof, and belongs to the second endoscopic probe scheme.
In combination with the above reasons, the main factors influencing the photoacoustic ultrasonic imaging in the blood vessel at present are that the endoscopic probe has low utilization rate of laser, low output light rate density and too concentrated laser aggregation; the inner snooping head has low utilization rate to laser and accelerates the damage of devices; the optical rate density output by the probe is low, so that the signal to noise ratio is low, and the imaging quality is influenced; too concentrated laser concentration can cause the optical rate density irradiated on the blood vessel wall to obviously change due to the fact that the endoscopic probe is deviated from the center of the blood vessel in a general experimental environment, and imaging image distortion is caused.
Disclosure of Invention
The invention aims to overcome the defects of the prior art and provide the intravascular photoacoustic/ultrasonic imaging endoscopic probe excited by high-efficiency collimated light, which fully utilizes the characteristics of C-Lens and a concave reflector, collimates pulse laser efficiently, improves the utilization rate of the laser and the luminous flux density incident to the surface of a tissue, solves the problem of image distortion caused by deviation of the probe from the center of a blood vessel due to the fact that the laser is gathered at one point, and improves the intravascular endoscopic imaging quality.
In order to achieve the purpose, the invention adopts the following technical scheme:
the invention provides an intravascular photoacoustic/ultrasonic imaging endoscopic probe excited by high-efficiency collimated light, which comprises: the ultrasonic probe comprises C-Lens, a concave reflector, an ultrasonic transducer, an optical fiber, a probe shell and a torsion coil, wherein the C-Lens, the concave reflector and the ultrasonic transducer are fixed on the probe shell; the C-Lens is positioned between the optical fiber and the concave mirror; the ultrasonic transducer is positioned above the C-Lens, one end of the ultrasonic transducer is fixed on the probe shell, and the coaxial line of the ultrasonic transducer is connected to the photoelectric slip ring of the externally connected three-dimensional spiral scanning device; one end of the optical fiber is fixed in the probe shell, and the other end of the optical fiber is connected to a photoelectric slip ring of the three-dimensional spiral scanning device; one end of the torsion coil is fixed at the tail end of the probe shell, the other end of the torsion coil is fixed in the three-dimensional spiral scanning device, and the torsion coil contains the optical fiber and a coaxial cable of the ultrasonic transducer; the C-Lens is used for collimating the pulse laser transmitted by the optical fiber, the concave reflector is used for optimizing the collimated pulse laser and reflecting the pulse laser to a sample to excite an ultrasonic signal, the ultrasonic signal is converted into an electric signal through the ultrasonic transducer and is transmitted to the acquisition system through a coaxial line, and the ultrasonic transducer independently completes ultrasonic imaging through sending and receiving.
As a preferred technical scheme, the C-Lens collimates the pulse laser, and the concave Lens continuously optimizes the collimated pulse laser.
As a preferable technical scheme, the diameter of the C-Lens is 0.2 mm-0.9 mm, the curvature radius is 0.1 mm-1 mm, the center length is 0.2 mm-5 mm, and the distance from the end face of the optical fiber to the C-Lens is 0 mm-3 mm.
Preferably, the light reflection angle of the concave reflector is 30 to 90 °.
As a preferable technical solution, the concave reflector is a concave spherical reflector, a concave elliptical reflector, or a concave irregular reflector having a concave surface.
As a preferable technical scheme, the concave reflector is plated with a dielectric film, a silver film, a gold film, a copper film and other high-reflection films.
Preferably, the emitting surface and the receiving surface of the ultrasonic transducer face the blood vessel wall, and the receiving surface of the ultrasonic transducer is arranged in parallel with the central axis of the integrated probe.
As a preferable technical scheme, the optical fiber is a single-mode optical fiber or a multimode optical fiber, the diameter of the core of the optical fiber is 1-500 mu m, and the transmitted laser wavelength is 400-2400 nm.
Preferably, one end of the torsion coil is fixed to the endoscopic probe case, and the distal end of the probe case is included therein.
Preferably, the front end of the probe shell is a curved surface, and the diameter of the endoscopic probe is 0.5 mm-1 mm.
Compared with the prior art, the invention has the following advantages and effects:
(1) the invention uses C-Lens to replace other focusing lenses such as a self-focusing Lens, improves the imaging resolution, improves the laser utilization rate, improves the imaging quality and reduces the image distortion rate.
(2) The invention uses the C-Lens and the concave reflector to collimate the pulse laser, solves the problem of image distortion caused by the non-concentricity of the endoscopic probe and the blood vessel in the experiment, and uses the C-Lens and the concave reflector to collimate the pulse laser, so that the collimated light spot is very small, the problems of small laser energy transmitted by using a single-mode fiber and large emergent light spot caused by using a multi-mode fiber are solved, and the invention has the advantages of small light spot of the single-mode fiber and large laser energy transmitted by the multi-mode fiber.
(3) Under the influence of working environment, the used laser wavelength is near infrared light or infrared light, the C-Lens uses a material with high refractive index for the wavelength band, the material has good acid and alkali corrosion resistance, the transmittance can reach more than 99.9 percent, and the self-focusing Lens is processed by silver ions or lithium ions in special glass in an exchange manner, because a mode of gradual change along the radial direction is adopted, the transmittance of the self-focusing Lens is not high due to the material.
(4) The C-Lens of the invention adopts 8 degree wedge angle to reduce loss, improve return loss db value and improve utilization rate of laser, thus reducing loss of devices.
(5) In the invention, the pulse laser and the focusing Lens are inevitably eccentric in the actual installation of the endoscopic probe, because the focusing modes are different, the C-Lens gradual change mode is gradual change along the axial direction, the self-focusing Lens gradual change mode is gradual change along the radial direction, and the influence on the optical field distribution caused by the eccentricity of the C-Lens is far smaller than the influence on the optical field distribution caused by the eccentricity of the self-focusing Lens.
Drawings
Fig. 1 is a structural schematic diagram of an intravascular photoacoustic/ultrasonic imaging endoscopic probe with high efficiency collimated light excitation.
FIG. 2 is a schematic diagram of the light field distribution of C-Lens.
Description of the drawing reference numerals: 1. C-Lens; 2. is a concave reflector; 3. is an ultrasonic transducer; 4. an optical fiber 4; 5. a probe housing; 6. a torsion coil; 7. C-Lens lumbar spot location; 8. the distance from the beam waist is Rayleigh distance ZRThe position of (a).
Detailed Description
The present invention will be described in further detail with reference to examples and drawings, but the present invention is not limited thereto.
Examples
As shown in fig. 1, the invention discloses an intravascular photoacoustic ultrasonic imaging endoscopic probe excited by high-efficiency collimated light, which comprises: C-Lens1, concave mirror 2, ultrasonic transducer 3, optical fiber 4, probe housing 5, and torsion coil 6. The C-Lens1 is used for collimating the pulse laser emitted by the optical fiber 4, the concave reflector 2 is used for optimizing the collimated pulse laser and reflecting the pulse laser to a sample to excite an ultrasonic signal, the ultrasonic signal is converted into an electric signal by the ultrasonic transducer 3 and transmitted to an acquisition system by a coaxial line, and the ultrasonic transducer 3 can independently complete ultrasonic imaging by emitting and receiving.
The C-Lens1, the concave reflecting mirror 2 and the ultrasonic transducer 3 are fixed on an endoscopic probe shell 5; C-Lens1 is between the optical fiber 4 and the concave mirror 2; the ultrasonic transducer 3 is positioned above the C-Lens; one end of the optical fiber 4 is fixed in the integrated probe shell 5, and the other end is connected to a photoelectric slip ring of the three-dimensional spiral scanning device; one end of a torsion coil 6 is fixed at the tail end of the integrated probe shell 5, and the other end is fixed in the three-dimensional spiral scanning device, wherein the torsion coil 6 contains an optical fiber 4 and a coaxial cable of the ultrasonic transducer 3; one end of the ultrasonic transducer 3 is fixed on the integrated probe shell 5, and the coaxial line of the ultrasonic transducer 3 is connected on the photoelectric slip ring; one end of the torsion coil 6 is fixed at the tail end of the endoscopic probe shell, the other end of the torsion coil is fixed in the three-dimensional spiral scanning device, and the coaxial cable of the optical fiber 4 and the ultrasonic transducer 3 is contained in the torsion coil 6.
As shown in fig. 2, C-Lens releases the optical field of the gaussian beam, where 7 is the C-Lens waist spot position, and 8 is the rayleigh distance Z from the waist spot 7RPosition of, Rayleigh distance ZRDepending on the radius of curvature, refractive index, diameter, etc. of the spherical surface of the C-Lens, the distance (Z) between the wave surface of the Gaussian beam passing through the C-Lens and the beam waist is Rayleigh distanceR) The spot area of the wave surface is twice the waist spot, and is usually defined within a certain range (± Z) of the laser beam waistR) Is composed ofCollimation distance of Gaussian beam, within which the Gaussian beam can be regarded as parallel light, Rayleigh distance ZRThe longer the gaussian beam, the greater the collimation range.
The C-Lens1 is used for collimating the pulse laser transmitted by the optical fiber and enabling the pulse laser to approach parallel light near the waist spot; through the cooperation with concave surface speculum 2, can increase the length of parallel light, make probe adaptability stronger.
The diameter of the C-Lens is 0.2 mm-0.9 mm, the curvature radius is 0.1 mm-1 mm, the center length is 0.2 mm-5 mm, and the distance between the end face of the optical fiber and the C-Lens is 0 mm-3 mm.
The concave reflector is used for changing the propagation direction of the pulse laser, so that the pulse laser is reflected to a sample to excite an ultrasonic signal, plays a certain collimation role, continuously optimizes the pulse laser collimated by the C-Lens and reduces the collimated light spot; the primary collimation is by C-Lens.
The light reflection angle of the concave reflector is 30-90 degrees; the concave reflector is a concave spherical reflector, a concave elliptical reflector or a concave irregular reflector and the like with concave surfaces; the concave reflector is plated with a dielectric film, a silver film, a gold film, a copper film and other high-reflection films (the plating sequence is not required).
The ultrasonic transducer is positioned above the C-Lens, the emitting surface and the receiving surface of the ultrasonic transducer are opposite to the vessel wall, and the receiving surface of the ultrasonic transducer is arranged in parallel with the central axis of the integrated probe, so that the receiving efficiency of the ultrasonic transducer is ensured to be optimal.
One end of the torsion coil is fixed at the tail end of the integrated probe, the tail end of the integrated probe is contained, the other end of the torsion coil is fixed in the three-dimensional spiral scanning device, and the torsion coil contains the optical fiber and a coaxial cable of the ultrasonic transducer; the integrated probe can rotate by 360 degrees, and the torsion coil is used for ensuring that the integrated probe can all keep the same torsion rotation.
The optical fiber is single-mode and multi-mode optical fiber, the diameter of the optical fiber core is 1-500 mu m, and the transmitted laser wavelength is 400-2400 nm.
The front end of the integrated endoscopic probe is a curved surface, so that the integrated probe can enter a blood vessel and the inner wall of the blood vessel cannot be abraded; the diameter of the endoscopic probe is 0.5 mm-1 mm.
In this example, a 50 μm optical fiber was used with a C-Lens having a center length of 1.45mm and a spherical radius of curvature of 0.75mm, a spot size at 2.5mm (the radius of an adult coronary artery is generally 2mm to 2.5mm) was 100 μm, and a collimated light length was 1.8 mm; the spot size and the length of the collimated light is related to the length of the fiber end face distance C-Lens, and the corresponding parameters may be modified to obtain other data.
The above embodiments are preferred embodiments of the present invention, but the present invention is not limited to the above embodiments, and any other changes, modifications, substitutions, simplifications, combinations, and equivalents which do not depart from the spirit and principle of the present invention should fall within the protection scope of the present invention.
Claims (7)
1. An efficient collimated light excited intravascular photoacoustic/ultrasound imaging endoscopic probe, comprising: the ultrasonic probe comprises C-Lens, a concave reflector, an ultrasonic transducer, an optical fiber, a probe shell and a torsion coil, wherein the C-Lens, the concave reflector and the ultrasonic transducer are fixed on the probe shell; the C-Lens is positioned between the optical fiber and the concave mirror; the ultrasonic transducer is positioned above the C-Lens, one end of the ultrasonic transducer is fixed on the probe shell, and a coaxial cable of the ultrasonic transducer is connected to an optoelectronic slip ring of an externally connected three-dimensional spiral scanning device; one end of the optical fiber is fixed in the probe shell, and the other end of the optical fiber is connected to a photoelectric slip ring of the three-dimensional spiral scanning device; one end of the torsion coil is fixed at the tail end of the probe shell, the other end of the torsion coil is fixed in the three-dimensional spiral scanning device, and the torsion coil contains a coaxial cable of the ultrasonic transducer and the optical fiber; the C-Lens is used for collimating the pulse laser transmitted by the optical fiber, the concave reflector is used for optimizing the collimated pulse laser and reflecting the pulse laser to a sample to excite an ultrasonic signal, the ultrasonic signal is converted into an electric signal through the ultrasonic transducer and is transmitted to an acquisition system through a coaxial cable, and the ultrasonic transducer independently completes ultrasonic imaging through sending and receiving; the diameter of the C-Lens is 0.2 mm-0.9 mm, the curvature radius is 0.1 mm-1 mm, the center length is 0.2 mm-5 mm, and the distance between the end face of the optical fiber and the C-Lens is 0 mm-3 mm; the light reflection angle of the concave reflector is 30-90 degrees.
2. The highly efficient collimated light excited intravascular photoacoustic/ultrasound imaging endoscopic probe according to claim 1, wherein the concave reflector is a concave spherical reflector, a concave elliptical reflector or a concave irregular reflector.
3. The endoscopic probe for highly efficient collimated light excited intravascular photoacoustic/ultrasound imaging according to claim 1, wherein the concave reflector is coated with a dielectric film, a silver film, a gold film, a copper film and other high reflective films.
4. The highly efficient collimated light excited intravascular photoacoustic/ultrasound imaging endoscopic probe according to claim 1, wherein the exit surface and the receiving surface of the ultrasound transducer face the wall of the blood vessel, and the receiving surface of the ultrasound transducer is placed parallel to the central axis of the endoscopic probe.
5. The endoscopic probe for highly efficient collimated light excited photoacoustic/ultrasound imaging in blood vessel according to claim 1, wherein the optical fiber is a single-mode or multi-mode optical fiber, the diameter of the core of the optical fiber is 1 μm to 500 μm, and the wavelength of the transmitted laser light is 400nm to 2400 nm.
6. The highly efficient collimated light excited intravascular photoacoustic/ultrasound imaging endoscopic probe of claim 1, wherein one end of said torsion coil is fixed to and contained by said probe housing tip.
7. The endoscopic probe for highly efficient collimated light excited photoacoustic/ultrasonic imaging in blood vessel according to claim 1, wherein the front end of the probe housing is curved, and the diameter of the endoscopic probe is 0.5mm to 1 mm.
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| CN108324249B (en) * | 2018-02-07 | 2021-06-22 | 华南师范大学 | Intravascular photoacoustic imaging probe capable of simultaneously realizing optical coupling and photoacoustic excitation based on tapered optical fiber |
| CN108420459A (en) * | 2018-02-09 | 2018-08-21 | 武汉艾欧医疗科技有限公司 | A kind of blood vessel endoscope imaging probe and imaging method |
| CN108618758A (en) * | 2018-04-27 | 2018-10-09 | 华南师范大学 | Intravascular photoacoustic-optical coherence tomography-near infrared light multi-modality imaging apparatus and method |
| CN112672690A (en) * | 2018-09-19 | 2021-04-16 | 深圳迈瑞生物医疗电子股份有限公司 | Photoacoustic dual-mode imaging probe |
| CN109620296B (en) * | 2019-01-14 | 2023-09-12 | 深圳英美达医疗技术有限公司 | Butt joint mechanism of dual-mode probe |
| CN112493997B (en) * | 2020-11-30 | 2023-03-31 | 中国科学院深圳先进技术研究院 | Photoacoustic endoscopic imaging device and photoacoustic endoscopic imaging method based on same |
| CN112730374A (en) * | 2020-12-03 | 2021-04-30 | 北京信息科技大学 | Optical fiber Raman probe for detecting low-concentration components in-vivo blood |
| CN112716450A (en) * | 2020-12-23 | 2021-04-30 | 广州大学 | Photoacoustic endoscopic imaging device and system |
| CN113080871B (en) * | 2021-04-12 | 2022-09-16 | 北京航空航天大学 | Imaging system |
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| CN101912250B (en) * | 2010-05-24 | 2012-01-04 | 华南师范大学 | Intravascular photoacoustic and ultrasonic double-mode imaging endoscope device and imaging method thereof |
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