CN116530914A - Optical coherence tomography endoscope imaging method and system based on spectrum section - Google Patents
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- 238000003384 imaging method Methods 0.000 title claims abstract description 71
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- A—HUMAN NECESSITIES
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- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
- A61B5/0062—Arrangements for scanning
- A61B5/0066—Optical coherence imaging
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- A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
- A61B1/00002—Operational features of endoscopes
- A61B1/00011—Operational features of endoscopes characterised by signal transmission
- A61B1/00013—Operational features of endoscopes characterised by signal transmission using optical means
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- 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
- A61B1/00165—Optical arrangements with light-conductive means, e.g. fibre optics
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- 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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Abstract
The invention relates to the technical field of medical imaging, and discloses an optical coherence tomography endoscope imaging method and system based on spectrum section, aiming at solving the problem of low imaging precision of the existing endoscope, and mainly comprising the following steps: acquiring interference spectrum data of a position to be imaged through an endoscope probe; preprocessing the interference spectrum data, performing section processing through a window function to obtain a plurality of section spectrum data, and determining center wavelength data corresponding to each section spectrum data; zero padding is carried out on each section of spectrum data respectively, so that each section of spectrum data contains the same pixel point, and inverse Fourier transform is carried out on each section of spectrum data, so as to obtain the inverse Fourier transform absolute value distribution corresponding to each section of spectrum data; and determining the relative structure size of the position to be imaged according to the inverse Fourier transform absolute value distribution and the center wavelength data corresponding to each section of spectrum data. The invention improves the imaging precision and is particularly suitable for bone joints.
Description
Technical Field
The invention relates to the technical field of medical imaging, in particular to an optical coherence tomography endoscope imaging method and system based on spectrum segments.
Background
In order to effectively check the size, the position and the nature of the lesions of the patient, the CT and MRI examination is mainly used at present, but the CT and the MRI are possibly harmful to radiation, are not suitable for the crowds such as children, pregnant women, lactating women and the like, and have limitation in examination. Meanwhile, for a patient with bone joint disease, single CT or MRI can not effectively identify pathological changes of structures such as synovium, cartilage and the like, and pathological tissues can not be identified, so that the detection precision is poor, and at present, for the patient with bone joint disease, an endoscope technology is generally adopted to image tissues in joints, and a doctor can further judge the disease according to joint imaging.
The endoscope technology is an important application of minimally invasive surgery in the field of orthopaedics, can be used for diagnosing and treating a large number of joint diseases, such as meniscus injury, anterior and posterior cruciate ligament rupture, osteoarthritis, inflammatory joint, pigmentation villus nodular synovitis, infectious arthritis, traumatic arthritis and the like, can be used for performing intra-articular tissue excision and injury repair under the condition of non-open surgery, is generally used for performing targeted surgery under the monitoring of the endoscope, can reduce the occurrence of postoperative complications, and has the advantages of small trauma and quick recovery. Because the endoscope can observe and probe the focus under direct vision, for example, the endoscope can directly observe the intra-articular structures such as synovium, cartilage, meniscus and ligament, which is equal to putting the eyes of doctors into the joints, the endoscope has a certain amplifying effect, can dynamically observe, and has the irreplaceable advantages of CT and MRI.
The basic structure of the endoscope used in clinic at present is an optical system, the center is a rod lens system for collecting images, the periphery is an optical fiber for guiding a light source, and the outside is a metal protective sheath. In application, the endoscope is placed into the joint after a tiny incision of about 0.8 mm-1.0 cm is made on the skin, and the imaging and display device is connected to the rear of the endoscope, so that the intra-joint morphology and lesions can be directly observed, and intra-joint diseases can be treated by using special instruments, thereby avoiding a plurality of arthroplasty operations.
Although an endoscope has become an important means for orthopedic diagnosis and treatment, the imaging method is a basic optical imaging method, only the surface of a tissue can be observed, penetration examination cannot be realized, the endoscope is easily affected by joint structures and the like, the visual field is not clear enough, the microstructure changes of synovium and cartilage cannot be accurately detected, and further diseases such as early-stage joint synovitis cannot be accurately detected, and the detection precision is not high.
Disclosure of Invention
The invention aims to solve the problem that the existing endoscope imaging can not accurately detect the micro change of a joint structure, and provides an optical coherence tomography endoscope imaging method and system based on spectrum section.
The technical scheme adopted by the invention for solving the technical problems is as follows:
in one aspect, there is provided a spectral-section-based optical coherence tomography endoscopic imaging method comprising the steps of:
acquiring interference spectrum data of a position to be imaged through an endoscope probe;
preprocessing the interference spectrum data, performing section processing through a window function to obtain a plurality of section spectrum data, and determining center wavelength data corresponding to each section spectrum data;
zero padding is carried out on each section of spectrum data respectively, so that each section of spectrum data contains the same pixel point, and inverse Fourier transform is carried out on each section of spectrum data, so as to obtain the inverse Fourier transform absolute value distribution corresponding to each section of spectrum data;
and determining the relative structure size of the position to be imaged according to the inverse Fourier transform absolute value distribution and the center wavelength data corresponding to each section of spectrum data.
As a further optimization, preprocessing the interference spectrum data specifically includes:
and carrying out denoising, background removing and spectrum data calibration processing on the interference spectrum data.
As a further optimization, the inverse fourier transform absolute value distribution is used for representing the inverse fourier transform absolute value corresponding to each pixel point in the truncated spectrum data.
As a further optimization, the number of pixels contained in each segment of spectral data is 2048.
As a further optimization, determining the relative structural size of the position to be imaged according to the inverse fourier transform absolute value distribution and the center wavelength data corresponding to each section of spectral data specifically includes:
sequentially determining the section where the maximum value of the inverse Fourier transform absolute value corresponding to each same pixel point is located in Fourier transform absolute value distribution corresponding to each section of spectral data, and taking the central wavelength corresponding to the section of spectral data as the relative structural size of the imaging point corresponding to the pixel point;
and obtaining the relative structural size of the position to be imaged according to the relative structural size of the imaging point corresponding to each pixel point.
As a further optimization, the method further comprises:
and respectively comparing the relative structure size of the imaging point corresponding to each pixel point with the corresponding threshold value to obtain a relative structure size comparison result.
In another aspect, there is provided an optical coherence tomography endoscopic imaging system based on spectral segments, comprising:
the spectrometer is used for acquiring interference spectrum data of a position to be imaged through the endoscope probe;
the processing device is used for preprocessing the interference spectrum data, then carrying out section processing through a window function to obtain a plurality of section spectrum data, determining center wavelength data corresponding to each section spectrum data, carrying out zero padding on each section spectrum data respectively so that each section spectrum data contains the same pixel point, and carrying out inverse Fourier transform on each section spectrum data to obtain inverse Fourier transform absolute value distribution corresponding to each section spectrum data;
and the determining device is used for determining the relative structure size of the position to be imaged according to the inverse Fourier transform absolute value distribution corresponding to each section of spectrum data and the center wavelength data.
As a further optimization, the endoscope probe is connected with the spectrometer through a single mode fiber, and the endoscope probe comprises: the external package and the spacer, the GRIN lens, the focusing lens and the miniature scanning galvanometer which are sequentially arranged in the external package, wherein the single-mode fiber and the endoscope probe are arranged in the endoscope shell.
As a further optimization, the processing device is specifically configured to:
and carrying out denoising, background removing and spectrum data calibration processing on the interference spectrum data.
As a further optimization, the inverse fourier transform absolute value distribution is used for representing the inverse fourier transform absolute value corresponding to each pixel point in the truncated spectrum data.
As a further optimization, the number of pixels contained in each segment of spectral data is 2048.
As a further optimization, the processing device is specifically configured to:
sequentially determining the section where the maximum value of the inverse Fourier transform absolute value corresponding to each same pixel point is located in Fourier transform absolute value distribution corresponding to each section of spectral data, and taking the central wavelength corresponding to the section of spectral data as the relative structural size of the imaging point corresponding to the pixel point;
and obtaining the relative structural size of the position to be imaged according to the relative structural size of the imaging point corresponding to each pixel point.
As a further optimization, the system further comprises:
and the comparison device is used for respectively comparing the relative structural size of the imaging point corresponding to each pixel point with the corresponding threshold value to obtain a relative structural size comparison result.
The beneficial effects of the invention are as follows: the optical coherence tomography endoscope imaging method and system based on the spectrum section have the advantages of no radiation, safety and the like, and have obvious advantages for examination of some children, pregnant women and lactating women. In addition, the imaging precision is far higher than that of CT, MRI and the traditional Optical Coherence Tomography (OCT) by the endoscopic imaging method of spectrum section optical coherence tomography, doctors can distinguish the submicron structure difference of biological tissues according to the imaging result of the invention, and the invention realizes high-precision inspection of the micro structure change brought by arthromeningitis and various arthritis prophase and has obvious advantages for early inspection of arthropathy and identification of pathological tissues. According to the imaging result of the invention, doctors can more accurately identify the tissues with lesions, can better show the range to be resected in the operation, and realize the navigation function of joint operation on the basis of optical imaging.
Drawings
FIG. 1 is a flow chart of an optical coherence tomography endoscopic imaging method based on spectral cut-off according to an embodiment of the present invention;
FIG. 2 is a schematic view of an endoscope probe according to an embodiment of the present invention;
FIG. 3 is a schematic diagram of an imaging result according to an embodiment of the present invention;
FIG. 4 is a schematic diagram of an optical coherence tomography endoscopic imaging system based on spectral segments according to an embodiment of the present invention;
reference numerals illustrate:
1-a single mode optical fiber; 2-optical cement; 3-spacers; 4-GRIN lenses; a 5-focus lens; 6-miniature scanning galvanometer; 7-an outsourcing kit; 7-endoscope housing.
Detailed Description
Embodiments of the present invention will be described in detail below with reference to the accompanying drawings.
The invention aims to improve the imaging precision of an endoscope, and provides an optical coherence tomography endoscope imaging method and system based on spectrum segments, wherein the main technical scheme comprises the following steps: acquiring interference spectrum data of a position to be imaged through an endoscope probe; preprocessing the interference spectrum data, performing section processing through a window function to obtain a plurality of section spectrum data, and determining center wavelength data corresponding to each section spectrum data; zero padding is carried out on each section of spectrum data respectively, so that each section of spectrum data contains the same pixel point, and inverse Fourier transform is carried out on each section of spectrum data, so as to obtain the inverse Fourier transform absolute value distribution corresponding to each section of spectrum data; and determining the relative structure size of the position to be imaged according to the inverse Fourier transform absolute value distribution and the center wavelength data corresponding to each section of spectrum data.
It will be appreciated that the scattered light field is modulated by the spatial frequency of the sample structure being measured, and that according to the first approximation theory of the born optics, when an object is illuminated by a broad spectrum plane wave, the light field scattering distribution formed in each direction depends on the spectral content of its sample structure, with each central wavelength carrying the corresponding object spatial frequency information. The different three-dimensional spatial frequencies can thus be represented by a Ehrlich-diffraction sphere, wherein different wavelengths correspond to different Ehrlich-diffraction sphere radii, and each point on the sphere corresponds to a different three-dimensional spatial frequency. Based on the principle of wide spectrum interference of OCT, the invention finally characterizes the spatial frequency information of the object structure by analyzing the spectrum in segments and by the center wavelength in segments, thereby representing the relative structure size of imaging points of the sample. Specifically, interference spectrum data of a position to be imaged is firstly obtained through an endoscope probe, central wavelength data corresponding to each section spectrum data is determined after preprocessing and section processing is carried out on the interference spectrum data, an inverse Fourier transform absolute value corresponding to each pixel point is determined for each section spectrum data after zero padding, and finally the relative structural size of the position to be imaged is determined according to the inverse Fourier transform absolute value distribution and the central wavelength data corresponding to each section spectrum data.
Examples
The optical coherence tomography endoscope imaging method based on spectrum segment, as shown in fig. 1, comprises the following steps:
s1, acquiring interference spectrum data of a position to be imaged through an endoscope probe;
in this embodiment, the spectrometer is connected to an endoscope probe through a single-mode optical fiber 1, as shown in fig. 2, the endoscope probe according to this embodiment includes: the external package 7 and the spacer 3, the GRIN lens 4, the focusing lens 5 and the micro scanning galvanometer 6 which are sequentially arranged in the external package 7, the single-mode fiber 1 is fixed through the optical cement 2, and the single-mode fiber 1 and the endoscope probe are arranged in the endoscope shell 8.
When the endoscope probe is used, broad spectrum near infrared light of the spectrometer is led into the endoscope probe through a single mode fiber, is collimated through the lens and then is incident on the GRIN lens 4 and the focusing lens 5, so that converging light is formed, point-by-point imaging is realized through scanning of the micro scanning galvanometer 6, interference spectrum data of a position to be imaged is obtained through the endoscope probe through the spectrometer, and in order to facilitate insertion of the endoscope probe into a lesion position, the diameter of the endoscope probe in the embodiment is not more than 10mm.
S2, preprocessing the interference spectrum data, performing section processing through a window function to obtain a plurality of section spectrum data, and determining center wavelength data corresponding to each section spectrum data;
in order to further improve imaging accuracy, preprocessing interference spectrum data in this embodiment specifically includes: and carrying out denoising, background removing and spectrum data calibration processing on the interference spectrum data.
After preprocessing the interference spectrum data, intercepting the spectrum data section by section through a window function, and determining the center wavelength corresponding to each section of spectrum data according to the intercepting result.
S3, respectively carrying out zero padding on each section of spectrum data so that each section of spectrum data contains the same pixel point, and carrying out inverse Fourier transform on each section of spectrum data to obtain inverse Fourier transform absolute value distribution corresponding to each section of spectrum data;
it can be understood that after obtaining the plurality of section spectrum data, for each section spectrum data, first, zero padding is performed respectively, and after zero padding, the pixels included in each section spectrum data are the same, in this embodiment, the number of pixels included in each section spectrum data is 2048, that is, each section spectrum data includes pixels 1 to 2048. And then, respectively carrying out inverse Fourier transform processing on each section of spectrum data to obtain an inverse Fourier transform absolute value distribution corresponding to each section of spectrum data, wherein the inverse Fourier transform absolute value distribution is used for representing the inverse Fourier transform absolute value corresponding to each pixel point in the section of spectrum data.
S4, determining the relative structure size of the position to be imaged according to the inverse Fourier transform absolute value distribution and the center wavelength data corresponding to the spectrum data of each section.
In this embodiment, determining the relative structure size of the position to be imaged according to the inverse fourier transform absolute value distribution and the center wavelength data corresponding to each section of spectral data specifically includes:
sequentially determining the section where the maximum value of the inverse Fourier transform absolute value corresponding to each same pixel point is located in Fourier transform absolute value distribution corresponding to each section of spectral data, and taking the central wavelength corresponding to the section of spectral data as the relative structural size of the imaging point corresponding to the pixel point; and obtaining the relative structural size of the position to be imaged according to the relative structural size of the imaging point corresponding to each pixel point.
Specifically, since the zero padding processing makes the pixel points included in each piece of spectrum data identical, for the same pixel point in each piece of spectrum data, the section where the maximum value of the corresponding inverse fourier transform absolute value is located is sequentially determined, and the center wavelength corresponding to the section of spectrum data is taken as the relative structural size of the imaging point corresponding to the pixel point. For example, firstly, respectively determining the absolute values of inverse fourier transforms corresponding to the pixel points 1 of the spectrum data of each section, then determining the maximum value from the absolute values of the inverse fourier transforms, determining the section of the pixel point 1 corresponding to the maximum value, and taking the central wavelength corresponding to the section as the relative structural size of the imaging point corresponding to the pixel point 1; and then respectively determining the absolute values of the inverse Fourier transforms corresponding to the pixel points 2 of the spectrum data of each section, determining the maximum value from the absolute values of the inverse Fourier transforms, determining the section of the pixel point 2 corresponding to the maximum value, taking the central wavelength corresponding to the section as the relative structural size of the imaging point corresponding to the pixel point 2, and deducing the relative structural size until the relative structural sizes of the imaging points corresponding to all the pixel points are determined, thus obtaining the relative structural size of the position to be imaged.
S4, comparing the relative structural size of the imaging point corresponding to each pixel point with the threshold value corresponding to the relative structural size to obtain a relative structural size comparison result.
According to the embodiment, the relative structural size of the imaging point corresponding to each pixel point is compared with the standard threshold, and a doctor can judge the size, the position and the nature of the lesion at the imaging position according to the comparison result of the relative structural size, so that subjective influence caused by experience judgment of the doctor according to the imaging result is avoided.
The left side (a) of fig. 3 shows a traditional OCT imaging result of a knee joint of a mouse, the right side (b) shows an imaging result of a knee joint of a mouse using the method of the present embodiment, and in the right side (b), different sizes of tissue structures are indicated by different colors (not shown in the drawing) when actually applied. It can be seen that, compared with the traditional OCT imaging, the optical coherence tomography endoscopic imaging method based on the spectrum segment in this embodiment can clearly show the size of the knee joint tissue structure of the mice, so as to assist the doctor in diagnosis or treatment.
In summary, by the optical coherence tomography endoscope imaging method based on spectrum segment according to the present embodiment, according to the broad spectrum interference principle of OCT, the spectrum is subjected to segment analysis, and finally the spatial frequency information of the tissue structure to be tested is represented by the segment-by-segment center wavelength, so as to represent the relative structural size of the imaging point of the tissue to be tested, and further realize the detection of the submicron structural difference.
Based on the above technical solution, this embodiment further provides an optical coherence tomography endoscope imaging system based on spectrum segments, as shown in fig. 4, including:
the spectrometer is used for acquiring interference spectrum data of a position to be imaged through the endoscope probe;
the processing device is used for preprocessing the interference spectrum data, then carrying out section processing through a window function to obtain a plurality of section spectrum data, determining center wavelength data corresponding to each section spectrum data, carrying out zero padding on each section spectrum data respectively so that each section spectrum data contains the same pixel point, and carrying out inverse Fourier transform on each section spectrum data to obtain inverse Fourier transform absolute value distribution corresponding to each section spectrum data;
and the determining device is used for determining the relative structure size of the position to be imaged according to the inverse Fourier transform absolute value distribution corresponding to each section of spectrum data and the center wavelength data.
It will be appreciated that, since the optical coherence tomography endoscope imaging system based on a spectrum segment according to the embodiment of the present invention is a system for implementing the optical coherence tomography endoscope imaging method based on a spectrum segment according to the embodiment, for the system disclosed in the embodiment, since it corresponds to the method disclosed in the embodiment, the description is simpler, and the relevant points will be referred to the part of the description of the method.
Claims (13)
1. An optical coherence tomography endoscopic imaging method based on spectral cut-off, characterized by comprising the following steps:
acquiring interference spectrum data of a position to be imaged through an endoscope probe;
preprocessing the interference spectrum data, performing section processing through a window function to obtain a plurality of section spectrum data, and determining center wavelength data corresponding to each section spectrum data;
zero padding is carried out on each section of spectrum data respectively, so that each section of spectrum data contains the same pixel point, and inverse Fourier transform is carried out on each section of spectrum data, so as to obtain the inverse Fourier transform absolute value distribution corresponding to each section of spectrum data;
and determining the relative structure size of the position to be imaged according to the inverse Fourier transform absolute value distribution and the center wavelength data corresponding to each section of spectrum data.
2. The spectral-segment-based optical coherence tomography endoscopic imaging method of claim 1, wherein preprocessing said interference spectral data comprises:
and carrying out denoising, background removing and spectrum data calibration processing on the interference spectrum data.
3. The spectral-segment-based optical coherence tomography endoscopic imaging method of claim 1, wherein said inverse fourier transform absolute value distribution is used to represent the inverse fourier transform absolute values corresponding to each pixel point in the segment spectral data.
4. A spectral segment-based optical coherence tomography endoscopic imaging method as recited in claim 1 or 3, wherein the number of pixels contained in each segment of spectral data is 2048.
5. A spectral-segment-based optical coherence tomography endoscope imaging method according to claim 3 and wherein determining the relative structural dimensions of the location to be imaged based on the corresponding inverse fourier transform absolute value distribution of each segment of spectral data and the center wavelength data comprises:
sequentially determining the section where the maximum value of the inverse Fourier transform absolute value corresponding to each same pixel point is located in Fourier transform absolute value distribution corresponding to each section of spectral data, and taking the central wavelength corresponding to the section of spectral data as the relative structural size of the imaging point corresponding to the pixel point;
and obtaining the relative structural size of the position to be imaged according to the relative structural size of the imaging point corresponding to each pixel point.
6. The spectral-segment-based optical coherence tomography endoscopic imaging method of claim 5, further comprising:
and respectively comparing the relative structure size of the imaging point corresponding to each pixel point with the corresponding threshold value to obtain a relative structure size comparison result.
7. An optical coherence tomography endoscopic imaging system based on spectral cut-off, comprising:
the spectrometer is used for acquiring interference spectrum data of a position to be imaged through the endoscope probe;
the processing device is used for preprocessing the interference spectrum data, then carrying out section processing through a window function to obtain a plurality of section spectrum data, determining center wavelength data corresponding to each section spectrum data, carrying out zero padding on each section spectrum data respectively so that each section spectrum data contains the same pixel point, and carrying out inverse Fourier transform on each section spectrum data to obtain inverse Fourier transform absolute value distribution corresponding to each section spectrum data;
and the determining device is used for determining the relative structure size of the position to be imaged according to the inverse Fourier transform absolute value distribution corresponding to each section of spectrum data and the center wavelength data.
8. The spectral-section-based optical coherence tomography endoscopic imaging system of claim 7, wherein said endoscopic probe is connected to a spectrometer by a single-mode fiber, said endoscopic probe comprising: the external package and the spacer, the GRIN lens, the focusing lens and the miniature scanning galvanometer which are sequentially arranged in the external package, wherein the single-mode fiber and the endoscope probe are arranged in the endoscope shell.
9. The optical coherence tomography endoscopic imaging system based on spectral segments as defined in claim 7, wherein said processing means are specifically adapted to:
and carrying out denoising, background removing and spectrum data calibration processing on the interference spectrum data.
10. The spectral-segment-based optical coherence tomography endoscopic imaging system of claim 7, wherein said inverse fourier transform absolute value distribution is used to represent the inverse fourier transform absolute values corresponding to each pixel point in the segment spectral data.
11. The optical coherence tomography endoscope imaging method based on spectrum segments of claim 7 or 10, wherein the number of pixels contained in each segment of spectrum data is 2048.
12. The optical coherence tomography endoscopic imaging system based on spectral segments as defined in claim 11, wherein said processing means are specifically adapted to:
sequentially determining the section where the maximum value of the inverse Fourier transform absolute value corresponding to each same pixel point is located in Fourier transform absolute value distribution corresponding to each section of spectral data, and taking the central wavelength corresponding to the section of spectral data as the relative structural size of the imaging point corresponding to the pixel point;
and obtaining the relative structural size of the position to be imaged according to the relative structural size of the imaging point corresponding to each pixel point.
13. The spectral-segment-based optical coherence tomography endoscopic imaging system of claim 12, further comprising:
and the comparison device is used for respectively comparing the relative structural size of the imaging point corresponding to each pixel point with the corresponding threshold value to obtain a relative structural size comparison result.
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| CN202210086738.9A Pending CN116530914A (en) | 2022-01-25 | 2022-01-25 | Optical coherence tomography endoscope imaging method and system based on spectrum section |
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| CN (1) | CN116530914A (en) |
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