CN218009671U - Endoscopic system - Google Patents
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- CN218009671U CN218009671U CN202221494021.XU CN202221494021U CN218009671U CN 218009671 U CN218009671 U CN 218009671U CN 202221494021 U CN202221494021 U CN 202221494021U CN 218009671 U CN218009671 U CN 218009671U
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Abstract
The utility model provides an endoscopic system. The endoscopic system comprises: a hard-tube endoscope; the light source module is connected with the hard tube type endoscope and is used for emitting light with various wave bands to the hard tube type endoscope; the light splitting module is used for reflecting and/or transmitting light collected by the hard tube type endoscope; the near-infrared first-zone acquisition module receives the light reflected or transmitted by the light splitting module and performs imaging; the near-infrared second-zone acquisition module receives the light reflected or transmitted by the light splitting module and performs imaging; and the control module is used for acquiring images generated by the near-infrared first-zone acquisition module, the near-infrared second-zone acquisition module and the visible light acquisition module, and processing and displaying the images. The utility model provides an peep system among the prior art have the penetration depth low, the SNR is low, autofluorescence signal disturb strong problem.
Description
Technical Field
The utility model relates to a fluorescence molecule imaging apparatus technical field particularly, relates to an peep system in.
Background
The fatality rate of cancer is increased year by year, and cancer is one of the key points and difficulties difficult to overcome in the medical field at present. Due to the pathological particularity of the cancer, the cancer can be rapidly diffused and developed in a human body, has low cure rate and easy metastasis in the late stage, simultaneously easily causes other complications and has high death rate. Therefore, early diagnosis and early treatment are important measures for improving the survival rate of cancer patients, and how to quickly determine the early diagnosis of the cancer is also the key to the timing of treatment.
At present, the optical endoscopic system has the advantages of high resolution, small damage, high imaging speed and the like, and is an important medical means for early detection, diagnosis and treatment of cancers. The common endoscopic system inspection generally adopts a white light endoscope, the imaging mode of the white light endoscope is based on anatomical structure change, diagnosis is mainly carried out by observing the microstructure, the capillary vessel form, the color change and the like of the mucosal surface, the imaging definition of the mucosal surface structure and the capillary vessel form is limited, the white light endoscope does not have the targeting identification capability on tumors, the identification and the judgment of lesion parts are not facilitated, the risks of wrong judgment of the lesion parts and missed detection of tiny lesions easily occur, and the treatment time is delayed.
In order to improve the targeting recognition capability of the tumor, the fluorescent molecular imaging can be used in an endoscopic system, and a targeting fluorescent probe for the fluorescent molecular imaging is used for realizing high-specificity marking on a specific molecular target, so that the sensitivity and the specificity are high, and the method is suitable for early diagnosis of the tumor. The fluorescent molecular imaging combined with the endoscopic system can assist doctors to find tiny tumor focuses and judge tumor boundaries in the process of tumor resection. The existing fluorescence camera system generally performs imaging in a 400-900nm (visible light + near infrared first-region light) wave band range, but in clinical application, absorption and scattering caused by various biomolecules (including hemoglobin, fat and water) are concentrated in visible light (400-700 nm) and near infrared first-region (700-900 nm), and near infrared first-region fluorescence imaging has the problems of autofluorescence intensity, low penetration depth, low signal-to-noise ratio, easy signal interference and the like, so that false positive nodules can be caused, and missed diagnosis or misdiagnosis is easily caused.
That is, the endoscopic system in the prior art has the problems of low penetration depth, low signal-to-noise ratio and strong interference of autofluorescence signals.
SUMMERY OF THE UTILITY MODEL
The main object of the present invention is to provide an endoscopic system to solve the problems of low penetration depth, low signal-to-noise ratio and strong interference of autofluorescence signal in the endoscopic system in the prior art.
In order to achieve the above object, the present invention provides an endoscopic system comprising: a hard-tube endoscope; the light source module is connected with the hard tube type endoscope and is used for emitting light with various wave bands to the hard tube type endoscope; the light splitting module is used for reflecting and/or transmitting light collected by the hard tube type endoscope; the near-infrared first-zone acquisition module receives the light reflected or transmitted by the light splitting module and performs imaging; the near-infrared second-zone acquisition module receives the light reflected or transmitted by the light splitting module and performs imaging; the visible light acquisition module is used for receiving the light reflected or transmitted by the light splitting module and imaging; the control module is electrically connected with the near-infrared first-zone acquisition module, the near-infrared second-zone acquisition module and the visible light acquisition module and is used for acquiring, processing and displaying images generated by the near-infrared first-zone acquisition module, the near-infrared second-zone acquisition module and the visible light acquisition module.
Furthermore, a plurality of light splitting modules are provided, and at least one light splitting module is arranged between the hard tube type endoscope and the near-infrared second-zone acquisition module so that the near-infrared second-zone acquisition module receives light transmitted by the light splitting modules; at least one other light splitting module is arranged between the visible light collection module and the near-infrared first-zone collection module, so that one of the visible light collection module and the near-infrared first-zone collection module receives light reflected by the light splitting module, and the other receives light transmitted by the light splitting module.
Furthermore, the plurality of light splitting modules comprise a first light splitting module and a second light splitting module, and the near-infrared second-zone acquisition module is positioned on a transmission path of the first light splitting module; the second light splitting module is positioned on the reflection path of the first light splitting module, the visible light acquisition module is positioned on the reflection path of the second light splitting module, and the near-infrared first-zone acquisition module is positioned on the transmission path of the second light splitting module.
Further, the light source module comprises a white light source and a multiband light source, the waveband range of the multiband light source can be set selectively, and the multiband light source can at least emit near infrared light.
Further, the multiband light source comprises: a near-infrared chip; the optical filter is a narrow-band optical filter; and the coupling mirror is positioned on one side of the optical filter far away from the near-infrared chip and is used for coupling the light passing through the optical filter into the optical fiber and then entering the hard tube type endoscope.
Furthermore, the endoscopic system further comprises a plurality of achromatic amplification modules, at least one achromatic amplification module is positioned at the light incident side of the near-infrared two-zone acquisition module, and at least another achromatic amplification module is positioned at the light incident sides of the near-infrared one-zone acquisition module and the visible light acquisition module.
Further, the achromatic magnification module sequentially comprises a first lens, a second lens, a third lens and a fourth lens from the object side to the image side, wherein the second lens and the fourth lens are double-cemented lenses.
Further, the first near-infrared region acquisition module comprises: a narrow band filter; a near-infrared first-zone imaging lens; the near-infrared first-zone fluorescence camera is used for collecting light passing through the narrow band filter and focusing the light on an imaging target surface of the near-infrared first-zone fluorescence camera, and the near-infrared first-zone fluorescence camera is used for converting optical signals into electric signals to carry out imaging display.
Further, the near-infrared two-zone acquisition module comprises: a long-pass filter; a near-infrared two-zone imaging lens; the near-infrared two-zone fluorescence camera is used for collecting light passing through the long-pass filter and focusing the light on an imaging target surface of the near-infrared two-zone fluorescence camera, and the near-infrared two-zone fluorescence camera is used for converting optical signals into electric signals to carry out imaging display.
Further, the hard tube endoscope at least comprises an optical lens group consisting of a plurality of lenses.
Furthermore, the endoscopic system also comprises a coupling lens and an image transmission optical fiber, wherein the coupling lens is connected with the image transmission optical fiber, and the coupling lens and the image transmission optical fiber are positioned between the light splitting module and the near-infrared two-zone acquisition module, so that light transmitted by the light splitting module is coupled by the coupling lens to enter the image transmission optical fiber for transmission and then is transmitted to the near-infrared two-zone acquisition module; or the coupling lens and the image transmission optical fiber are positioned between the hard tube type endoscope and the light splitting module, and light collected by the hard tube type endoscope is coupled into the image transmission optical fiber through the coupling lens for transmission and then transmitted to the light splitting module.
Use the technical scheme of the utility model, peep the system in and include hard tube endoscope, light source module, beam split module, near-infrared one district collection module, near-infrared two district collection modules, visible light collection module and control module. The light source module is connected with the hard tube type endoscope and is used for emitting light with various wave bands to the hard tube type endoscope; the light splitting module is used for reflecting and/or transmitting light collected by the hard tube type endoscope; the near-infrared first-zone acquisition module receives light reflected or transmitted by the light splitting module and images the light; the near-infrared second-zone acquisition module receives the light reflected or transmitted by the light splitting module and images; the visible light acquisition module is used for receiving the light reflected or transmitted by the light splitting module and imaging; the control module is electrically connected with the near-infrared first-zone acquisition module, the near-infrared second-zone acquisition module and the visible light acquisition module, and is used for acquiring, processing and displaying images generated by the near-infrared first-zone acquisition module, the near-infrared second-zone acquisition module and the visible light acquisition module.
Through adopting hard tube type endoscope, guarantee that hard tube type endoscope itself is inflexible, it detects time measuring to wait the region to get into the human body at hard tube type endoscope like this, hard tube type endoscope is with the light irradiation of the multiple wave band of light source module transmission to waiting to detect the region, and collect and wait the light of detecting regional reflection, the resolution ratio has been guaranteed, be favorable to improving the definition of formation of image, the clear advantage of formation of image has been guaranteed, be favorable to improving the accuracy to waiting to detect the discernment of region and judgement. The light splitting module is arranged, so that the light splitting module has a light splitting function, the reasonable division of the distribution positions of all devices in the endoscopic system is facilitated, and the integration and the use of the endoscopic system are facilitated.
The application provides an endoscopic system for common imaging of visible light, near-infrared first-zone light and near-infrared second-zone light through the mutual matching of the light source module, the near-infrared first-zone acquisition module, the near-infrared second-zone acquisition module and the visible light acquisition module, greatly improves imaging definition, and avoids the defects that the traditional white light endoscopic imaging cannot determine a tumor boundary and is difficult to detect a small tumor focus. The tumor can be identified in a targeting manner by utilizing a common imaging mode of the near-infrared first-zone light and the near-infrared second-zone light, meanwhile, the penetration depth of the near-infrared second-zone light to a region to be detected can be greatly increased, interference such as autofluorescence and light scattering can be better avoided, and the problems of high false positive, low penetration depth, low signal-to-noise ratio and the like caused by only near-infrared first-zone imaging are avoided. Images generated by the near-infrared first-region acquisition module, the near-infrared second-region acquisition module and the visible light acquisition module are acquired, processed and displayed through the control module, and the pathological change region of the mucous membrane tissue can be marked by utilizing a fluorescent molecular imaging technology, so that a doctor is better helped to distinguish normal tissue and pathological change tissue, and the diagnosis accuracy is favorably improved.
Drawings
The accompanying drawings, which form a part of the present application, are included to provide a further understanding of the invention, and are incorporated in and constitute a part of this specification, illustrate embodiments of the invention and together with the description serve to explain the invention and not to limit the invention. In the drawings:
fig. 1 is a schematic view showing an optical path of an endoscopic system according to a first embodiment of the present invention;
fig. 2 is a schematic view showing an optical path of an endoscopic system according to a second embodiment of the present invention;
fig. 3 is a schematic view of a light source module of an endoscopic system according to an alternative embodiment of the present invention;
fig. 4 is a schematic view of an achromatic magnification module of an endoscopic system according to an alternative embodiment of the present invention.
Wherein the figures include the following reference numerals:
10. a hard-tube endoscope; 20. a light source module; 21. a white light source; 22. a multiband light source; 221. a near-infrared chip; 222. an optical filter; 223. a coupling mirror; 31. a first light splitting module; 32. a second light splitting module; 40. a near-infrared first-zone acquisition module; 50. a near-infrared second-zone acquisition module; 60. a visible light collection module; 70. a control module; 80. an achromatic amplification module; 81. a first lens; 82. a second lens; 83. a third lens; 84. a fourth lens; 90. a coupling lens; 100. image transmission optical fiber.
Detailed Description
It should be noted that, in the present application, the embodiments and features of the embodiments may be combined with each other without conflict. The present invention will be described in detail below with reference to the accompanying drawings in conjunction with embodiments.
It is to be noted that, unless otherwise indicated, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this application belongs.
In the present application, where the contrary is not intended, the use of directional terms such as "upper, lower, top, bottom" generally refer to the orientation as shown in the drawings, or to the component itself being oriented in a vertical, perpendicular, or gravitational direction; likewise, for ease of understanding and description, "inner and outer" refer to the inner and outer relative to the profile of the components themselves, but the above directional words are not intended to limit the invention.
In order to solve the problems of low penetration depth, low signal-to-noise ratio and strong interference of autofluorescence signals of the endoscopic system in the prior art, the utility model provides an endoscopic system.
As shown in fig. 1 to 4, the endoscopic system includes a hard tube endoscope 10, a light source module 20, a light splitting module, a near-infrared first-region acquisition module 40, a near-infrared second-region acquisition module 50, a visible light acquisition module 60, and a control module 70. The light source module 20 is connected with the hard tube endoscope 10 and is used for emitting light with various wave bands to the hard tube endoscope 10; the light splitting module is used for reflecting and/or transmitting the light collected by the hard tube type endoscope 10; the near-infrared first-zone acquisition module 40 receives the light reflected or transmitted by the light splitting module and performs imaging; the near-infrared second-zone acquisition module 50 receives the light reflected or transmitted by the light splitting module and performs imaging; the visible light collection module 60 is configured to receive light reflected or transmitted by the light splitting module and perform imaging; the control module 70 is electrically connected to the first near-infrared region acquisition module 40, the second near-infrared region acquisition module 50 and the visible light acquisition module 60, and the control module 70 is configured to acquire, process and display images generated by the first near-infrared region acquisition module 40, the second near-infrared region acquisition module 50 and the visible light acquisition module 60.
Through adopting hard tube endoscope 10, guarantee that hard tube endoscope 10 itself is inflexible, it examines time measuring to treat the detection region like this at hard tube endoscope 10 entering human body, hard tube endoscope 10 with the multiple wave band's of light source module 20 transmission light-struck to waiting to detect the region, and collect and treat the light of regional reflection, the resolution ratio has been guaranteed, be favorable to improving the definition of formation of image, the clear advantage of formation of image has been guaranteed, be favorable to improving the accuracy to the discernment of waiting to detect the region and judge. The light splitting module plays a role in light splitting, is favorable for reasonable division of distribution positions of all devices in the endoscopic system, and is favorable for integration and use of the endoscopic system.
The application provides an endoscopic system for common imaging of visible light, near-infrared first-region light and near-infrared second-region light by mutually matching the light source module 20, the near-infrared first-region acquisition module 40, the near-infrared second-region acquisition module 50 and the visible light acquisition module 60, greatly improves imaging definition, and avoids the defects that the tumor boundary cannot be determined and the tiny tumor focus cannot be detected due to traditional white light endoscopic imaging. The tumor can be identified in a targeted manner by utilizing a common imaging mode of the near-infrared first-zone light and the near-infrared second-zone light, meanwhile, the penetration depth of the near-infrared second-zone light to a region to be detected can be greatly increased, interference such as autofluorescence and light scattering can be better avoided, and the problems of high false positive, low penetration depth, low signal-to-noise ratio and the like caused by only near-infrared first-zone imaging are avoided. The images generated by the near-infrared first-zone acquisition module 40, the near-infrared second-zone acquisition module 50 and the visible light acquisition module 60 are acquired, processed and displayed through the control module 70, and the pathological change area of the mucous membrane tissue can be marked by utilizing a fluorescent molecular imaging technology, so that a doctor is better helped to distinguish normal tissues from pathological change tissues, and the diagnostic accuracy can be improved.
It should be noted that the internal structure of the rigid tube endoscope 10 is an optical lens assembly composed of a plurality of cylindrical lenses, the endoscope body is not bendable, and the rigid tube endoscope 10 mainly enters human body sterile tissues and organs or enters human body sterile chambers through surgical incisions, such as laparoscopes, thoracoscopes, arthroscopes, and the like. The method has the advantages of clear imaging and high resolution, and can be matched with a plurality of working channels to select a plurality of visual fields.
Specifically, the number of the light splitting modules is multiple, and at least one light splitting module is arranged between the hard tube endoscope 10 and the near-infrared secondary acquisition module 50, so that the near-infrared secondary acquisition module 50 receives light transmitted by the light splitting modules; at least one other spectral module is disposed between the visible light collection module 60 and the first near-infrared collection module 40, so that one of the visible light collection module 60 and the first near-infrared collection module 40 receives light reflected by the spectral module and the other receives light transmitted by the spectral module. By arranging the plurality of light splitting modules, one light splitting module corresponds to the near-infrared two-zone acquisition module 50, so that the near-infrared two-zone acquisition module 50 can accurately receive the light in the near-infrared two-zone wavelength range transmitted by the light splitting module, the near-infrared two-zone light is collected, and the subsequent image display work is facilitated; meanwhile, the visible light transmitted or reflected by the other light splitting module can be collected by the visible light collecting module 60, and the transmitted or reflected near-infrared first-zone light can be collected by the near-infrared first-zone collecting module 40, so as to facilitate the subsequent image display.
As shown in fig. 1 and fig. 2, the two light splitting modules include a first light splitting module 31 and a second light splitting module 32, respectively, light reflected by an area to be detected is transmitted to the first light splitting module 31 through the hard tube endoscope 10, the first light splitting module 31 is configured to transmit light with a wavelength range of 900nm to 1700nm, that is, near-infrared second-zone light, and since the near-infrared second-zone collecting module 50 is located on a transmission path of the first light splitting module 31, the transmitted near-infrared second-zone light can smoothly enter the near-infrared second-zone collecting module 50; the first light splitting module 31 is used for reflecting light with a wavelength range of 400nm to 900nm, because the second light splitting module 32 is positioned on a reflection path of the first light splitting module 31, the light reflected by the first light splitting module 31 enters the second light splitting module 32, and then the second light splitting module 32 transmits light with a wavelength range of 700nm to 900nm, namely near infrared first-zone light, because the near infrared first-zone acquisition module 40 is positioned on a transmission path of the second light splitting module 32, the transmitted near infrared first-zone light can be ensured to smoothly enter the near infrared first-zone acquisition module 40; the second light splitting module 32 reflects light with a wavelength range of 400nm to 700nm, that is, reflects visible light, and since the visible light collection module 60 is located on the reflection path of the second light splitting module 32, it is ensured that the visible light reflected by the second light splitting module 32 can smoothly enter the visible light collection module 60 for imaging display. By arranging the first light splitting module 31 and the second light splitting module 32, light splitting of light with different wave bands is realized, so that the near-infrared first-zone acquisition module 40, the near-infrared second-zone acquisition module 50 and the visible light acquisition module 60 can be ensured to accurately receive light with corresponding wave band ranges, and further the imaging stability is ensured.
The light splitting module is a dichroic mirror.
As shown in fig. 3, the light source module 20 includes a white light source 21 and a multiband light source 22, and the band range of the multiband light source 22 is selectively set, and the multiband light source 22 can emit at least near infrared light. The white light source 21 can provide visible light illumination, the multiband light source 22 is used for exciting a fluorescent reagent on a region to be detected to enable the fluorescent reagent to emit fluorescence (near-infrared first-region light and near-infrared second-region light), the white light source 21 and the multiband light source 22 are coupled to an optical fiber for transmission and then transmitted into the hard tube endoscope 10, and then the hard tube endoscope 10 irradiates the region to be detected with light of multiple wave bands emitted by the white light source 21 and the multiband light source 22.
Specifically, the multiband light source 22 includes a near-infrared chip 221, a filter 222 and a coupling mirror 223, wherein the near-infrared chip 221 is a near-infrared LED chip; according to the excitation wavelength of the common fluorescent reagent, the multiband light source 22 is integrated by near-infrared LED chips with central wave bands of 785nm, 808nm and 830 nm; filter 222 is a narrow band filter corresponding to the central band, which is selected according to the excitation wavelength of the fluorescent reagent used. The coupling mirror 223 is located on a side of the optical filter 222 away from the near infrared chip 221, and the coupling mirror 223 is used for coupling the light passing through the optical filter 222 into the coupling optical fiber and further into the hard tube endoscope 10. The light source module 20 of the present application employs a combination of a white light source 21 and a multiband light source 22, and is suitable for excitation of different fluorescent reagents.
It should be noted that the white light source 21 is a white light LED, and the multiband light source 22 is a multiband LED, and the multiband LED realizes output of various central bands by integrating near-infrared chips of various central bands.
As shown in fig. 1 and fig. 2, the endoscope system further includes a plurality of achromatic amplification modules 80, at least one achromatic amplification module 80 is located at the light incident side of the secondary near-infrared acquisition module 50, so that the achromatic amplification module 80 can amplify or reduce the secondary near-infrared light by a certain magnification, and reduce aberration, so that the secondary near-infrared light fills the imaging target surface of the camera of the secondary near-infrared acquisition module 50 to the maximum extent and the influence of chromatic aberration on the image is reduced, thereby improving imaging performance. At least one other achromatic amplification module 80 is located at the light incident side of the first near-infrared region acquisition module 40 and the visible light acquisition module 60, that is, at the light incident side of the second light splitting module 32 and at the light emergent side of the first light splitting module 31, so that the achromatic amplification module 80 can amplify or reduce the reflected light of the first light splitting module 31 by a certain magnification and reduce aberration, and further the visible light reflected by the second light splitting module 32 can fill the imaging target surface of the camera of the visible light acquisition module 60 to the maximum extent and reduce the influence of the chromatic aberration on the image, thereby improving the imaging performance; meanwhile, the near-infrared first-zone light transmitted by the second light splitting module 32 can fill the imaging target surface of the camera of the near-infrared first-zone acquisition module 40 to the maximum extent, and the influence of chromatic aberration on the image can be reduced, so that a better imaging effect is obtained.
As shown in fig. 4, the achromatic magnification module 80 includes four lenses, and the achromatic magnification module 80 includes, in order from the object side to the image side, a first lens 81, a second lens 82, a third lens 83, and a fourth lens 84, where the second lens 82 and the fourth lens 84 are double cemented lenses. The curvature of the surface of each lens and the thickness of each lens are different, and the black line connecting the lenses in the figure represents light.
Specifically, the visible light collection module 60 includes a visible light camera and a visible light imaging lens, and the visible light imaging lens is connected to the visible light camera through a camera bayonet and is used for collecting a white light image; the visible light imaging lens is used for collecting light beams and focusing the light beams on an imaging target surface of the visible light camera; the visible light camera is used for converting the optical signal into an electric signal for imaging display.
Specifically, the near-infrared first-region acquisition module 40 includes a narrowband optical filter, a near-infrared first-region imaging lens, and a near-infrared first-region fluorescence camera, where the narrowband optical filter is an optical filter with a wavelength range of 700nm to 900nm, and is capable of filtering out stray light that does not belong to the above wavelength range, so as to ensure that only light in the near-infrared first-region enters the near-infrared first-region fluorescence camera, thereby avoiding the influence of the stray light on imaging performance, the near-infrared first-region imaging lens is used for collecting light passing through the narrowband optical filter and focusing on an imaging target surface of the near-infrared first-region fluorescence camera, and the near-infrared first-region fluorescence camera is used for converting optical signals into electrical signals for imaging display.
Specifically, the near-infrared two-zone acquisition module 50 includes a long-pass filter, a near-infrared two-zone imaging lens, and a near-infrared two-zone fluorescence camera, where the long-pass filter can filter out stray light below a 900nm band to ensure that only light in a near-infrared two-zone band range enters the near-infrared two-zone fluorescence camera, so as to avoid the influence of stray light of other wavelengths on imaging quality, thereby achieving an imaging effect, the near-infrared two-zone imaging lens is used for collecting light passing through the long-pass filter and focusing on an imaging target surface of the near-infrared two-zone fluorescence camera, and the near-infrared two-zone fluorescence camera is used for converting an optical signal into an electrical signal for imaging display.
As shown in fig. 1 and 2, the endoscopic system further includes a coupling lens 90 and an image transmission fiber 100, the coupling lens 90 is connected with the image transmission fiber 100 for use in combination, and the coupling lens 90 and the image transmission fiber 100 are located between the spectral module and the near-infrared two-zone acquisition module 50, so that light transmitted by the spectral module is coupled by the coupling lens 90 into the image transmission fiber 100 for transmission, and then transmitted to the near-infrared two-zone acquisition module 50; or the coupling lens 90 and the image transmission optical fiber 100 are located between the hard tube type endoscope 10 and the light splitting module, and light collected by the hard tube type endoscope 10 is coupled into the image transmission optical fiber 100 through the coupling lens 90 for transmission, and then is transmitted to the light splitting module. The coupling lens 90 is generally arranged on the light incident side of the image transmission fiber 100, the coupling lens 90 couples the collected light into the image transmission fiber 100, the image transmission fiber 100 is used for transmitting image light, and the image light is transmitted through the image transmission fiber 100, so that the volume of one end of the hard tube endoscope 10 is favorably reduced, the operation of a doctor is facilitated, and the application convenience is improved.
The following detailed explanation and description are made according to specific embodiments of the present invention and corresponding drawings.
Example one
Fig. 1 is an optical path diagram of an endoscopic system according to a first embodiment of the present invention.
Specifically, light of multiple wavebands emitted by the light source module 20 is transmitted to the hard tube endoscope 10 through the coupling optical fiber, the hard tube endoscope 10 irradiates light of multiple wavebands emitted by the light source module 20 to an area to be detected, collects reflected light and fluorescence emission light of the area to be detected, transmits the reflected light and the fluorescence emission light to the first light splitting module 31, couples near-infrared two-zone light transmitted by the first light splitting module 31 into the image transmitting optical fiber 100 through the coupling lens 90, transmits the near-infrared two-zone light to the achromatic aberration amplifying module 80 through the image transmitting optical fiber 100, amplifies the near-infrared two-zone light to a certain magnification ratio through the achromatic aberration amplifying module 80, eliminates aberration and chromatic aberration, and then enters the near-infrared two-zone acquisition module 50 for imaging. The visible light and the near-infrared first-region light reflected by the first light splitting module 31 reach the second light splitting module 32 after being amplified by the achromatic amplification module 80 for a certain magnification and eliminating aberration and chromatic aberration, the second light splitting module 32 reflects the visible light to the visible light acquisition module 60 for imaging, and the second light splitting module 32 transmits the near-infrared first-region light to the near-infrared first-region acquisition module 40 for imaging.
Further, the control module 70 transmits signals to the visible light collection module 60, the first near-infrared collection module 40, and the second near-infrared collection module 50, correspondingly collects the visible light image, the first near-infrared fluorescence image, and the second near-infrared fluorescence image, performs image preprocessing, performs pseudo color processing and image fusion processing on the preprocessed images, obtains a fused image, and displays the fused image.
Example two
Fig. 2 is an optical path diagram of an endoscopic system according to a second embodiment of the present invention.
The difference from the first embodiment is that the positions of the coupling lens 90, the image transmission fiber 100, and the achromatic magnification module 80 are different.
Specifically, light of multiple wave bands emitted by the light source module 20 is transmitted to the hard tube endoscope 10 through the coupling optical fiber, the hard tube endoscope 10 irradiates the light of multiple wave bands emitted by the light source module 20 to an area to be detected, collects reflected light and fluorescence emitted light of the area to be detected, transmits the reflected light and the fluorescence emitted light to the coupling lens 90, couples the reflected light and the fluorescence emitted light into the image transmission optical fiber 100 through the coupling lens 90, transmits the image transmission optical fiber 100 to the achromatic magnification module 80 through the image transmission optical fiber 100, enters the first light splitting module 31 after being magnified by a certain magnification and eliminating aberration and chromatic aberration through the achromatic magnification module 80, and transmits near-infrared two-zone light into the near-infrared two-zone acquisition module 50 for imaging. The visible light and the near-infrared first-region light reflected by the first light splitting module 31 reach the second light splitting module 32 after being amplified by the achromatic amplification module 80 for a certain magnification and eliminating aberration and chromatic aberration, the second light splitting module 32 reflects the visible light to the visible light acquisition module 60 for imaging, and the second light splitting module 32 transmits the near-infrared first-region light to the near-infrared first-region acquisition module 40 for imaging.
Further, the control module 70 transmits signals to the visible light collection module 60, the first near-infrared collection module 40, and the second near-infrared collection module 50, correspondingly collects the visible light image, the first near-infrared fluorescence image, and the second near-infrared fluorescence image, performs image preprocessing, performs pseudo color processing and image fusion processing on the preprocessed images, obtains a fused image, and displays the fused image.
The present application further provides an imaging method of an endoscopic system, which performs imaging by using the endoscopic system of the first embodiment, including:
step S1: placing the probing end of the hard tube endoscope 10 on the surface of the area to be tested;
step S2: adjusting the wave band range of a light source module 20 of the endoscopic system to be adapted to the excitation wave band corresponding to the fluorescent reagent of the area to be detected, and irradiating the area to be detected;
and step S3: reflected light and fluorescence emission light of the area to be detected are transmitted to a first light splitting module 31 of the endoscopic system through the hard tube type endoscope 10 and are split into near-infrared two-zone light, visible light and near-infrared first-zone light through the first light splitting module 31;
and step S4: the near-infrared second-zone light sequentially passes through the coupling lens 90 and the image transmission optical fiber 100 of the endoscopic system to enter the achromatic amplification module 80, is amplified by a certain magnification through the achromatic amplification module 80, eliminates aberration and chromatic aberration and then enters the near-infrared second-zone acquisition module 50 to be imaged; the light of the combination of the visible light and the near-infrared first-zone light is amplified by another achromatic amplification module 80 for a certain magnification, eliminated from aberration and chromatic aberration, enters the second light splitting module 32, is split into the visible light and the near-infrared first-zone light by the second light splitting module 32, and correspondingly enters the visible light collection module 60 and the near-infrared first-zone collection module 40 for imaging;
step S5: the control module 70 of the endoscopic system transmits signals to the visible light acquisition module 60, the near-infrared first-zone acquisition module 40 and the near-infrared second-zone acquisition module 50, and correspondingly acquires a visible light image, a near-infrared first-zone fluorescence image and a near-infrared second-zone fluorescence image;
step S6: the visible light image, the near-infrared first-region fluorescence image and the near-infrared second-region fluorescence image are subjected to preprocessing of image denoising processing and image enhancement processing, and then the preprocessed images are subjected to pseudo-color processing and image fusion processing, so that a fused image of white light and fluorescence is obtained.
In the imaging method of the endoscopic system according to the first embodiment, the coupling lens 90 and the image transmission fiber 100 of the endoscopic system are located between the light splitting module and the near-infrared two-zone collecting module 50, and more specifically, the coupling lens 90 and the image transmission fiber 100 are located between the first light splitting module 31 and the achromatic magnification module 80, and light transmitted by the first light splitting module 31 is coupled by the coupling lens 90 to enter the image transmission fiber 100 for transmission, and then is transmitted to the near-infrared two-zone collecting module 50.
The utility model also provides an imaging method of the endoscopic system, which adopts the endoscopic system of the second embodiment to image, comprising:
step S1: placing the detection end of a hard tube endoscope 10 of an endoscopic system on the surface of an area to be detected;
step S2: according to the excitation wave band corresponding to the fluorescent reagent of the area to be detected, the wave band range of the light source module 20 of the endoscopic system is adjusted to be adapted to the excitation wave band, and the area to be detected is irradiated;
and step S3: reflected light and fluorescence emission light of an area to be detected are transmitted to a coupling lens 90 and an image transmission optical fiber 100 of an endoscopic system after passing through a hard tube endoscope 10, are transmitted to an achromatic amplification module 80 after passing through the coupling lens 90 and the image transmission optical fiber 100, enter a first light splitting module 31 after being amplified by the achromatic amplification module 80 for a certain multiplying power and eliminating aberration and chromatic aberration, and are split into combined light of visible light and near-infrared first-zone light and near-infrared second-zone light by the first light splitting module 31;
and step S4: the near-infrared second-zone light enters the near-infrared second-zone acquisition module 50, the combined light of the visible light and the near-infrared first-zone light correspondingly enters the second light splitting module 32 after being amplified by another achromatic amplification module 80 for a certain magnification and eliminating aberration and chromatic aberration, and the combined light is divided into the visible light and the near-infrared first-zone light by the second light splitting module 32 and correspondingly enters the visible light acquisition module 60 and the near-infrared first-zone acquisition module 40 for imaging;
step S5: the control module 70 of the endoscopic system transmits signals to the visible light acquisition module 60, the near-infrared first-zone acquisition module 40 and the near-infrared second-zone acquisition module 50, and correspondingly acquires a visible light image, a near-infrared first-zone fluorescence image and a near-infrared second-zone fluorescence image;
step S6: and carrying out pretreatment of image denoising treatment and image enhancement treatment on the visible light image, the near-infrared first-zone fluorescence image and the near-infrared second-zone fluorescence image, and then carrying out pseudo-color treatment and image fusion treatment on the pretreated images so as to obtain a fused image of white light and fluorescence.
In the imaging method using the endoscopic system according to the second embodiment, the coupling lens 90 and the image transmission fiber 100 of the endoscopic system are located between the rigid tube endoscope 10 and the spectroscopic module, and light of the rigid tube endoscope 10 is coupled into the image transmission fiber 100 through the coupling lens 90 for transmission, and then transmitted to the first spectroscopic module 31.
It should be noted that the control module 70 is used for controlling the acquisition of the white light image and the fluorescence image (including the near-infrared first-region fluorescence image and the near-infrared second-region fluorescence image). And after the acquisition is finished, preprocessing the fluorescence image by image denoising and image enhancement, then carrying out pseudo-color processing on the preprocessed image, and carrying out image fusion processing on the processed fluorescence image and the white light image to obtain a fused image. The control module 70 may be a series of devices, such as a computer, capable of collecting images and performing algorithmic processing and display of the images.
The image enhancement processing adopted by the application: the self-adaptive contrast enhancement obtains the relative light and shade relation between a target pixel point and surrounding pixel points thereof through differential calculation so as to adjust the dynamic range of an image, and the specific algorithm comprises the following steps:
step S61: setting a pixel point in an image (fluorescent image) to be processed as x (i, j), calculating a mean value m of the pixel point in the region with the window size of (2n + 1) (2n + 1) by taking the x point as the center x (i, j) and the standard deviation σ x (i, j), the specific formula comprises:
step S62: calculating a pixel value f (i, j) after local enhancement, wherein the calculation formula of f (i, j) is as follows:
and D is the global mean value of the image to be processed.
Performing processing by adopting gray morphological closed operation, namely performing expansion processing on the image, and communicating discontinuous edge pixel points to form a closed edge so as to enhance micro information; and then carrying out corrosion treatment on the image to remove the image noise points. The effective fluorescence signal in the gray level image is highlighted by reserving a fluorescence area in a large range, and background noise or local fluorescence signals in a small range are removed, so that the enhancement effect of the fluorescence image is realized.
The respective pseudo color mapping functions of the red, green and blue channels of the gray scale conversion method for performing pseudo color processing on the image are generally shown by the following formulas:
where H (i, j) is the gray scale value of the gray scale image at (i, j), and R (i, j), G (i, j), and B (i, j) are the three primary colors of red, green, and blue, respectively, obtained by gray scale value conversion.
The image fusion of the application can adopt a weighted average method, the weighted average method is a fusion method for carrying out weighted processing on pixel points corresponding to an original image, and the formula is as follows:
wherein the content of the first and second substances,
and
respectively the lowest frequency sub-coefficient of the image A to be processed and the image B to be processed after N-layer decomposition,
for the fused image transform coefficients, w A And w B Is a weighting coefficient, and satisfies w A +w B =1 (generally take w) A =0.5 and w B ＝0.5)。
It is obvious that the above described embodiments are only some of the embodiments of the present invention, and not all of them. Based on the embodiments in the present invention, all other embodiments obtained by a person skilled in the art without creative efforts shall belong to the protection scope of the present invention.
It is noted that the terminology used herein is for the purpose of describing particular embodiments only and is not intended to be limiting of exemplary embodiments according to the present application. As used herein, the singular is intended to include the plural unless the context clearly dictates otherwise, and it should be further understood that the terms "comprises" and/or "comprising," when used in this specification, specify the presence of features, steps, operations, devices, components, and/or combinations thereof.
It should be noted that the terms "first," "second," and the like in the description and claims of this application and in the drawings described above are used for distinguishing between similar elements and not necessarily for describing a particular sequential or chronological order. It is to be understood that the data so used is interchangeable under appropriate circumstances such that the embodiments of the application described herein are capable of operation in other sequences than those illustrated or described herein.
The above description is only a preferred embodiment of the present invention and is not intended to limit the present invention, and various modifications and changes may be made by those skilled in the art. Any modification, equivalent replacement, or improvement made within the spirit and principle of the present invention should be included in the protection scope of the present invention.
Claims (11)
1. An endoscopic system, comprising:
a rigid tube endoscope (10);
a light source module (20), wherein the light source module (20) is connected with the hard tube type endoscope (10) and is used for emitting light with a plurality of wave bands to the hard tube type endoscope (10);
a spectroscopy module for reflecting and/or transmitting light collected by the hard tube endoscope (10);
the near-infrared first-zone acquisition module (40), the near-infrared first-zone acquisition module (40) receives the light reflected or transmitted by the light splitting module and images;
the near-infrared two-region acquisition module (50), the near-infrared two-region acquisition module (50) receives the light reflected or transmitted by the light splitting module and images;
the visible light acquisition module (60), the visible light acquisition module (60) is used for receiving the light reflected or transmitted by the light splitting module and imaging;
the control module (70) is electrically connected with the near-infrared first-region acquisition module (40), the near-infrared second-region acquisition module (50) and the visible light acquisition module (60), and the control module (70) is used for acquiring images generated by the near-infrared first-region acquisition module (40), the near-infrared second-region acquisition module (50) and the visible light acquisition module (60) and processing and displaying the images.
2. The endoscopic system of claim 1, wherein the spectroscopy module is plural, at least one of the spectroscopy module being disposed between the rigid tube endoscope (10) and the near-infrared two-zone acquisition module (50) such that the near-infrared two-zone acquisition module (50) receives light transmitted by the spectroscopy module; at least one other light splitting module is arranged between the visible light collection module (60) and the near-infrared first-zone collection module (40), so that one of the visible light collection module (60) and the near-infrared first-zone collection module (40) receives the light reflected by the light splitting module, and the other receives the light transmitted by the light splitting module.
3. The endoscopic system of claim 2, wherein the plurality of spectroscopic modules comprises a first spectroscopic module (31) and a second spectroscopic module (32), the near infrared second zone acquisition module (50) being located on a transmission path of the first spectroscopic module (31); the second light splitting module (32) is located on a reflection path of the first light splitting module (31), the visible light collecting module (60) is located on a reflection path of the second light splitting module (32), and the near-infrared first region collecting module (40) is located on a transmission path of the second light splitting module (32).
4. The endoscopic system of claim 1, wherein said light source module (20) comprises a white light source (21) and a multiband light source (22), a band range of said multiband light source (22) being selectably arranged, said multiband light source (22) being capable of emitting at least near-infrared light.
5. The endoscopic system of claim 4, wherein the multiband light source (22) comprises:
a near-infrared chip (221);
a filter (222), the filter (222) being a narrow band filter;
the coupling mirror (223) is located on one side, far away from the near-infrared chip (221), of the optical filter (222), and the coupling mirror (223) is used for enabling light passing through the optical filter (222) to enter the hard tube type endoscope (10) after being coupled into an optical fiber.
6. The endoscopic system of claim 1, further comprising an achromatic magnification module (80), said achromatic magnification module (80) being plural, at least one achromatic magnification module (80) being located on the light-incident side of said near-infrared two-zone acquisition module (50), and at least another achromatic magnification module (80) being located on the light-incident sides of said near-infrared one-zone acquisition module (40) and said visible light acquisition module (60).
7. The endoscopic system of claim 6, wherein the achromatic magnification module (80) comprises, in order from an object side to an image side, a first lens (81), a second lens (82), a third lens (83), and a fourth lens (84), wherein the second lens (82) and the fourth lens (84) are both double cemented lenses.
8. The endoscopic system of claim 1, wherein the near-infrared first-zone acquisition module (40) comprises:
a narrow band filter;
a near-infrared first-zone imaging lens;
the near-infrared first-zone fluorescence camera is used for collecting light passing through the narrow-band filter and focusing the light on an imaging target surface of the near-infrared first-zone fluorescence camera, and the near-infrared first-zone fluorescence camera is used for converting optical signals into electric signals to perform imaging display.
9. The endoscopic system of claim 1, wherein said near-infrared two-region acquisition module (50) comprises:
a long-pass filter;
a near-infrared two-zone imaging lens;
the near-infrared two-zone fluorescence camera is used for collecting light passing through the long-pass filter and focusing the light on an imaging target surface of the near-infrared two-zone fluorescence camera, and the near-infrared two-zone fluorescence camera is used for converting optical signals into electric signals to carry out imaging display.
10. The endoscopic system of claim 1, wherein said rigid tube endoscope (10) comprises at least an optical lens assembly of a plurality of lenses.
11. The endoscopic system according to any of claims 1 to 10, further comprising a coupling lens (90) and an image-transmitting fiber (100), the coupling lens (90) being connected with the image-transmitting fiber (100),
the coupling lens (90) and the image transmission optical fiber (100) are positioned between the light splitting module and the near-infrared two-zone acquisition module (50), so that light transmitted by the light splitting module is coupled by the coupling lens (90) to enter the image transmission optical fiber (100) for transmission, and then is transmitted to the near-infrared two-zone acquisition module (50); or
Coupling lens (90) with pass like optic fibre (100) and be located hard tube type endoscope (10) with between the spectral module, the light that hard tube type endoscope (10) was collected is through coupling lens (90) couple is advanced pass like optic fibre (100) in transmit, and then transmit to spectral module department.
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