CN211131438U - Operation microscope system - Google Patents
Operation microscope system Download PDFInfo
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- CN211131438U CN211131438U CN201920996402.XU CN201920996402U CN211131438U CN 211131438 U CN211131438 U CN 211131438U CN 201920996402 U CN201920996402 U CN 201920996402U CN 211131438 U CN211131438 U CN 211131438U
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Abstract
The utility model relates to an operation microscope system, including eyepiece (17), objective (12), first spectroscope (13) and first filter (15), still include laser source, laser image acquisition unit (21), computer (3) and display element (4), laser source produces the laser irradiation operation region, and the regional reflection laser of operation loops through objective (12), first spectroscope (13) and first filter (15) to laser image acquisition unit (21), laser image acquisition unit (21) and computer (3) interconnect, computer (3) and display element (4) interconnect, objective (12), display element (4), first spectroscope (13) and eyepiece (17) set gradually. Compared with the prior art, the utility model discloses additional blood flow image information is looked over in real time to the accessible eyepiece, reduces the doctor simultaneously and puts aside the needs in order to look over other displays to the eyesight from the microscope eyepiece.
Description
Technical Field
The utility model belongs to the technical field of microsurgery operation equipment and specifically relates to an operation microscope system is related to.
Background
In modern medicine, an operating microscope is essential for the surgeon. The different magnifications, chosen as required, can provide a magnifying attempt of the operative field, allowing the surgeon to operate even on structures that are hardly visible to the naked eye, in particular for neurosurgery, for the treatment of delicate structures such as capillaries or nerves. Meanwhile, the light source is directly integrated inside the surgical microscope, so that the surgical microscope can provide good surgical field illumination.
The existing technology and the commonly used operation microscope equipment mainly provide morphological observation assistance for surgeons, but cannot reflect functional information such as blood flow velocity in blood vessels, blood flow perfusion of tissues and the like in real time. This additional information is of great importance for neurosurgical operations. For example, in the intracranial aneurysm clipping operation and cerebrovascular malformation excision, monitoring the cerebral blood flow in real time is beneficial for an operator to dynamically master the blocking degree of abnormal blood flow, and meanwhile, the mistaken clipping of normal blood vessels is avoided; in the cerebrovascular bypass surgery process, the real-time monitoring of the cerebral cortex blood flow can also help to evaluate the patency degree of the bypass blood vessel and whether the cerebral blood flow is recovered to the normal level.
At present, in part of clinical practice, a microscope with a fluorescence unit is used to observe blood vessels intraoperatively, and with the aid of a fluorescent dye (such as indocyanine green ICG), a fluorescence image of the blood vessels can be observed on an additional display after excitation, which is convenient for intraoperative reference of a doctor. However, this method only observes the presence or absence of blood vessels, does not include real-time dynamic blood flow information such as flow rate, and requires the injection of fluorescent dye in advance, which imposes a burden on the patient.
In the aspect of multi-modal data display, a scholarly proposes an improved mode of adding an O L ED display inside a surgical microscope, and the mode needs to digitally display full-field visual field information, so that the authenticity of tissues observed by the microscope is lost.
In the aspect of blood vessel blood flow imaging, a laser speckle imaging (L SI) technology is used as a new blood vessel and blood flow optical imaging method, a visual quantitative real-time tissue blood flow perfusion image can be obtained by analyzing speckles caused by coherent superposition of diffuse reflection laser through different propagation paths, and the method is a two-dimensional full-field blood flow imaging method which is free of marks, non-contact, free of contrast agents and high in time and space resolution.
SUMMERY OF THE UTILITY MODEL
The present invention is directed to a surgical microscope system for overcoming the above-mentioned drawbacks of the prior art.
The purpose of the utility model can be realized through the following technical scheme:
the utility model provides an operation microscope system, includes eyepiece, objective, first spectroscope and first filter, still includes laser source, laser image acquisition unit, computer and display element, laser source produces the laser irradiation operation area, and the reflection laser of operation area loops through objective, first spectroscope and first filter to laser image acquisition unit, laser image acquisition unit and calculation interconnect, computer and display element interconnect, objective, display element, first spectroscope and eyepiece set gradually.
The display unit comprises a projector and a display, the projector is connected with the computer, and light rays of the projector are projected to the display through the semi-transparent and semi-reflective mirror.
The display is located at the position of a virtual image formed in the microscope in the operation area, and the semi-transparent and semi-reflective mirror is located between the display and the first spectroscope.
The projector is a D L P projector, and the display is a HUD.
The laser light source and the white light source form a composite light source.
The second filter and the second spectroscope are arranged between the ocular lens and the first spectroscope, and the white light reflected by the operation area sequentially passes through the objective lens, the first spectroscope, the second filter and the second spectroscope to the white light image acquisition unit.
The first filter is a filter for filtering white light.
The second filter is a filter for filtering laser.
The white light image acquisition unit comprises a second CCD camera.
The laser image acquisition unit comprises a first CCD camera.
Compared with the prior art, the utility model has the advantages of it is following:
(1) the blood flow information can be superposed in the operation visual field, so that more guidance and reference are provided for the operation.
(2) The blood flow information is positioned at the position of a virtual image formed by the actual operation visual field in the microscope, and the operation visual field and the blood flow information can be simultaneously seen through the ocular lens, so that the requirement that a doctor removes the eye from the ocular lens of the microscope to see other displays is reduced.
(3) The projector is D L P projector, and the display is the HUD, can show operation field of vision stack blood flow information better.
(4) The laser light source and the white light source form a composite light source, so that the two light sources share a light path, and the operation microscope system is more reasonable in arrangement.
Drawings
Fig. 1 is a schematic structural view of the present invention;
FIG. 2 is a structural diagram of the composite light source and multi-modal image acquisition module of the present invention;
FIG. 3 is a schematic view of the connection structure of the computer of the present invention;
FIG. 4 is a diagram of a display unit structure according to the present invention;
reference numerals:
1 is a composite light source; 3 is a computer; 4 is a display unit; 12 is an objective lens; 13 is a first spectroscope; 14 is a second spectroscope; 15 is a first filter; 16 is a second filter; 17 is an ocular lens; 21 is a laser image acquisition unit; 22 is a white light image acquisition unit; 41 is a projector; 42 is a display; reference numeral 43 denotes a half mirror.
Detailed Description
The present invention will be described in detail below with reference to the accompanying drawings and specific embodiments. The embodiment is implemented on the premise of the technical solution of the present invention, and a detailed implementation manner and a specific operation process are given, but the scope of the present invention is not limited to the following embodiments.
Examples
In this embodiment, all the illumination and imaging sources are integrated directly into the optical path of the conventional surgical microscope, and the display 42 is integrated inside the surgical microscope to provide external image data, so that the doctor can observe the surgical tissue and simultaneously observe the information such as real-time blood flow images obtained by L SI technology directly through the eyepiece 17, thereby avoiding the inconvenience of moving the sight line away from the microscope and turning the sight line to the external display.
Fig. 1 is a schematic structural diagram, and it can be obtained that this embodiment includes a composite light source 1, a multi-modal image collection module, a computer 3 and a Display unit 4, where the composite light source 1 adopts a common optical path system, and includes a laser light source and a common white light source, and irradiates on an operation area to be imaged, the multi-modal image collection module includes a laser image collection unit 21 and a white light image collection unit 22, and is used to obtain a laser speckle image and a white light image of the operation area, and transmit the laser speckle image and the white light image to the computer 3, and after calculation and analysis, generate an auxiliary operation medical image, i.e., a real-time blood flow image, the Display unit 4 includes a projector 41 and a Display 42, the computer 3 is connected to the projector 41 in the Display unit 4, and projects the processed blood flow image onto a Head-Up Display (Head-Up Display) located inside a microscope through a D L P (Digital L light Processing) projector, so as to realize a function of superimposing blood flow information in an operation field.
The laser image acquisition unit 21 includes a first CCD (charged coupled device) camera.
The white light image capturing unit 22 includes a second CCD camera.
A typical commercial D L P projector includes two important components, a digital micro lens array (DMD) chip with hundreds of thousands of small mirrors each having a switching capability to independently control light, and a color wheel (color filter), where the light source is refracted through the color wheel onto the DMD chip, and the chip receives the control signal and adjusts the angle of the light reflected by the small mirrors to finally emit the light to the display 42.
HUDs were the first flight aids used on aircraft to project important information or parameters relating to flight safety using the principle of light reflection onto a piece of glass, the focal length of the projected information being adjusted to infinity, and the height of the piece of glass being substantially equal to the eye height of the pilot, so that when the pilot looks straight ahead, the external scene can be merged with the information displayed by the HUD. The core of this image display device is the special sandwich glass design, generally, the outer layer is two simple pieces of glass, and the interlayer is a wedge-shaped PVB (polyvinyl butyral) film, so that the glass is thick at the top and thin at the bottom to avoid image double images. The HUD screen has the semi-transparent and semi-reflective characteristic, so that when the HUD screen is used, human eyes can observe information projected on the screen, and can also observe actual objects through the screen.
Fig. 2 is a structural diagram of the composite light source and the multi-modal image acquisition module. The laser light source generates laser with narrow spectral width and emits the laser to an operation area, the wavelength range of the laser is about 650-980 nm, the power range is about 2-10 mW, and the spectral width is as narrow as possible in order to ensure the imaging quality. The laser light source and a white light source of a common operation microscope form a common light path system in the microscope, the common light path system reaches a first spectroscope 13 through an objective lens 12, a first optical filter filters white light, only speckle information under laser is reserved, the speckle information is collected by a first CCD camera, and the first CCD camera is a high-sensitivity CCD camera. The second optical filter is used for filtering laser and keeping image information under white light, so that the image information passes through the second spectroscope 14, reaches the microscope eyepiece 17 for a doctor to observe, and is collected by the second CCD camera for a common microscope for subsequent processing and analysis. Particularly, the camera is specially used for collecting laser speckle images obtained under laser irradiation, so that the camera is required to have higher sensitivity, and the exposure time is within the range of 5-10 ms; the second CCD camera is specially used for collecting the operation visual field image under the irradiation of common white light.
The computer 3 is provided with mature laser speckle image processing software, uses an optimization processing program accelerated by a GPU to realize that a speckle image obtained by the first CCD camera is efficiently calculated in real time to obtain a contrast image, the contrast image is processed by pseudo color to be a blood flow image convenient for human eyes to observe, the blood flow image comprises blood flow information, and simultaneously, the blood vessel center line in the blood vessel skeleton and the blood vessel center line in the blood flow image under the white light image are accurately registered and finally output to a D L P projector connected with the computer 3.
The following prior art procedure was used to analyze the laser speckle imaging to obtain a blood flow image.
The computer 3 is loaded with a conventional program for analyzing laser speckle imaging to obtain a blood flow image.
Laser speckle imaging utilizes the concept of contrast to quantify the degree of speckle blurring, which in turn reflects the position and velocity of the motion of the speckle particles, i.e., blood flow distribution and velocity. The contrast K is basically defined as follows:
where σ represents the standard deviation of the speckle intensity and μ represents the average of the intensity.
The processing method of the original speckle image mainly comprises a time contrast algorithm and a space contrast algorithm, and the scattering particle velocity information is obtained through the time and space statistical characteristics of speckles respectively. The time contrast algorithm needs to continuously shoot and record a plurality of frames of speckle images, for each pixel point, the average value and the standard deviation of the gray value data of the point in different frames are calculated, and then the time contrast value is obtained through ratio calculation; the spatial contrast algorithm needs to select a square sliding spatial window on an original speckle image, calculate the average value and the standard deviation of the gray values of all points in the window, use the average value and the standard deviation as the spatial average value and the spatial standard deviation of the speckle intensity of the central point position, and further obtain the spatial contrast value of the point according to the ratio of the average value and the standard deviation.
In order to ensure that the computing power of software adapts to the real-time imaging requirements in the operation, the embodiment applies an enhanced laser speckle contrast analysis (e L ASCA) algorithm based on monotonic point transformation, reduces the calculated amount, improves the dynamic range of data, greatly improves the operation speed and keeps the effectiveness of the data2(M, N, l) is transformed into a one-dimensional vector f (i) (i is 1, …, M × N ×L), and a random variable f is transformed to satisfy p (f) based on a monotonic point transformation theorye) F of [ identical to ] 1eNamely, the following conditions are satisfied:
where, the constant b is a proportionality coefficient and v is a blood flow velocity.
F is calculated according to the following formulaeFinally will feIs reconstructed back to the three-dimensional matrix Ke 2And then a contrast image is obtained.
Wherein, NumfFor numbers not greater than f in the contrast value data,
fig. 4 is a structural diagram of a display unit, in this embodiment, the display unit 4 mainly includes a D L P projector, a half mirror, and a HUD L P projector, after receiving a signal from the computer 3, the angle of a small mirror on an internal DMD chip is automatically adjusted, and an image obtained by processing and only retaining a blood flow portion is projected onto the half mirror in real time and is finally projected onto a HUD placed inside the surgical microscope after reflection.
When a doctor performs a surgical operation such as aneurysm occlusion operation requiring real-time monitoring of blood flow conditions around an operation area, the doctor can turn on a laser light source and a display unit 4 while turning on a white light source, laser is irradiated on the surface of a tissue, a multi-modal image acquisition unit such as a high-sensitivity CCD camera or a high-sensitivity CMOS camera acquires laser speckle images changing in real time through light splitting, filtering light paths and the like and transmits the laser speckle images to a computer 3 connected with the multi-modal image acquisition unit, the computer 3 calculates speckle contrast ratio values by using an L SI algorithm program accelerated by a GPU, finally obtains real-time blood flow information, and the real-time blood flow information is projected onto an HUD through a D L P projector, so that the doctor can conveniently observe real-time blood flow perfusion condition changes near the operation area.
It is to be understood that the above implementation methods are only for illustrating the specific principles and available scenarios of the present embodiments, but are not limited thereto. It will be appreciated that various modifications and variations based on the embodiment will also be considered as the protective scope of the embodiment for those skilled in the art.
Claims (10)
1. The utility model provides an operation microscope system, includes eyepiece (17), objective (12), first spectroscope (13) and first filter (15), its characterized in that still includes laser source, laser image acquisition unit (21), computer (3) and display element (4), laser source produces laser irradiation operation area, and operation area's reflection laser loops through objective (12), first spectroscope (13) and first filter (15) to laser image acquisition unit (21), laser image acquisition unit (21) and computer (3) interconnect, computer (3) and display element (4) interconnect, objective (12), display element (4), first spectroscope (13) and eyepiece (17) set gradually.
2. An operating microscope system according to claim 1, wherein the display unit (4) comprises a projector (41) and a display (42), the projector (41) is connected to the computer (3), and the light of the projector (41) is projected to the display (42) through the half mirror (43).
3. An operating microscope system as claimed in claim 2, characterised in that the display (42) is located at a virtual image of the operating field within the microscope, and the half mirror (43) is located between the display (42) and the first beam splitter (13).
4. A surgical microscope system according to claim 2, wherein the projector (41) is a D L P projector and the display (42) is a HUD.
5. A surgical microscope system according to claim 1, wherein the laser light source and the white light source form a composite light source (1).
6. The surgical microscope system according to claim 5, wherein a second filter (16) and a second spectroscope (14) are arranged between the ocular lens (17) and the first spectroscope (13), and the white light reflected by the surgical field passes through the objective lens (12), the first spectroscope (13), the second filter (16) and the second spectroscope (14) to the white light image acquisition unit (22) in sequence.
7. An operating microscope system as claimed in claim 6, wherein the second filter (16) is a laser filter.
8. An operation microscope system according to claim 6, characterized in that the white light image acquisition unit (22) comprises a second CCD camera.
9. An operating microscope system as claimed in claim 1, characterized in that the first filter (15) is a filter for filtering out white light.
10. An operation microscope system according to claim 1, characterized in that the laser image acquisition unit (21) comprises a first CCD camera.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201920996402.XU CN211131438U (en) | 2019-06-28 | 2019-06-28 | Operation microscope system |
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| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201920996402.XU CN211131438U (en) | 2019-06-28 | 2019-06-28 | Operation microscope system |
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Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN110200707A (en) * | 2019-06-28 | 2019-09-06 | 上海德芬生物科技有限公司 | A kind of operating microscope system and imaging method showing blood flow information |
| CN112526739A (en) * | 2020-12-21 | 2021-03-19 | 上海美沃精密仪器股份有限公司 | Operating microscope with navigation information display module |
| CN117031720A (en) * | 2023-09-28 | 2023-11-10 | 微纳动力(北京)科技有限责任公司 | Automatic integrated optical device and system |
-
2019
- 2019-06-28 CN CN201920996402.XU patent/CN211131438U/en active Active
Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN110200707A (en) * | 2019-06-28 | 2019-09-06 | 上海德芬生物科技有限公司 | A kind of operating microscope system and imaging method showing blood flow information |
| CN112526739A (en) * | 2020-12-21 | 2021-03-19 | 上海美沃精密仪器股份有限公司 | Operating microscope with navigation information display module |
| CN117031720A (en) * | 2023-09-28 | 2023-11-10 | 微纳动力(北京)科技有限责任公司 | Automatic integrated optical device and system |
| CN117031720B (en) * | 2023-09-28 | 2023-12-29 | 微纳动力(北京)科技有限责任公司 | Automatic integrated optical device and system |
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| TR01 | Transfer of patent right |
Effective date of registration: 20221219 Address after: 226007 Room 1403-1406, Building 3, Zhongjiang International Plaza, No. 6, Tongjia Road, Chongchuan District, Nantong City, Jiangsu Province Patentee after: Nantong Ruixiang Health Medical Technology Co.,Ltd. Address before: Room 322, No. 359-367, 371-385, Guangyan Road, Jing'an District, Shanghai, 200072 Patentee before: SHANGHAI DOLPHIN BIOTECH Co.,Ltd. |
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