CN106236016B - A kind of in-situ projection method for vein imaging - Google Patents
A kind of in-situ projection method for vein imaging Download PDFInfo
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- 210000003462 vein Anatomy 0.000 title claims abstract description 46
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- 238000002834 transmittance Methods 0.000 claims description 2
- 210000004204 blood vessel Anatomy 0.000 description 3
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- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
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- A61B5/4887—Locating particular structures in or on the body
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- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
- A61B5/0075—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence by spectroscopy, i.e. measuring spectra, e.g. Raman spectroscopy, infrared absorption spectroscopy
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- A—HUMAN NECESSITIES
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Abstract
It the present invention relates to a kind of in-situ projection method for vein imaging, realizes that steps are as follows: opening near-infrared module and visible optical module, it is ensured that region uniform illumination to be measured absorbs image using image capture module, while obtaining visible images and near-infrared image；Enhance formula according to contrast, image processing module enhances venous information, waits to be projected；Concentric circles test block is placed in suitable distance on front side of image capture module, finely tunes camera；When Projection surveying, projector successively projects the red visible rectangular image of the blue visible light rectangular image that size determines and correction position coordinate, circulation amendment, until offset error is less than 2mm；After the completion of calibration, by enhancing image using green light mode in-situ projection to detection zone.The present invention can guarantee that virtual image is presented in situ, accurately instruct puncture process.
Description
Technical field
The present invention relates to medical assistance field, in particular to a kind of in-situ projection method for vein imaging.
Background technique
Venipuncture is a kind of common medical means clinically, such as drug injection, infusion, extraction blood etc..Currently,
In traditional operation, medical staff mainly passes through range estimation or experience positioning blood vessel.But meticulous to part blood vessel, fatty thicker or blood
The particular patients ' (such as children, fat person, old man etc.) that pipe collapses, blood vessel is difficult to distinguish, seriously affects success rate of venous puncture.
Therefore, it is badly in need of a kind of vein developing method of auxiliary positioning to instruct to puncture.
Currently, the vein displaying image space fado of mainstream uses near-infrared vein imaging principle, enhancing vein and surrounding tissue pair
Than being imaged after degree, such as a kind of Chinese patent " vein development imaging system " (number of patent application: 201320064740.2), " one
Kind infusion assisted IV visualizer " (number of patent application: 201320007342.7) etc..Such imager all uses transmission-type light
Source, detection zone is limited, and with display performance imaging as a result, being not easy to practical operation.Hereafter, occur using direct light source
Projection imager, such as " a kind of double beam system suitable for peripheral blood vessel vein display " (number of patent application:
201320376695.4) Chinese patent " a kind of vein developing method and vein imaging system " (number of patent application:
201510606622.3) etc..But heat mirror structure is all used in above scheme, the installation of frangible and mating optical component is complicated, together
When calibration process complete by rule of thumb entirely, be unfavorable for the in situ of vein projection and present.
Summary of the invention
The problem to be solved by the present invention is that providing one for the various defects of projection imager in the prior art
In-situ projection method of the kind for vein imaging can guarantee that virtual image is presented in situ, accurately instruct puncture process.
The present invention, which solves the above problems, to be achieved through the following technical solutions:
A: vein region to be measured is placed in specified check bit；
B: near-infrared module and visible optical module are opened, it is ensured that region uniform illumination to be measured；
C: image is absorbed using image capture module, while obtaining visible images and near-infrared image；
D: image processing module pre-processes acquisition image, removes the interference in vein image and noise；
E: formula is enhanced according to contrast, image processing module enhances venous information, waits to be projected；
F: being placed in suitable distance on front side of image capture module for concentric circles test block, finely tune camera position, guarantees acquisition figure
As coaxial and detection faces top edge is parallel with concentric circles；
G: before projection, the light channel structure of projector is adjusted, it is ensured that projected image and acquisition image are completely coincident；
H: when Projection surveying, projector successively projects a kind of visible light rectangular image and correction position coordinate that size determines
Another visible light rectangular image, circulation amendment, until offset error be less than 2mm；
I: demarcate by totally 3 faces for Projection surveying, is coincidence face (i.e. camera adopts the clearest place of figure) and the camera in F and G respectively
Minimum depth of field face and camera the maximal field depth face respectively repeat H step；
J: after the completion of calibration, by the enhancing image in E using green light mode in-situ projection to detection zone.
In the step A, vein region to be measured can be head, neck, the back of the hand, instep, elbow inside etc..
In the step B, near-infrared module refers to high-power near-infrared LED, be furnished with dodging device, can be frosted glass,
The uniform light board of 70% or more light transmittance or Fresnel Lenses etc..Near infrared light wave band can be in 760nm, 850nm, 940nm
One or several kinds of set.It can be seen that optical module can be the LED of 450nm~650nm wave band, it is also possible in external environment
Natural light.
In the step C, image capture module mainly passes through multispectral camera and is automatically separated near-infrared image and visible
Light image, multispectral camera here have more lens types, multiphase type and light velocity divergence type, wherein the 2CCD based on light velocity separation
Camera effect is best.
In the step D, image processing module is using the scanning window of 5 × 5 pixels to pressing in the testing image of acquisition
It is scanned according to sequence from top to bottom, from left to right, calculates in scanning window mean and variance Var in each image, if side
Poor Var is greater than given threshold TD, then the point is smoothed using Fast Median Filtering method, removes vein image to be measured
In interference and noise.
In the step E, it is f that contrast, which enhances formula,boost=m (fnir-nfvis).Wherein, fboostTo scheme after enhancing
Picture, fnirFor near-infrared image, fvisFor visible images, m is that scaling coefficient is (unsaturated according to the maximum of image pixel value
Degree is to determine), n is by formula n=(hnir/hvis)[(Gboost-Gnir)/(Gboost-Gvis)] obtain.In the calculation formula of n, hnirWith
hvisThe respectively gray scale mean intensity of near-infrared image and visible images, GboostFor desired enhancing image medium sized vein
With the intensity contrast rate (experiment adjustable value) of other tissues, GnirAnd GvisRespectively near-infrared image and visible images medium sized vein
With the intensity contrast rate of other tissues, by formula G=| Kvein-Kskin|/(Kvein+Kskin) determine.In the formula, KveinIt is corresponding
The average gray value in image medium sized vein region, KskinFor the average gray value of other tissues of vein neighbouring in respective image.
In the step F, concentric circles is coaxial with the holding of CCD imaging surface center, while both perpendicular to ground level,
CCD lower edges are parallel to horizon.
In the step G, it is assumed that projector is located on the mandrel of F, acquires image size it is known that then by imaging formula
fc=lcdc/Lc(fcIndicate camera focus, lcIndicate the horizontal width of image, LcIndicate the horizontal width of acquisition image-region) it can
Calculate camera operating distance dc.Meanwhile ρ is compared by camera camera shootingc=dc/LcWith projector projects ratio ρp=dp/Lp(dpIndicate projection
Distance of the picture to projector, LpIndicate the horizontal width of projected picture), if acquisition image is overlapped with projected image, need to meet?.After the completion, it by projector WidFin a distance, prevents from interfering with camera installation position.
In the step H and I, Projection surveying share 3 times calibration, be respectively the best face of the camera depth of field, the camera depth of field most
Facet and camera depth of field largest face.Every time when calibration, it is flat in white to be measured that projector projects the blue rectangle that size determines first
Face, camera meet at image processing module after acquiring image, which calculates 4 angular coordinates automatically.Wherein, the normal bit of rectangle
Setting (can calculate automatically or be stored in registration table) known to coordinate.Then, it calculates at this time and standard coordinate deviation, after amendment, through throwing
Shadow instrument launches red rectangle.If calculating deviation again is less than 2mm, calibration terminates, otherwise launches modified blue rectangle again, follow
Ring is to meeting condition.Here the purpose for successively launching blue, red rectangle, which is to prevent from demarcating, too fast leads to front and back modified twice rectangle
Unrecognized situation.
In described step G, H, I, the J, used projector is based on DLP technology, controls dmd chip by DSP, meets
The requirement that optical path projection is overlapped in G projects image.
Compared with prior art, the invention has the benefit that
(1) a kind of in-situ projection method for vein imaging proposed by the present invention replaces traditional heat mirror structure, optical path letter
It is single compact, convenient for operating with；
(2) a kind of in-situ projection method for vein imaging proposed by the present invention, realizes software automatic Calibration, entangles in real time
Orthographic projection deviation；
(3) a kind of in-situ projection method for vein imaging proposed by the present invention, it is in situ that virtual image is presented, accurately refer to
Lead puncture procedure.
Detailed description of the invention
Fig. 1 is the structure chart of in-situ projection method preferred embodiment of the present invention.
Fig. 2 is the flow chart of in-situ projection method of the present invention.
Fig. 3 is a kind of projection lens structure chart of in-situ projection method of the present invention；(a) 4 pieces of eyeglasses are shared for the lens group,
Operating distance 261mm, 16 degree of field angle, real focal length 25.9mm, 90% or more relative illumination.It (b) is projection lens position point
Cloth (c) is four pieces of lens；
Fig. 4 is the calibration process schematic diagram of vein developing method of the present invention.
Specific embodiment
The present invention is further described below with reference to case study on implementation (attached drawing).These case study on implementation are merely to illustrate this hair
It is bright and be used to limit the scope of the invention.In addition, it should also be understood that, after reading the content taught by the present invention, those skilled in the art
Member can make various changes and modification to the present invention, and it is as defined in the appended claims that such equivalent forms equally fall within the application
Range.
The case study on implementation includes near-infrared to the structure chart of the preferable case study on implementation of in-situ projection method of the present invention as shown in Figure 1:
Light source module 101, image capture module 102, image processing module 103 and in-situ projection module 104.
The near infrared light source module 101 includes 111, reflectors 112 of two panels Fresnel Lenses and two 3~5W big
Power near-infrared LED 113 is located at 102 front side of image capture module.Two power near-infrared LEDs are at a distance of about 70mm, wave band difference
For 850nm and 960nm.940nmLED is located in reflector, can be with extraneous natural light diffusing reflection simultaneously to region to be measured.
Described image acquisition module 102 includes multispectral camera 121 and automatic diaphragm lens 122.Wherein, multispectral camera
For light beam divergence type 2CCD camera.
Described image processing module 103 includes central control unit 131 and image processing algorithm.Central control unit 131
It is one or more of digital signal processor (DSP), programmable gate array (FPGA), microprocessor (ARM) or industrial personal computer
Combination.
The in-situ projection module 104 includes digital optical processing projector (DLP) 141 and in-situ projection algorithm.Miniature throwing
Shadow instrument is digital optical processing projector (DLP), by dmd chip, DLP circuit, image controller, colour wheel, convergent lens, Gao Liangguang
The first-class composition in source and projection lens.
According to this embodiment, the flow chart of in-situ projection method of the present invention is as shown in Figure 2:
1) vein region to be measured is lain against into check bit；
2) the high-power near-infrared LED of 850nm and 940nm is opened；
3) visible images and near-infrared image are obtained by light beam divergence type 2CCD camera simultaneously；
4) enhance venous information using the image processing algorithm in industrial personal computer, wait to be projected；
5) concentric circles test block is placed in front of camera at 260mm, fine tuning camera guarantees acquisition image and concentric circles to clear
It is coaxial and parallel with detection faces top edge；
6) projection lens installed and designed is opened, fine tuning is so that projected image and acquisition image are completely coincident；
7) Projection surveying is carried out in the best face of the camera depth of field, camera depth of field minimal face and camera depth of field largest face respectively；
8) 4) medium sized vein image is projected into the back of the hand with green light mode in situ.
According to this case study on implementation, a kind of projection lens structure chart such as (a) institute in Fig. 3 of in-situ projection method of the present invention
Show: the lens group shares 4 pieces of eyeglasses, operating distance 261mm, 16 degree of field angle, real focal length 25.9mm, relative illumination 90% with
On.(b) it is projection lens position distribution, (c) is the actual size of each eyeglass.
Fig. 3 is a kind of projection lens structure chart of in-situ projection method of the present invention；(a) 4 pieces of eyeglasses are shared for the lens group,
Operating distance 261mm, 16 degree of field angle, real focal length 25.9mm, 90% or more relative illumination.It (b) is projection lens position point
Cloth (c) is four pieces of lens, and four pieces of eyeglasses are arranged by optical principle, realizes the effect for focusing setting visual field size.
(c) upper left lens are double lens in, and section is round, 9.00 ± 0.05mm of diameter, former and later two radius of curvature are
55.85mm, lens center thickness are 1.5 ± 0.05mm, side thickness 1.14mm；(c) upper right lens in Fig. 3 are concave-convex lens, are cut
Face is circle, and diameter 9.00-0.05mm, the previous equal 8.00mm of curvature radius, the latter curvature radius is 6.35mm, after
One face diameter is 7.00mm, and lens center thickness is 2.20 ± 0.05mm, side thickness 1.07mm；Lower-left lens in (c) in Fig. 3
For plano-convex lens, section is circle, and diameter 9.00-0.05mm, previous face is plane, and the latter curvature radius is
34.43mm, the latter face diameter are 8.40mm, and lens center thickness is 1.20 ± 0.05mm, side thickness 2.25mm；(c) in Fig. 3
Middle bottom right lens are double lens, and section is rectangle, high 9-0.05mm, wide 7-0.05mm, former and later two curvature radius are
29.65mm, lens center thickness are 2.00 ± 0.05mm, side thickness 1.31mm.
According to this case study on implementation, the calibration process schematic diagram of in-situ projection method of the present invention is as shown in Figure 4: Projection surveying is total
There are 3 calibration, is the best face 2 of the camera depth of field, camera depth of field minimal face 3 and camera depth of field largest face 4 respectively.Every time when calibration,
Projector projects the first visible light rectangle in the step H of 64mm*36mm in white plane to be measured first, and camera acquires image
After meet at image processing module, which calculates this 4 angular coordinates of a, b, c, d automatically.Wherein, the normal place coordinate of rectangle
Known (rectangle abcd in figure).Then, it calculates at this time and standard coordinate deviation, after amendment, the in step H is launched through projector
Two kinds of visible light rectangles.If calculating deviation again is less than 2mm, calibration terminates, and otherwise launches the first modified visible light again
Rectangle is recycled to the condition of satisfaction.Here the purpose for successively launching above two different visible light rectangular image is to prevent from demarcating
It is too fast to lead to the unrecognized situation of front and back modified twice rectangle.
Claims (9)
1. a kind of in-situ projection method for vein imaging, it is characterised in that realize that steps are as follows:
A: vein region to be measured is placed in specified check bit；
B: near-infrared module and visible optical module are opened, it is ensured that region uniform illumination to be measured；
C: image capture module absorbs image by camera, while obtaining visible images and near-infrared image；
D: image processing module pre-processes acquisition image, removes the interference in vein image and noise；
E: formula is enhanced according to contrast, image processing module enhances venous information, waits to be projected；
F: being placed in suitable distance on front side of image capture module for concentric circles test block, finely tune camera position, guarantee acquisition image with
Concentric circles is coaxial and detection faces top edge is parallel；
G: before projection, the light channel structure of projector is adjusted, it is ensured that projected image and acquisition image are completely coincident；
H: when Projection surveying, projector successively projects three kinds of different visible light rectangular images of the determining color of size, Yi Zhongke
The visible light rectangle of light-exposed rectangle and another correction position coordinate, circulation amendment, until offset error is less than 2mm；
I: demarcate by totally 3 faces for Projection surveying, is the coincidence face in F and G step respectively, i.e., camera adopts the clearest place of figure and camera
Minimum depth of field face and camera the maximal field depth face respectively repeat H step；
J: after the completion of calibration, by the enhancing image in E using the third visible mode in-situ projection to detection zone；
In the step E, it is f that contrast, which enhances formula,boost=m (fnir-nfvis), wherein fboostFor image after enhancing, fnir
For near-infrared image, fvisFor visible images, m is scaling coefficient, according to the maximum degree of unsaturation of image pixel value come really
Fixed, n is by formula n=(hnir/hvis)[(Gboost-Gnir)/(Gboost-Gvis)] obtain；In the calculation formula of n, hnirAnd hvisRespectively
For the gray scale mean intensity of near-infrared image and visible images, GboostFor desired enhancing image medium sized vein and other groups
The intensity contrast rate knitted, GnirFor the intensity contrast rate of near-infrared image and other tissues, GvisFor visible images medium sized vein with
The intensity contrast rate of other tissues, by formulaWithIt determines,For the average gray value in near-infrared image medium sized vein region,For
The average gray value of other tissues of neighbouring vein in near-infrared image,Respectively visible images medium sized vein
The average gray value of the average gray value in region and neighbouring vein tissue.
2. the in-situ projection method according to claim 1 for vein imaging, it is characterised in that: in the step B,
Near-infrared module refers to high-power near-infrared LED, be furnished with dodging device, can be frosted glass, 70% or more light transmittance uniform light board,
Or Fresnel Lenses；Near infrared light wave band is one of 760nm, 850nm, 940nm or several set.
3. the in-situ projection method according to claim 1 for vein imaging, it is characterised in that: in the step B,
It can be seen that optical module is the LED of 450nm~650nm wave band, the natural light being also possible in external environment.
4. the in-situ projection method according to claim 1 for vein imaging, it is characterised in that: in the step C,
Image capture module is automatically separated near-infrared image and visible images by multispectral camera, and the multispectral camera has more mirrors
Head dummy, multiphase type and light velocity divergence type, wherein the 2CDD camera effect based on light velocity separation is best.
5. the in-situ projection method according to claim 1 for vein imaging, it is characterised in that: in the step D,
Image processing module is using the scanning window of 5 × 5 pixels to suitable according to from top to bottom, from left to right in the testing image of acquisition
Sequence is scanned, and calculates in scanning window mean and variance Var in each image, if variance Var is greater than given threshold TD, then adopt
It is smoothed with Fast Median Filtering method, removes the interference in vein image to be measured and noise.
6. the in-situ projection method according to claim 1 for vein imaging, it is characterised in that: in the step F,
Concentric circles is coaxial with the holding of CCD imaging surface center, while both perpendicular to ground level, CCD lower edges are parallel to horizon.
7. the in-situ projection method according to claim 1 for vein imaging, it is characterised in that: in the step G,
Assuming that projector is located on the mandrel of F, image size is acquired it is known that then by imaging formula fc=lcdc/LcCamera work can be calculated
Make distance dc, fcIndicate camera focus, lcIndicate the horizontal width of image, LcIndicate the horizontal width of acquisition image-region；Together
When, ρ is compared by camera camera shootingc=dc/LcWith projector projects ratio ρp=dp/Lp, dpIndicate distance of the projected picture to projector, Lp
It indicates the horizontal width of projected picture, if acquisition image is overlapped with projected image, needs to meet?；It completes
Afterwards, it by projector WidFin a distance, prevents from interfering with camera installation position.
8. the in-situ projection method according to claim 1 for vein imaging, it is characterised in that: the step H and I
In, multiple projections calibration is carried out, is demarcated in the best face of the camera depth of field, camera depth of field minimal face and camera depth of field largest face；Often
Deutero-albumose timing, projector projects the first visible light rectangular image in the step H of size determination in white plane to be measured first,
Image processing module is met at after camera acquisition image, which calculates 4 angular coordinates automatically, wherein the normal place of rectangle
Known to coordinate；Then, it calculates at this time and standard coordinate deviation, after amendment, launches in step H through projector and sat for correction position
Target visible light rectangular image；If calculating deviation again is less than 2mm, calibration terminates, and otherwise launches and sits for correction position again
Target visible light rectangular image, is recycled to the condition of satisfaction.
9. the in-situ projection method according to claim 1 for vein imaging, it is characterised in that: the step G, H,
I, in J, used projector is based on DLP technology, controls dmd chip by DSP, meets the requirement that optical path projection is overlapped in G
Project image.
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| CN108143501B (en) * | 2017-12-15 | 2021-11-30 | 苏州科灵医疗科技有限公司 | Anatomical projection method based on body surface vein features |
| CN111248855A (en) * | 2018-11-30 | 2020-06-09 | 财团法人金属工业研究发展中心 | Optical developing device and optical developing method |
| CN111568373A (en) * | 2020-04-20 | 2020-08-25 | 南京师范大学 | OCTA capillary network imaging method for repeated scanning |
| CN111639556B (en) * | 2020-05-15 | 2023-06-20 | 圣点世纪科技股份有限公司 | Non-uniform interpolation finger axis rotation finger vein image correction method |
| CN111603140B (en) * | 2020-06-04 | 2021-12-21 | 北京瀚丞医用设备有限公司 | In-situ visual positioning method and system for biological target |
Citations (16)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6178340B1 (en) * | 1998-08-24 | 2001-01-23 | Eduardo Svetliza | Three-dimensional infrared imager for subcutaneous puncture and study of vascular network |
| CN102184528A (en) * | 2011-05-12 | 2011-09-14 | 中国人民解放军国防科学技术大学 | Low-quality finger vein image enhancement method |
| CN102894960A (en) * | 2012-08-29 | 2013-01-30 | 北京理工大学 | Transmission-type hand back vein three-dimensional infrared imager |
| CN103226817A (en) * | 2013-04-12 | 2013-07-31 | 武汉大学 | Superficial venous image augmented reality method and device based on perspective projection |
| CN203314943U (en) * | 2013-07-08 | 2013-12-04 | 深圳市中科微光医疗器械技术有限公司 | Double-light-source vein angiography device |
| CN103860147A (en) * | 2014-03-28 | 2014-06-18 | 广州中国科学院先进技术研究所 | Method for manufacturing double-lens multi-spectral imaging lens set and vein display system thereof |
| CN203802443U (en) * | 2013-11-22 | 2014-09-03 | 浙江铭众生物医学创业投资有限公司 | Portable blood-vessel imaging device based on near-infrared absorption and projection |
| CN203885479U (en) * | 2014-05-27 | 2014-10-22 | 深圳市中科微光医疗器械技术有限公司 | Glasses type vein imaging device |
| CN104123703A (en) * | 2014-07-09 | 2014-10-29 | 广州中国科学院先进技术研究所 | Primary skin color keeping vein development method |
| CN104146683A (en) * | 2014-04-24 | 2014-11-19 | 深圳大学 | Vein viewing instrument and imaging method thereof |
| CN104605819A (en) * | 2015-01-09 | 2015-05-13 | 深圳元华医疗设备技术有限公司 | Device and method for near-infrared vein angiography point-to-point projection |
| CN105286785A (en) * | 2014-07-25 | 2016-02-03 | 美国科视数字系统公司 | Multispectral medical imaging devices and methods thereof |
| CN105395252A (en) * | 2015-12-10 | 2016-03-16 | 哈尔滨工业大学 | Wearable three-dimensional image navigation device for vascular intervention operation and realizing man-machine interaction |
| CN105426843A (en) * | 2015-11-19 | 2016-03-23 | 安徽大学 | Single-lens palm vein and palmprint image acquisition apparatus and image enhancement and segmentation method |
| CN105581785A (en) * | 2016-02-05 | 2016-05-18 | 深圳新航向科技有限公司 | Light path system of vein projector and vein projector |
| CN105848566A (en) * | 2013-10-23 | 2016-08-10 | 因索诺有限责任公司 | Device for non-invasive detection of predetermined biological structures |
Family Cites Families (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US9492117B2 (en) * | 2006-01-10 | 2016-11-15 | Accuvein, Inc. | Practitioner-mounted micro vein enhancer |
| US8730321B2 (en) * | 2007-06-28 | 2014-05-20 | Accuvein, Inc. | Automatic alignment of a contrast enhancement system |
| US9289160B2 (en) * | 2013-04-11 | 2016-03-22 | Yaroslav Ryabov | Portable biometric identification device using a dorsal hand vein pattern |
-
2016
- 2016-08-18 CN CN201610685272.9A patent/CN106236016B/en active Active
Patent Citations (16)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6178340B1 (en) * | 1998-08-24 | 2001-01-23 | Eduardo Svetliza | Three-dimensional infrared imager for subcutaneous puncture and study of vascular network |
| CN102184528A (en) * | 2011-05-12 | 2011-09-14 | 中国人民解放军国防科学技术大学 | Low-quality finger vein image enhancement method |
| CN102894960A (en) * | 2012-08-29 | 2013-01-30 | 北京理工大学 | Transmission-type hand back vein three-dimensional infrared imager |
| CN103226817A (en) * | 2013-04-12 | 2013-07-31 | 武汉大学 | Superficial venous image augmented reality method and device based on perspective projection |
| CN203314943U (en) * | 2013-07-08 | 2013-12-04 | 深圳市中科微光医疗器械技术有限公司 | Double-light-source vein angiography device |
| CN105848566A (en) * | 2013-10-23 | 2016-08-10 | 因索诺有限责任公司 | Device for non-invasive detection of predetermined biological structures |
| CN203802443U (en) * | 2013-11-22 | 2014-09-03 | 浙江铭众生物医学创业投资有限公司 | Portable blood-vessel imaging device based on near-infrared absorption and projection |
| CN103860147A (en) * | 2014-03-28 | 2014-06-18 | 广州中国科学院先进技术研究所 | Method for manufacturing double-lens multi-spectral imaging lens set and vein display system thereof |
| CN104146683A (en) * | 2014-04-24 | 2014-11-19 | 深圳大学 | Vein viewing instrument and imaging method thereof |
| CN203885479U (en) * | 2014-05-27 | 2014-10-22 | 深圳市中科微光医疗器械技术有限公司 | Glasses type vein imaging device |
| CN104123703A (en) * | 2014-07-09 | 2014-10-29 | 广州中国科学院先进技术研究所 | Primary skin color keeping vein development method |
| CN105286785A (en) * | 2014-07-25 | 2016-02-03 | 美国科视数字系统公司 | Multispectral medical imaging devices and methods thereof |
| CN104605819A (en) * | 2015-01-09 | 2015-05-13 | 深圳元华医疗设备技术有限公司 | Device and method for near-infrared vein angiography point-to-point projection |
| CN105426843A (en) * | 2015-11-19 | 2016-03-23 | 安徽大学 | Single-lens palm vein and palmprint image acquisition apparatus and image enhancement and segmentation method |
| CN105395252A (en) * | 2015-12-10 | 2016-03-16 | 哈尔滨工业大学 | Wearable three-dimensional image navigation device for vascular intervention operation and realizing man-machine interaction |
| CN105581785A (en) * | 2016-02-05 | 2016-05-18 | 深圳新航向科技有限公司 | Light path system of vein projector and vein projector |
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