CN201026212Y - Blood sugar nondestructive testing apparatus with photics coherent chromatography technique eyeground imaging - Google Patents
Blood sugar nondestructive testing apparatus with photics coherent chromatography technique eyeground imaging Download PDFInfo
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- CN201026212Y CN201026212Y CNU200620141296XU CN200620141296U CN201026212Y CN 201026212 Y CN201026212 Y CN 201026212Y CN U200620141296X U CNU200620141296X U CN U200620141296XU CN 200620141296 U CN200620141296 U CN 200620141296U CN 201026212 Y CN201026212 Y CN 201026212Y
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Abstract
The utility model discloses a blood sugar nondestructive inspection method and device for OCT (Optical Coherence Tomography) retinal imaging. OCT (Optical Coherence Tomography) is applied to conduct tomography imaging for the retinal capillary layer. Through analysis about the change of the scattering coefficient in the layer tissue, the blood sugar content in human body can be tested, finally realizing the nondestructive inspection to the blood sugar in human body. The device of the inspection method adopts the optical fiber OCT (Optical Coherence Tomography) system, which is composed of broadband light source, a 2*2 broadband optical fiber coupling, a phase modulator, a rapid-scanning optical delay line, a polarization controller, a collimation lens, objective lens, a detector, an XY-direction scanning module, a pre-positioned enlarger, a data collecting card, a computer, etc. The method can obtain the tomography image of the retinal capillary layer under different blood sugar consistency. The utility model has the properties of no destruction, tomography and high resolution. Through identifying the light intensity change of the retinal capillary layer, the device can reflect the change of the blood sugar in human body.
Description
Technical Field
The utility model relates to a blood sugar nondestructive test device based on optical coherence tomography technique eye ground formation of image.
Background
Along with the gradual improvement of living standard of people, the physical labor amount of people is obviously reduced, and simultaneously along with the unreasonable diet structure, diabetes becomes a disease which influences the health of people more and more. The blood sugar content of a patient with diabetes needs to be frequently detected in order to ensure that the blood sugar content of the patient with diabetes tends to be reasonable, and then a proper amount of medicine is manually injected according to the content of the blood sugar content to control the blood sugar content.
The existing blood sugar detection methods approved by the FDA in the united states are destructive or micro-destructive detection methods, such as Onetouch glucometer of qiangsheng corporation in the united states, which needs to collect a certain amount of blood samples from a human body to test the blood sugar content of the human body. Even minute amounts of blood taken can be very painful for patients who are to be tested several times a day. Compared with destructive detection, the nondestructive detection mode has obvious advantages: (1) The pain of the patient in blood sampling measurement every day is reduced, and the life quality of the patient is improved; (2) The blood sugar test frequency can be conveniently increased, the blood sugar control accuracy is improved, and the risk of diabetic complications is reduced; and (3) reducing the cost of each measurement. In view of the huge number of diabetes patients all over the world, the nondestructive blood sugar detector has a large market space, and large companies and research institutions abroad invest a great deal of energy to research the nondestructive detection problem of the blood sugar of the human body. The methods which are frequently studied abroad include near infrared spectrum analysis, optical rotation polarization, raman spectrum analysis, photoacoustic method and the like, but the methods generally have the defects of low signal-to-noise ratio, insufficient precision and sensitivity and the like, and cannot be clinically applied up to now.
Optical Coherence Tomography (OCT) is a recently developed technique, but has shown great strength in non-destructive analytical detection of tissue volumes, enabling it to achieve high precision and resolution in the detection of biological tissue volumes.
The unique optical characteristic of the human eye structure brings convenience to the optical imaging of the fundus structure. Light from the eye pupil is incident on the pigmented layer at the outermost layer of the retina and is reflected back to be detected by the photosensitive cells. The structure of the retina of the eye ground is well-arranged, and the retina of the eye ground has abundant vascular network supply and provides nutrients for optic nerves and sensitive cells.
The sub-level structures of the retinal layer and choroid layer of the fundus are clear. There are two main blood supply layers:
(a) Next to the choroid layer of the retina. The choroid is rich in arteries and veins and a specialized layer of capillary vessels that supply nutrients to the photosensitive cells (rod cells and cone cells) in the outer layer of the retina.
(b) The blood supply layer in the retina, the artery and vein, extends outward from the optic nerve papilla to provide nutrients to the tissues in the eye of the nuclear layer in the whole retina.
According to the Mie theory, the difference of the refractive indexes of the scatterers and the medium where the scatterers are located can be reflected through the scattering coefficient of a scattering system. The change of blood sugar concentration can change the refractive index of the body fluid of the tissue body, and further influences the integral scattering coefficient of the tissue body. The relationship between scattering coefficient and refractive index difference inside and outside the cell can be formulated as follows:
where r is the radius of the scattering sphere, ρ s Is the number of scattering spheres in a unit volume, λ is the incident light wavelength, n s Refractive index of intracellular material, n medium Is the refractive index of extracellular fluid, and n s ＞n medium . As the blood glucose concentration increases, n medium The scattering coefficient represented by the above formula becomes small. Conversely, the blood sugar concentration becomes smaller, n medium The smaller the scattering coefficient becomes.
The utility model discloses what survey is the backscatter signal of the tissue body, its intensity curve slope has represented the size of tissue body scattering coefficient. The attenuation of light in a medium with scattering and absorption can be approximated as:
the slope of the exponential decay of the intensity signal of light in the tissue volume as the blood glucose concentration of the tissue volume changes reflects u s Therefore, the value of the scattering coefficient can be obtained according to the value of the slope of the curve through the tissue intensity signal curve detected by the OCT, and the value of the blood glucose concentration content of the tissue can be indirectly obtained.
Disclosure of Invention
An object of the utility model is to provide a blood sugar nondestructive test device of optical coherence tomography eye ground formation of image. The capillary vessel layer of retina of human eye is chromatographically imaged by Optical Coherence Tomography (OCT), and the change of scattering coefficient of tissue body in the layer is analyzed to indirectly detect the blood sugar content of human body, so as to realize the non-destructive detection of blood sugar in human body.
In order to achieve the above purpose, the utility model adopts the technical proposal that:
1. blood sugar nondestructive testing method for fundus imaging by optical coherence tomography
Carrying out tomography on a capillary vessel layer of a retina of a human eye by using an optical coherence tomography technology, and indirectly detecting the blood sugar content of the human body by analyzing the change of a scattering coefficient of a tissue body of the layer so as to finally achieve the nondestructive detection of the blood sugar of the human body; the method comprises the following specific steps:
1) After a beam of light enters the tissue body, the slope of the exponential attenuation of the intensity signal of the light in the tissue body reflects the information of the tissue body, the intensity signal curve of the tissue body is detected through OCT, the size of the scattering coefficient can be obtained according to the numerical value of the slope of the curve, and the change of the blood sugar concentration can change the refractive index of the body fluid of the tissue body so as to influence the integral scattering coefficient of the tissue body, so that the slope of the intensity curve of the backward scattering signal of the tissue body is detected to represent the size of the scattering coefficient of the tissue body;
2) The backward scattered light of a specific measured position of a capillary vessel layer of human retina enters an OCT system, interferes with sample light when the backward scattered light is converged at an optical fiber coupler, and carries out layer surface scanning through an XY direction scanning component to obtain a multi-point modulation signal of the specific layer, and then the multi-point modulation signal is converted into an electric signal by a detector and a preamplifier, a data acquisition card converts the signal into a digital signal, and a computer carries out image reconstruction work, and the size of the blood sugar concentration content of a tissue body can be indirectly obtained through data processing.
2. Blood sugar nondestructive testing device for optical coherence tomography fundus imaging
Low-coherence light of a broadband light source enters a 2X 2 broadband fiber coupler through an optical fiber, is split and then respectively enters a reference arm and a sample arm, and enters a fast scanning system which is sequentially composed of a collimating lens, a diffraction grating, a Fourier transform lens and a vibrating mirror after one path of light entering the reference arm passes through a phase modulator; one path entering the sample arm is projected to the sample pool through the polarization controller, the collimating lens, the XY direction scanning assembly, the collimating lens and the objective lens in sequence; after two paths of reflected light interfere with each other when being converged by the 2X 2 broadband optical fiber coupler, the two paths of reflected light are connected into the detector and the preamplifier and are electrically connected with the data acquisition card and the computer in sequence.
Compared with the background art, the utility model the beneficial effect who has is:
the method for imaging and nondestructively detecting the blood sugar content of the human body by using the Optical Coherence Tomography (OCT) has the following advantages compared with the OCT detection of the skin:
a. although the skin has a relatively large detection depth (1-2 mm) to the wavelength (1310 nm) of the detection light, the stratum corneum on the surface of the skin has relatively large attenuation to the light signal, but the eye is almost transparent to the detection light, and the detection depth can reach 2-3 cm.
b. A large number of large tissue bodies such as hair follicles and cellulite in dermal tissues interfere with OCT detection signals, retina structures are relatively uniform, layered structures are very obvious, and OCT tomography can be more effectively detected.
c. The blood supply system of human eyes is more abundant than that of skin, and the change of blood sugar content has great influence on the change of tissue scattering coefficient, thus being beneficial to detection.
And (II) the change of the scattering coefficient is detected by using the OCT to indirectly detect the blood sugar content of the human body, and compared with other nondestructive detection methods, the method has the characteristics of high precision, high sensitivity, high anti-interference performance brought by chromatography and the like.
And (III) establishing a fundus capillary vascular layer scattering model, and further carrying out a microsphere simulation system simulating tissue volume scattering coefficient change by detecting the change of sugar concentration in the model.
And (IV) the structure of the device is non-contact measurement, which is similar to the ophthalmic examination, so the device is easy to accept and is convenient to use and operate.
Drawings
FIG. 1 is a structural diagram of the blood sugar nondestructive testing device for imaging the fundus based on the optical coherence tomography of the present invention;
FIG. 2 is a graph of OCT signal and fitted intensity;
FIG. 3 is a graph comparing OCT signal intensity curves for solutions of different refractive indices.
In the figure: 1. the device comprises a broadband light source, 2 optical fibers, 3, 2 x 2 broadband optical fiber couplers, 4, a phase modulator, 5, a fast scanning system, 5-1 of a collimating mirror, 5-2 of a diffraction grating, 5-3 of a Fourier transform lens, 5-4 of a vibrating mirror, 6 of a polarization controller, 7 of the collimating mirror and an objective lens, 8 of a detector and a preamplifier, 9 of a data acquisition card, 10 of an XY direction scanning component, 11 of a computer, 12 of a sample cell.
Detailed Description
According to the Mie theory, the difference in refractive index between the scatterer and the medium in which the scatterer is located will be reflected by the scattering coefficient of the scattering system. The change of blood sugar concentration can change the refractive index of the body fluid of the tissue body, and further influences the integral scattering coefficient of the tissue body. The scattering coefficient as a function of the refractive index difference between the inside and outside of the cell can be formulated as follows:
where r is the radius of the scattering sphere, ρ s Is the number of scattering spheres in a unit volume, λ is the wavelength of the incident light, n s Refractive index of intracellular material, n medium Is the refractive index of extracellular fluid, and n s ＞n medium . As the blood glucose concentration increases, n medium The scattering coefficient represented by the above formula becomes small. Conversely, the blood sugar concentration decreases, n medium The smaller the scattering coefficient becomes.
The utility model discloses what survey is the backscatter signal of the tissue body, its intensity curve slope has represented the size of tissue body scattering coefficient. The attenuation of light in a medium with scattering and absorption can be approximated as:
the slope of the exponential decay of the intensity signal of light in the tissue volume as the blood glucose concentration of the tissue volume changes reflects u s So that the intensity signal curve of the tissue body detected by OCT can obtain the magnitude of scattering coefficient according to the value of the slope of the curve, and further can indirectly obtain the blood sugar of the tissue bodyThe size of the concentration content.
The device of the utility model is shown in figure 1, and comprises a broadband light source 1, optical fibers, a 2X 2 broadband optical fiber coupler 3, a phase modulator 4, a fast scanning system 5, a polarization controller 6, a collimating mirror and an objective lens 7, a detector and a preamplifier 8, a data acquisition card 9, an XY direction scanning component 10 and a computer 11. The low-coherence light of a broadband light source 1 is incident to a 2 multiplied by 2 broadband fiber coupler 3 through a fiber 2, and respectively enters a reference arm and a sample arm after being split, and then enters a fast scanning system 5 which sequentially consists of a collimating mirror 5-1, a diffraction grating 5-2, a Fourier transform lens 5-3 and a vibrating mirror 5-4 after one path of light entering the reference arm passes through a phase modulator 4; one path entering the sample arm is projected to a sample cell 12 through a polarization controller 6, a collimating mirror, an XY direction scanning component 10 and an objective lens 7 in sequence; after two paths of reflected light interfere with each other when being converged by the 2 x 2 broadband optical fiber coupler 3, the two paths of reflected light are connected into the detector and the preamplifier 8 and are electrically connected with the data acquisition card 9 and the computer 11 in sequence.
After entering an OCT system, the backward scattered light at a specific measured position of a capillary vessel layer of the retina of the human eye interferes with sample light when being converged at an optical fiber coupler, and is subjected to layer scanning through an XY direction scanning assembly to obtain a multipoint modulation signal of the specific layer, and then the multipoint modulation signal is converted into an electrical signal by a detector and a preamplifier; the data acquisition card converts the signal into a digital signal, and the computer carries out image reconstruction.
FIG. 2 is an OCT image of the model and its depth signal intensity curve after transverse averaging, with the exponential slope of the curve reflecting the magnitude of the scattering coefficient. From the exponential slope of the OCT signal and the system resolution, a specific scattering coefficient can be calculated.
FIG. 3 shows OCT depth signal curves of polystyrene microsphere suspensions with different sugar-doped concentrations, and the curves in the graph show that the scattering coefficients of 6 samples are in the relationship of 3-1 > 3-2 > 3-3 > 3-4 > 3-5 > 3-6, which is consistent with the theoretical calculation result. Experimental data in the graph prove that the OCT can detect the change of the model scattering coefficient caused by the change of 5% of sugar concentration, thereby verifying the feasibility of detecting the blood sugar content of the human body by the OCT method.
(1) OCT scattering detection of fundus capillary vessel layer
The scattering method is suitable for tissue body parts with abundant capillary vessels and obvious scattering, the eyeground is provided with two blood supply layers which are respectively positioned in front of and behind the photosensitive cell layer, and the change of the blood sugar concentration has larger influence on the refractive index of tissue body fluid at the position. Therefore, it is the main content of the present invention to accurately and rapidly find two blood supply layers and obtain a backscattering signal with good repeatability.
Considering the interference of multiple scattered lights in the OCT signal, the relationship to be actually established is much more complicated. The OCT signal curve is obtained by processing original OCT signal data, and because OCT detection is carried out on a backward scattering coherent light signal, scattered light intensity information of different depth layers can be obtained through axial scanning of a scanning arm. After transverse multiple averaging, a uniform and stable OCT scattering intensity curve with depth as an independent variable can be obtained. Since the sub-layers of the fundus retina vary relatively greatly in thickness from location to location, the lateral averaging needs to take into account the problem of depth differences at different locations of the target layer.
(2) OCT scatter detection of blood in central retinal vein
Given that the retinal vessels are relatively large (typically up to 150um in maximum diameter), there are relatively large venous vessels at the optic nerve head, which are sufficient to detect with respect to OCT resolution on the um scale, and the scattering caused by blood glucose concentration changes is more pronounced in addition to the larger scattering coefficient of blood. Therefore, an ideal measured blood vessel is searched, and on the premise of acquiring signals, reasonable detection points in the blood vessel are searched to acquire the optimal correlation.
The utility model discloses blood sugar nondestructive test method to eye ground formation of image based on optics coherent chromatography technique includes following step:
and (I) low-coherence light from the broadband light source enters a 2X 2 broadband optical fiber coupler, and is split and then enters a reference arm and a sample arm respectively.
And (II) light entering the reference arm firstly passes through a Phase modulator and then enters a Rapid Scanning Optical Delay Line (RSOD) consisting of a collimating mirror, a diffraction grating, a Fourier transform lens and a galvanometer.
And (III) projecting the light incident on the sample arm to a capillary layer of the fundus retina through a collimating lens and an objective lens after the light passes through the polarization controller.
And (IV) if the optical path difference of the light returned from the reference arm and the sample arm is within the coherence length of the light source, interference occurs when the light is converged at the optical fiber coupler, and if the layer scanning is carried out, a multipoint modulation signal of any fault is obtained.
And fifthly, the generated interference signals are input to a data acquisition card after passing through a detector and a preamplifier, and subsequent processing and image reconstruction are carried out by a computer, so that a chromatographic image of a capillary vessel layer of the fundus retina is obtained.
The utility model discloses the light that used broadband light source sent is low coherent light, and its central wavelength lambda =1310nm, and bandwidth delta lambda =65nm.
The device scans the sample in the Z direction through RSOD, and the XY direction scanning selects a sample scanning mode and is realized by using a two-dimensional electric micro-displacement platform.
The utility model discloses an interference signal's carrier frequency technique will refer to the phase modulation frequency of the PM in the arm and establish at 500KHz, make signal and low frequency noise effectively separate on the frequency domain.
The utility model adopts a low noise preamplifier to implement the digital filtering of circuit filtering and follow-up software.
Select each component connection to constitute cost means, wherein: the broadband light source 1 is a light source which is produced by B & W Tek company, has the central wavelength lambda =1310nm and the bandwidth delta lambda =65 nm; the optical fiber 2 can be quartz optical fiber (with core diameter of 0.1mm and numerical aperture of 0.37) provided with a collecting lens and produced by Nanjing glass fiber research institute; 2 x 2 broadband optical fiber coupler 3 is a broadband optical fiber coupler with 50/50 of spectral degree and 80nm of bandwidth produced by Hangzhou Futong company; the phase modulator 4 is a product produced by JDS Uniphase company; the fast scanning system 5 is formed by sequentially connecting a collimating mirror 5-1, a diffraction grating 5-2, a Fourier transform lens 5-3 and a galvanometer 5-4, wherein the collimating mirror 5-1 is in optical coupling connection with a phase modulator 4; one end of the polarization controller 6 is connected with the 2 multiplied by 2 broadband optical fiber coupler 3 through an optical fiber, and the other end is connected with the collimating mirror 7 through optical coupling; the collimating lens and the objective lens 7 can be conventional ones of Shunhu, zhejiang; the detector and the preamplifier 8 are made of products of Japan Binsha corporation; the data acquisition card 9 is a Combuscopel 2100 type high-speed acquisition card (acquisition rate is 10 MHz) of Gage Applied company; the XY-direction scanning component 10 is a two-dimensional electric micro-displacement platform, and can make the sample cell 12 make micro-displacement on a two-dimensional plane; the computer 11 can be selected from a Pentium 586 microcomputer and is equipped with a GPIB card; the sample cell 12 is made of organic glass material, and has a pair of windows on both sides, and is inlaid with quartz window sheet, its thickness is 1mm, the simulation medium in the sample cell is polystyrene microsphere suspension, and the simulated target tissue is a colloidal cube (5 mm x 5 mm), and is used for replacing human eye fundus retina capillary vessel layer.
Claims (1)
1. The blood sugar nondestructive testing device of the optical coherence tomography eyeground imaging is characterized in that: the method comprises the following steps that low-coherence light of a broadband light source (1) enters a 2 x 2 broadband optical fiber coupler (3) through an optical fiber (2), is split and then respectively enters a reference arm and a sample arm, enters one path of the reference arm, passes through a phase modulator (4), and then enters a fast scanning system (5) which sequentially consists of a collimating lens (5-1), a diffraction grating (5-2), a Fourier transform lens (5-3) and a vibrating lens (5-4); one path entering the sample arm is projected to a sample cell (12) through a polarization controller (6), a collimating mirror, an XY direction scanning component (10), the collimating mirror and an objective lens (7) in sequence; after two paths of reflected light generate interference when being converged by the 2 multiplied by 2 broadband optical fiber coupler (3), the two paths of reflected light are connected into a detector and a preamplifier (8) and are electrically connected with a data acquisition card (9) and a computer (11) in sequence.
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Cited By (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN100438829C (en) * | 2006-12-21 | 2008-12-03 | 浙江大学 | Non-invasive blood sugar detecting method and equipment based on optical coherent chromatographic ophthalmoscopic imaging |
| CN102349834A (en) * | 2011-06-20 | 2012-02-15 | 深圳职业技术学院 | Human body blood sugar concentration noninvasive detection method and system thereof |
| CN103315749A (en) * | 2013-05-30 | 2013-09-25 | 苏州光环科技有限公司 | Skin area positioning device, method and system applicable to blood glucose detection |
| WO2013159280A1 (en) * | 2012-04-24 | 2013-10-31 | 深圳市斯尔顿科技有限公司 | Ophthalmic optical coherence tomography system and protomerite/deutomerite imaging method by quick switching |
| JP2017099748A (en) * | 2015-12-03 | 2017-06-08 | 株式会社吉田製作所 | Optical coherence tomographic image display control device and program thereof |
-
2006
- 2006-12-21 CN CNU200620141296XU patent/CN201026212Y/en not_active Expired - Lifetime
Cited By (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN100438829C (en) * | 2006-12-21 | 2008-12-03 | 浙江大学 | Non-invasive blood sugar detecting method and equipment based on optical coherent chromatographic ophthalmoscopic imaging |
| CN102349834A (en) * | 2011-06-20 | 2012-02-15 | 深圳职业技术学院 | Human body blood sugar concentration noninvasive detection method and system thereof |
| WO2013159280A1 (en) * | 2012-04-24 | 2013-10-31 | 深圳市斯尔顿科技有限公司 | Ophthalmic optical coherence tomography system and protomerite/deutomerite imaging method by quick switching |
| CN103315749A (en) * | 2013-05-30 | 2013-09-25 | 苏州光环科技有限公司 | Skin area positioning device, method and system applicable to blood glucose detection |
| CN103315749B (en) * | 2013-05-30 | 2015-01-14 | 苏州光环科技有限公司 | Skin area positioning device, method and system applicable to blood glucose detection |
| JP2017099748A (en) * | 2015-12-03 | 2017-06-08 | 株式会社吉田製作所 | Optical coherence tomographic image display control device and program thereof |
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Effective date of abandoning: 20081203 |
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| C25 | Abandonment of patent right or utility model to avoid double patenting |