CN113456069B - Device and equipment for near infrared blood sugar detection based on polarized light imaging - Google Patents
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Abstract
An apparatus and device for near infrared blood glucose detection based on polarized light imaging, the apparatus comprising a processor which, when executed on a computer program stored on a computer readable storage medium, performs the steps of: s1: according to the skin condition of the human body, establishing a skin optical model of the human body double-layer; s2: setting relevant optical parameters of photon propagation in skin, and establishing a Monte Carlo simulation process; s3: the Monte Carlo simulation calculation is carried out to obtain a Mueller matrix of the back of the human skin; s4: calculating each polarization parameter through each array element of the Mueller matrix; s5: by comparing the change rate of each polarization parameter along with the scattering coefficient and the absorption coefficient, the specific polarization parameter which is better than the absorption information of blood sugar extracted by only using light intensity information is obtained. The device reduces the scattering influence of the shallow surface layer based on the polarization parameter, thereby obtaining other microstructure information such as deep absorption, improving the signal to noise ratio of blood sugar detection and improving the deep absorption measurement precision.
Description
Technical Field
The present invention relates to blood glucose detection using optical methods such as near infrared spectroscopy, and more particularly, to a device and apparatus for near infrared detection of blood glucose based on polarized light imaging.
Background
The blood sugar detection by utilizing optical methods such as near infrared spectrum has great application prospect due to noninvasive property, but is extremely easy to be influenced by self metabolism and surrounding environment due to complex change of human background, and the content of glucose in human blood is low, and the characteristic absorption in a near infrared region is weak, so that the signal to noise ratio of the method is low.
Methods such as dual-optical path and orthogonal signal correction are often used for removing background interference of near infrared spectrum, but are not suitable for a complex system such as a human body. It is therefore important to find a way to reduce the effect of scattering on the superficial layers of the skin in order to improve the signal-to-noise ratio of blood glucose tests and the like.
It should be noted that the information disclosed in the above background section is only for understanding the background of the present application and thus may include information that does not form the prior art that is already known to those of ordinary skill in the art.
Disclosure of Invention
The invention mainly aims to provide a device and equipment for detecting blood sugar by near infrared based on polarized light imaging, which solve the problem of low blood sugar absorption detection precision in the existing near infrared blood sugar detection method.
In order to achieve the above purpose, the present invention adopts the following technical scheme:
a near infrared blood glucose detection device based on polarized light imaging, comprising a processor which, when executing a computer program stored on a computer readable storage medium, performs the steps of:
s1: according to the skin condition of the human body, establishing a skin optical model of the human body double-layer;
s2: setting relevant optical parameters of photon propagation in skin, and establishing a Monte Carlo simulation process;
s3: the Monte Carlo simulation calculation is carried out to obtain a Mueller matrix of the back of the human skin;
s4: calculating each polarization parameter through each array element of the Mueller matrix;
s5: by comparing the change rate of each polarization parameter along with the scattering coefficient and the absorption coefficient, the specific polarization parameter which is better than the absorption information of blood sugar extracted by only using light intensity information is obtained.
Further:
the double-layer skin optical model in the step S1, wherein the first layer is an epidermis layer and a dermis layer, the second layer is subcutaneous tissue, the change of the scattering coefficient of the first layer is used for representing the instability of a shallow surface layer, and the absorption coefficient of the second layer is used for representing the concentration of glucose to be detected.
The optical parameters of the bilayer skin optical model in step S2 specifically include: the thickness of the first layer is set to 0.3mm, and the thickness of the second layer is set to 10mm; photon number of 10 7 The wavelength of the incident light is 1200nm, and the refractive index of the medium is 1.33; the first layer is a pure spherical scattering system, wherein the relevant parameters of the spherical scattering body comprise: the radius is 0.3 mu m, the variation range of the scattering coefficient is 50-300/cm, the interval is 10/cm, and the refractive index is 1.43; the second layer is a spherical scattering absorption system, the variation range of the absorption coefficient of the medium is 3/cm, the refractive index of the medium is 1.43, the radius of the spherical scattering body is 0.3 mu m, the refractive index of the spherical scattering body is 1.38, and the scattering coefficient is 60/cm.
In step S3, a muller matrix representing sample information 4*4 of the skin optical model is generated after the monte carlo simulation, m11 array elements of the muller matrix carry light intensity information, and the remaining 15 muller matrix array elements all carry different polarization information, and the polarization information can provide microstructure information of samples except the light intensity information.
The polarization parameters in the step S4 include parameters formed by combining the mueller matrix elements, including: m11, m22, m44, m11+m22+m33, m11+m22+m33+m44, m11× (m22+m33+m44), m11× (m22+m33), m11×m44,
m11/m22+m33+m44、m11/m22、m11/m44、/>
m11×m22、m11×(m22+m44)、m11×(m22+m33+m44)、(m22+m33+m44) 2 、m11×(m22+m33+m44) 2 。
The change rate in the step S5 includes a change rate of each parameter with a change in the scattering coefficient of the first layer, and a change rate of each parameter with a change in the absorption coefficient of the second layer representing the blood glucose concentration.
Wherein the rate of change of the scattering coefficient with the first layer is:
wherein the rate of change with the absorption coefficient of the second layer is:
where y (mus 1) represents the value of each parameter when the scattering coefficient is mus1, y (mus 2) represents the value of each parameter when the scattering coefficient is mus2, y (mua 1) represents the value of each parameter when the absorption coefficient is mua1, and y (mua 2) represents the value of each parameter when the absorption coefficient is mua2, wherein mua1, mua2, mus1, mus2 are arbitrary values within the parameter variation range.
The criteria for selecting parameters are: k (k) mus The change rate of the light intensity is small, k mua The rate of change of the relative light intensity is large.
A computer readable storage medium storing a computer program which, when executed by a processor, performs the steps S1 to S5 implemented by the apparatus.
A near infrared blood glucose detection device based on polarized light imaging, which comprises a processor, a polarized light detection and imaging device and the computer readable storage medium.
The invention has the following beneficial effects:
the invention provides a device and equipment for near infrared detection of blood sugar based on polarized light imaging, which reduces the scattering influence of a shallow surface layer based on polarization parameters, thereby obtaining other microstructure information such as deep absorption and the like, improving the signal-to-noise ratio of blood sugar detection and improving the deep absorption measurement precision.
Specifically, the invention combines the polarization technology and the near infrared blood sugar detection technology, and adopts a Monte Carlo simulation mode based on a human body double-layer skin model to obtain various parameters related to blood sugar absorption. The Mueller matrix obtained by using the polarization technology can obtain 16-dimensional information, the 16-dimensional information not only comprises light intensity information which can be obtained by a traditional method, but also additionally comprises 15-dimensional polarization information, and more microstructure information can be obtained by using the polarization light detection technology. The invention can effectively reduce the influence of unstable skin superficial state in blood sugar detection and improve the accuracy of detecting blood sugar by an optical method.
Drawings
FIG. 1 is a flowchart of a process for reducing the effect of skin shallow scattering based on polarization parameters in accordance with an embodiment of the present invention.
Fig. 2 is a flow chart of monte carlo simulation in accordance with an embodiment of the present invention.
FIG. 3 is a schematic diagram of an optical path system according to an embodiment of the present invention.
FIG. 4 is a graph showing the rate of change of various parameters with respect to the absorption coefficient of the second layer according to an embodiment of the present invention.
Fig. 5 is a plot of the rate of change ordering of parameters for an embodiment of the invention Δ mua =0.9/cm.
FIG. 6 is a graph showing the rate of change of various parameters with the scattering coefficient of the first layer according to an embodiment of the present invention.
Fig. 7 shows the ordering of the rate of change of the parameters for Δmus=90/cm in accordance with an embodiment of the present invention.
Detailed Description
In order to make the technical problems solved, the technical scheme adopted and the technical effects achieved by the invention clearer, the technical scheme of the embodiment of the invention will be further described in detail with reference to the accompanying drawings. It will be apparent that the described embodiments are only some, but not all, embodiments of the invention. All other embodiments, which can be made by those skilled in the art based on the embodiments of the present invention without making any inventive effort, are intended to fall within the scope of the present invention. It should be emphasized that the following description is merely exemplary in nature and is in no way intended to limit the scope of the invention or its applications.
Referring to fig. 1, fig. 1 is a flowchart illustrating a process for reducing the effect of superficial skin scattering based on polarization parameters according to an embodiment of the present invention. The treatment process for reducing the influence of the superficial skin scattering based on the polarization parameter comprises the following steps:
step S1: and establishing an optical model of the human double-layer skin according to the skin condition of the human body.
The human skin is in a layered structure and is divided into an epidermal layer, a dermis layer, subcutaneous tissues and the like. The epidermis and dermis layers are divided into the same layers because they have similar optical parameters in the problem we have studied. The optical model referred to in the present invention is a two-layer skin model in which the first layer is the epidermis layer and dermis layer and the second layer is subcutaneous tissue. Since the background of human skin is complicated to change, the superficial layer is extremely susceptible to self metabolism and the surrounding environment, and thus the instability of the superficial layer is represented by the change of the scattering coefficient of the first layer. Near infrared spectroscopy is mainly based on the characteristic absorption to detect glucose, and blood sugar is mainly in the second layer of subcutaneous tissue, so that the absorption coefficient of the second layer is used for representing the concentration of glucose to be detected.
Step S2: setting the relevant optical parameters of photon propagation in skin and establishing Monte Carlo simulation process.
The optical parameters of the bilayer skin model in step S2 specifically include: the thickness of the first layer was set to 0.3mm and the thickness of the second layer was set to 10mm. Photon number of 10 7 The wavelength of the incident light was 1200nm and the refractive index of the medium was 1.33. The first layer is a pure spherical scattering system, wherein the relevant parameters of the spherical scatterers include: the radius is 0.3 mu m, the scattering coefficient variation range is 50-300/cm, the interval is 10/cm, and the refractive index is 1.43. The second layer is a spherical scattering absorption system, the variation range of the absorption coefficient of the medium is 3/cm, the refractive index of the medium is 1.43, the radius of the spherical scattering body is 0.3 mu m, the refractive index of the spherical scattering body is 1.38, and the scattering coefficient is 60/cm. Wherein, the fluctuation caused by unstable factors such as environment in the shallow surface layer is represented by the change of the scattering coefficient in the first layer medium.
And step S3, performing Monte Carlo simulation calculation to obtain a Mueller matrix of the human skin facing away.
Referring to fig. 1 and 2, monte carlo simulation is a method of statistically simulating random sampling, and can be used to study the propagation of photons in a scattering medium. The flow of the monte carlo simulation in step S3 is as shown in fig. 2:
first a plurality of photons (10 7 And a) loading into the model, initializing the polarization state of one of the photons to S. The photons are then randomly moved in all directions by a step s to determine if the photons are still in the scattering medium.
(1) If the photon is still in the medium, the scattering coefficient of the sphere is determined, further scattering is carried out, and further whether the photon is absorbed or not is judged.
(a) If not, the step s is moved again, and the above-mentioned judgment is repeated.
(b) If it has already been absorbed, it is determined if it is the last photon in the system.
(i) If not the last photon in the system, reloading the photon, giving it its initial polarization state S, and repeating the above process.
(ii) If the photon is already the last photon in the system, the entire simulation process is ended.
(2) If a photon has left the scattering medium, it is rotated to the detector reference frame and it is determined if the photon is the last photon.
(i) If not the last photon in the system, reloading the photon, giving it its initial polarization state S, and repeating the above process.
(ii) If the photon is already the last photon in the system, the entire simulation process is ended.
After this monte carlo simulation a mueller matrix characterizing the skin model sample information 4 x 4 will be generated. The m11 array elements of the mueller matrix carry light intensity information, and the rest 15 mueller matrix array elements all carry different polarization information. The polarization information may provide microstructure information of the sample in addition to the light intensity information.
Step S4: and calculating each polarization parameter through each array element of the Mueller matrix.
The polarization parameters in step S4 are mainly parameters obtained by combining the Mueller matrix elements, including but not limited toThe method is limited to: m11, m22, m44, m11+m22+m33, m11+m22+m33+m44, m11× (m22+m33+m44), m11× (m22+m33), m11×m44,
m11/(m22+m33+m44)、m11/m22、m11/m44、/>
m11×m22、m11×(m22+m44)、m11×(m22+m33+m44)、(m22+m33+m44) 2 、m11×(m22+m33+m44) 2 。
Step S5: by comparing the change rate of each polarization parameter along with the scattering coefficient and the absorption coefficient, the specific polarization parameter which is better than the absorption information of blood sugar extracted by only using light intensity information is obtained.
Referring to fig. 3, fig. 3 is a schematic diagram of an optical path system model according to an embodiment of the present invention, and the main devices include a light source (a module 1 formed by an LED and a lens L1), a polarizing module (a module 2 formed by a polarizer P1 and a 1/4 wave plate QW 1), a sample (mainly referred to as human skin), a polarization analyzer (a module 3 formed by a 1/4 wave plate QW2 and a polarizer P2), a lens L2, and a CCD (a module 4).
Referring to fig. 1, 4-7, the change rate used in step S5 includes the change rate of each parameter with the change of the scattering coefficient of the first layer, and the change rate of the absorption coefficient of each parameter with the change of the absorption coefficient of the second layer representing the blood glucose concentration.
Wherein the rate of change of the scattering coefficient with the first layer is:
wherein the rate of change with the absorption coefficient of the second layer is:
y (mus 1) represents the value of each parameter at a scattering coefficient of mus1, and y (mus 2) represents the value of each parameter at a scattering coefficient of mus 2. Similarly, y (mua 1) represents the value of each parameter at an absorption coefficient of mua, and y (mua 2) represents the value of each parameter at an absorption coefficient of mua 2. Mua1, mua, mus1, mus2 are arbitrary values within the parameter variation range.
In order to better reduce the influence of superficial skin scattering, the parameters are selected as follows: k (k) mus The change rate of the light intensity is small, k mua The rate of change of the relative light intensity is large. The parameters which meet the two points are parameters which are insensitive to the scattering signals of the shallow surface layer and sensitive to the absorption signals of the deep layer.
Referring to FIGS. 4 and 5, when the absorption coefficient of the second layer varies from 0.1/cm to 3/cm with a step size of 0.1/cm, there is always (m22+m33+m44) 2 、m11×(m22+m33+m44) 2 、m11/(m22+m33+m44)、m11/m22、m11/m44、m22、m44、
The sensitivity of the isoparametric to absorption is better than the simple light intensity effect represented by m 11. That is, the parameters are simpler than the simple light intensity signals, and the deep absorption signals are easier to collect.
Referring to FIGS. 6 and 7, when the scattering coefficient of the first layer varies from 10/cm to 250/cm with a step size of 10/cm, there are always m11+m22+m33, m11+m22+m33+m44, m11×m44, m22, m44,
m11/m22、m11/(m22+m33+m44)、/>
The insensitivity of the isoparametric to scattering is better than the simple light intensity effect represented by m 11. I.e. these parameters are less susceptible to changes in the state of the superficial skin than the simple intensity signal.
Referring to FIGS. 4-7, m11/m22, m 11/(m22+m33+m44), m22, m44,
The parameters can not only reduce the instability of the shallow surface layer caused by the environmental state, but also improve the deep layerAccuracy of absorption coefficient. The invention can effectively reduce the influence of unstable skin superficial state in blood sugar detection and improve the accuracy of detecting blood sugar by an optical method.
The background section of the present invention may contain background information about the problems or environments of the present invention and is not necessarily descriptive of the prior art. Accordingly, inclusion in the background section is not an admission of prior art by the applicant.
The foregoing is a further detailed description of the invention in connection with specific/preferred embodiments, and it is not intended that the invention be limited to such description. It will be apparent to those skilled in the art that several alternatives or modifications can be made to the described embodiments without departing from the spirit of the invention, and these alternatives or modifications should be considered to be within the scope of the invention. In the description of the present specification, reference to the terms "one embodiment," "some embodiments," "preferred embodiments," "examples," "specific examples," or "some examples," etc., means that a particular feature, structure, material, or characteristic described in connection with the embodiment or example is included in at least one embodiment or example of the invention. In this specification, schematic representations of the above terms are not necessarily directed to the same embodiment or example. Furthermore, the particular features, structures, materials, or characteristics described may be combined in any suitable manner in any one or more embodiments or examples. Those skilled in the art may combine and combine the features of the different embodiments or examples described in this specification and of the different embodiments or examples without contradiction. Although embodiments of the present invention and their advantages have been described in detail, it should be understood that various changes, substitutions and alterations can be made herein without departing from the scope of the invention as defined by the appended claims.
Claims (8)
1. A near infrared blood glucose detection device based on polarized light imaging, comprising a processor which, when executing a computer program stored on a computer readable storage medium, performs the steps of:
s1: according to the skin condition of a human body, a skin optical model of a human body double-layer is built, wherein a first layer in the skin optical model of the double-layer is a epidermis layer and a dermis layer, a second layer is subcutaneous tissue, the change of a scattering coefficient of the first layer is used for representing the instability of a shallow surface layer, and the absorption coefficient of the second layer is used for representing the concentration of glucose to be detected;
s2: setting relevant optical parameters of photon propagation in skin, and establishing a Monte Carlo simulation process;
s3: the Monte Carlo simulation calculation is carried out to obtain a Mueller matrix of the back of the human skin;
s4: calculating each polarization parameter through each array element of the Mueller matrix;
s5: by comparing the change rate of each polarization parameter along with the scattering coefficient and the absorption coefficient, the specific polarization parameter which is better than the absorption information of blood sugar extracted by only using light intensity information is obtained.
2. The device according to claim 1, wherein the optical parameters of the optical model of the skin of the bilayer in step S2 specifically include: the thickness of the first layer is set to 0.3mm, and the thickness of the second layer is set to 10mm; photon number of 10 7 The wavelength of the incident light is 1200nm, and the refractive index of the medium is 1.33; the first layer is a pure spherical scattering system, wherein the relevant parameters of the spherical scattering body comprise: the radius is 0.3 mu m, the variation range of the scattering coefficient is 50-300/cm, the interval is 10/cm, and the refractive index is 1.43; the second layer is a spherical scattering absorption system, the variation range of the absorption coefficient of the medium is 3/cm, the refractive index of the medium is 1.43, the radius of the spherical scattering body is 0.3 mu m, the refractive index of the spherical scattering body is 1.38, and the scattering coefficient is 60/cm.
3. The apparatus according to any one of claims 1 to 2, wherein in step S3, a mueller matrix representing sample information 4*4 of the skin optical model is generated after the monte carlo simulation, m11 elements of the mueller matrix carry light intensity information, and the remaining 15 mueller matrix elements each carry different polarization information, and the polarization information is capable of providing microstructure information of samples other than the light intensity information.
4. The apparatus according to any one of claims 1 to 2, wherein the polarization parameters in step S4 include parameters obtained by combining mueller matrix elements, including: m11, m22, m44, m11+m22+m33, m11+m22+m33+m44, m11× (m22+m33+m44), m11× (m22+m33), m11×m44,
m11/m22+m33+m44、m11/m22、m11/m44、
m11×m22、m11×(m22+m44)、m11×(m22+m33+m44)、(m22+m33+m44) 2 、m11×(m22+m33+m44) 2 。
5. The apparatus according to any one of claims 1 to 2, wherein the rate of change in step S5 includes a rate of change of each parameter with a scattering coefficient of the first layer, and a rate of change of each parameter with an absorption coefficient of the second layer representing blood glucose concentration.
6. The apparatus of claim 5, wherein,
wherein the rate of change of the scattering coefficient with the first layer is:
wherein the rate of change with the absorption coefficient of the second layer is:
wherein y (mus 1) represents the value of each parameter when the scattering coefficient is mus1, y (mus2) Representing the value of each parameter when the scattering coefficient is mus2, y (mua 1) represents the value of each parameter when the absorption coefficient is mua1, and y (mua 2) represents the value of each parameter when the absorption coefficient is mua2, wherein mua1, mua2, mus1 and mus2 are arbitrary values within the parameter variation range; the criteria for selecting parameters are: k (k) mus The change rate of the light intensity is small, k mua The rate of change of the relative light intensity is large.
7. A computer readable storage medium storing a computer program, which, when run by a processor, performs the steps S1 to S5 implemented by the apparatus according to any one of claims 1 to 6.
8. A near infrared blood glucose testing device based on polarized light imaging comprising a processor, polarized light detection and imaging means and a computer readable storage medium according to claim 7.
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