CN106580328B - Burn degree and area detection system and method based on red blood cell concentration measurement - Google Patents
Burn degree and area detection system and method based on red blood cell concentration measurement Download PDFInfo
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Abstract
The invention discloses a burn degree and area detection system based on red blood cell concentration measurement, which comprises a laser light source, a beam expander, a polarizer, an analyzer, an imaging device and a graphic processor, wherein the laser light source emits laser to the beam expander, the diameter of the laser is expanded by the beam expander, the irradiation area of the laser is expanded, the laser is converted into polarized light by the polarizer to irradiate a wound to be detected, the polarized light is reflected to the analyzer to form a speckle image, the imaging device collects speckle image signals and transmits the speckle image signals as image data to the graphic processor, and the graphic processor processes the received image data. According to the invention, the COMS area array camera is used for receiving speckle light intensity signals, the image processor is used for processing the signals to obtain the red blood cell concentration information of the detection part so as to judge the burn degree of the part and calculate the burn degree area, the full view angle is used for measuring the surface skin burn degree and the burn area, the detection area is large, the accuracy is high, the reliability is high, and the measurement speed is high.
Description
Technical Field
The invention relates to the field of burn diagnosis, in particular to a burn degree and area detection system and method based on red blood cell concentration measurement.
Background
The classification standard of the burn severity degree commonly used in China at present is a standard developed by national burn conference in 1970, the burn is classified into 4 categories of slight degree, moderate degree, severe degree and extra heavy degree according to the burn depth and area, a doctor is very important to obtain accurate burn area and parameters of the burn depth before performing an operation of cutting off a burn part, the basic method used for detection so far is to judge the burn depth according to the wound surface performance by the clinical experience of the doctor, the accuracy of the empirical diagnosis by the doctor is not high, the accuracy is not precise, however, accurate and timely measurement data is very important for treatment, the treatment difficulty of the doctor can be reduced, and the precious treatment time of a patient can be saved.
The partial burn skin necrosis is caused by the formation of micro thrombus at the burn part, the flow of red blood cells is blocked, the oxygen supply to partial tissue cells is not possible, and the oxygen supply condition of the red blood cells can indirectly reflect the burn degree of the burn part, so that the timely and accurate measurement data can be provided by measuring the concentration of the red blood cells to diagnose the burn degree and the area. Patent 201510314640.4 discloses a skin burn detection system and method based on near infrared laser diffusion spectrum detection, which uses a computer to control the middle of a probe to emit 808nm laser irradiation, then uses a circle of acquisition optical fiber in the probe to acquire signals, and uses the computer to process the signals to obtain diffusion spectrum so as to know burn information; in addition, patent 201410041799.9 discloses a near infrared spectrum imaging system and method for burn skin necrosis depth and area diagnosis, which uses computer controlled laser and filter to emit light with wavelength of 900nm to 2500nm to burn skin, then uses LCTF or AOTF and CCD camera to collect spectrum image with wavelength of 1100 to 2500nm, and processes the spectrum image by computer to obtain three-dimensional image of target area, but the two methods have the following disadvantages: 1. the detected area is smaller; 2. instead of using the red blood cell concentration to determine the burn degree, the determination result is not accurate enough; 3. the degree of burn and the corresponding degree of burn area cannot be obtained at the same time.
Disclosure of Invention
The invention aims to provide a burn degree and area detection system based on red blood cell concentration measurement, which can diagnose the burn degree and area by using the measurement data of the red blood cell concentration, thereby improving the accuracy and timeliness of diagnosis and solving the defects in the prior art.
The invention realizes the aim by the following technical scheme:
the burn degree and area detection system based on red blood cell concentration measurement comprises a laser light source, a beam expander, a polarizer, an analyzer, an imaging device and a graphic processor, wherein the laser light source emits laser to the beam expander, the diameter of the laser is expanded by the beam expander, the irradiation area of the laser is expanded, the laser is converted into polarized light by the polarizer to irradiate a wound to be detected, the laser is reflected to the analyzer, reflected light is filtered by the analyzer to form a speckle image, the speckle image signal is collected by the imaging device and is used as image data to be transmitted to the graphic processor, and the graphic processor processes the received image data to obtain the red blood cell concentration of the wound to be detected so as to obtain the burn degree and burn area; the optical centers of the polarizer beam expander and the polarizer are positioned on a horizontal line, the optical centers of the analyzer and the area array camera are positioned on another horizontal line, and an included angle formed by the two horizontal lines accords with the law of reflection. Further, the laser light source is in a single longitudinal mode, and the wavelength of emitted laser is 840nm.
Furthermore, a telecentric lens which is positioned on the same horizontal line with the optical center of the analyzer is also arranged between the analyzer and the imaging device, and because the magnification of the telecentric lens is constant, the telecentric lens does not change along with the change of the depth of field, and no parallax is matched with the imaging device for use, more accurate speckle image data can be provided.
Further, the imaging device is a COMS area-array camera, so that not only can image data with higher spatial resolution be obtained, but also the cost can be saved.
Another object of the present invention is to provide a burn degree and area detection method based on red blood cell concentration measurement, which uses the burn degree and area detection system based on red blood cell concentration measurement, comprising the steps of:
s1, placing a wounded person on a detection table board, enabling a wound to be detected to be positioned right below an analyzer, and setting the acquisition speed and the exposure time of an imaging device;
s2, after the setting is finished, the image processor sends out an instruction to send out laser by the laser source, the laser sequentially passes through the expansion of the beam expander and the polarizer to enable the obtained polarized light to be irradiated onto a wound to be measured, reflected light is eliminated by the analyzer to form a speckle image, the imaging device collects speckle image signals, the telecentric lens is matched with the imaging device to be used, the magnification of the telecentric lens is constant, the change caused by the change of depth of field is avoided, and the parallax-free measurement accuracy can be improved;
s3, the graphic processor processes the speckle image signals:
s31, burn degree diagnosis:
the signal intensity I of any pixel point acquired by the imaging device p (t) can be expressed as:
I 0 for background light intensity, it does not change with time, I, under the condition of neglecting the influence of indoor illumination light n And (t) is the system noise, distributed over the frequency range,representing dynamic speckle intensity, I i Amplitude of interference term of the i-th term, f i Is the modulation frequency, pi T/2 [t-t 0 ]Is a rectangular function, defined as pi T/2 [t-t 0 ]＝H[t-t 0 +T/2]-H[t-t 0 -T/2]，t 0 The time T is the total acquisition time, and the T is related to the acquisition frame number and the acquisition rate, so that the acquisition process of the signal is limited by a rectangular function;
performing Fourier transform on the acquired original speckle image signals, wherein the Fourier transform is as follows:
FFT t→u [I p (t)]＝i s [u]+i n [u]+i d [u±f i ] (2)
wherein i is s [u]＝I 0 sinc (Tu) is a frequency domain static signal, i n [u]Is a spectral signal of the system noise,is a frequency domain dynamic signal, then respectively carries out inverse Fourier transform on a low-frequency signal (static state) and a high-frequency signal (dynamic state), and the time domain static signal is FFT [ i ] s [u]]＝I s (x, y, t) the dynamic signal is FFT [ i ] d [u]]＝I d (x,y,t)；
Reliability to other thingsThe average value of dynamic signal intensity and the average value of static signal intensity are used for obtaining the ratio MD t (x, y), expressed as:
from MD t (x, y) to determine the relative concentration of red blood cells and thereby determine the extent of burn, wherein,<I d (x,y,t)〉 t representing the dynamic signal corresponding to the moving scattering particles, i.e. the third term in equation (1) is averaged in the time direction,<I s (x,y,t)> t representing the intensity signal I against the background 0 The average is taken in the time direction.
The method also comprises the following steps:
s32, burn area calculation and diagnosis: dividing the collected speckle image by using the relative concentration of red blood cells obtained in the step S31, and passing through the MD obtained in the step S31 t The (x, y) values classify and add the segmented small regions to obtain burn areas, which are calculated as follows:
setting ratio intervals (j, k) to be detected, wherein j and k are respectively a minimum value and a maximum value, screening pixels in the value range (j, k), and judging a value I of a pixel point jk(x,y) Expressed by the following relation:
I jk(x,y) ＝(MD t (x,y)＞j)×(MD t (x,y)＜k) (4)
if MD t (x, y) is in the value range (j, k), then I jk(x,y) 1, otherwise 0;
accumulating the pixel points falling in the region (j, k) to obtain the sum S of the pixel points meeting the threshold (j, k) jk ：
S jk ＝∑I jk(x,y) (5)
Sum of pixel points S jk The conversion is the actual burn area S, and the relation is expressed as follows:
S＝K×S jk (6)
k is the conversion ratio, and K is measured by the ratio of the pixel size to the actual ratio.
Compared with the prior art, the burn degree and area detection system and method based on red blood cell concentration measurement provided by the invention have the following beneficial effects:
1. the injury condition is judged according to the difference of the red blood cell concentration of the burn part, namely, the deeper the burn degree is, the lower the red light reflected speckle change intensity is, the weaker the MD value is, and the accuracy of burn diagnosis is improved;
2. the scattered light intensity signals received by the COMS area array camera are processed to obtain the red blood cell concentration information of the detection part, so that the burn degree of the part can be judged, the area of the burn degree can be calculated, and comprehensive and accurate burn degree and burn area measurement data can be provided for treatment;
3. the calculation processing of the data does not need complex calculation, adopts Fourier transformation, has high processing speed, can provide accurate and timely measurement data for doctors, reduces the treatment difficulty, can save the precious treatment time of patients, and has very important significance for treatment;
4. by using the speckle imaging method, the burn degree and burn area of the surface skin are measured at full visual angles, the detection area is large, the accuracy is high, the reliability is high, and the measurement speed is high.
Drawings
FIG. 1 is a schematic diagram of a burn degree and area detection system based on red blood cell concentration measurement according to an embodiment of the present invention;
FIG. 2 is a flow chart of burn degree diagnosis when using the detection system of FIG. 1 for detection;
FIG. 3 is a flow chart of burn area calculation for detection using the detection system of FIG. 1;
wherein: 1-laser source, 2-beam expander, 3-polarizer, 4-analyzer, 5-telecentric lens, 6-imaging device and 7-wound to be measured.
Detailed Description
Embodiments of the present invention will be described in further detail below with reference to the accompanying drawings.
As shown in fig. 1, a burn degree and area detection system based on red blood cell concentration measurement comprises a laser light source 1, a beam expander 2, a polarizer 3, a polarization analyzer 4, an imaging device 6 and a graphic processor (not shown in the figure), wherein the imaging device 6 adopts a COMS area camera, the laser light source 1 emits laser light to the beam expander, the diameter of the laser light is expanded by the beam expander 2, the irradiation area of the light source is expanded, the laser light is converted into polarized light by the polarizer 3 to irradiate the wound 7 to be measured, the laser light is reflected to the polarization analyzer 4, the reflected light is filtered by the polarization analyzer 4 to form a speckle image, the speckle image signal is collected by the imaging device 6 and is used as image data to be transmitted to the graphic processor, the graphic processor processes the received image data to obtain the red blood cell concentration at the wound 7 to be measured, so as to obtain the burn degree and the burn area, wherein the optical centers of the beam expander 2 and the polarizer 3 are positioned on a horizontal line, the optical centers of the polarization analyzer 4 and the COMS area camera are positioned on another horizontal line, the included angle formed by the two horizontal lines conforms to the reflection law, and the laser light source emits the laser light with the wavelength of 840nm.
In addition, in order to improve the accuracy of speckle image data acquisition, a telecentric lens 5 which is positioned on the same horizontal line with the optical center of the analyzer is also arranged between the analyzer 4 and the imaging device 6.
As shown in fig. 2 and 3, a burn degree and area detection method based on red blood cell concentration measurement, using the burn degree and area detection system based on red blood cell concentration measurement, comprises the steps of:
s1, placing a wounded person on a detection table board, enabling a wound to be detected to be positioned right below an analyzer 4, and setting the acquisition speed and the exposure time of an imaging device 6;
s2, after the setting is finished, the image processor sends out an instruction to send out laser by a laser light source, the laser sequentially passes through the expansion of the beam expander 2 and the polarizer 3 to enable the obtained polarized light to be irradiated onto a wound to be measured, reflected light is eliminated by the analyzer 4 to form a speckle image, the imaging device 6 collects speckle image signals, the telecentric lens 5 is matched with the imaging device 6 to be used, the magnification of the telecentric lens is constant, the change along with the change of depth of field is avoided, and the measurement accuracy can be improved due to no parallax;
s3, the graphic processor processes the speckle image signals:
s31, burn degree diagnosis:
signal intensity I of any pixel point acquired by imaging device 6 p (t) can be expressed as:
wherein the speckle intensity signal I p (t) the background light intensity mainly comprises the light intensity directly reflected by the tested sample and the back scattering light intensity caused by scattering particles, the system noise mainly comprises the electronic noise and the noise caused by the movement of the sample, and the light scattered by the moving scattering particles is subjected to multiple interference, so that dynamic speckle is generated, and the dynamic speckle can be expressed as the sum of cosine signal intensities of different frequencies;
I 0 for background light intensity, it does not change with time, I, under the condition of neglecting the influence of indoor illumination light n (t) is system noise, which is distributed over the entire frequency range, and since the motion of the sample to be measured can seriously affect the sharpness of the image, and the noise caused by the motion is mainly distributed at low frequencies, low frequency filtering can be performed in the process of eliminating noise,representing dynamic speckle intensity, I i Amplitude of interference term of the i-th term, f i Is the modulation frequency, pi T/2 [t-t 0 ]Is a rectangular function, defined as pi T/2 [t-t 0 ]＝H[t-t 0 +T/2]-H[t-t 0 -T/2]，t 0 The method is characterized in that the method is an intermediate time of acquisition, T is total acquisition time, T is related to the number of acquisition frames and the acquisition rate, and acquired data and acquisition time are limited in experiments, so that the acquisition process of signals is limited by a rectangular function;
performing Fourier transform on the acquired original speckle image signals, wherein the Fourier transform is as follows:
FFT t→u [I p (t)]＝i s [u]+i n [u]+i d [u±f i ] (2)
wherein i is s [u]＝I 0 sinc (Tu) is a frequency domain static signal, i n [u]Is a spectral signal of the system noise,is a frequency domain dynamic signal, then respectively carries out inverse Fourier transform on a low-frequency signal (static state) and a high-frequency signal (dynamic state), and the time domain static signal is FFT [ i ] s [u]]＝I s (x, y, t) the dynamic signal is FFT [ i ] d [u]]＝I d (x,y,t)；
Then, the average value of the dynamic signal intensity and the average value of the static signal intensity are utilized to calculate the ratio MD t (x, y), expressed as:
wherein,<I d (x,y,t)> t representing the dynamic signal corresponding to the moving scattering particles, i.e. the third term in equation (1) is averaged in the time direction,<I s (x,y,t)> t representing the intensity signal I against the background 0 The average is taken in the time direction.
From MD t The relative concentration of the red blood cells can be obtained by (x, y), the injury condition can be judged according to the difference of the red blood cell concentrations of the burn parts, and the smaller the MD value is, the weaker the speckle change intensity of red light emitted by the laser light source, reflected to the area array camera after irradiating the wound to be measured, namely the deeper the burn degree is, the lower the concentration of the red blood cells is relatively.
S32, burn area calculation and diagnosis: dividing the collected speckle image by using the relative concentration of red blood cells obtained in the step S31, and passing through the MD obtained in the step S31 t The (x, y) values classify and add the segmented small regions to obtain burn areas, which are calculated as follows:
setting ratio interval (j, k) to be detected, j and k are respectively the mostSmall value and maximum value, filtering pixels in the value range (j, k), and judging the value I of the pixel point jk(x,y) Expressed by the following relation:
I jk(x,y) ＝(MD t (x,y)＞j)×(MD t (x,y)＜k) (4)
if MD t (x, y) is in the value range (j, k), then I jk(x,y) 1, otherwise 0;
accumulating the pixel points falling in the region (j, k) to obtain the sum S of the pixel points meeting the threshold (j, k) jk ：
S jk ＝∑I jk(x,y) (5)
Sum of pixel points S jk The conversion is the actual burn area S, and the relation is expressed as follows:
S＝K×S jk (6)
k is the conversion ratio, and K is measured by the ratio of the pixel size to the actual ratio.
What has been described above is merely some embodiments of the present invention. It will be apparent to those skilled in the art that various modifications and improvements can be made without departing from the spirit of the invention.
Claims (4)
1. The burn degree and area detection system based on red blood cell concentration measurement is characterized by comprising a laser light source, a beam expander, a polarizer, an analyzer, an imaging device and a graphic processor, wherein the laser light source emits laser to the beam expander, the diameter of the laser is expanded by the beam expander and then the irradiation area of the light source is expanded, the laser is converted into polarized light by the polarizer and irradiated to a wound to be detected, the laser is reflected to the analyzer and filtered by the analyzer to form a speckle image, the speckle image signal is collected by the imaging device and transmitted to the graphic processor as image data, and the graphic processor processes the received image data to obtain the red blood cell concentration of the wound to be detected so as to obtain the burn degree and burn area; the optical centers of the polarizer beam expander and the polarizer are positioned on a first axis, the optical centers of the analyzer and the area array camera are positioned on a second axis, and an included angle formed by the first axis and the second axis accords with the law of reflection;
the burn degree and area detection system based on the red blood cell concentration measurement performs a burn degree and area detection method based on the red blood cell concentration measurement, the detection method comprising the steps of:
s1), placing a wounded person on a detection table board, enabling a wound to be detected to be positioned right below an analyzer, and setting the acquisition speed and the exposure time of an imaging device;
s2) after the setting is finished, the image processor sends out an instruction to send out laser by a laser light source, the laser sequentially passes through the expansion of the beam expander and the polarizer to enable the obtained polarized light to irradiate the wound to be measured, then the reflected light is eliminated by the analyzer to form a speckle image, the imaging device collects speckle image signals, and the telecentric lens is matched with the imaging device for use;
s3), the graphic processor processes the speckle image signal:
s31), burn degree diagnosis: the signal intensity Ip (t) of any pixel point acquired by the imaging device can be expressed as:
I 0 for background light intensity, it does not change with time, I, under the condition of neglecting the influence of indoor illumination light n And (t) is the system noise, distributed over the frequency range,representing dynamic speckle intensity, I i Amplitude of interference term of the i-th term, f i Is modulation frequency, pi T/2 [t-t 0 ]Is a rectangular function, defined as pi T/2 [t-t 0 ]＝H[t-t 0 +T/2]-H[t-t 0 -T/2]，t 0 The method is characterized in that the method comprises the steps of collecting the original speckle image signals, wherein the time T is the total collecting time, the T is related to the collecting frame number and the collecting rate, and the collected original speckle image signals are subjected to Fourier transformation, and the Fourier transformation is as follows:
FFT t→u [I p (t)]＝i s [u]+i n [u]+i d [u±f i ] (2)；
wherein i is s [u]＝I 0 sinc (Tu) is a frequency domain static signal, i n [u]Is a spectral signal of the system noise,is a frequency domain dynamic signal, then respectively carries out inverse Fourier transform on a static signal and a dynamic signal, and the time domain static signal is FFT [ i ] s [u]]＝I s (x, y, t) the dynamic signal is FFT [ i ] d [u]]＝I d (x,y,t)；
Then, the average value of the dynamic signal intensity and the average value of the static signal intensity are utilized to calculate the ratio MD t (x, y), expressed as:
the relative concentration of red blood cells can be obtained from MDt (x, y), thereby determining the degree of burn, wherein,<I d (x,y,t)> t representing the averaging of the dynamic signal corresponding to the moving scattering particles in the time direction, i.e. the third term in equation (1),<I s (x,y,t)> t representing the intensity signal I against the background 0 Averaging along the time direction;
the method further comprises the following steps:
s32), burn area calculation diagnosis: dividing the acquired speckle image by using the relative concentration of red blood cells obtained in the step S31), classifying and adding the divided small areas by using the MDt (x, y) value obtained in the step S31) to obtain a burn area, wherein the specific calculation is as follows:
setting ratio interval (j, k) to be detected, wherein j and k are respectively minimum value and maximum value, screening pixels in the ratio interval (j, k), and judging value I of pixel points jk(x,y) Expressed by the following relation:
I jk(x,y) ＝(MD t (x,y)＞j)×(MD t (x,y)＜k) (4)；
if MD t (x, y) is within the ratio interval (j, k), then I jk(x,y) 1, otherwise 0; accumulating the pixel points in the ratio interval (j, k) to obtain the sum S of the pixel points meeting the ratio interval (j, k) jk ：
S jk ＝ΣI jk(x,y) (5)；
Sum of pixel points S jk The conversion is the actual burn area S, and the relation is expressed as follows:
S＝K×S jk (6)；
k is the conversion ratio, and K is measured by the ratio of the pixel size to the actual ratio.
2. The system for detecting the degree and area of burn based on the measurement of the concentration of red blood cells according to claim 1, wherein the laser light source is a single longitudinal mode laser light source, and the wavelength of the emitted laser light is 840nm.
3. The system for detecting the degree and area of burn based on the measurement of the concentration of red blood cells according to claim 1, wherein a telecentric lens which is positioned on the same axis as the optical center of the analyzer is further arranged between the analyzer and the imaging device.
4. The hemoglobin concentration measurement-based burn degree and area detection system of any one of claims 1-3, wherein said imaging device is a COMS area array camera.
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| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201611199894.7A CN106580328B (en) | 2016-12-22 | 2016-12-22 | Burn degree and area detection system and method based on red blood cell concentration measurement |
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| CN109431484B (en) * | 2018-12-10 | 2023-11-28 | 佛山科学技术学院 | Device and method for identifying gender of egg embryo based on heart rate measurement |
| CN109883908A (en) * | 2019-01-29 | 2019-06-14 | 黑龙江科技大学 | A kind of apparatus for measuring dust concentration based on polarised light |
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