CN108968922A - A kind of hand-held compact oedema detection device and its data processing method based on near-infrared absorption - Google Patents

Abstract

The invention discloses a hand-held compact edema detection device based on near-infrared light absorption and a data processing method thereof. And receive the returned two-way infrared light, combine the two to form a beam splitter for interference light; provide a reference arm for reference light; focus the other infrared light and project it on the tissue under test, and receive the reflected light from the tissue under test The sample arm of the returned infrared light; receives the combined near-infrared light and irradiates the beam to the CCD camera after passing through the transmission grating and dispersing it according to the wavelength. The invention utilizes the detected backscattered light to estimate the relative water content of the measured tissue.

Description

A hand-held compact edema detection device based on near-infrared light absorption and its digital data processing method

technical field

The invention relates to the field of edema detection, in particular to a hand-held compact edema detection device based on near-infrared light absorption and a data processing method thereof.

Background technique

As living standards improve, people are increasingly concerned about health issues, accompanied by high costs of environmental degradation. Real-time non-invasive monitoring technology has the functions of screening monitoring, early detection, and auxiliary diagnosis. Therefore, high sensitivity, safety and harmlessness are the cores of all monitoring technologies. For the diagnosis of edema in patients with heart failure and renal failure, the estimation of dialysis intervals has long relied on doctors' palpation and blood tests, lacking real-time, rapid, and non-invasive inspection methods. It is extremely necessary to develop a highly sensitive and easy-to-operate edema detection device suitable for actual clinical applications.

Optical coherence technology has ultra-high sensitivity and resolution, and its fast imaging capability has made it widely used in basic biological and biomedical research in recent years. Traditional optical coherence technology uses the low absorption and strong scattering of the 1310nm band to obtain reflection tomographic imaging capabilities; uses the high scattering and low absorption of the 800nm band to obtain high-resolution and high-contrast tomograms, but it is also limited The penetrating power of the imaging beam is reduced, reducing its inherent tomographic advantages. The penetration ability of near-infrared light to biological tissues increases with the increase of wavelength. The wavelength of 1470 nanometers is a water absorption peak in the near-infrared band, and this band is commonly used in clinical practice for some thermomelting treatments. According to Lambert Beer's law, the amount of light absorbed by a solution containing a light-absorbing substance is exponentially related to the content of the substance in the solution. Therefore, when the 1470nm near-infrared light is irradiated in the water-rich tissue, the light is absorbed by the water in a large amount, and compared with the tissue with normal water content, both the transmitted light and the reflected light decrease exponentially.

For safety reasons, clinically there are strict restrictions on the light intensity and lighting time of optical methods. Combined with the high absorption of water at 1470nm wavelength and the high sensitivity of optical coherence technology, it is worth exploring to use the detected backscattered light to estimate the relative content of accumulated water by irradiating the edema part with a small light intensity. method.

Contents of the invention

The object of the present invention is to provide a hand-held compact edema detection device based on near-infrared light absorption and a data processing method thereof, and realize the purpose of estimating the relative content of stagnant water by using the detected backscattered light.

The technical solution of the present invention is: a hand-held compact edema detection device based on near-infrared light absorption, comprising:

Ultra-broad-spectrum near-infrared light source for generating infrared light in specific bands;

The beam splitter receives the outgoing light of the near-infrared light source, divides the infrared light into two beams for output, and receives the returned two-way infrared light, and combines them to generate interference light and output it to the spectrometer;

The reference arm is connected to one optical path of the beam splitter, the reference arm includes a plano-convex cylindrical mirror, a dispersion compensation module and a high-reflectivity plane mirror, and the one-way infrared light is focused on the plane mirror by the plano-convex cylindrical mirror , and then return to the beam splitter after being reflected by a plane mirror, and the dispersion compensation module is used to match the dispersion difference between the reference arm and the sample arm;

The sample arm is connected with another optical path of the beam splitter, the sample arm includes an anti-reflection optical probe, and the optical probe focuses the infrared light on the tissue under test and receives the infrared light reflected from the tissue under test , sent back to the beam splitter;

A near-infrared spectrum detector is connected with the combined optical path output port of the beam splitter. The spectrum detector includes a grating, a scanning lens and a CCD camera. The infrared light returned by the reference arm is combined with the infrared light reflected from the measured tissue. The light forms an interference signal in the beam splitter, which is detected by the near-infrared spectrum detector, specifically, the light beam is dispersed by the transmission grating according to the wavelength and then irradiated on the CCD camera to generate an image;

Drivers for control, synchronizing drive signals, data acquisition, digitizing data, processing and storing and displaying data.

In one embodiment, the near-infrared light source includes a wide-spectrum near-infrared laser, a high-pass filter, and a free optical fiber coupler arranged in sequence, the wide-spectrum near-infrared laser is used as a light source, and the high-pass filter performs high-pass on the light source. After filtering, the infrared light of a specific band is reserved, and the coupler serves as an output port of the generated infrared light.

In one embodiment, the near-infrared light source further includes a polarization controller, and the polarization controller is disposed between the high-pass filter and the coupler for controlling the polarization state of the infrared light to ensure the maximum output power of the light source.

In one embodiment, the dispersion compensation module is any one of a prism pair, an optical fiber, a plano-convex cylindrical mirror of the same type as that in the probe, or an achromatic lens.

In one embodiment, the probe of the sample arm adopts a two-dimensional forward light emitting mode without a built-in scanning function, and the optical probe adopts a plano-convex cylindrical mirror as an objective lens for focusing the imaging beam.

In one embodiment, the probe of the sample arm adopts a two-dimensional or three-dimensional side light emitting mode with a built-in MEMS scanning galvanometer.

In one embodiment, the optical probe uses a plano-convex cylindrical mirror or an achromatic focusing lens as the objective lens for focusing the imaging beam , The plano-convex cylindrical mirror or the achromatic focusing lens both emits the detection light beam and collects the signal light beam.

In one embodiment, the specific band infrared light generated by the near-infrared light source is a broad-spectrum continuous near-infrared light with a central wavelength of 1475 nanometers and a bandwidth at half maximum of 400 nanometers.

In one embodiment, the near-infrared spectroscopic detector further includes a prism arranged between the grating and the scanning lens, the prism is matched with the grating to convert the received wavelength linear detection light into wavenumber linear detection light, The CCD camera is an area array CCD camera.

An embodiment of the present invention also provides a data processing method for an edema detection device, including:

Average the signals of multiple images of the same position or multiple continuous scanning points in an image to remove noise interference;

Using the detected images to obtain backscattered light intensity signal values corresponding to different positions and depths i;

The local relative water content was calculated according to the following formula:

Among them, C _i is the local relative water content at tissue depth i, I _i is the signal value at depth _i , Δd is the distance between different depths, and In is the signal value at different positions below depth i.

The invention has the advantages that the provided edema content detection device has high sensitivity, miniaturization and good operability. The introduction of the dispersion compensation module matches the dispersion difference between the reference arm and the sample arm in the interferometer, thereby improving the longitudinal resolution. The introduction of the polarization controller maximizes the output power and improves the signal-to-noise ratio. By matching and combining the grating-prism pair, the received wavelength linear detection light is converted into wavenumber linear detection light, so as to reduce the consumption of the computer system by software post-processing, thereby increasing the speed of the entire detection process. Compared with the high radiation of X-ray or CT and the high cost of MRI technology, the device of the present invention uses optical means, which is safe, harmless and economical, and more likely to benefit patients.

Description of drawings

The present invention will be further described below in conjunction with accompanying drawing and embodiment:

Fig. 1 is a schematic diagram of the structure of the sample arm probe adopting a two-dimensional forward light output mode without built-in scanning function in the embodiment of the present invention, and the optical probe adopting a plano-convex cylindrical mirror as the objective lens;

Fig. 2 is a schematic structural diagram of the sample arm probe adopting a three-dimensional side light output mode with a built-in MEMS scanning galvanometer in the embodiment of the present invention, and the optical probe adopting an achromatic focusing lens as an objective lens;

3 is a schematic diagram of a hand-held compact edema detection device based on near-infrared light absorption according to an embodiment of the present invention;

Fig. 4 is a logarithmic relationship diagram between detected backscattered light intensity and tissue depth under different water contents according to the embodiment of the present invention;

Fig. 5 is a water content map estimated under the condition that the water content in different depths is equal by using the detected backscattered light intensity according to the embodiment of the present invention, wherein the C value in the legend is the theoretical water content, and the value next to the arrow mark is the water content estimated by the algorithm;

FIG. 6 is a graph showing the relationship between depth, water content, and backscattered light intensity estimated by using the detected backscattered light intensity and the water content at different depths according to an embodiment of the present invention.

Detailed ways

The principles and features of the present invention are described below in conjunction with the accompanying drawings, and the examples given are only used to explain the present invention, and are not intended to limit the scope of the present invention.

The invention uses near-infrared light and the principle of spectral domain optical coherence to perform imaging. Simply put, the light emitted by the light source is divided into two beams, one beam is emitted to the object under test, this optical path is called the sample arm, and the other beam forms a reference signal through the reflector, this optical path is called the reference arm. , when the optical path difference between the sample arm and the reference arm is within the interference length of the light source, the two beams returning from the tissue (sample arm) and from the mirror (reference arm) are superimposed to form an interference signal. The light signal reflected from the tissue varies in strength depending on the nature of the tissue (scattering and absorption, etc.). These optical signals can be processed by computer Fourier transform to obtain tissue tomographic images. A hand-held compact edema detection device based on near-infrared light absorption provided by the present invention includes: an ultra-broadband near-infrared light source for generating infrared light in a specific band. Preferably, the near-infrared light source includes sequentially arranged Broad-spectrum near-infrared laser 01, high-pass filter 02 and free optical path fiber coupler 03, the wide-spectrum near-infrared laser 01 is used as a light source, and the high-pass filter retains infrared light of a specific band after performing high-pass filtering on the light source, The coupler 03 serves as an outlet for the generated infrared light. Preferably, the specific band infrared light generated by the near-infrared light source is a broad-spectrum supercontinuous near-infrared light with a center wavelength of 1475 nanometers and a half-maximum bandwidth of 400 nanometers; a beam splitter 04 receives the outgoing light of the near-infrared light source , divide the infrared light into two beams for output, and receive the returned two-way infrared light, and output them to the spectrometer after being combined; the reference arm is connected with one optical path of the beam splitter, and the reference arm includes a plano-convex cylinder Mirror 14, dispersion compensation module 06 and high reflectivity plane mirror 07, the infrared light of one path is focused on the plane mirror 07 through the plano-convex cylindrical mirror, and then reflected by the plane mirror 07 and returned to the beam splitter; the sample arm, with the The other optical path of the beam splitter is connected, and the sample arm includes an anti-reflection optical probe 12. The optical probe focuses the infrared light on the tissue under test, and receives the infrared light reflected from the tissue under test, and sends it back to the Beam splitter; Near-infrared spectral detector, detects the interference signal formed at the beam splitter, and transmits it to the computer for post-processing to generate a tomogram. The spectral detector includes a grating, a scanning lens and a CCD camera, and the The infrared light returned by the reference arm and the infrared light reflected from the measured tissue form an interference signal in the beam splitter, which is detected by the near-infrared spectrum detector. Specifically, the beam is dispersed by the transmission grating according to the wavelength and irradiated on the CCD camera. , to generate an image. The device also includes drivers for controlling and synchronizing drive signals and data acquisition, digitization, processing and storage of data acquisition, display and storage modules. If the MEMS scanning galvanometer is built-in, it also includes driving the MEMS scanning galvanometer. The device of the present invention is shown in Fig. 3, the weak signal from the sample arm can be detected by the spectrometer after being amplified by the reference arm signal. Among them, after the supercontinuum broadband light source 01 is subjected to high-pass filter processing by the high-pass filter 02 (Thorlabs, FEL1200), the light with a wavelength above 1200 nanometers is retained as the input of the beam splitter 04, and the beam passes through the beam splitter 04 , the near-infrared light with a center wavelength of 1475 nanometers and a bandwidth at half maximum width of 400 nanometers is sent to the reference arm and the sample arm of the interferometer with a split ratio of 50:50. A bandwidth of 400 nanometers enables the device of the present invention to achieve a longitudinal resolution of 2.4 microns. Combined with the above-mentioned horizontal resolution of 2-12 microns, the present invention not only has high sensitivity, but also has ultra-high vertical and horizontal resolution. Using the above method, the device has a sensitivity as high as -100dB.

Preferably in the embodiment of the present invention, the near-infrared light source further includes a polarization controller 05, the polarization controller is arranged between the high-pass filter and the coupler, and is used to control the polarization state of the infrared light, and the output power of the light source is the largest. This ensures a high signal-to-noise ratio.

Preferably in the embodiment of the present invention, the reference arm also includes a dispersion compensation module 06 for matching the dispersion difference between the reference arm and the sample arm. Either of the plano-convex cylindrical mirror or achromatic lens, the dispersion compensation can make the actual longitudinal resolution of the system approach the theoretical value.

Preferably in an embodiment of the present invention, the sample arm adopts a two-dimensional forward light output mode without a built-in scanning function, and the optical probe 12 uses a plano-convex cylindrical mirror as an objective lens for focusing the imaging beam. As shown in Figure 1. The diameter of the beam emitted from the fiber collimator is 3.6 mm, and is focused by a plano-convex cylindrical lens 14 at a distance of 1.4 mm from the cylindrical lens, and the lateral resolution of the focused spot is 2 microns. A glass window 15 with a diameter of 11 mm and a thickness of 1 mm protects the plano-convex cylindrical mirror from contamination by the sample. All the above-mentioned components are integrated in a section of thin-walled stainless steel tube 13 . The probe uses a plano-convex cylindrical mirror as the objective lens for focusing the imaging beam. The collimated beam with a circular spot is focused in the direction of the curvature of the cylindrical mirror, while maintaining a width of 3.6 mm in the vertical direction. Therefore, What hits the sample is a narrow strip of light with a width of 2 microns and a length of 3.6 mm, which makes the probe naturally capable of two-dimensional detection, without the need for scanning galvanometers to achieve two-dimensional imaging like ordinary point scanning imaging.

In an embodiment of the present invention, preferably, the sample arm adopts a two-dimensional or three-dimensional side light emitting mode with a built-in MEMS scanning galvanometer. The vibrating mirror can freely realize one-dimensional or two-dimensional arbitrary mode scanning, combined with the inherent tomographic capability of the device, it can provide two-dimensional or three-dimensional tissue tomographic images and two-dimensional or three-dimensional water content distribution maps. Wherein, the optical probe 12 can use a plano-convex cylindrical mirror or an achromatic focusing lens as an objective lens for focusing the imaging beam, and the plano-convex cylindrical mirror or an achromatic focusing lens can both emit the detection beam and collect the signal beam. As shown in Figure 2, the light beam emitted from the achromatic lens 17 is reflected by the MEMS vibrating mirror 18 and focused on a distance of 0.5 mm outside the protective glass window 16. The lateral resolution of the resulting focused circular spot is 12 mm, and all the above-mentioned components are covered. Integrated in a section of thin-walled stainless steel pipe 13. The two-dimensional tissue structure map and the two-dimensional water content distribution map can be obtained by uniaxial scanning of the MEMS galvanometer; the three-dimensional tissue structure map and the three-dimensional water content distribution map can be obtained by biaxial scanning of the MEMS galvanometer; the scanning range is determined by the MEMS galvanometer Drive voltage control.

In an embodiment of the present invention, the near-infrared spectrum detector further includes a prism arranged between the grating and the scanning lens, and the prism is matched with the grating to convert the received wavelength linear detection light into wavenumber linear detection light , to save numerical resampling time and increase the detection rate, the CCD camera is an area array CCD camera. A commonly used spectrometer generally consists of a grating 08, a scanning lens 10 and a CCD camera 11. After the light beam passes through the transmission grating 08 and is dispersed according to the wavelength, it is irradiated on the CCD, and the wavelength is linear along the pixel direction. However, the device of the present invention uses Fourier transform to reconstruct the signal detected by the spectrometer into an image with tissue structure information. Due to the ultra-high resolution of this device, when the field of view is 5 mm × 5 mm, according to the Nyquist sampling law, at least a total of 2222 × 4000 pixels can be fully represented, which means 4000 times 4096 (2222 must be zero-filled The Fourier transform of up to 4096) points will be invoked in the reconstruction of an image. However, to perform Fourier reconstruction on the original interference signal, the original signal must be linear with respect to the wave number (frequency domain). Therefore, before the Fourier transform, each image must be subjected to 4000 times of difference operations in advance to convert the signal from wavelength linearity to wavenumber linearity. This process takes up more computer resources and drags down the real-time display. The spectrometer in the device of the present invention introduces a prism 09, and utilizes the negative dispersion of the grating and the positive dispersion of the prism to obtain a light beam with linear wave number, thus saving time-consuming and resource-consuming numerical interpolation. At the same time, because the device uses parallel detection, one dimension of scanning is reduced, so an area array CCD camera is used.

An embodiment of the present invention also provides a data processing method for an edema detection device, including:

Average the signals of multiple images of the same position or multiple consecutive scanning points in an image to subtract noise interference;

Using the detected images to obtain backscattered light intensity signal values corresponding to different positions and depths i;

The local relative water content was calculated according to the following formula:

Among them, C _i is the local relative water content at tissue depth i, I _i is the signal value at depth _i , Δd is the distance between different depths, and In is the signal value at different positions below depth i.

Specifically, according to the method for measuring water content with tomographic capability proposed by the present invention, firstly, the signals of multiple images of the same position or multiple continuous scanning points in an image are averaged to remove noise interference. The formula we derived from Lambert Beer's law:

Among them, I ₀ is the initial incident light intensity, μ _s is the scattering coefficient, μ _a is the absorption coefficient, and C is the water content. Since the μ _s and μ _a are relatively constant in specific tissues, such as skin, muscle, fat, connective tissue, etc., when measuring edema at a specific site, the sum of the two, collectively called the attenuation coefficient, can be regarded as a constant value. Since the judgment of edema degree is compared with normal tissue, we set the C of normal tissue as 1, and define (μ _s +μ _a )C as the relative water content, and its value can be approximated by nonlinear least square Combined with the interference signal after Fourier transform.

The relationship between different water contents, that is, different degrees of edema and the detected signal intensity was investigated. As shown in Fig. 4, the difference in water content leads to a large difference in signal intensity, and as the depth increases, the resulting difference in signal intensity becomes more obvious. For a water content of 5, the signal has been attenuated by 40dB at a depth of 1mm. Because of the sensitivity of the inventive device as high as -100dB, the signal attenuation can still be detected.

Fig. 5 shows the water content value obtained from the detection signal by nonlinear least squares fitting according to formula (1). The expected value is given in the legend in the upper right corner, and the five curves correspond to the detected signals under different expected values. The left arrow indicates the water content value estimated from the correlation signal. By comparing the expected value with the actual estimate, we found that the two were very close, with an error of only 5 parts per thousand.

The above analysis and calculation are only applicable to the situation where the water content is uniformly distributed within the imaging depth, and then the situation where the water content is not uniformly distributed at different depths is analyzed. According to the further deduction of formula (2), the following relationship can be obtained:

Among them, C _i is the local relative water content at tissue depth i, I _i is the signal value at depth _i , Δd is the distance between different depths, and In is the signal value at different positions below depth i. According to this formula, independent relative water content values at different depths can be easily obtained. As shown in Figure 6, the relative water content at 0-0.2 mm is 0.5, the relative water content at 0.2-0.4 mm is 1, the relative water content at 0.4-0.6 mm is 0.3, etc. It can be found that the water content in the range of 0.2-0.4 is the highest, which means that water has the strongest absorption of light, so the signal intensity decreases the fastest in this range. Relatively, the water content in the range of 0.4-0.6 is the least, which means that water has the weakest ability to absorb light, so the signal intensity decreases the slowest in this range.

The hand-held compact edema detection device based on near-infrared light absorption disclosed by the present invention makes full use of the high absorption of water in the 1470 nanometer band and the high sensitivity of optical coherence technology, and provides a convenient and reliable method for clinical edema detection . According to the high absorption of water to 1470nm near-infrared light, by detecting tissue backscattering signals, this detection method can automatically calculate the water content distribution of edema parts at different tissue depths (compared with the water content of non-edema parts of the same tissue ). In addition, the device can also be used as a conventional near-infrared optical tomography device to observe the histological morphology of the skin, eyes, mouth, etc., and provide an important reference for the early diagnosis of related diseases. Moreover, compared with the high radiation of X-ray or CT, and the high cost of MRI technology, the device of the present invention uses optical means, which is safe, harmless and economical, and more likely to benefit patients. The present invention can also be used for real-time and non-invasive monitoring of patients requiring long-term hemodialysis such as heart failure and renal failure, or high-risk groups of such diseases, so as to guide patients and doctors to make corresponding countermeasures in due course.

The invention relates to a high-sensitivity detection device for edema content in a living body. In addition to high sensitivity, the miniaturization and good operability of the device are also requirements for clinical applications. The hand-held optical probe included in the device of the present invention is very compact in appearance (diameter 12 mm×length 22 mm), which contains various optical elements for scanning and focusing and collecting tissue backscattered light.

The above-mentioned embodiments are only to illustrate the technical conception and characteristics of the present invention, and its purpose is to enable those skilled in the art to understand the content of the present invention and implement it accordingly, and not to limit the protection scope of the present invention. All modifications made according to the spirit of the main technical solutions of the present invention shall fall within the protection scope of the present invention.

Claims (10)

1. a kind of hand-held compact oedema detection device based on near-infrared absorption characterized by comprising

The near-infrared light source of ultra-wide spectrum, for generating specific band infrared light；

Beam splitter receives the emergent light of the near-infrared light source, the infrared light is divided into two bundles output, and receive the two of return Road infrared light generates interference light and is output to spectrometer after merging；

Reference arm is connected with the optical path all the way of the beam splitter, the reference arm include plano-convex cylindrical lens, dispersion compensation module and High reflectance plane mirror, the infrared light all the way focus on the plane mirror through plano-convex cylindrical lens, then return through plane mirror reflection The beam splitter is returned, the dispersion compensation module is used to match the dispersion differences of reference arm and sample arm；

Sample arm is connected with the another way optical path of the beam splitter, and the sample arm includes antireflective optical probe, the optics Probe focuses on infrared light in tested tissue, and receives from the reflected infrared light of tested tissue, is transmitted back to beam splitter；

Near infrared spectrum survey meter is connect with the merging optical output mouth of the beam splitter, the spectrum detection instrument include grating, Scanning lens and CCD camera, the infrared light that the reference arm returns with from the reflected infrared light of tested tissue in beam splitter Interference signal is formed, is detected by the near infrared spectrum survey meter, specifically light beam is after transmission grating is by wavelength dispersion It is irradiated in CCD camera, generates image；

Driver, for controlling, the acquisition of synchronized signal, data, digitalized data, processing and store and display data.

2. the hand-held compact oedema detection device based on near-infrared absorption as described in claim 1, which is characterized in that institute Stating near-infrared light source includes the wide range near infrared laser being sequentially arranged, high-pass filter and free optical path fiber coupler, institute Wide range near infrared laser is stated as light source, after the high-pass filter carries out high-pass filtering processing to light source, retains certain wave The infrared light of section, delivery outlet of the coupler as the infrared light generated.

3. the hand-held compact oedema detection device based on near-infrared absorption as claimed in claim 2, which is characterized in that institute Stating near-infrared light source further includes Polarization Controller, and the Polarization Controller is set between high-pass filter and coupler, is used for The polarization state for controlling infrared light guarantees that the light source power of output is maximum.

4. the hand-held compact oedema detection device based on near-infrared absorption as described in claim 1, which is characterized in that institute State dispersion compensation module be prism to, an optical fiber, a plano-convex cylindrical lens identical with the interior model of probe or achromatism Any one of lens.

5. the hand-held compact oedema detection device based on near-infrared absorption as described in claim 1, which is characterized in that institute The probe of sample arm is stated using, to optical mode out, the optic probe uses plano-convex cylindrical lens before the two dimension of no built-in scan function Object lens as focal imaging light beam.

6. the hand-held compact oedema detection device based on near-infrared absorption as described in claim 1, which is characterized in that institute The probe of sample arm is stated using the two dimension for being built-in with MEMS scanning galvanometer or three-dimensional lateral optical mode out.

7. the hand-held compact oedema detection device based on near-infrared absorption as claimed in claim 6, which is characterized in that institute Optic probe is stated using the object lens of plano-convex cylindrical lens or achromatism condenser lens as focal imaging light beam, The piano convex cylindrical Mirror or achromatism condenser lens have both outgoing detection light beam and collecting signal light beam.

8. the hand-held compact oedema detection device based on near-infrared absorption as described in claim 1, which is characterized in that institute State the wide range that specific band infrared light is 1475 nanometers of center wavelength and bandwidth halfwidth is 400 nanometers of near-infrared light source generation Continuous near infrared light.

9. the hand-held compact oedema detection device based on near-infrared absorption as described in claim 1, which is characterized in that institute Stating near infrared spectrum survey meter further includes the prism being set between grating and scanning lens, and the prism is matched with grating In pairs, wavelength linear detection light will be received and be converted into wave number linear probing light, the CCD camera is area array CCD camera.

10. a kind of oedema detection device data processing method characterized by comprising

The signal of multiple continuous scanning points in image or a sub-picture to several same positions is averaged to remove noise Interference；

Different location and the corresponding backscattering light intensity signal value of depth i are obtained using the image detected；

Local Phase is calculated according to the following formula to water content:

Wherein, C_iIt is the Local Phase at tissue depth i to water content, I_iIt is the signal value at depth i, Δ d is different depth The distance between, I_nIt is the following different location signal value of depth i.