WO2015113460A1 - 一种用于烧伤皮肤坏死深度和面积诊断的近红外光谱成像系统及方法 - Google Patents

一种用于烧伤皮肤坏死深度和面积诊断的近红外光谱成像系统及方法 Download PDF

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WO2015113460A1
WO2015113460A1 PCT/CN2015/070456 CN2015070456W WO2015113460A1 WO 2015113460 A1 WO2015113460 A1 WO 2015113460A1 CN 2015070456 W CN2015070456 W CN 2015070456W WO 2015113460 A1 WO2015113460 A1 WO 2015113460A1
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spectral
burn
skin
depth
reflectance curve
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PCT/CN2015/070456
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English (en)
French (fr)
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吴军
刘仓理
杨俊杰
骆永全
黄立贤
罗高兴
陈志强
赵剑恒
张大勇
沈志学
李剑峰
贺伟峰
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重庆西南医院
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Priority to EP15743391.3A priority Critical patent/EP3100674B1/en
Priority to US15/114,794 priority patent/US10278636B2/en
Publication of WO2015113460A1 publication Critical patent/WO2015113460A1/zh

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/44—Detecting, measuring or recording for evaluating the integumentary system, e.g. skin, hair or nails
    • A61B5/441—Skin evaluation, e.g. for skin disorder diagnosis
    • A61B5/445—Evaluating skin irritation or skin trauma, e.g. rash, eczema, wound, bed sore
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0075—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence by spectroscopy, i.e. measuring spectra, e.g. Raman spectroscopy, infrared absorption spectroscopy
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0077—Devices for viewing the surface of the body, e.g. camera, magnifying lens
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7235—Details of waveform analysis
    • A61B5/7246—Details of waveform analysis using correlation, e.g. template matching or determination of similarity
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/02—Details of sensors specially adapted for in-vivo measurements
    • A61B2562/0233—Special features of optical sensors or probes classified in A61B5/00
    • A61B2562/0242—Special features of optical sensors or probes classified in A61B5/00 for varying or adjusting the optical path length in the tissue

Definitions

  • the present invention relates to the field of tissue damage and spectral imaging techniques.
  • the accuracy of the world's best burn doctors for the empirical diagnosis of wounds is only about 70%, that is, at least 30% of healthy tissues in burn surgery may be mistakenly removed or 30% of necrotic tissue is delayed; the former can be wounded Residual and extremely valuable skin attachments and their associated stem cells and other normal tissues are removed along with necrotic tissue, which has an important effect on the speed and quality of wound healing; the latter can increase the depth of burns, ie from shallow to deeper Wounds.
  • deep burn skin tissue lesions can reach deep into muscles and even bones, far beyond the depth of skin tissue anatomy, such injury treatment and prognosis is more complicated, so the empirical diagnosis of burn depth is based solely on the naked eye recognition.
  • the guiding role of treatment is limited. Research data shows that timely and accurate judgment and treatment can prevent the speed and extent of burn wounds from shallow to deep, which can effectively save patients' lives, reduce complications, promote wound healing and accelerate patient recovery.
  • the "gold standard" for burn diagnosis is still histopathological biopsy, which leads to the fact that it can not be practically applied to the clinic for the following reasons: 1.
  • the biopsy operation is invasive to the body, and some patients are unacceptable; 2.
  • Due to the histopathology of burns Changes occur dynamically over a period of time, so a single biopsy in the early stages of burns to initially assess the extent of injury may not accurately predict the outcome; 3.
  • An experienced pathologist is needed and has long been committed to this jobs. For the same reason, subsequent skin collagen and vimentin immunohistochemical staining techniques have not been popularized in clinical testing.
  • burn depth diagnostic techniques have emerged in the field of burn wound diagnosis, such as fluorescence detection technology, near-infrared thermal imaging technology, ultrasonic detection technology, laser Doppler technology, and spectral biotechnology.
  • Fluorescence detection technology is to inject the fluorescent substance to evaluate the depth of the wound according to the fluorescence intensity, peak size and phase characteristics of the wound under different excitation light irradiation, but the wound ointment, preservative, dressing, and raw Substances such as preparations have a great influence on the ICG test results of burn wounds.
  • the fluorescence is weak, resulting in an increase in detection error.
  • Infrared thermal imaging technology evaluates the burn depth of wounds by detecting the thermal radiation of different burned skins. Lawson et al first used this technique to detect wound depth, but this method requires high detection conditions and requires constant ambient temperature and equilibrium time. The evaporative cooling of the wound will greatly affect the test results, and the instrument cost is high and individual differences Many factors such as high sex and high false positives make it difficult to distinguish deep II and III wounds, which limits its wide clinical application.
  • Kalus first used B-scan to evaluate the depth of burns. The main principle was to observe the boundary between living tissue and necrotic tissue, and to diagnose according to the echo map of normal skin and different burn tissues. The need to contact the wound during operation is the main factor limiting its clinical application. In addition, it has proved that its diagnostic accuracy is low, which is not superior to subjective experience diagnosis.
  • Laser Doppler technology products are currently the only devices approved by the US FDA for the diagnosis of burn wound depth.
  • the principle is to use Doppler shift to detect blood cell flow in the microvascular of wound tissue.
  • the blood flow in shallow burn wounds is relatively fast, while the deep burn wounds flow slowly, which can distinguish between shallow and deep burns.
  • the early spectroscopy technique used different spectroscopy to evaluate the depth of burn after different absorption of blood in the wound surface.
  • Anselmo et al. first proposed the technique and used it for clinical diagnosis. They used green, red and blue spectra to treat the wound surface. The diagnostic accuracy is up to 79%. Based on this technology, Heimbach et al. designed the instrument and applied it in the clinic, and found that the diagnostic accuracy of this technique for non-healing wounds within three weeks was 80%.
  • methods for diagnosing burn depth based on spectroscopy have been further developed and gradually extended to the field of near-infrared spectroscopy. In 2001, Sowa et al.
  • spectral imaging technology has matured in the fields of space remote sensing mapping, agriculture, exploration, etc.
  • This technology combines spectral analysis technology with image analysis technology to meet the new concept of comprehensive qualitative, quantitative and localization analysis. Its visualization and non-contact And non-invasive and other excellent characteristics have shown its potential as a new high-specificity, high-precision burn wound diagnostic tool.
  • its imaging band is mainly in the visible and near-infrared spectra, but the spectral resolution is generally low. The scanning accuracy is around 50 nm, which still cannot meet the needs of medical fine research.
  • the imaging spectrometers used to study burn medicine are mainly in the range of 400-700 nm and 700-1100 nm.
  • the existing spectral imaging technology can not accurately distinguish the skin necrotic tissue and obtain the tomographic image of the skin tissue.
  • Another key point is that its spectral resolution and imaging spectral range fail to reach the level of skin necrotic tissue and obtain its tomographic image. That is, a narrow-band, wide-spectrum tunable filter with high resolution is a core issue.
  • the present invention is directed to the above-mentioned deficiencies of the prior art, and aims to provide a near-infrared spectroscopy imaging system and method for diagnosing the depth and area of burn skin necrosis, using hyperspectral imaging with high resolution, wide field of view, and high efficiency.
  • the instrument obtains the key information of degenerative and necrotic tissue of burned skin in a non-contact and non-invasive manner, achieves visualization, and obtains accurate information on the area and depth of burned skin necrosis through information processing, and provides the clinician with the key to skin burn degeneration and necrosis. Information to guide clinical treatment and clinical surgery.
  • a near-infrared spectral imaging system for depth and area diagnosis of burn skin necrosis including a spectral imager and a computer control system.
  • the spectral imager includes a light source, an optical lens, a wide-spectrum liquid crystal tunable filter (LCTF) or an acousto-optic tunable filter (AOTF), a drive controller, and a CCD camera; the wide-spectrum liquid crystal tunable filter Sheet (LCTF) or acousto-optic tunable filter (AOTF) acquires spectral signals in the 1100-2500 nm band;
  • LCTF wide-spectrum liquid crystal tunable filter
  • AOTF acousto-optic tunable filter
  • the computer control system has a built-in universal module, a data module, a spectrum correction module, a spectrum matching module, and a burn wound three-dimensional synthesis module.
  • the system acquires spectral image data of the burned skin necrotic tissue of the target area through the spectral imager, inputs the computer control system, and performs image analysis processing, that is, first performs spectral correction by the spectral correction module, and then corrects by the spectral matching module.
  • the spectral reflectance curve corresponding to each pixel in the post-spectrum image is spectrally matched with the standard spectral reflectance curve of the burn necrotic skin spectral database in the data module to obtain the burn depth and burn area of the target area, and finally the burn wound surface is three-dimensional.
  • the composite module synthesizes a three-dimensional image of the target area and displays it through the display.
  • the standard spectral reflectance curve in the burn necrotic skin spectral database has a one-to-one matching relationship with the depth of skin burn in the pathological database, which is quantified by utilizing the spectral reflectance curve characteristics of burn necrotic skin in the 1100-2500 nm band.
  • the necrotic signal in the burned skin, and the necrotic signal is correlated with the pathological data, so that the standard spectral reflectance curve in the burn necrotic skin spectral database matches the depth of the skin burn in the pathological database, and each of the burn necrotic skin spectral databases Standard spectral curves represent a depth of burn.
  • the spectral reflectance curve characteristics of the burn necrotic skin in the 1100-2500 nm band include the shape of the spectral reflectance curve, the average amplitude of the curve, and the difference between the peak and the trough amplitude in the curve.
  • the necrotic signal in the skin is the skin degeneration and necrosis of the skin tissue.
  • the original proteins, nucleic acids and high molecular weight hydrocarbons in the skin are damaged by heat, and the chemical bonds are broken, mainly CN, NH, OH.
  • the liquid crystal tunable filter (LCTF) used in this system is critical.
  • the liquid crystal tunable filter (LCTF) includes a liquid crystal tunable filter and a drive controller (Fig. 3).
  • the liquid crystal tunable filter is a multi-stage cascade structure, comprising: a set of electronically controlled liquid crystal wave plates, a set of fixed phase retarder films and a set of polarizing plates.
  • the polarizing plate and the electrically controlled liquid crystal wave plate and the fixed phase retarder are sequentially arranged in parallel with each other and stacked to form a plurality of stages, but the fixed phase retarder may or may not be disposed in the first stage (FIG. 4).
  • the direction of the transmitted polarization of all the polarizers is parallel to each other, and the direction of the fast axis of all the electrically controlled liquid crystal waves is at an angle of 45 with the direction of the polarized light of all the polarizers.
  • the electronically controlled liquid crystal wave plate in each stage structure is controlled by the drive controller to load the drive signal (Fig. 5).
  • the electronically controlled liquid crystal wave plate comprises an intermediate nematic liquid crystal layer and an alignment film symmetrically disposed on both sides, a transparent conductive film and a transparent substrate, and the alignment film on both sides of the nematic liquid crystal layer is reversed in rubbing direction
  • liquid crystal molecules in the liquid crystal layer are arranged along the surface, and the thickness of the liquid crystal layer is controlled by providing a transparent spacer therein (Fig. 6).
  • the above liquid crystal tunable filter can adopt the conventional LCTF driving control mode, but the spectral scanning speed is slow, and the response time can generally reach several hundred milliseconds.
  • the spectral imaging is largely restricted. The time when the system acquires the spectral information brings great difficulty to the clinical imaging acquisition work and subsequent image processing. Therefore, in order to provide an image processing speed of the instrument and better achieve the high efficiency of the present invention, the overvoltage driving method adopted by the present invention, that is, the driving controller loads the AC overvoltage driving signals of different amplitudes on the electronically controlled liquid crystal wave plate.
  • a light source illuminates a target area on the burned skin
  • Spectral matching identification Compare the spectral reflectance curve of each pixel in the spectral image of the corrected target area with the standard spectral reflectance curve of the burn necrotic skin spectrum database, that is, use the skin reflection of the known burn depth The spectral curve is matched to identify the spectral reflectance curve of the target region, and the similarity value between the spectral reflectance curve of the target region pixel and the standard spectral reflectance of various skins with different burn depths is calculated, and the similarity value is the highest.
  • the burn depth is used as the burn depth of the target area pixel, and then each pixel of the target area is matched and recognized to obtain the burn depth and the burn area of the target area;
  • the imaging system and method provided by the invention have the characteristics of high resolution, wide field of view and high efficiency, and can indicate changes in spatial structure caused by tissue protein denaturation before and after skin burn, thereby making non-contact, non-invasive
  • the method provides micro-level information on the boundaries of normal skin tissue and necrotic tissue and the depth of necrosis of burned skin, and forms a visualization that ultimately provides clinicians with critical information about the depth and area of microscopic necrosis of skin burn necrotic tissue, which is beneficial for guiding clinical treatment and Clinical surgery, and to avoid cross-infection and patient pain caused by medical testing, to support clinical diagnosis, treatment and prognosis.
  • the burns of the present invention include thermal burns, burns, chemical burns, electric shocks, radiation injuries, frostbites, and the like.
  • Figure 1 is a schematic structural view of a diagnostic system of the present invention
  • Figure 3 is a structure of a liquid crystal wave plate
  • FIG. 4 is a schematic diagram of an optical path of a response time measurement of a liquid crystal wave plate
  • Figure 5a is a photo-response measurement result of a liquid crystal wave plate having a thickness of 4.8 mm and perfused with a liquid crystal material of SLC-9023 under overvoltage driving;
  • Figure 5b is a photo-response measurement result of a liquid crystal wave plate with a thickness of 8.0 mm and perfused with SLC-9023 liquid crystal material under overvoltage driving;
  • Figure 6 is a schematic view showing the driving mode of the overvoltage driver
  • Figure 7 is a flow chart of image analysis processing
  • Figure 8 water, hemoglobin, deoxyhemoglobin absorption spectrum
  • Figure 9 is a spectrum detection diagram of an isolated human skin burn model
  • Figure 10 is a statistical histogram of the results of spectral detection of human skin burns model
  • Figure 11 is a spectrum detection diagram of a rat scald model
  • Figure 12 is a statistical histogram of the results of spectral detection of the rat scald model
  • Figure 13 is a spectrum detection diagram of an adult pig skin burn model
  • Figure 14 is a statistical diagram of the spectral detection of the pig skin burn model
  • Figure 15 is a graph showing the results of spectral examination of clinical burn patients.
  • the diagnostic system mainly includes a spectral imager and a computer control system, the structure of which is shown in Figure 1, wherein:
  • Spectral imager by illumination source 101, optical lens 102, filter 103 (using liquid crystal tunable filter LCTF and acousto-optic tunable filter AOTF), CCD camera 106, LCTF controller 105a and AOTF controller 105b And an overvoltage driver 104. They are assembled in the form of a conventional spectral imager.
  • the performance parameters of each component can be specifically selected as follows:
  • Liquid crystal tunable filter operating band: 900 nm ⁇ 2500 nm; spectral resolution: 5-20 nm; optical transmittance: 5-30%; field of view: 1-10 °.
  • CCD camera Model: Daheng DH-SV1411GX; Resolution: 1394 ⁇ 1040 pixels; Frame rate: 15 frames / sec; Data interface: Gigabit Ethernet port
  • Illumination source halogen lamp source: OCEANSI USA; spectral range: 400nm ⁇ 2500nm; light source illumination: ring illumination.
  • Optical lens Model: Optistar; focal length: 50mm (fixed focus lens), clear aperture: 55mm.
  • LCTF overvoltage drive controller t ranges from 0-50ms, its voltage amplitude V 3 >V 2. , V 3 amplitude ranges between 10-50V, and then V 2 drive voltage is applied The voltage amplitude is between 0-10V and the alternating frequency is between 0.5-5KHz ( Figure 7).
  • the main parameters of the spectral imager thus formed are: working band: 900 nm to 2500 nm; spectral resolution: 5-20 nm; spatial resolution: 10-200 ⁇ m, optical transmittance: 5-30%; field of view: 1 -10°.
  • LCTF liquid crystal tunable filter
  • FIG 2 uses a five-stage cascaded liquid crystal tunable filter comprising polarizers (1, 2, 3, 4, 5, 6) and electronically controlled liquid crystal waves (7, 8, 9). , 10, 11) and fixed phase retarder (12, 13, 14, 15) (a total of five levels, the first stage is not reinforced positioning phase retarder).
  • the polarized light beams (1, 2, 3, 4, 5, 6) have parallel transmission polarization directions, and the fast axis direction of the electronically controlled liquid crystal wave plates (7, 8, 9, 10, 11) and the polarizing plate (1, 2,3,4,5,6) Transmitted polarized light at an angle of 45°, polarizing plates (1, 2, 3, 4, 5, 6) and electronically controlled liquid crystal waves (7, 8, 9, 10, 11) And the fixed phase retarder (12, 13, 14, 15) are arranged in parallel with each other and stacked at intervals.
  • the liquid crystal wave plate in each stage structure is controlled by a drive controller.
  • the right side of Figure 4 is a schematic diagram of the voltage driving signal loaded on the electronically controlled liquid crystal wave plate in each stage of the liquid crystal tunable filter.
  • the signal is an AC overvoltage driving signal, and the voltage amplitude is between 0-20V, alternating The frequency is between 0.5 and 5 kHz.
  • the driving method is: if the driving voltage required for the liquid crystal wave plate is V 2 , a narrow pulse is first applied when driving, its amplitude V 3 >V 2 , and then the driving voltage of V 2 is applied, under the control of the driving controller, The liquid crystal wave plate is loaded with AC overvoltage driving signals of different amplitudes, which can realize fast spectral scanning of the liquid crystal tunable filter.
  • FIG. 3 is a schematic structural view of an electrically controlled liquid crystal wave plate (7, 8, 9, 10, 11) including a glass substrate (16, 17), an ITO transparent conductive film (18, 19), and a PI alignment film (20, 21).
  • the thickness controls the transparent spacers (22, 23) and the liquid crystal layer 24.
  • the ITO transparent conductive film layer (18, 19) is connected to the driving controller (ie, the multi-channel driving source) through the electrode, and provides an electric field for the liquid crystal layer 24 to rotate the pointing of the liquid crystal molecules to change the electronically controlled liquid crystal wave plate (7).
  • the driving controller ie, the multi-channel driving source
  • the liquid crystal molecules in the liquid crystal layer 24 can be induced to be aligned in a specific direction, so that the electronically controlled liquid crystal wave plate has crystal birefringence optical characteristics; the liquid crystal layer 24 is formed by injecting a nematic liquid crystal material between the glass substrates.
  • the thickness of the liquid crystal layer 24 is controlled by the thickness control spacers (22, 23), and the refractive index difference ⁇ n is between 0.05 and 0.30.
  • the thickness control spacers (22, 23) may be glass fibers, glass beads, or plastic beads or photo spacers.
  • the overvoltage driving signal is loaded on a single-stage liquid crystal wave plate, and the response time is measured.
  • the time response characteristic measurement optical path is shown in Fig. 4.
  • the liquid crystal wave plate is provided with an overvoltage driving signal by the driving controller, and is placed between two parallel polarizers, the wavelength of the laser is 632.8 nm, and the photodetector adopts a visible light sensor. Piece, with sub-microsecond photoelectric response speed, the detector's photoelectric signal is sent to the oscilloscope record.
  • Fig. 5a and Fig. 5b show the photoelectric response measurement results of the liquid crystal wave plate of the SLC-9023 liquid crystal material with a thickness of 4.8 mm and 8.0 mm, respectively, under overvoltage driving. It can be seen from Fig. 5a that the liquid crystal wave plate with a thickness of 4.8 mm has a steady state of 25 ms under the normal driving of 5 V voltage, and the time to reach the steady state is only under the overvoltage driving of 10 V, 3 ms.
  • the system can also be automatically switched using an acousto-optic tunable filter (AOTF) and a liquid crystal tunable filter (LCTF).
  • AOTF acousto-optic tunable filter
  • LCTF liquid crystal tunable filter
  • Acousto-optic tunable filter (AOTF) is an acousto-optic modulation device consisting of a uniaxial birefringent crystal (usually made of TeO2) bonded to one side of a uniaxial crystal.
  • An electric transducer, and a high frequency signal source acting on the piezoelectric transducer acting on the piezoelectric transducer.
  • AOTF's spectral scanning speed is extremely fast, suitable for scanning objects in transient state.
  • AOTF has been widely used in many aspects such as image processing, monitoring and monitoring, color information collection, electro-optical signal scanning generator, and technology.
  • the AOTF works by utilizing the Bragg diffraction of light incident into the propagation medium as it propagates through an anisotropic medium.
  • the AOTF diffracts the incident polychromatic light, and selects a monochromatic light of a wavelength ⁇ .
  • the wavelength ⁇ of the monochromatic light has a one-to-one correspondence with the radio frequency f, and the wavelength of the desired light can be quickly selected by tuning the electrical signal.
  • the selected light wave enters the image acquisition system through the CCD detector, and the spectral image is saved in the computer by the image acquisition software. After a series of algorithms and databases are provided for comparison, the ideal image can be displayed on the computer.
  • a universal module that controls the turn-on and turn-off of the light source, the power distribution of the various parts of the spectrum imager, and the various ports and interfaces of the system;
  • the data module includes a burn necrotic skin spectral database and a burn skin necrosis pathology database; the spectral reflectance curve of the burn necrotic skin spectral database is in the range of 1100-2500 nm, and the source of the spectral reflectance curve data includes a fiber spectrometer and a medical spectral imager.
  • the spectral reflectance curve of the burn necrotic skin spectral database has a one-to-one match with the skin burn depth in the burn skin necrosis pathology database, and the spectral reflectance curve can be used to represent the burn depth.
  • the characteristic of the spectral reflectance curve of burned necrotic skin in the 1100-2500 nm band is used to quantify the necrotic signal in the burned skin, and the necrotic signal is correlated with the pathological data to make the burn necrotic skin spectrum database.
  • the standard spectral reflectance curve matches the skin burn depth in the pathology database, and each standard spectral curve in the burn necrotic skin spectral database represents a burn depth.
  • the spectral reflectance curve characteristics of the above burned necrotic skin in the 1100-2500 nm band include the shape of the spectral reflectance curve, the average amplitude of the curve, and the difference between the peak and the trough amplitude in the curve.
  • the spectral correction module is configured to divide the amplitude of the spectral curve corresponding to each spectral image pixel in the original spectral image of the target region by the spectral curve amplitude corresponding to the spectral image pixel of the whiteboard under the same condition to remove the background light and the light source. The effect of uniformity, the spectral reflectance curve of the target region is obtained;
  • a spectral matching module for correcting the spectral reflectance curve of each pixel in the spectral image of the corrected target region and the standard spectral reflectance curve of the burn necrotic skin spectral database, that is, using the skin reflectance spectrum curve of the known burn depth
  • the depth is used as the burn depth of the target area pixel, and then each pixel of the target area is matched and recognized, and the burn depth and the burn area of the target area are obtained.
  • the three-dimensional synthesis module of burn wounds is used to synthesize and display the data of burn depth and burn area in the target area.
  • the human body skin is from the special skin library of the Southwest Institute of Burns.
  • SD rat was purchased from the Experimental Animal Center of the Third Military Medical University
  • Bama Xiang pig purchased from the Experimental Animal Center of the Third Military Medical University
  • DMEM medium was added with NaHCO 33 g, HEPES 4 g, glutamine 2 g, penicillin 100,000 U, streptomycin 100,000 U, pH 7.2, 0.22 ⁇ m membrane filtration, and stored at 4 ° C. Add 10% FBS before use.
  • trypsin 0.25 g trypsin was added to 100 ml PBS (m/V) and stored at -20 °C until use.
  • the near-infrared fiber spectrum detector of the invention is subjected to internal reference calibration, and the optimal distance, angle and working time of the biological detection in the body spectrum are combined with the actual measurement environment, and the adverse effects of the background factors are eliminated;
  • the standard infrared whiteboard is used to calibrate the near-infrared fiber optic spectrum detector.
  • the light intensity is calibrated again for 10 min, 30 min, 60 min, 2 h, and 4 h, and the mean value is stable.
  • the human skin tissue derived from the pico library is taken out from the liquid nitrogen; the storage time is half a year, the size is about 9 ⁇ 13 cm 2 , and the average thickness is about 3 mm.
  • the burn time is 3s, 5s, 10s, 15s, 20s, 30s, 45s, 60s, 90s, 120s.
  • the specimen is made into a 6-8 micron thickness slice on the microtome for use;
  • Rats were intraperitoneally injected with 1% sodium pentobarbital (calculated per 0.5 ml/100 g);
  • the burn time is 3s, 5s, 10s, 15s, 20s, 30s, 45s, 60s, 90s, 120s.
  • the specimen is made into a 6-8 micron thickness slice on the microtome for use;
  • the burn time is 3s, 5s, 10s, 15s, 20s, 30s, 45s, 60s, 90s, 120s.
  • the specimen is made into a 6-8 micron thickness slice on the microtome for use;
  • the reflectance spectrum curve changes from 1100nm to 2500nm. As the burn time increases, the characteristic amplitude at the specific peak shows a decreasing trend.
  • the position where the specific peak is located is 1100 nm to 2500 nm.
  • the position where the specific peak is located is 1100 nm to 2500 nm.
  • the position where the specific peak is located is 1100 nm to 2500 nm.
  • the biometric band of near-infrared reflectance spectrum after skin burn is: 1100nm ⁇ 2500nm.
  • the change characteristics of the information are as follows: as the burn time is prolonged, the burn depth increases, and the characteristic amplitude of the characteristic band shows a decreasing trend.
  • the real-time detection data of the burn detector on the fresh burn wounds of the spectrum detector represents the skin burn depth detected by the corresponding gold standard, and the relevant alignment is completed.
  • specimens can be obtained by surgical resection, conventional HE staining, pathological photographing under 200 times high magnification, and standard lesions to measure the depth of skin lesions.
  • the reflectance spectrum curve changes from 1100nm to 2500nm.
  • the characteristic amplitude at the specific peak shows a decreasing trend; the specific peak is located at 1100nm ⁇ 2500nm;
  • the intraoperative pathological resection specimens were routinely fixed, HE stained, pathologically photographed under 200 times high magnification, and the standard lesion was used to measure the depth of skin lesions;
  • the results of the real-time detection data of the burned fresh burn wounds by the 5 spectrum detector represent the skin burn depth detected by the corresponding gold standard, and the correlation comparison is completed.
  • Basic information display the patient's general information and medical history, detailed records of the injury site, etc.; the patient is a metal aluminum solution with multiple burns throughout the body, and the skin of the ankle is typically characterized by a change in charcoal black. The texture is hard and there is no obvious pain;
  • Spectral detection data match the record and number according to the damage site and the test data
  • Pathological results record the lesion site was removed during the operation and sent to the pathological test results.
  • Spectral detector in the near red band (1100nm ⁇ 2500nm) can achieve real-time detection and analysis of wounds of skin burn patients with different depths; the patient's long-wavelength (1100nm ⁇ 2500nm) wound test results compared with normal skin, skin burns after reflection
  • the spectral curve changes from 1100nm to 2500nm. With the prolonged scald time, the characteristic amplitude at the specific peak shows a decreasing trend. With the depth deepening, the curve of the burn center area (the pink corner mark) is gradually flat and horizontal. The angle of the baseline becomes smaller;
  • the patient finally confirmed that the diagnosis result of the lumbosacral skin burn area of the patient was: the central area of the wound (pink mark) was a third degree burn.
  • 1 collection site drawing on the principle of skin cosmetic calibration, the spectral collection calibration points are forehead, face, upper arm, lateral neck, and inferior clavicle; each part is collected repeatedly 3 times;
  • 3Environmental conditions indoor temperature 18-22 degrees, humidity 55%-60%, working environment light conditions when collecting spectral information inside and outside the uniform ward;
  • Basic information includes: ID number, name, gender, age, weight and contact details.
  • the near-infrared spectroscopy imager collects the spectrum image of the hand wound of the burned patient on the spot, and can accurately distinguish the normal tissue and the burned area through the three-dimensional color map display. It shows the good location of the burn site of the burned image and the injury area of the burned part.
  • the judgment function and accurate spectral biological diagnosis function have achieved the diagnostic effect of “integration of the map”.

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Abstract

一种用于烧伤皮肤坏死深度和面积诊断的近红外光谱成像系统，包括光谱成像仪和计算机控制系统。所述光谱成像仪包括光源（101）、光学镜头（102）、滤波器（103）、驱动控制器（105a，105b，104）和CCD像机（106）；所述滤波器（103）采用宽谱液晶可调滤光片（LCTF）或声光可调滤光片（AOTF），它们获取目标区域烧伤皮肤坏死组织的1100-250Onm波段的光谱信号。所述计算机控制系统内置有通用模块、数据模块、光谱校正模块、光谱匹配模块、烧伤创面三维合成模块。所述光谱成像仪获取目标区域烧伤皮肤坏死组织的光谱图像数据，输入所述计算机控制系统，由计算机控制系统经图像分析处理，通过将光谱图像中每个像元对应的光谱反射率曲线与数据模块中烧伤坏死皮肤光谱数据库的标准光谱反射率曲线进行光谱匹配识别，得到目标区域的烧伤身体和烧伤面积，并合成目标区域的三维图像显示。

Description

一种用于烧伤皮肤坏死深度和面积诊断的近红外光谱成像系统及方法 技术领域
本发明涉及组织损伤以及光谱成像技术领域。
背景技术
烧伤在平时和战时均为常见病，战时尤其高发。烧伤后死亡率、容貌毁损率及致残率高，救治周期长，直接威胁生命安全和机体健康，给社会及家庭带来沉重负担。
目前，烧伤所致皮肤组织损伤程度的准确判断仍是烧伤外科的重大难题，但临床上用于烧伤深度诊断的最常见方法仍主要依赖于临床经验，包括观察烧伤创面的外观、毛细血管再充盈状况以及创面对触摸和针刺疼痛的感觉等。资料显示，世界最好的烧伤医生对创面经验性诊断的准确率只有70％左右，即烧伤手术至少有30％的健康组织可能被错误切除或30％的坏死组织被贻误保留；前者可将创面残留的极其宝贵的皮肤附件及其相关干细胞和其它正常组织连同坏死组织一并被清除，对创面愈合的速度和质量产生重要影响；后者可加重烧伤的深度，即由较浅转变为较深的创面。此外，深度烧伤皮肤组织病变可深达肌肉甚至骨质，远超皮肤组织解剖深度，此类伤情治疗及预后更为复杂，故单纯以肉眼识别为依据进行烧伤深度的经验性诊断，对临床治疗的指导作用有限。研究资料表明，及时准确的判断和治疗可以阻止烧伤创面由浅度向深度转变的速度和程度，能有效挽救患者生命、减少并发症、促进创面愈合、加快患者康复。
目前烧伤诊断的“金标准”仍为组织病理活检，导致其无法实际应用于临床的原因有以下几点：1、取活检操作对机体有创，部分患者无法接受；2、由于烧伤的组织病理改变在一定时间内是动态持续发生的，因而在烧伤早期进行单一的切片检查来初步评估损伤程度，可能无法准确地预测结果；3、需要一个经验丰富的病理学专家，并长期致力于此项工作。同样的原因，随后出现的皮肤胶原蛋白、波形蛋白免疫组织化学染色技术也未能在临床检测中普及。
自20世纪60年代以来，在烧伤创面诊断领域应运而生出现了多种烧伤深度诊断技术，如荧光检测技术、近红外热成像技术、超声检测技术、激光多普勒技术、光谱生物技术等。
荧光检测技术是通过静脉注射荧光物质，根据创面在不同的激发光照射下激发产生的荧光强度、峰值大小和时相特点来对创面深度进行评价，但创面药膏、防腐剂、敷料、生 物制剂等物质对烧伤创面的ICG检测结果都有较大影响；另外，深度烧伤血管损坏或闭塞时荧光较弱，造成检测误差增大。
红外热成像技术是通过探测不同烧伤皮肤的热辐射来对创面的烧伤深度进行评价。Lawson等人首先将该技术用于检测创面深度，但该方法对检测条件要求较高，需要恒定的环境温度及平衡时间，创面的蒸发冷却都会很大的影响检测结果，仪器成本高、个体差异性大、假阳性高等诸多因素导致其不能很好地区分深Ⅱ度和Ⅲ度创面，限制了其在临床的广泛应用。
Kalus首先使用B超扫描来评价烧伤深度，主要原理是观察活组织和坏死组织的边界，根据正常皮肤和不同烧伤组织的回声图谱进行诊断。操作时需接触创面是限制其临床应用的主要因素，另外实践证明其诊断准确率较低，并不优于主观经验诊断。
激光多普勒技术产品是目前唯一被美国FDA批准可用于诊断烧伤创面深度的设备。其原理是利用多普勒频移来探测创面组织微血管中的血细胞流动情况，浅度烧伤创面的血液流动相对较快，而深度烧伤创面流动较慢，据此可以区分浅度和深度烧伤。
早期的光谱技术是利用不同光谱被创面中的血液吸收后的不同衰减来对烧伤深度进行评价，Anselmo等人最早提出该技术并用于临床诊断，他们采用绿、红和蓝三种光谱对创面进行诊断的准确率可达79％。基于该技术，Heimbach等人设计了仪器并在临床进行应用，发现采用该技术对创面在三周内不愈合的诊断准确率为80％。近年来，基于光谱技术诊断烧伤深度的方法得到了进一步发展，并逐渐扩展到近红外光谱领域。2001年，Sowa等人在700-1000纳米的波长范围内利用皮肤烧伤后血液中含氧血红蛋白、脱氧血红蛋白和组织水分在近红外光的吸收光谱上的差异，通过测量血液中血红蛋白总量(tHb)、组织含氧饱和度(StO2)和水(H2O)的含量来判断烧伤深度的新方法，并对伤后3h的动物模型进行了试验研究。2005年,Milner等人首次用波长548nm(血红蛋白吸收波长)的正交偏振光谱(orthogonal polarization spectral，OPS)评价烧伤程度。2009年，Cross等人在500-1000纳米的波长范围内研究了烧伤后皮肤组织水肿程度与烧伤深度之间的关系。但以上研究的核心原理都是基于皮肤烧伤前后血液中红细胞携氧状况改变和组织水分的变化来间接判断烧伤深度(见图9)，并不能直接提供烧伤皮肤组织坏死深度及面积的精确信息。
目前光谱成像技术已成熟用于空间遥感测绘、农业、勘探等科学领域，该技术将光谱分析技术与图像分析技术相融合，满足综合定性、定量和定位分析的新概念，其可视化、非接触性及非侵害性等优异特性都显示出将其作为一种新的高特异性、高精度烧伤创面诊断利器的潜在可能。目前其成像波段主要在可见光和近红外光谱，但光谱分辨率普遍较低， 扫描精度在50nm左右，尚不能满足医学精细研究的需要。而目前用于研究烧伤医学的成像光谱仪波段主要在400-700nm及700-1100nm，光谱生物基本原理仍旧以分析皮肤血液中红细胞携氧状况改变和组织水分的变化为主。其中典型的是专利文献“可见-近红外光谱技术在烧伤损伤评估”(美国，NO.860554B2)，该专利主要研究了在500-1100nm波段，烧伤前后皮肤血液中氧合血红蛋白、脱氧血红蛋白、以及水分的变化，间接提示烧伤的深度；因此，并不能提供有关皮肤组织坏死的精确信息。
现有的光谱成像技术还不能精确分辨皮肤坏死组织和获取皮肤组织断层光谱图像，还有一个关键点在于其光谱分辨率和成像光谱范围未能达到分辨皮肤坏死组织和获取其断层图像的水平，即具有高分辨率的窄带、宽谱可调滤光片是核心问题。
因此，迄今为止尚无能够直接精确区分坏死组织深度、精确辨别坏死组织和正常组织界限的诊断仪器设备和相关方法。
发明内容
本发明针对现有技术存在的上述不足，目的是提供一种对烧伤皮肤坏死深度和面积诊断的近红外光谱成像系统及方法，采用具有高分辨率、宽视场角、高效率的超光谱成像仪，以非接触、非侵害方式获取烧伤皮肤变性坏死组织的关键信息，达到可视化，并通过信息处理，得到烧伤皮肤坏死面积及深度的精确信息，提供给临床医生有关皮肤烧伤变性坏死组织的关键信息，指导临床治疗和临床手术。
本发明采用的技术方案如下：
一种用于烧伤皮肤坏死深度和面积诊断的近红外光谱成像系统，包括光谱成像仪和计算机控制系统。
其中光谱成像仪包括光源、光学镜头、宽谱液晶可调滤光片(LCTF)或声光可调滤光片(AOTF)、驱动控制器和CCD像机；所述宽谱液晶可调滤光片(LCTF)或声光可调滤光片(AOTF)获取1100-2500nm波段的光谱信号；
计算机控制系统内置有通用模块、数据模块、光谱校正模块、光谱匹配模块、烧伤创面三维合成模块。
所述系统通过所述光谱成像仪获取目标区域烧伤皮肤坏死组织的光谱图像数据，输入所述计算机控制系统，经图像分析处理，即首先通过光谱校正模块进行光谱校正，然后通过光谱匹配模块将校正后的光谱图像中每个像元对应的光谱反射率曲线与数据模块中烧伤坏死皮肤光谱数据库的标准光谱反射率曲线进行光谱匹配识别，得到目标区域的烧伤深度和烧伤面积，最后由烧伤创面三维合成模块合成目标区域的三维图像，并通过显示器显示。
所述烧伤坏死皮肤光谱数据库中的标准光谱反射率曲线与病理数据库中的皮肤烧伤深度具有一对一的匹配关系，其是利用烧伤坏死皮肤在1100-2500nm波段的光谱反射率曲线特征，来定量烧伤皮肤中的坏死信号，并将坏死信号与病理数据进行关联，使烧伤坏死皮肤光谱数据库中的标准光谱反射率曲线与病理数据库中的皮肤烧伤深度的匹配，烧伤坏死皮肤光谱数据库中的每一条标准光谱曲线均代表一种烧伤深度。
所述烧伤坏死皮肤在1100-2500nm波段的光谱反射率曲线特征包括光谱反射率曲线的形状、曲线的平均幅值、以及曲线中波峰与波谷幅值的差值。
所述皮肤中的坏死信号为皮肤组织烧伤变性坏死后，皮肤中原有的蛋白质、核酸以及高相对分子量的碳氢化合物等生物大分子受热力损伤，其化学键发生断裂，主要为C-N、N-H、O-H键的断裂，还包括不饱和共轭键：C＝C、N＝N、N＝O的断裂导致的光谱信息的改变，这种光谱信息的改变即为坏死信号。
本系统中采用的液晶可调滤波器(LCTF)非常关键，该液晶可调滤波器(LCTF)包括液晶可调滤光片和驱动控制器(图3)。
其中，液晶可调滤光片为多级级联结构，包括：一组电控液晶波片、一组固定位相延迟片和一组偏振片。所述偏振片与电控液晶波片和固定位相延迟片依次相互平行排列、间隔叠放形成多级，但第一级中可以设置或不设置固定位相延迟片(图4)。
其中所有偏振片的透射偏振光方向相互平行，所有电控液晶波片的快轴方向与所有偏振片透射偏振光方向成45°角。
每级结构中电控液晶波片由驱动控制器控制，加载驱动信号(图5)。
尤其是电控液晶波片，其包括中间的向列相液晶层和两侧依次对称设置的取向膜、透明导电膜和透明基板，所述向列相液晶层两侧的取向膜摩擦方向反向平行，液晶层中的液晶分子沿面排列，所述液晶层的厚度通过在其中设置透明隔垫进行控制(图6)。
上述液晶可调滤光片可以采用常规LCTF的驱动控制方式，但是会导致其光谱扫描速度较慢，响应时间一般可达到几百毫秒，对于动态光谱成像来说，在很大程度上制约光谱成像系统获取光谱信息的时间，对临床成像采集工作及后续图像处理带来很大的难度。因此，为了提供仪器的图像处理速度，更好的实现本发明高效率的目的，本发明采用的过压驱动方式，即驱动控制器对电控液晶波片加载不同幅值的交流过压驱动信号，采用过压驱动器驱动：如果液晶波片需要的驱动电压为V2，驱动时首先施加一个持续时间t很短的窄脉冲，t的取值范围在0-50ms之间，t不等于0，其电压幅度V3>V2.,V3的幅值范围在10-50V之间，然后再施加V2的驱动电压，电压幅值在0-10V之间但不等于0，交变频率在0.5-5KHz(图 7)。
因此，利用以上系统，就可以对正常皮肤组织和烧伤皮肤坏死组织的界线及烧伤皮肤坏死组织的深度进行诊断，其步骤如下(图8)：
(1)光源照明所述烧伤皮肤上的目标区域；
(2)用LCTF或AOTF以及CCD摄像机收集所述目标区域在1100-2500nm波段的光谱图像，获取烧伤皮肤坏死组织的光谱数据和图像数据，输入计算机控制系统；
(3)计算机控制系统进行图像分析处理：
(3.1)光谱校正：将目标区域原始光谱图像中每一个光谱图像像元对应的光谱曲线幅值除以相同条件下白板的光谱图像像元对应的光谱曲线幅值，以去除背景光及光源不均一性导致的影响，得到目标区域的光谱反射率曲线；
(3.2)光谱匹配识别：将校正后目标区域的光谱图像中每个像元的光谱反射率曲线与烧伤坏死皮肤光谱数据库的标准光谱反射率曲线进行对比分析，即用己知烧伤深度的皮肤反射光谱曲线去匹配识别目标区域的光谱反射率曲线，通过计算目标区域像元的光谱反射率曲线与各种不同烧伤深度皮肤的标准光谱反射率之间的相似度值，取相似度值最高所对应的烧伤深度作为将目标区域像元的烧伤深度，然后对目标区域每个像元进行匹配识别，得到目标区域的烧伤深度及烧伤面积；
(3.3)光谱图像合成与显示：将目标区域烧伤深度和烧伤面积的数据进行三维合成与显示。
本发明以上提供的成像系统及方法具有高分辨率、宽视场角、高效率的特点，能够指明在皮肤烧伤前后由于组织蛋白质变性而导致其空间结构发生的变化，从而以非接触、非侵入方式提供有关正常皮肤组织和坏死组织界限和烧伤皮肤坏死深度的微米级信息，并形成可视化，最终提供给临床医生有关皮肤烧伤坏死组织微米级的坏死深度和面积关键信息，有利的指导临床治疗和临床手术，并最大限度地避免由医疗检测引发的交叉感染及患者疼痛，有利支持临床诊断、治疗和预后判断。
本发明所述的烧伤涵盖热力烧伤、烫伤、化学烧伤、电击伤、放射损伤、冻伤等。
附图说明
图1是本发明的诊断系统的结构示意图；
图2为液晶可调滤光片的结构；
图3为液晶波片的结构；
图4为液晶波片响应时间测量光路示意图；
图5a为厚度为4.8mm、灌注SLC-9023液晶材料的液晶波片在过压驱动下的光电响应测量结果；
图5b为厚度为8.0mm、灌注SLC-9023液晶材料的液晶波片在过压驱动下的光电响应测量结果；
图6为过压驱动器的驱动方式示意图；
图7为图像分析处理处理流程图；
图8水、血红蛋白、脱氧血红蛋白吸收光谱；
图9离体人皮肤烫伤模型光谱检测图；
图10人离体皮肤烫伤模型光谱检测结果统计柱状图；
图11大鼠烫伤模型光谱检测图；
图12大鼠烫伤模型光谱检测结果统计柱状图；
图13成年猪皮肤烫伤模型光谱检测图；
图14猪皮肤烫伤模型光谱检测统计图；
图15是临床烧伤患者光谱检测结果图。
具体实施方式
为了更好的解释和说明本发明技术及其效果，以下结合附图和本发明的研究实验过程进行详细说明：
一、烧伤皮肤坏死面积及深度临床诊断系统
诊断系统主要包括光谱成像仪和计算机控制系统，其结构参见图1，其中：
1、光谱成像仪：由照明光源101、光学镜头102、滤波器103(采用液晶可调滤波器LCTF和声光可调滤光片AOTF)、CCD摄像机106、LCTF控制器105a和AOTF控制器105b和过压驱动器104组成。它们按常规的光谱成像仪的组成形式进行装配。其中各部件的性能参数可以具体选择如下：
液晶可调滤波器(LCTF)：工作波段：900nm～2500nm；光谱分辨率：5-20nm；光学透过率：5-30％；视场角：1-10°。
CCD摄像机：型号：大恒DH-SV1411GX；分辨率：1394×1040像素；帧率：15帧/秒；数据接口：千兆网口
照明光源：卤素灯光源：OCEANS美国；光谱范围：400nm～2500nm；光源照明方式：环形照明。
光学镜头：型号：Optistar；焦距：50mm(定焦镜头)，通光口径：55mm。
LCTF过压驱动控制器：t的取值范围在0-50ms之间，其电压幅度V3>V2.,V3的幅值范围在10-50V之间，然后再施加V2的驱动电压，电压幅值在0-10V之间，交变频率在0.5-5KHz(图7)。
由此组成的光谱成像仪的主要参数为，工作波段：900nm～2500nm；光谱分辨率：5-20nm；空间分辨率：10-200μm，光学透过率：5-30％；视场角：1-10°。
本发明采用液晶可调滤波器(LCTF)的结构和驱动如图2所示：
参见图2，它采用的是五级级联结构的液晶可调滤光片，其包括偏振片(1，2，3，4，5，6)、电控液晶波片(7，8，9，10，11)和固定位相延迟片(12，13，14，15)(一共五级，第一级没加固定位相延迟片)。其中偏振片(1，2，3，4，5，6)的透射偏振光方向相互平行，电控液晶波片(7，8，9，10，11)的快轴方向与偏振片(1，2，3，4，5，6)透射偏振光方向成45°角，偏振片(1，2，3，4，5，6)与电控液晶波片(7，8，9，10，11)和固定位相延迟片(12，13，14，15)相互平行排列、间隔叠放。每级结构中液晶波片由驱动控制器控制。图4右侧为加载在液晶可调滤光片每级结构中电控液晶波片上的电压驱动信号的示意图，该信号为交流过压驱动信号，电压幅值在0-20V之间，交变频率在0.5-5KHz。驱动方式为：如果液晶波片需要的驱动电压为V2，驱动时首先施加一个窄脉冲，其幅度V3>V2，然后再施加V2的驱动电压，在驱动控制器的控制下，每级液晶波片加载不同幅值的交流过压驱动信号，可实现液晶可调滤光片的快速光谱扫描。
图3是电控液晶波片(7，8，9，10，11)的结构示意图，包括玻璃基板(16，17)、ITO透明导电膜(18，19)、PI取向膜(20，21)、厚度控制透明隔垫(22，23)和液晶层24。其中ITO透明导电膜层(18，19)通过电极与驱动控制器(即多通道驱动源)相连接，为液晶层24提供电场，使液晶分子的指向发生旋转，改变电控液晶波片(7，8，9，10，11)的相位延迟，从而控制入射光的偏振态，PI取向膜(20，21)涂敷在玻璃基板(16，17)的内表面上，经过烘烤、摩擦等工艺处理后，可以诱导液晶层24中的液晶分子按照特定的方向排列，使电控液晶波片具有晶体的双折射光学特性；液晶层24是在玻璃基板之间的灌注向列相液晶材料形成的，液晶层24的厚度通过厚度控制隔垫(22，23)进行控制，折射率差Δn在0.05～0.30之间。厚度控制隔垫(22，23)可以采用玻璃纤维、玻璃微珠、或塑料微珠或photo spacer等。
为了验证过压驱动方式的有效性，将过压驱动信号加载于单级液晶波片上，测量其响应时间。其时间响应特性测量光路如图4所示，液晶波片由驱动控制器提供过压驱动信号，并被放置在两平行偏振器之间，激光器的波长为632.8nm，光电探测器采用可见光敏感器 件，具有亚微秒级光电响应速度，探测器的光电信号送入示波器记录。
图5a和图5b所示是厚度分别为4.8mm和8.0mm、灌注SLC-9023液晶材料的液晶波片在过压驱动下的光电响应测量结果。由图5a可以看出，厚度为4.8mm的液晶波片，在5V电压的常规驱动下，到达稳态的时间为25ms，采用在10V，3ms的过压驱动下，到达稳态的时间仅为3～5ms(电压在10-50V之间较为合适)；同样的，由图5b可以看出，厚度为8.0mm的液晶波片，在2V电压的常规驱动下，到达稳态的时间为450ms，采用在9.6V，7ms的冲击驱动下，到达稳态的时间仅为7ms。由实验结果可以看出，过压驱动方法可以有效提高液晶波片的光电响应时间，从而实现液晶可调滤光片的快速光谱扫描和成像。
本系统也可采用声光可调滤波器(AOTF)与液晶可调滤波器(LCTF)进行自动切换。声光可调谐滤光器(Acousto-optic tunable filter，简称AOTF)是一种声光调制器件，由单轴双折射晶体(通常采用的材料为TeO2)，粘合在单轴晶体一侧的压电换能器，以及作用于压电换能器的高频信号源组成。
AOTF的光谱扫描速极快，适合对瞬间状态的物体进行扫描。近年来，AOTF在光谱分析的图像处理、监察监测、釆集彩色信息、电光信号扫描发生器、技术等技术诸多方面获得了广泛应用。AOTF的工作原理是利用声波在各向异性介质中传播时对入射到传播介质中的光的布拉格衍射作用。当输入一定频率的射频信号时，AOTF会对入射多色光进行衍射，从中选出波长为λ的单色光。单色光的波长λ与射频频率f有一一对应的关系，只要通过电信号的调谐,即可快速选择所需要的光波波长。所被选择的光波用过CCD探测器进入图像采集系统，光谱图像被图像采集软件保存在计算机中，经过一系列的算法和数据库的提供比对，即可在计算机上显示出理想的图像。
2、计算机控制系统，内置有内置有通用模块、数据模块、光谱校正模块、光谱匹配模块、烧伤创面三维合成模块；其图像分析处理过程件图7。
通用模块，控制光源的接通和关断、光谱成像仪中各部分硬件的电源功率配给、以及本系统的各种端口和接口；
数据模块，包括烧伤坏死皮肤光谱数据库及烧伤皮肤坏死病理数据库；所述烧伤坏死皮肤光谱数据库的光谱反射率曲线波段在1100-2500nm，其光谱反射率曲线数据的来源包括光纤光谱仪和医用光谱成像仪；所述的烧伤坏死皮肤光谱数据库的光谱反射率曲线与烧伤皮肤坏死病理数据库中的皮肤烧伤深度具有一对一的匹配，即可用光谱反射率曲线代表烧伤深度。具体是利用烧伤坏死皮肤在1100-2500nm波段的光谱反射率曲线特征，来定量烧伤皮肤中的坏死信号，并将坏死信号与病理数据进行关联，使烧伤坏死皮肤光谱数据库中 的标准光谱反射率曲线与病理数据库中的皮肤烧伤深度的匹配，烧伤坏死皮肤光谱数据库中的每一条标准光谱曲线均代表一种烧伤深度。以上的烧伤坏死皮肤在1100-2500nm波段的光谱反射率曲线特征包括光谱反射率曲线的形状、曲线的平均幅值、以及曲线中波峰与波谷幅值的差值。
光谱校正模块，用于将目标区域原始光谱图像中每一个光谱图像像元对应的光谱曲线幅值除以相同条件下白板的光谱图像像元对应的光谱曲线幅值，以去除背景光及光源不均一性导致的影响，得到目标区域的光谱反射率曲线；
光谱匹配模块，用于校正后目标区域的光谱图像中每个像元的光谱反射率曲线与烧伤坏死皮肤光谱数据库的标准光谱反射率曲线进行对比分析，即用己知烧伤深度的皮肤反射光谱曲线去匹配识别目标区域的光谱反射率曲线，通过计算目标区域像元的光谱反射率曲线与各种不同烧伤深度皮肤的标准光谱反射率之间的相似度值，取相似度值最高所对应的烧伤深度作为将目标区域像元的烧伤深度，然后对目标区域每个像元进行匹配识别，得到目标区域的烧伤深度及烧伤面积。
烧伤创面三维合成模块，用于将目标区域烧伤深度和烧伤面积的数据进行三维合成与显示。
二、以下说明本发明的系统和方法的研究过程，以及烧伤坏死皮肤光谱数据库和烧伤皮肤坏死病理数据库的形成：
(一)实验
1、实验材料及动物、细胞
人尸体皮来源于西南医院烧伤研究所专用皮库
SD大鼠购自第三军医大学实验动物中心
巴马香猪购自第三军医大学实验动物中心
人皮肤成纤维细胞来自外科手术皮肤弃料原代培养
2、主要仪器
Figure PCTCN2015070456-appb-000001
Figure PCTCN2015070456-appb-000002
3、主要试剂
Figure PCTCN2015070456-appb-000003
4、主要溶液及配制
3.1DMEM培养基：
每千毫升DMEM培养基加NaHCO33g，HEPES 4g，谷胺酰胺2g，青霉素100,000U，链霉素100,000U，PH 7.2，0.22μm膜过滤除菌，4℃保存。临用前加10％FBS。
3.20.25％胰蛋白酶消化液：
0.25g胰蛋白酶加入100mlPBS(m/V)配制，-20℃贮存备用。
3.3PBS溶液：
Na2HPO 40.2g，NaH2PO 40.2g，KCl 0.02g，NaCl 0.8g，ddH2O定容至1000ml，PH 7.2，高压灭菌，4℃保存。
(二)实验方法
1、光谱数据采集条件的标定。
对本发明的近红外光纤光谱检测仪进行内参标定，结合实际测量环境标定出在体光谱生物检测的最佳距离、角度、工作时间，并消除背景因素的不利影响；
1.1利用标准白板对近红外光纤光谱检测仪进行标定，连续工作10min、30min、60min、2h、4h再次标定光强度，均值稳定。
1.2考虑到样本表面的不均一性对入射光的散射导致的光强减弱的特点，实际检测距离不宜离样本过远，否则系统误差过大。本实验采取光纤探头距离样本1-50cm进行测量。
1.3针对探测角度不同会对近红外光纤光谱检测仪检测到的光强的造成影响，我们采取检测仪与样本表面垂直的角度进行数据采集。
(三)建立人离体皮肤烧伤模型、大鼠皮肤烧伤模型及巴马香猪皮肤烧伤动物模型，用近红外光纤光谱检测仪实现实时在体光谱生物检测。
1、人离体皮肤烫伤模型建立
1.1人离体皮肤获得及处理
1)将皮库来源的人离体皮肤组织从液氮中取出；存放时间半年，规格约9×13cm2大小，平均厚度约3mm。
2)常温下浸入含PBS的无菌容器内复温；反复洗脱杂质及异物，至清亮无沉淀；
3)用无菌剪刀修整边界并去除杂物；
4)无菌PBS冲洗3-5遍至液体清亮无异味；无菌湿纱布覆盖待用。
1.2人离体皮肤烫伤模型建立
1)取修剪、清洗后人离体皮肤铺至无菌单，表皮面超上；
2)取干燥无菌纱布拭干皮肤表面水分，保证离体皮肤表面铺至平整；
3)取恒温烫伤仪，加热至90度，观察恒温稳定效果，待用；
4)取YLS-5Q恒温烫伤仪，1.5×1.5cm2大小探头，加热至92度待用。用500g重力施压作用于离体皮肤表面造成烫伤，烫伤时间分别为3s、5s、10s、15s、20s、30s、45s、60s、90s、120s、150s、180s。
1.3人离体皮肤致热烫伤模型制备及光谱数据采集
1)取近红外光纤光谱检测仪，打开光源，调试检测软件参数，用标准白板内标，去除噪音及背景曲线，调试仪器至工作状态，运行十分钟，观察工作电源稳定程度及光源强度状态，待用；
2)取标准白板，调整光纤探头对样本标准白板检测的最佳距离，固定光纤探头位置，用近红外光纤光谱检测仪检测并显示标准白板曲线，核实正常后待机；
3)取很稳加热探头，用500g重力施压作用于离体皮肤表面造成烫伤，烫伤时间分别为3s、5s、10s、15s、20s、30s、45s、60s、90s、120s。
4)取烫伤后人离体皮肤以及正常皮肤样本，置于近红外光谱观察并记录检测结果；
1.4人离体皮肤烫伤模型病理样本采集及固定
1)用无菌手术器械剪取烫伤创面人离体皮肤条约0.5×2.0cm2；
2)保证离体皮肤标本修剪平整，放入10％甲醛溶液固定；
3)取固定离体烫伤皮肤标本，常规石蜡包埋待用；
4)将标本在切片机上制成6-8微米厚度切片待用；
5)常规脱蜡至水，HE染色；
6)显微镜下观察、拍照并记录。
光谱检测结果图9和图10。
2、大鼠皮肤烫伤模型建立
2.1大鼠皮肤烫伤模型制作
1)取体重300克左右大鼠，雌雄不限；
2)将大鼠腹腔注射1％戊巴比妥钠(按每0.5ml/100g计算)；
3)麻醉后，用肥皂液浸湿背部毛发，用无菌刀片剔除；使背部皮肤裸露；
4)取恒温烫伤仪，加热至90度，观察温度恒温效果，待用；
5)取2.25cm2恒温烫头，用500g重力施压作用于大鼠背部皮肤造成烫伤，烫伤时间分别为3s、5s、10s、15s、20s、30s、45s、60s、90s、120s。
2.2大鼠皮肤烫伤模型光谱数据采集
1)取近红外光纤光谱检测仪，打开光源，调试检测软件参数，用标准白板内标，去除噪音及背景曲线，调试仪器至工作状态，运行十分钟，观察工作电源稳定程度及光源强度状态，待用；
2)取标准白板，调整光纤探头对样本标准白板检测的最佳距离，固定光纤探头位置，用近红外光纤光谱检测仪检测并显示标准白板曲线，核实后待机；
3)取烫伤后麻醉大鼠，至于固定好的光纤探头下，设定距离为1cm，分别检测烫伤创面和正常皮肤，观察并记录检测结果；
2.3大鼠皮肤烫伤模型病理样本采集及固定
1)用无菌手术器械剪取大鼠烫伤创面皮肤条约0.5×2.0cm2；
2)保证离体皮肤标本修剪平整，放入10％甲醛溶液固定；
3)取已固定好的烫伤皮肤切除标本，常规石蜡包埋待用；
4)将标本在切片机上制成6-8微米厚度切片待用；
5)常规脱蜡至水，HE染色；
6)显微镜下观察、拍照并记录。
光谱检测结果如图11和图12。
3、成年巴马香猪皮肤汽油三度烧伤及幼猪恒温仪致热二度烫伤模型建立
3.1成年猪皮肤汽油三度烧伤模型制作
1)取2年左右成年巴马香猪，雌雄不限；
2)腹腔注射4％戊巴比妥钠(按每0.5ml/1kg计算)；
3)麻醉妥善后，用肥皂液浸湿背部毛发，用无菌刀片剔除；
4)取纯工业汽油均匀涂抹至背部皮肤，待用；
5)明火点燃汽油，造成背部汽油烧伤，时间为30s。
3.2巴马香猪幼猪皮肤二度烧伤模型制作
1)取6月左右巴马香猪，雌雄不限；
2)腹腔注射4％戊巴比妥钠(按每0.5ml/1kg计算)；
3)麻醉妥善后，用肥皂液浸湿背部毛发，用无菌刀片剔除；
4)取恒温烫伤仪，加热至90度，观察温度恒温效果，待用；
5)取2.25cm2恒温烫头，用500g重力施压作用于大鼠背部皮肤造成烫伤，烫伤时间分别为3s、5s、10s、15s、20s、30s、45s、60s、90s、120s。
3.3成年猪皮肤汽油烧伤模型光谱数据采集
1)取近红外光纤光谱检测仪，打开光源，调试检测软件参数，用标准白板内标，去除噪音及背景曲线，调试仪器至工作状态，运行十分钟，观察工作电源稳定程度及光源强度状态，待用；
2)取标准白板，调整光纤探头对样本标准白板检测的最佳距离，固定光纤探头位置，用近红外光纤光谱检测仪并显示标准白板曲线，核实后待机；
3)取烧伤后麻醉成年猪，调整光纤探头位置，设定距离为1cm，分别检测汽油烧伤创面和二度烫伤及正常皮肤，观察并记录检测结果；
3.4巴马香猪背部皮肤烫伤模型病理样本采集及固定
1)用无菌手术器械剪取成年猪背部烧伤创面皮肤条约0.5×2.0cm2；
2)保证离体皮肤标本修剪平整，放入10％甲醛溶液固定；
3)取已固定好皮肤标本，常规石蜡包埋待用；
4)将标本在切片机上制成6-8微米厚度切片待用；
5)常规脱蜡至水，HE染色；显微镜下观察、拍照并记录。
光谱检测结果如图13和图14。
(四)分析各类烧伤模型的光谱生物数据，总结归纳正常皮肤与烧伤后坏死皮肤光谱检测的特征波段，特征幅值及其内在规律
1、人离体皮肤烫伤后光谱检测结果分析
1)皮肤烫伤后反射光谱曲线在1100nm～2500nm波段出现变化，随烫伤时间延长，在特定波峰处的特征幅值呈递减趋势；
2)特定波峰所在的位置为1100nm～2500nm。
2、大鼠皮肤烫伤后光谱检测结果分析
1)皮肤烫伤后反射光谱曲线在1100-2100nm波段出现变化，随烫伤时间延长，在特定波峰处的特征幅值呈递减趋势；
2)特定波峰所在的位置为1100nm～2500nm。
3、巴马香猪皮肤烫伤后光谱检测结果分析
1)皮肤烫伤后反射光谱曲线在1100-2100nm波段出现变化，随烫伤时间延长，在特定波峰处的特征幅值呈递减趋势；
2)特定波峰所在的位置为1100nm～2500nm。
4、各类烫伤模型检测结果汇总及科学规律总结
1)各种烫伤模型能够规范建立，并达到光谱检测的实际要求，确保实验数据稳定可靠。同时，检测不同的烫伤模型得到的实验结果也初步显示出一定的共性。
2)皮肤烫伤后近红外反射光谱生物特征波段为：1100nm～2500nm。
3)其信息变化特征为：随烫伤时间延长，烫伤深度增加，特征波段的特征幅值呈递减趋势。
(五)分析各类烧伤模型的病理结果，与光谱生物数据对照分析，总结归纳正常皮肤 与烧伤后坏死皮肤光谱检测结果与皮肤病损深度病理结果的内在规律。
1、对取自相同部位、相同深度、相同一般情况的各类烧伤模型正常皮肤及烧伤后病损皮肤光谱数据进行样本统计分析，确立特征波段及特异峰型稳定性，确保检测结果的高度一致及数据可靠性；
2、对以上创面采集部位病理切除标本进行常规固定，HE染色，200倍高倍镜下病理拍照，标准标尺测量皮肤损伤深度；
3、将创面光谱检测结果与金标准HE病理切片深度测量检测数据结果进行匹配，检测匹配结果稳定性，排除系统及人为误差，即得到烧伤创面光谱曲线数据与传统金标准之间的匹配结果；
4、光谱检测仪对烧伤新鲜烧伤创面实时检测数据结果即代表了相应的金标准检测出的皮肤烧伤深度，完成了相关比对匹配。
(六)对临床烧伤病例的光谱生物数据进行检测验证，总结归纳正常皮肤与烧伤后坏死皮肤光谱检测结果与皮肤病理结果的内在规律。建立临床烧伤患者不同深度病损皮肤的光谱生物数据库。病例采集流程皆符合西南医院伦理委员会相关要求并征得患者本人同意。
1)、建立了创面检测标准和数据采集策略
①采集部位：尽量多采集患者正常皮肤及不同程度病损的超光谱数据；
②采集条件：安静状态，卧位，采集时目标部位无强烈晃动及抖动；光纤探头垂直于目标区域进行采集，定标1cm；
③入选标准：以青中年患者的四肢暴露创面优先，广泛采集各类临床病例；
④记录方法：患者基本信息+实时照片资料+光谱采集数据+病理诊断信息；
⑤病理标本采集策略：可通过手术切除获得采集部位标本，常规HE染色，200倍高倍镜下病理拍照，标准标尺测量皮肤损伤深度。
2)总结归纳正常皮肤与烧伤后坏死皮肤光谱检测结果
①有效反映烧伤后病理变化光谱生物检测波段：1100nm～2500nm；
②皮肤烫伤后反射光谱曲线在1100nm～2500nm波段出现变化，随烫伤时间延长，在特定波峰处的特征幅值呈递减趋势；特定波峰所在的位置为1100nm～2500nm处；
③正常皮肤与烧伤后坏死皮肤光谱检测结果显示的生物学规律与先前对离体皮肤烧伤模型、大鼠及巴马香猪烧伤模型光谱生物学检测中所总结归纳的光谱生物规律在特征生物波段的特征幅值上随烧伤深度的增加，其体现出的光谱生物学规律大致相同；
④近红外光谱检测(1100-2500nm)可应用于对临床烧伤患者皮肤病损深度的有效检测。
3)研究分析了创面光谱数据与金标准匹配比对方法
①对相同部位、相同深度、相同一般情况的典型烧伤病例超光谱采集数据结果进行大样本统计学分析，确立特征波段及特异峰型稳定性，确保检测结果的高度一致及数据可靠性；
②对以上病例创面采集部位术中病理切除标本进行常规固定，HE染色，200倍高倍镜下病理拍照，标准标尺测量皮肤损伤深度；
③将创面检测结果与金标准HE病理切片深度测量检测数据结果进行匹配，检测匹配结果稳定性，排除系统及人为误差，即得到烧伤创面光谱曲线数据与传统金标准之间的匹配结果；
④建立临床正常皮肤、烧伤病损光谱检测数据库；不断扩大数据库数据样本量，保证检测结果稳定可靠；开发相应的数据分析软件，将光谱仪对烧伤创面的光谱实时监测结果进行数据库比对匹配，减小误差；
⑤光谱检测仪对烧伤新鲜烧伤创面实时检测数据结果即代表了相应的金标准检测出的皮肤烧伤深度，完成了相关比对匹配。
4)烧伤患者光谱生物数据库建立及相关生物数据展示，如图15。
①病例数据结果包括四部分资料：
a.基本情况资料:显示患者一般资料及病史、损伤部位详细记录等；该患者为金属铝溶液全身多处烧伤，骶部皮肤局部呈典型的炭黑色改变，质地坚硬，触之无明显疼痛；
b.光谱检测数据：按损伤部位与检测数据匹配记录并编号；
c.临床病例标准照片记录：如实反映入院时病损情况；
d.病理结果记录：病损部位术中切除送病理检验检测结果。
②光谱检测仪在近红波段(1100nm～2500nm)可实现对不同深度的皮肤烧伤患者创面进行实时检测分析；该患者长波段(1100nm～2500nm)创面检测结果与正常皮肤相比，皮肤烫伤后反射光谱曲线在1100nm～2500nm波段出现变化，随烫伤时间延长，在特定波峰处的特征幅值呈递减趋势；随深度加深烧伤中心区(粉红色角标示意部位)曲线渐趋平直，与横轴基线夹角变小；
③临床烧伤病例应用光谱仪在体、实时、无创检测结果与各种烫伤模型在可见光光谱检测不同深度创面所得到的特异性曲线形态、波段及规律方面趋势相同。
④结合切除部位病损皮肤金标准检测结果，与光谱检测结果再次匹配比对，该患者最终确认该患者腰骶部皮肤烧伤区诊断结果为：创面中央区(粉红色标识)为三度烧伤。
5)建立正常皮肤光谱生物检测数据库。设立创面检测标准和数据采集策略。病例采集流程皆符合西南医院伦理委员会相关要求并征得患者本人同意。
①采集部位：借鉴皮肤美容定标原则，光谱采集定标点分别为额头、面部、上臂、颈外侧、及锁骨内下侧；每个部位采集重复3次；
②采集条件：安静状态，卧位，采集时目标部位无强烈晃动及抖动；光纤探头垂直于目标区域进行采集，定标1cm；
③环境条件：室内温度18-22度，湿度55％-60％，统一病房内外采集光谱信息时工作环境光线条件；
④入选标准：避免毛发，无外伤、红斑、过敏、凹陷、瘢痕、痤疮、痣、癣、疣及蚊虫叮咬等异常；采集过程无无汗渍及油渍，有则清之；
⑤记录方法：患者基本信息+实时照片资料+光谱采集数据。基本信息包括：ID号，姓名、性别、年龄、体重及联系方式等。
(七)光谱成像仪临床检测功能测定
近红外光谱成像仪现场采集烫伤患者手部创面光谱图像，并通过三维彩图显示，能准确区分正常组织、烫伤区域，显示了光谱成像仪良好的烧伤部位伤情定位功能、烧伤部位伤情面积判定功能及精确的光谱生物学诊断功能，已达到了“图谱合一”的诊断效果。

Claims (11)

  1. 一种用于烧伤皮肤坏死深度和面积诊断的近红外光谱成像系统，包括光谱成像仪和计算机控制系统；其特征在于：
    所述光谱成像仪，包括光源、光学镜头、滤波器、驱动控制器和CCD像机；所述滤波器采用宽谱液晶可调滤光片(LCTF)或声光可调滤光片(AOTF)，它们获取1100-2500nm波段的光谱信号；
    所述计算机控制系统内置有通用模块、数据模块、光谱校正模块、光谱匹配模块、烧伤创面三维合成模块；
    所述系统通过所述光谱成像仪获取目标区域烧伤皮肤坏死组织的光谱图像数据，输入所述计算机控制系统，经图像分析处理，即首先通过光谱校正模块进行光谱校正，然后通过光谱匹配模块将校正后的光谱图像中每个像元对应的光谱反射率曲线与数据模块中烧伤坏死皮肤光谱数据库的标准光谱反射率曲线进行光谱匹配识别，得到目标区域的烧伤深度和烧伤面积，最后由烧伤创面三维合成模块合成目标区域的三维图像，并通过显示器显示；
    所述烧伤坏死皮肤光谱数据库中的标准光谱反射率曲线与病理数据库中的皮肤烧伤深度具有一对一的匹配关系，其是利用烧伤坏死皮肤在1100-2500nm波段的光谱反射率曲线特征，来定量烧伤皮肤中的坏死信号，并将坏死信号与病理数据进行关联，使烧伤坏死皮肤光谱数据库中的标准光谱反射率曲线与病理数据库中的皮肤烧伤深度的匹配，烧伤坏死皮肤光谱数据库中的每一条标准光谱曲线均代表一种烧伤深度。
  2. 根据权利要求1所述的用于烧伤皮肤坏死深度和面积诊断的近红外光谱成像系统，其特征在于：所述烧伤坏死皮肤在1100-2500nm波段的光谱反射率曲线特征包括光谱反射率曲线的形状、曲线的平均幅值、以及曲线中波峰与波谷幅值的差值。
  3. 根据权利要求1或2所述的近红外光谱成像系统，其特征在于：所述宽谱液晶可调滤光片(LCTF)包括液晶可调滤光片为多级级联结构，包括：一组电控液晶波片、一组固定位相延迟片和一组偏振片；所述偏振片与电控液晶波片和固定位相延迟片依次相互平行排列、间隔叠放，形成多级，但第一级中可以设置或不设置固定位相延迟片；其中所有偏振片的透射偏振光方向相互平行，所有电控液晶波片的快轴方向与所有偏振片透射偏振光方向成45°角；每级结构中电控液晶波片由过压驱动控制器控制，加载不同幅值的交流过压驱动信号。
  4. 根据权利要求3所述的近红外光谱成像系统，其特征在于：所述电控液晶波片包括中间的向列相液晶层和两侧依次对称设置的取向膜、透明导电膜和透明基板，所述向列相液晶层两侧的取向膜摩擦方向反向平行，液晶层中的液晶分子沿面排列，所述液晶层的厚度通 过在其中设置透明隔垫进行控制。
  5. 根据权利要求4所述的近红外光谱成像系统，其特征在于：所述LCTF驱动控制器采用过压驱动，对电控液晶波片加载不同幅值的交流过压驱动信号，采用过压驱动器驱动：如果液晶波片需要的驱动电压为V2，驱动时首先施加一个持续时间t很短的窄脉冲，t的取值范围在0-50ms之间，t不等于0，其电压幅度V3>V2，V3的幅值范围在10-50V之间，然后再施加V2的驱动电压，电压幅值在0-10V之间但不等于0，交变频率在0.5-5KHz。
  6. 根据权利要求4所述的近红外光谱成像系统，其特征在于：所述宽谱液晶可调滤光片(LCTF)的工作波段覆盖900nm～2500nm；光谱分辨率：5-20nm；光学透过率：5-30％；视场角：1-10°。
  7. 根据权利要求1-6之任一项所述的近红外光谱成像系统，其特征在于：所述光源提供同轴或者接近同轴的照明光源，照明光源的光谱范围覆盖900-2500nm，对目标区域进行均匀或者接近均匀的照明。
  8. 根据权利要求1-6之任一项所述的所述的近红外光谱成像系统，其特征在于所述计算机控制系统中：
    通用模块，控制光源的接通和关断、光谱成像仪中各部分硬件的电源功率配给、以及本系统的各种端口和接口；
    数据模块，包括烧伤坏死皮肤光谱数据库及烧伤皮肤坏死病理数据库；所述烧伤坏死皮肤光谱数据库的光谱反射率曲线波段在1100-2500nm，其光谱反射率曲线数据的来源包括光纤光谱仪和医用光谱成像仪；所述的烧伤坏死皮肤光谱数据库的光谱反射率曲线与烧伤皮肤坏死病理数据库中的皮肤烧伤深度具有一对一的匹配，即可用光谱反射率曲线代表烧伤深度；
    光谱校正模块，用于将目标区域原始光谱图像中每一个光谱图像像元对应的光谱曲线幅值除以相同条件下白板的光谱图像像元对应的光谱曲线幅值，以去除背景光及光源不均一性导致的影响，得到目标区域的光谱反射率曲线；
    光谱匹配模块，用于校正后目标区域的光谱图像中每个像元的光谱反射率曲线与烧伤坏死皮肤光谱数据库的标准光谱反射率曲线进行对比分析，即用己知烧伤深度的皮肤反射光谱曲线去匹配识别目标区域的光谱反射率曲线，通过计算目标区域像元的光谱反射率曲线与各种不同烧伤深度皮肤的标准光谱反射率之间的相似度值，取相似度值最高所对应的烧伤深度作为将目标区域像元的烧伤深度，然后对目标区域每个像元进行匹配识别，得到目标区域的烧伤深度及烧伤面积；
    烧伤创面三维合成模块，用于将目标区域烧伤深度和烧伤面积的数据进行三维合成与显示。
  9. 利用权利要求1-8所述的近红外光谱成像系统获得目标区域烧伤皮肤烧伤深度和烧伤面积成像信息的方法，步骤如下：
    (1)光源照明所述烧伤皮肤上的目标区域；
    (2)用LCTF或AOTF以及CCD摄像机收集所述目标区域在1100-2500nm波段的光谱图像，获取烧伤皮肤坏死组织的光谱数据和图像数据，输入计算机控制系统；
    (3)计算机控制系统经图像分析处理，即首先进行光谱校正，然后将校正后的光谱图像中每个像元对应的光谱反射率曲线与烧伤坏死皮肤光谱数据库中的标准光谱反射率曲线进行光谱匹配识别，得到目标区域的烧伤深度和烧伤面积，最后合成目标区域的三维图像，并通过显示器显示；
    所述烧伤坏死皮肤光谱数据库中的标准光谱反射率曲线与病理数据库中的皮肤烧伤深度具有一对一的匹配关系，其是利用烧伤坏死皮肤在1100-2500nm波段的光谱反射率曲线特征，来定量烧伤皮肤中的坏死信号，并将坏死信号与病理数据进行关联，使烧伤坏死皮肤光谱数据库中的标准光谱反射率曲线与病理数据库中的皮肤烧伤深度的匹配，烧伤坏死皮肤光谱数据库中的每一条标准光谱曲线均代表一种烧伤深度。
  10. 根据权利要求9所述的获得目标区域烧伤皮肤烧伤深度和烧伤面积成像信息的方法，其特征在于：所述烧伤坏死皮肤在1100-2500nm波段的光谱反射率曲线特征包括光谱反射率曲线的形状、曲线的平均幅值、以及曲线中波峰与波谷幅值的差值。
  11. 根据权利要求10所述的利用近红外光谱成像系统获得目标区域烧伤皮肤烧伤深度和烧伤面积成像信息的方法，其特征在于：所述步骤(3)的具体过程如下：
    (3.1)光谱校正：将目标区域原始光谱图像中每一个光谱图像像元对应的光谱曲线幅值除以相同条件下白板的光谱图像像元对应的光谱曲线幅值，以去除背景光及光源不均一性导致的影响，得到目标区域的光谱反射率曲线；
    (3.2)光谱匹配识别：将校正后目标区域的光谱图像中每个像元的光谱反射率曲线与烧伤坏死皮肤光谱数据库的标准光谱反射率曲线进行对比分析，即用己知烧伤深度的皮肤反射光谱曲线去匹配识别目标区域的光谱反射率曲线，通过计算目标区域像元的光谱反射率曲线与各种不同烧伤深度皮肤的标准光谱反射率之间的相似度值，取相似度值最高所对应的烧伤深度作为将目标区域像元的烧伤深度，然后对目标区域每个像元进行匹配识别，得到目标区域的烧伤深度及烧伤面积；
    (3.3)光谱图像合成与显示：将目标区域烧伤深度和烧伤面积的数据进行三维合成与显示。
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