CN101019758A - Non-invasive early cervical carcinoma detecting infrared diffused ray system and method - Google Patents

Abstract

The present invention discloses non-invasive early cervical carcinoma detecting infrared diffused ray system and method. The system includes a computer, a video CCD camera, a probe, a heterodyne measurement system, a near infrared source system, a tungsten halogen lamp, and a change-over switch. The method includes the following steps: feeding the probe into the uterus neck, checking and image displaying with video CCD camera, detecting the suspicious points with the near infrared source system, computer controlling the infrared diffused ray, obtaining the beat frequency signal and feeding to the computer, computer reconstructing, and calculating the saturation oxygen of the tissue, so as to realize the diagnosis. The present invention realizes the early detection of cervical carcinoma and the real-time detection of tumor.

Description

Infrared diffused ray non-invasive early cervical carcinoma detection system and detection method thereof

Technical field

The present invention relates to a kind of detection to early cervical carcinoma.Particularly relate to and do not need consumptive material in a kind of use or only need very a spot of consumptive material, realize the infrared diffused ray non-invasive early cervical carcinoma detection system and the detection method thereof of noinvasive, real-time lesion detection.

Background technology

Cervical cancer occupies second in global woman cancer mortality rate.In developing country, because the cervix uteri screening is not perfect, therefore, the cervical cancer incidence rate is 6 times of developed country, and its mortality rate occupies first of the woman cancer.According to the relevant expert of Beijing Friendship Hospital routine cervical lesions patients' up to ten thousand examination result is shown, the cervical cancer patient age was distributed in 34～48 years old, wherein person below 40 years old accounts for 33.3%, 40～48 years old person and accounts for 66.6%, this explanation cervical cancer serious threat to the health and lives of young and middle-aged women.

Cervix uteri is the pipeline of an about 10mm of thickness, is divided into mucous epithelium and basal layer is two-layer.The development of cervical cancer is a process slowly, and a series of forerunner's pathological changes is arranged, normally by the continuous evolution of cervix uteri atypical hyperplasia → cancer in situ (be wrapped in cervix uteri upper epidermis the inside) → early invasive carcinoma (the basad layer development of canceration) → infiltrating carcinoma.To misgrowth, arrive the infiltrative type cancer again needs 5～10 years or longer time to general cervical epithelial tissue, if canceration is diagnosed in the evolution of pathological changes and handled, just can stop its development to infiltrating carcinoma from normally.

Traditional inspection method to cervix uteri mainly contains Pap smear method and colposcope.The former major defect is: the accuracy of inspection is subject to operator's level, and high misdiagnosis rate (15～55%), person under inspection's misery, proof cycle are long; Though latter's sensitivity is higher, (＞90%), specificity low (＜50%), epithelial tissue that promptly can't distinguishing benign changes and malignant tumor.Thereby now general audit program is first plate coating checking, colposcope then, again through once in addition biopsy several times just can make a definite diagnosis, such process had both increased patient's painful and cost undoubtedly, had incured loss through delay treatment time again.The shortcoming of above diagnostic method makes more and more stronger to demand convenient, effectively aided diagnosis method clinically.

Detecting cervical cancer with optical means is a Noninvasive medical diagnostic method that grew up in recent years, it be the more important thing is and can realize optical biopsy by the metabolism situation of tissues observed body except having equipment at a low price and portability and to the advantages such as operator's horizontal dependency is low.Optics cervical cancer diagnosis research mainly adopts infrared diffused ray detection technique, fluorescent technique and optical correlation chromatography imaging technique (OCT) at present.Fluorescent technique is differentiated the degree of pathological changes by the autofluorescence of measuring ultraviolet excitation cervical tissue down, but owing to fluorescence is very faint, thereby and the absorption of fluorescence be subjected to the very big diagnostic result that influences of influence in age and menstrual period.Though OCT has higher spatial resolution, still there is the too little problem of investigation depth at present.

In recent years achievement in research shows that the infrared diffused ray detection technique has great practical application potentiality, it not only can provide the accurate diagnosis of precancerous lesion, but also the reaction information of organism optical, laser power therapy (PDT) organizer can be provided, also be a very promising application of infrared diffused ray detection technique with this technology for optical dynamic therapy provides harmless, real-time curative effect report.

Study the more successful seminar that surely belongs to professor R.R.Richards-Kortum of Texas ,Usa university leader of infrared diffused ray cervical cancer diagnostic techniques in the world, its method can reach 70% and 80% to the detection sensitivity and the specificity of normal structure and infiltrating carcinoma, but lower to the cancer in situ diagnosis, almost there is not resolving ability to organizing before the cancer.

Summary of the invention

Technical problem to be solved by this invention is, providing does not need consumptive material or only need very a spot of consumptive material in a kind of use, realizes the infrared diffused ray non-invasive early cervical carcinoma detection system and the detection method thereof of noinvasive, real-time lesion detection.

The technical solution adopted in the present invention is: a kind of infrared diffused ray non-invasive early cervical carcinoma detection system and detection method thereof.Wherein, detection system includes and is used to realize computer that the control and the data of whole detection system are read, handle, shown, the ccd video camera that is used to show common colposcopy result that links to each other with computer, also be provided with the light that is used for light source is sent and introduce in the body, and reception is by the probe of the light of tested organizer scattering and reflection; Link to each other with computer, be used to realize frequency domain heterodyne measurement system by the measurement of the faint diffused light of organizer outgoing; System links to each other with the frequency domain heterodyne measurement, and frequency domain heterodyne measurement system is provided the near infrared light origin system of light source by probe; Ccd video camera is provided the halogen tungsten lamp of light source by probe; Link to each other with halogen tungsten lamp with computer, near infrared light origin system respectively, be used to realize the permutator of checkout gear conversion between visual function and the infrared diffused ray audit function in common by computer control.

Described probe is the probe with colposcope and infrared diffused ray diagnosis dual-use function, includes: shell; One end setting is used for the light that light source sends is imported to intravital incident optical in the enclosure: an end setting is used for and will imports to external outgoing optical fiber by the light of cervix uteri surface reflectance with by the light of organizer scattering in the enclosure; Be provided with in the enclosure, be used to realize 90 ° of bendings of light beam direct of travel, realize that the light that incident optical is sent projects on the cervix uteri wall, and will collect conical mirror on the outgoing optical fiber by the light that reflects on the cervix uteri wall; Be arranged on the shell, and between optical fiber and conical mirror, be used for logical light and prevent that body fluid from entering the unthreaded hole in the probe.

Described near infrared light origin system includes: the semiconductor laser that is used to provide the required light of infrared diffused ray detection of three different wave lengths: link to each other with permutator and semiconductor laser with computer respectively, be used to realize the photoswitch to the selection of three semiconductor laser wavelengths: input links to each other with frequency domain heterodyne measurement system, outfan links to each other with three semiconductor lasers, is used for three semiconductor lasers are realized the direct current biasing simultaneously and the biasing device of rf modulations; Link to each other with the biasing device, be used to three semiconductor lasers that the direct current biasing power supply of required dc bias current is provided.

Described frequency domain heterodyne measurement system includes: link to each other with the biasing device in the near infrared light origin system, be used to three semiconductor lasers that first signal source of rf modulations is provided; By the detector of shutter detection by the infrared diffused ray of organizer 2 outgoing; Be used to detector that the power supply of running voltage is provided; Link to each other with detectors, be used to obtain by the signal of detector output and first frequency mixer and second frequency mixer of the difference frequency between the signal source; Link to each other with signal source, frequency mixer respectively, be used to first frequency mixer and second frequency mixer that reference RF signal is provided, realize the secondary signal source of heterodyne measurement; Be connected between first signal source and the secondary signal source, be used to obtain to have identical initial phase with source signal, frequency differs the offset frequency signal of Δ ω, realizes the three-mixer of the difference frequency between first signal source and secondary signal source; Link to each other with first frequency mixer, second frequency mixer and three-mixer respectively, be used for the amplifier that the signal that detector is exported is amplified; Link to each other with amplifier, be used for the wave filter of filtering output medium-high frequency composition; Link to each other with wave filter, realize by the A/D changer of analogue signal to the conversion of digital signal.

Described first signal source and secondary signal source keep synchronously, and the frequency difference between them is lower than 10KHz.

Wherein, infrared diffused ray non-invasive early cervical carcinoma detection method is to adopt infrared diffused ray non-invasive early cervical carcinoma detection system, is finished by following steps:

(1) at first the probe with colposcope and infrared diffused ray diagnosis dual-use function in the detection system is sent into cervix uteri to be looked into;

(2) person under inspection is carried out common colposcopy, the result shows with the ccd video camera in the detection system;

(3) after finding suspicious points, adopt the near infrared light origin system in the detection system to detect to suspicious points;

Describedly adopt the near infrared light origin system in the detection system to detect to suspicious points, be light source to be switched to semiconductor laser in the homologous ray by the permutator in the detection system, three semiconductor laser time-sharing works of computer control in the homologous ray, and light projected the Suspected Area by above-mentioned probe with dual-use function.

(4) the preceding shutter of near infrared light detector is opened in the computer control in the detection system, is detected the near-infrared diffuse reflection of outgoing by frequency domain heterodyne measurement system;

(5) the Δ ω difference frequency signal that after mixing and low-pass filtering, obtains of the signal that detects by detector provide that emergent light changes with respect to the phase place of incident illumination and amplitude fading information to computer;

(6) analysis software of computer passes through to adopt the method for fast contrary Monte Carlo simulation to realize the reconstruct to the optical parametric of tubulose, thin layer tissue;

(7) thus realize diagnosis according to the blood oxygen saturation of the reconstruction value computation organization body of optical parametric to suspect tissue.

Infrared diffused ray non-invasive early cervical carcinoma detection system of the present invention and detection method thereof, shortcoming such as the proof cycle that has overcome present cervical cancer detection method is long, specificity is low has realized the earlier detection of cervical cancer by utilizing tumor tissues and normal structure in different absorbent properties near infrared light; Have the probe of colposcope and infrared diffused ray diagnosis dual-use function by employing, under the preliminary examination of colposcope, tissue is done further in the body diagnosis, thereby realize noinvasive, real-time lesion detection; The present invention adopts optical detective technology, does not need consumptive material in the use or only needs very a spot of consumptive material.

Description of drawings

Fig. 1 is a non-invasive early cervical carcinoma infrared diffused ray detection system block diagram of the present invention;

Fig. 2 is the probe with colposcope and infrared diffused ray diagnosis dual-use function of the present invention;

Fig. 3 is a near infrared light origin system of the present invention;

Fig. 4 is a frequency domain heterodyne measurement of the present invention system.

Wherein:

1: probe 2: organizer

3: permutator 4: the near infrared light origin system

5: halogen tungsten lamp 6:CCD video camera

7: frequency domain heterodyne measurement system 8: computer

9: incident optical 10: outgoing optical fiber

11: shell 12: unthreaded hole

13: conical mirror 14,15,16: semiconductor laser

17: direct current biasing power supply 18: the biasing device

19: 20: the first signal sources of photoswitch

21: secondary signal source 22: power supply

23,24: 25: the first frequency mixers of detector

27: the three-mixers of 26: the second frequency mixers

28: amplifier 29: wave filter

The 30:A/D changer

The specific embodiment

Below in conjunction with embodiment infrared diffused ray non-invasive early cervical carcinoma detection system of the present invention and detection method thereof are made a detailed description.

As shown in Figure 1, infrared diffused ray non-invasive early cervical carcinoma detection system of the present invention, include and be used to realize computer 8 that the control and the data of whole detection system are read, handle, shown, the ccd video camera 6 that is used to show common colposcopy result that links to each other with computer 8, it is characterized in that, also be provided with the light that is used for light source is sent and introduce in the body, and reception is by the probe 1 of the light of tested organizer 2 scatterings and reflection; Link to each other with computer 8, be used to realize frequency domain heterodyne measurement system 7 by the measurement of the faint diffused light of organizer 2 outgoing; Link to each other with frequency domain heterodyne measurement system 7, and the near infrared light origin system 4 of light source is provided by the 1 pair of frequency domain heterodyne measurement system 7 of popping one's head in; Provide the halogen tungsten lamp 5 of light source by the 1 pair of ccd video camera 6 of popping one's head in, the model of halogen tungsten lamp 5 is J254, the model DVC-800 of ccd video camera 6; Link to each other with computer 8, near infrared light origin system 4 and halogen tungsten lamp 5 respectively, be used to realize the permutator 3 of checkout gear conversion between visual function and the infrared diffused ray audit function in common by computer 8 control, the model of permutator 3 is GTQ2Z-63.

As shown in Figure 2, described probe 1 is the probe with colposcope and infrared diffused ray diagnosis dual-use function.Include: shell 11; One end is arranged in the shell 11, is used for that the light that light source sends is imported to 9: one ends of intravital incident optical and is arranged in the shell 11, is used for importing to external outgoing optical fiber 10 by the light of cervix uteri surface reflectance with by the light of organizer 2 scatterings; Be arranged in the shell 11, be used to realize 90 ° of bendings of light beam direct of travel, realize that the light that incident optical 9 is sent projects on the cervix uteri wall, and will collect conical mirror 13 on the outgoing optical fiber 10 by the light that reflects on the cervix uteri wall; Be arranged on the shell 11, and between optical fiber and conical mirror 13, be used for logical light and prevent that body fluid from entering the unthreaded hole 12 in the probe 1.

As shown in Figure 3, described near infrared light origin system 4 includes: the semiconductor laser 14 that is used to provide the required light of infrared diffused ray detection of three different wave lengths, 15,16: respectively with computer 8 and permutator 3 and semiconductor laser 14,15,16 link to each other, be used for realizing to three semiconductor lasers 14,15, the photoswitch 19 of the selection of 16 wavelength: input links to each other with frequency domain heterodyne measurement system 7, outfan and three semiconductor lasers 14,15,16 link to each other, and are used for three semiconductor lasers 14,15,16 realize the direct current biasing simultaneously and the biasing device 18 of rf modulations; Link to each other with biasing device 18, be used to three semiconductor lasers 14,15,16 that the direct current biasing power supply 17 of required dc bias current is provided, the model of direct current biasing power supply 17 is JBP-150, and biasing device 18 adopts the product P BTC-1G of Minicircuits company.

Three wavelength of the semiconductor laser 14,15,16 of three above-mentioned different wave lengths are chosen as 760nm respectively, 790nm, and 830nm to satisfy the requirement of accurately calculating hemoglobin concentration, helps to improve the diagnosis accuracy of early-stage cancer, and model is HL7852G.Above-mentioned photoswitch is 3*1 or 3*N photoswitch, is used to realize the selection to three wavelength, and model is MSW-14-N-M6-1-FC.Two signal sources, 20,21 models are PTS250

As shown in Figure 4, described frequency domain heterodyne measurement system 7 includes: link to each other with the biasing device 18 in the near infrared light origin system 4, be used to three semiconductor lasers 14,15,16 to provide the frequency of first signal source, 20, the first signal sources 20 of rf modulations to get 100-200MHz, model is PTS250; By the detector 23,24 that shutter 31 detects by the infrared diffused ray of organizer 2 outgoing, detector 23,24 adopts APD, and model is C30737; Be used to detector 23,24 that the power supply 22 of running voltage is provided, the model of power supply 22 is JBP-1000; Link to each other corresponding with detector 23,24, being used to obtain by the signal of detector 23,24 outputs and first frequency mixer 25 of the difference frequency between the signal source 20 and the model of second frequency mixer, 26, two frequency mixers is Mini-Circuits TUF-5H; Link to each other with signal source 20, frequency mixer 25,26 respectively, be used to first frequency mixer 25 and second frequency mixer 26 that reference RF signal is provided, realize the secondary signal source 21 of heterodyne measurement, the model in secondary signal source 21 is PTS250; Be connected between first signal source 20 and the secondary signal source 21, be used to obtain to have identical initial phase with source signal, frequency differs the offset frequency signal of Δ ω, realizes the three-mixer 27 of the difference frequency in 21 in first signal source 20 and secondary signal source; Link to each other with first frequency mixer 25, second frequency mixer 26 and three-mixer 27 respectively, be used for the amplifier 28 that the signal to detector 23,24 output amplifies, the model C A3140 of amplifier; Link to each other with amplifier 28, be used for the wave filter 29 of filtering output medium-high frequency composition, the model of wave filter is BLP-1.9; Link to each other with wave filter 29, realize that the model of A/D changer is AD10242TZ by the A/D changer 30 of analogue signal to the conversion of digital signal.

Described first signal source 20 and secondary signal source 21 keep synchronously, and the frequency difference between them is lower than 10KHz.

Infrared diffused ray non-invasive early cervical carcinoma detection system of the present invention and detection method thereof, data processing method wherein is according to intensity and the phase place change information measured, and the method that adopts contrary Monte Carlo simulation is to realize the reconstruct to the optical parametric of tubulose, thin layer tissue.Blood oxygen saturation according to the reconstruction value computation organization body of optical parametric can realize the measurement of cervical tissue state and the diagnosis of early cervical carcinoma.

Infrared diffused ray non-invasive early cervical carcinoma detection method of the present invention is to adopt above-mentioned infrared diffused ray non-invasive early cervical carcinoma detection system, is finished by following steps:

(1) at first the probe 1 with colposcope and infrared diffused ray diagnosis dual-use function in the detection system is sent into cervix uteri to be looked into;

(2) person under inspection is carried out common colposcopy, the result shows with the ccd video camera in the detection system 6;

(3) after finding suspicious points, adopt the near infrared light origin system 4 in the detection system to detect to suspicious points;

Describedly adopt the near infrared light origin system 4 in the detection system to detect to suspicious points, be light source to be switched to semiconductor laser 14,15,16 in the homologous ray by the permutator in the detection system 3, three semiconductor laser 14,15,16 time-sharing works of computer 8 controls in the homologous ray, light source adopts internal modulation, promptly use high frequency electrical signal (100-200MHz) directly to modulate the driving signal of telecommunication of LD 14,15,16, and light is projected the Suspected Area by above-mentioned probe 1 with dual-use function.

(4) shutter 31 before the near infrared light detector 23,24 is opened in the computer in the detection system 8 control, is detected the near-infrared diffuse reflection of outgoing by frequency domain heterodyne measurement system 7;

(5) the Δ ω difference frequency signal that after mixing and low-pass filtering, obtains of the signal that detects by the detector 23,24 of phase sensitive provide that emergent light changes with respect to the phase place of incident illumination and amplitude fading information to computer 8:

Detector 23,24 adopts avalanche optoelectronic pipe (APD), and the mode that adopts multichannel to survey simultaneously, can avoid adopting photoswitch 19 to switch the high problem of system cost that detection optical fiber brings.

The difference frequency signal that obtains after mixing and low-pass filtering has comprised the amplitude and the phase information of former high-frequency signal, and Δ ω is lower than 10KHz, and this filtering signal is handled by the digital circuit of standard, draws DC component and the decline that exchanges amplitude.Frequency mixer 27 between signal source is sent the offset frequency signal that has identical initial phase with source signal, and this reference signal provides the initial phase information of high-frequency modulation signal for measurement, thereby realizes the measurement of Phase delay.

(6) analysis software of computer 8 passes through to adopt the method for fast contrary Monte Carlo simulation to realize the reconstruct to the optical parametric of tubulose, thin layer tissue;

Adopt fast contrary Monte Carlo simulation method to provide absorptance μ _aWith optimization scattering coefficient μ _sExact value.Absorptance μ _aAbsorbed probability of photon on the unit length, just the light energy d Φ that photon loses because of absorption in the dz of unit road in the expression organizer _aRatio, i.e. μ _a=d Φ _a/ dz.μ _s' for optimizing scattering coefficient, the virtual value μ of representation unit length isotropy scattering _s=μ _s(1-g), μ wherein _sBe scattering coefficient, the ratio that photon is scattered, i.e. a μ on the unit length in the expression organizer _s=d Φ _a/ dz, g are anisotropy factor.

Suppose that the source has form q (t)=I (1+M exp (i ω t)), g (t) (has optical parametric μ for Green's function _aAnd μ _s' the photon density distribution that solves by radiation transfer equation down in δ (t) excitation of organizer), the distribution of the photon density that then detects

Г (t) can be obtained by convolution theorem:

$\mathrm{\Γ}\left(t\right)=\underset{0}{\overset{\∞}{\∫}}q(t-t^{\′}).{g\left(t^{\′}\right)\mathrm{dt}}^{\′}=I\underset{0}{\overset{\∞}{\∫}}g\left(t^{\′}\right){\mathrm{dt}}^{\′}+\mathrm{IMexp}\left(\mathrm{i\ωt}\right)\underset{0}{\overset{\∞}{\∫}}g\left(t^{\′}\right)\exp \left({-\mathrm{i\ωt}}^{\′}\right){\mathrm{dt}}^{\′}---\left(1\right)$

We can see DC terms $\mathrm{DC}=\underset{0}{\overset{\∞}{\∫}}g\left(t^{\′}\right){\mathrm{dt}}^{\′}$ Promptly be the value of the Fourier transformation of Green's function at ω=0 place, and the interchange amplitude $\mathrm{AC}=\left|\underset{0}{\overset{\∞}{\∫}}g\left(t^{\′}\right)\exp \left({-\mathrm{i\ωt}}^{\′}\right){\mathrm{dt}}^{\′}\right|$ And Phase delay $\mathrm{\φ}=\mathrm{Arg}\left(\underset{0}{\overset{\∞}{\∫}}g\left(t^{\′}\right)\exp \left({-\mathrm{i\ωt}}^{\′}\right){\mathrm{dt}}^{\′}\right)$ The Fourier transformation of respectively corresponding Green's function is in the mould and the phase place at ω place, so the interior Monte Carlo simulation of frequency domain fully can be with the method for the description photon transmission behavior in CW or the time domain.At first follow the trail of photon that synchronization sets out outgoing distribution of photons, carry out Fourier transform then, obtain DC component, interchange amplitude and Phase delay in the corresponding frequency domain through the organizer scattering, after absorbing.

Contrary Monte Carlo simulation is based upon on the basis of Monte Carlo simulation, make the direct current that calculates by progressively revising optical parametric, exchange range value, phase value progressively approaches measured value, the optical parametric of the relative error of value of calculation and measuring amount during less than preset value is considered to the optical parametric of tested tissue body.Be the basic thought of quick Monte Carlo simulation below:

A key property of Green's function is μ _aSeparating of＞0 o'clock transmission equation can be passed through μ at an easy rate _a=0 separate obtained:

g(t，μ _a)＝g(t，μ _a＝0)exp{-μ _avt} (2)

Supposing has N ₀Individual photon incides on the organizer at synchronization, to on the border, be divided into the T group according to its path (flight time) by detected photon, every group interval is Δ t, reasonably gets Δ t, can think that then the photon in this interval has identical path.If have path l _jNumber of photons be n _j, the area of detector is Δ S, the outgoing photon density rate that defines in this path is:

$f(t_j,{\mathrm{\μ}}_a=0)=\frac{n_j}{N_0\mathrm{\Δt\ΔS}}---\left(3\right)$

Utilize (4) formula, then consider the outgoing photon density rate after the absorption characteristic:

$f(t_j,{\mathrm{\μ}}_a)=\frac{n_j\exp \left({-\mathrm{\μ}}_a{l}_j\right)}{N_0\mathrm{\Δt\ΔS}}---\left(4\right)$

In practical operation, Monte Carlo simulation is divided into two parts, in first, supposes μ _a=0, calculate the path of photon and store with given optical parametric initial value and organizer structural parameters.Second portion in program is read photon path, brings formula (4) into suitable absorptance, and the value of revising absorptance repeatedly makes error of calculation minimum.

(7) thus realize diagnosis according to the blood oxygen saturation of the reconstruction value computation organization body of optical parametric to suspect tissue.That is: according to absorptance object oxygenation status to be measured is calculated, when the oxygen saturation at tested position is lower than normal structure, think that this tested position is doubtful cancerous issue.

At the near infrared light wave band, the absorption of organizer can think that mainly the organizer absorptance under certain wavelength can be expressed as by HbO2 Oxyhemoglobin (HbO) and reduced hemoglobin (Hb) contribution:

${\mathrm{\μ}}_a^{\mathrm{\λ}}=\left({\mathrm{\ϵ}}_{\mathrm{HbO}}^{\mathrm{\λ}}\right[\mathrm{HbO}]+{\mathrm{\ϵ}}_{\mathrm{Hb}}^{\mathrm{\λ}}[\mathrm{Hb}\left]\right)+{\mathrm{\μ}}_a^{\mathrm{back}}---\left(5\right)$

Wherein ε is chromophoric extinction coefficient under known certain wavelength, μ _a ^BackRepresentative is by the absorption of other chromophore contribution.

Then can be according to the μ under three wavelength _aHemoglobin concentration and blood saturation (SO in the value computation organization body ₂), and then provide the organizer pathological parameter relevant with canceration:

$\left[\mathrm{HbO}\right]=\frac{{\mathrm{\Δ}}_{\mathrm{\μa}}^1({\mathrm{\ϵ}}_{\mathrm{Hb}}^{{\mathrm{\λ}}_3}-{\mathrm{\ϵ}}_{\mathrm{Hb}}^{{\mathrm{\λ}}_2})-{\mathrm{\Δ}}_{\mathrm{\μa}}^3({\mathrm{\ϵ}}_{\mathrm{Hb}}^{{\mathrm{\λ}}_1}-{\mathrm{\ϵ}}_{\mathrm{Hb}}^{{\mathrm{\λ}}_2})}{{\mathrm{\ϵ}}_{\mathrm{HbO}}^{{\mathrm{\λ}}_1}({\mathrm{\ϵ}}_{\mathrm{Hb}}^{{\mathrm{\λ}}_3}-{\mathrm{\ϵ}}_{\mathrm{Hb}}^{{\mathrm{\λ}}_2})-{\mathrm{\ϵ}}_{\mathrm{HbO}}^{{\mathrm{\λ}}_2}({\mathrm{\ϵ}}_{\mathrm{Hb}}^{{\mathrm{\λ}}_3}-{\mathrm{\ϵ}}_{\mathrm{Hb}}^{{\mathrm{\λ}}_1})-{\mathrm{\ϵ}}_{\mathrm{HbO}}^{{\mathrm{\λ}}_3}({\mathrm{\ϵ}}_{\mathrm{Hb}}^{{\mathrm{\λ}}_1}-{\mathrm{\ϵ}}_{\mathrm{Hb}}^{{\mathrm{\λ}}_2})}$

$\left[\mathrm{Hb}\right]=-\frac{{\mathrm{\Δ}}_{\mathrm{\μa}}^1({\mathrm{\ϵ}}_{\mathrm{HbO}}^{{\mathrm{\λ}}_3}-{\mathrm{\ϵ}}_{\mathrm{HbO}}^{{\mathrm{\λ}}_2})-{\mathrm{\Δ}}_{\mathrm{\μa}}^3({\mathrm{\ϵ}}_{\mathrm{HbO}}^{{\mathrm{\λ}}_1}-{\mathrm{\ϵ}}_{\mathrm{HbO}}^{{\mathrm{\λ}}_2})}{{\mathrm{\ϵ}}_{\mathrm{HbO}}^{{\mathrm{\λ}}_1}({\mathrm{\ϵ}}_{\mathrm{Hb}}^{{\mathrm{\λ}}_3}-{\mathrm{\ϵ}}_{\mathrm{Hb}}^{{\mathrm{\λ}}_2})-{\mathrm{\ϵ}}_{\mathrm{HbO}}^{{\mathrm{\λ}}_2}({\mathrm{\ϵ}}_{\mathrm{Hb}}^{{\mathrm{\λ}}_3}-{\mathrm{\ϵ}}_{\mathrm{Hb}}^{{\mathrm{\λ}}_1})-{\mathrm{\ϵ}}_{\mathrm{HbO}}^{{\mathrm{\λ}}_3}({\mathrm{\ϵ}}_{\mathrm{Hb}}^{{\mathrm{\λ}}_1}-{\mathrm{\ϵ}}_{\mathrm{Hb}}^{{\mathrm{\λ}}_2})}---\left(6\right)$

${\mathrm{SO}}_2=\frac{{\mathrm{\Δ}}_{\mathrm{\μa}}^1({\mathrm{\ϵ}}_{\mathrm{Hb}}^{{\mathrm{\λ}}_3}-{\mathrm{\ϵ}}_{\mathrm{Hb}}^{{\mathrm{\λ}}_2})-{\mathrm{\Δ}}_{\mathrm{\μa}}^3({\mathrm{\ϵ}}_{\mathrm{Hb}}^{{\mathrm{\λ}}_1}-{\mathrm{\ϵ}}_{\mathrm{Hb}}^{{\mathrm{\λ}}_2})}{{\mathrm{\Δ}}_{\mathrm{\μa}}^1({\mathrm{\ϵ}}^{{\mathrm{\λ}}_3}-{\mathrm{\ϵ}}^{{\mathrm{\λ}}_2})-{\mathrm{\Δ\ϵ}}_{\mathrm{\μa}}^{3\mathrm{\λ}}({\mathrm{\ϵ}}^{{\mathrm{\λ}}_3}-{\mathrm{\ϵ}}^{{\mathrm{\λ}}_2})}$

Wherein ${\mathrm{\ϵ}}^{\mathrm{\λ}}={\mathrm{\ϵ}}_{\mathrm{Hb}}^{\mathrm{\λ}}-{\mathrm{\ϵ}}_{\mathrm{HbO}}^{\mathrm{\λ}},(\mathrm{\λ}={\mathrm{\λ}}_1,{\mathrm{\λ}}_2,{\mathrm{\λ}}_3),$ ${\mathrm{\Δ}}_{\mathrm{\μa}}^1={\mathrm{\μ}}_a^{{\mathrm{\λ}}_1}-{\mathrm{\μ}}_a^{\mathrm{\λ}2},$ ${\mathrm{\Δ}}_{\mathrm{\μa}}^3={\mathrm{\μ}}_a^{{\mathrm{\λ}}_3}-{\mathrm{\μ}}_a^{\mathrm{\λ}2}.$

Claims (8)

1. infrared diffused ray non-invasive early cervical carcinoma detection system, include and be used to realize computer (8) that the control and the data of whole detection system are read, handle, shown, the ccd video camera that is used to show common colposcopy result (6) that links to each other with computer (8), it is characterized in that, also be provided with the light that is used for light source is sent and introduce in the body, and reception is by the probe (1) of the light of (2) scattering of tested organizer and reflection; Link to each other with computer (8), be used for realizing frequency domain heterodyne measurement system (7) by the measurement of the faint diffused light of organizer (2) outgoing; Link to each other with frequency domain heterodyne measurement system (7), and frequency domain heterodyne measurement system (7) is provided the near infrared light origin system (4) of light source by probe (1); Ccd video camera (6) is provided the halogen tungsten lamp (5) of light source by probe (1); Link to each other with computer (8), near infrared light origin system (4) and halogen tungsten lamp (5) respectively, be used to realize the permutator (3) of checkout gear conversion between visual function and the infrared diffused ray audit function in common by computer (8) control.

2. infrared diffused ray non-invasive early cervical carcinoma detection system according to claim 1 is characterized in that, described probe (1) is the probe with colposcope and infrared diffused ray diagnosis dual-use function.

3. infrared diffused ray non-invasive early cervical carcinoma detection system according to claim 1 is characterized in that, described probe (1) includes: shell (11); One end is arranged in the shell (11), be used for the light that light source sends is imported to intravital incident optical (9): an end is arranged in the shell (11), is used for importing to external outgoing optical fiber (10) by the light of cervix uteri surface reflectance with by the light of organizer (2) scattering; Be arranged in the shell (11), be used to realize 90 ° of bendings of light beam direct of travel, realize that the light that incident optical (9) is sent projects on the cervix uteri wall, and will collect conical mirror (13) on the outgoing optical fiber (10) by the light that reflects on the cervix uteri wall; Be arranged on the shell (11), and be positioned between optical fiber and the conical mirror (13), be used for logical light and prevent that body fluid from entering the unthreaded hole (12) in the probe (1).

4. infrared diffused ray non-invasive early cervical carcinoma detection system according to claim 1, it is characterized in that, described near infrared light origin system (4) includes: the semiconductor laser (14 that is used to provide the required light of infrared diffused ray detection of three different wave lengths, 15,16): respectively with computer (8) and permutator (3) and semiconductor laser (14,15,16) link to each other, be used for realizing to three semiconductor lasers (14,15,16) photoswitch of the selection of wavelength (19): input links to each other with frequency domain heterodyne measurement system (7), outfan and three semiconductor lasers (14,15,16) link to each other, be used for three semiconductor lasers (14,15,16) realize the direct current biasing simultaneously and the biasing device (18) of rf modulations; Link to each other with biasing device (18), be used to three semiconductor lasers (14,15,16) that the direct current biasing power supply (17) of required dc bias current is provided.

5. infrared diffused ray non-invasive early cervical carcinoma detection system according to claim 1, it is characterized in that, described frequency domain heterodyne measurement system (7) includes: link to each other with the biasing device (18) in the near infrared light origin system (4), be used to three semiconductor lasers (14,15,16) that first signal source (20) of rf modulations is provided; By the detector (23,24) of shutter (31) detection by the infrared diffused ray of organizer 2 outgoing; Be used to detector (23,24) that the power supply (22) of running voltage is provided; Link to each other corresponding, be used to obtain by the signal of detector (23,24) output and first frequency mixer (25) and second frequency mixer (26) of the difference frequency between the signal source (20) with detector (23,24); Link to each other with signal source (20), frequency mixer (25,26) respectively, be used to first frequency mixer (25) and second frequency mixer (26) that reference RF signal is provided, realize the secondary signal source (21) of heterodyne measurement; Be connected between first signal source (20) and secondary signal source (21), be used to obtain to have identical initial phase with source signal, frequency differs the offset frequency signal of Δ ω, realizes the three-mixer (27) of the difference frequency between first signal source (20) and secondary signal source (21); Link to each other with first frequency mixer (25), second frequency mixer (26) and three-mixer (27) respectively, be used for the amplifier (28) that the signal that detector (23,24) is exported is amplified; Link to each other with amplifier (28), be used for the wave filter (29) of filtering output medium-high frequency composition; Link to each other with wave filter (29), realize by the A/D changer (30) of analogue signal to the conversion of digital signal.

6. infrared diffused ray non-invasive early cervical carcinoma detection system according to claim 1 is characterized in that, described first signal source (20) and secondary signal source (21) keep synchronously, and the frequency difference between them is lower than 10KHz.

7. an infrared diffused ray non-invasive early cervical carcinoma detection method is characterized in that, adopts infrared diffused ray non-invasive early cervical carcinoma detection system, is finished by following steps:

(1) at first the probe (1) with colposcope and infrared diffused ray diagnosis dual-use function in the detection system is sent into cervix uteri to be looked into;

(2) person under inspection is carried out common colposcopy, the result shows with the ccd video camera (6) in the detection system;

(3) after finding suspicious points, adopt the near infrared light origin system (4) in the detection system to detect to suspicious points;

(4) the preceding shutter (31) of near infrared light detector (23,24) is opened in the computer in the detection system (8) control, is detected the near-infrared diffuse reflection of outgoing by frequency domain heterodyne measurement system (7);

(5) the Δ ω difference frequency signal that after mixing and low-pass filtering, obtains of the signal that detects by detector (23,24) provide that emergent light changes with respect to the phase place of incident illumination and amplitude fading information to computer (8);

(6) analysis software of computer (8) passes through to adopt the method for fast contrary Monte Carlo simulation to realize the reconstruct to the optical parametric of tubulose, thin layer tissue;

(7) thus realize diagnosis according to the blood oxygen saturation of the reconstruction value computation organization body of optical parametric to suspect tissue.

8. infrared diffused ray non-invasive early cervical carcinoma detection method according to claim 7, it is characterized in that, describedly adopt the near infrared light origin system (4) in the detection system to detect to suspicious points, be light source to be switched to semiconductor laser (14,15,16) in the homologous ray by the permutator in the detection system (3), computer (8) in the homologous ray is controlled three semiconductor lasers (14,15,16) time-sharing work, and light is projected the Suspected Area by above-mentioned probe (1) with dual-use function.

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