CN103385695B - The method of multi-wavelength liver reserve function detector and detection ICG concentration - Google Patents

Abstract

The present invention relates to a kind of method of multi-wavelength liver reserve function detector and detection ICG concentration, comprise embedded microprocessor, light source driving circuit, multi-wave length illuminating light source, photodetector, signal processing circuit, liquid crystal display, data storage, printer and the outside PC that is connected or browser, it is characterized in that: embedded microprocessor is connected with light source driving circuit, signal processing circuit, liquid crystal display, SD card, printer, PC or browser respectively; Multi-wave length illuminating light source is connected with light source driving circuit; Photodetector is connected with signal processing circuit.Multi-wavelength liver reserve function detector provided by the invention, pulse process medium-sized artery, vein and tissue change and scattering can be counted on the impact of signal simultaneously, obtain ICG concentration value, ICG curve, artery and vein blood oxygen saturation and other liver function parameter, improve the certainty of measurement of ICG concentration etc., ensure that this detector has good shock resistance.<!--1-->

Description

The method of multi-wavelength liver reserve function detector and detection ICG concentration

Technical field

The present invention relates to medical treatment detection device, particularly relate to a kind of method of multi-wavelength liver reserve function detector and detection ICG concentration.

Background technology

Liver is the hinge of human metabolism, to the judgement of liver function impairment degree and reserve function, is the focus that people pay close attention to always.To the accurate evaluation of liver function impairment degree and reserve function before liver surgery, very important to the clinical anesthesia safety of liver cirrhosis patient.Preoperative correct assessment liver reserve function, rationally grasping in art and cut liver amount, is the important measures avoiding postoperative liver failure.

The mensuration of liver reserve function is the research topic of the important of liver surgery in recent years and hot topic, the many effective appraisal procedure of scholars's research and development, such as: the excretion test of indocyanine-green blood collection method, aminoacid clearance test, lignocaine clearance test, Keto body ratio in arterial blood measures, oral glucose tolerance test etc., the pigment dilution method that wherein indocyanine-green excretion test uses is proved to be able to reflect patient's hepatic functional reserve objectively, has certain effect to the selection of surgical method, the determination of opportunity of operation.But these technology are repeatedly drawn blood after mostly needing administration, exist patient trauma comparatively large, method is complicated, the problem of time-consuming length.How to find a kind of noinvasive, evaluate the method for liver function just one of important directions becoming Genneral Surgery accurately.

The principle of pulse oximetry measuring instrument is used for pigment By Dilution, and the dual wavelength pulse dye density method that development is formed can the concentration of indocyanine-green in noinvasive METHOD FOR CONTINUOUS DETERMINATION arterial blood, and method is fast and convenient, is suitable for clinical monitoring and uses.By measuring the absorbance ratio at 805nm/900nm two wavelength places, utilize pulse spectrophotography just can obtain the concentration proportion of dyestuff indocyanine-green and Hb, the Hb concentration recorded by peripheral blood substitutes into the concentration that just can obtain dyestuff indocyanine-green.This method has Wicresoft, the advantage such as easy, real-time, quick, and the product that current Jin You Nihon Kohden Corporation utilizes the method to be formed applies to market.

Existing dual wavelength pulse dye density method only considers the absorbance change that transmission absorption that arterial pulse causes causes; Also there is researcher to consider the change of arterial oxygen saturation, regard variable instead of constant as by arterial oxygen saturation, propose three wavelength method eliminating arterial oxygen saturation impact.But, owing to all only considering arterial pulse change, do not consider that venous pulsation changes and organizes the impact of pulsatile change, do not consider the impact of scattering yet, therefore cause its reliability and certainty of measurement not, measure not accurate enough.

Light, in the transmitting procedure of tissue, has stronger scattering effect.

Therefore arterial pulse changes to provide one not only to consider, also considers venous pulsation change and organizes the impact of pulsatile change, in also considering to detect scattering on the detector of the impact of signal and detection method particularly important.

Summary of the invention

Arterial pulse changes to the object of the present invention is to provide one not only to consider, also considers that venous pulsation changes and organizes the impact of pulsatile change, also considers the impact of scattering, record simultaneously: S _a, S _v, V, and C _dfive independently unknown quantitys, can improve the precision of detection and the multi-wavelength liver reserve function detector of reliability and detect the method for ICG concentration.

The object of the invention is to be achieved through the following technical solutions:

A kind of multi-wavelength liver reserve function detector, embedded microprocessor is connected with light source driving circuit, signal processing circuit, liquid crystal display, data storage or SD card, printer, PC or browser respectively; Multi-wave length illuminating light source is connected with light source driving circuit; Photodetector is connected with signal processing circuit;

Embedded microprocessor controls light source driving circuit, pulse train circuit for generating in light source driving circuit inputs to decoder by square-wave generator clocking, carry out frequency division by decoder and export 6 tunnel timesharing rectangular signals, drive the LED of 6 different wave lengths luminous respectively by drive circuit again, photoelectric detector through tissue transillumination and convert the signal of telecommunication to, signal processing circuit by the signal of telecommunication first through one-level processing and amplifying, again the signal of telecommunication of different wave length is separated, then the A/D converter in embedded microprocessor is input to after carrying out filtering and secondary processing and amplifying respectively, A/D converter converts the signal of telecommunication of different wave length to digital signal, embedded microprocessor obtains ICG concentration value with process by analysis according to the signal of each wavelength, ICG curve, arterial oxygen saturation, Svo2 and other liver function parameter, Simultaneous Transmission of Data is to display, printer, PC/browser, and be stored in data storage or SD card.

Detect the method for ICG concentration with multi-wavelength liver reserve function detector, when after intravenous injection ICG, use the light of 6 different wave lengths by tissue, detect the light intensity signal of 6 different wave length emergent lights respectively, wherein arbitrary two kinds of different wave length λ _iand λ _jthe ratio of pulsating quantity of transillumination be:

${\mathrm{\&Phi;}}_{\mathrm{ij}}=\frac{{\mathrm{\&Delta;I}}_i/I_i}{{\mathrm{\&Delta;I}}_j/I_j}\&ap;\frac{{\mathrm{\&Delta;A}}_i}{{\mathrm{\&Delta;A}}_j}=\frac{\sqrt{({\mathrm{\&epsiv;}}_a^i+{\mathrm{\&epsiv;}}_d^{i}Z)({\mathrm{\&epsiv;}}_a^i+{\mathrm{\&epsiv;}}_d^{i}Z+F)}+\sqrt{({\mathrm{\&epsiv;}}_V^i+{\mathrm{\&epsiv;}}_d^{i}Z)({\mathrm{\&epsiv;}}_V^i+{\mathrm{\&epsiv;}}_d^{i}Z+F)}V+E_x^i}{\sqrt{({\mathrm{\&epsiv;}}_a^j+{\mathrm{\&epsiv;}}_d^{j}Z)({\mathrm{\&epsiv;}}_a^j+{\mathrm{\&epsiv;}}_d^{j}Z+F)}+\sqrt{({\mathrm{\&epsiv;}}_V^j+{\mathrm{\&epsiv;}}_d^{j}Z)({\mathrm{\&epsiv;}}_V^j+{\mathrm{\&epsiv;}}_d^{j}Z+F)}V+E_x^i}$

6 different wave lengths have 5 independently light intensity ratio equations, are solved: S by 5 independent equations _a, S _v, V, and C _dfive independently unknown quantitys;

In formula: i and j represents the sequence number of any two different wave lengths in 6 wavelength respectively,

Φ _ijtwo kinds of wavelength X _iand λ _jthe ratio of pulsating quantity of transillumination ,

the change ratio of two kinds of wavelength absorbance,

ε _a, ε _vand ε _drepresent that wavelength is λ respectively _ior λ _jtime arterial blood specific absorbance, venous blood specific absorbance and light by the specific absorbance of ICG,

F is light scattering coefficient,

Z=C _d/ C _hb, C _hband C _dthe concentration of hemoglobin and ICG respectively,

, Δ D _awith Δ D _varterial blood thickness changes values and venous blood thickness changes values respectively,

with be and hemoglobin concentration C _hband tissue, the relevant variable of tremulous pulse varied in thickness, , A _iand B _iconstant, can be by represent, namely only have an independent variable;

ε _a=S _aε _o+ (1-S _a) ε _r, ε _v=S _vε _o+ (1-S _v) ε _r, S _aand S _vrepresent arterial oxygen saturation and Svo2 respectively.

The present invention uses the light of 6 different wave lengths by tissue, detects the light intensity signal of 6 different wave length emergent lights respectively, utilizes 5 independently light intensity ratio equations, solve: S simultaneously _a, S _v, V, and C _dfive independently unknown quantity, wherein ICG concentration C _dnot by the impact of other unknown quantity.

The invention has the beneficial effects as follows: adopt the present invention not only to consider that arterial pulse changes, also consider that venous pulsation changes and organizes the impact of pulsatile change, also consider the impact of scattering, the value of the concentration value of ICG, ICG curve, arterial oxygen saturation and Svo2 can be drawn in real time, accurately, also can obtain other liver function parameter simultaneously, precision and the reliability of detection can be improved.

Accompanying drawing explanation

Fig. 1 is a kind of structured flowchart of multi-wavelength liver reserve function detector;

Fig. 2 is light source driving circuit structure chart;

Fig. 3 is pulse train circuit for generating structure chart;

Fig. 4 is multi-wave length illuminating light-source structure schematic diagram;

Fig. 5 is signal processing circuit structure block diagram;

Fig. 6 is multi-wavelength liver reserve function detector software program flow chart.

Detailed description of the invention

In order to make object of the present invention, technical scheme and advantage clearly understand, below in conjunction with drawings and Examples, the present invention is further elaborated.

In embodiments of the present invention, by a kind of multi-wave length illuminating pattern, achieve liver reserve function detection method and the device thereof of considering that arterial pulse changes, venous pulsation changes, organizes pulsatile change and diffuse transmission influence simultaneously.

As shown in Figure 1, a kind of multi-wavelength liver reserve function detector is made up of embedded microprocessor, light source driving circuit, multi-wave length illuminating light source, photodetector, signal processing circuit, liquid crystal display, data storage or SD card, printer and the outside PC that is connected or browser.Embedded microprocessor is key control unit.

Embedded microprocessor is connected with light source driving circuit, signal processing circuit, liquid crystal display, data storage or SD card, printer, PC or browser respectively; Multi-wave length illuminating light source is connected with light source driving circuit; Photodetector is connected with signal processing circuit.

With reference to Fig. 2, light source driving circuit is made up of pulse train circuit for generating and the drive circuit that is attached thereto.

Pulse train circuit for generating shown in Fig. 3 inputs to decoder by square-wave generator clocking, carry out frequency division by decoder and export generation 6 tunnel timesharing sequence signal, this 6 road sequence signal, by inputing to drive circuit, drives the LED timesharing of 6 wavelength in the multi-wave length illuminating light source shown in Fig. 4 luminous.

Multi-wave length illuminating light source shown in Fig. 4 is made up of the LED of 6 different wave lengths, and the wave-length coverage of 6 LED is respectively: λ ₁=650nm-680nm, λ ₂=700nm-730nm, λ ₃=750nm-780nm, λ ₄=790nm-810nm, λ ₅=900nm-920nm, λ ₆=930nm-950nm.

With reference to Fig. 5, the one-level amplifying circuit of signal processing circuit connects multichannel filtering circuit respectively through demultiplexing circuit, and multichannel filtering circuit connects multichannel second amplifying circuit respectively.

Photoelectric detector shown in Fig. 1 through tissue transillumination and convert the signal of telecommunication to, signal processing circuit shown in Fig. 5 by the signal of telecommunication first through the process of one-level amplifying circuit, again the signal of telecommunication of different wave length is carried out Signal separator through demultiplexing circuit, then carry out through filter circuit and second amplifying circuit the A/D converter that is input to after filtering and secondary processing and amplifying in embedded microprocessor respectively, A/D converter converts the signal of telecommunication of different wave length to digital signal, embedded microprocessor obtains the concentration value of ICG with process by analysis according to the signal of each wavelength, ICG curve, the value of arterial oxygen saturation and Svo2, also can obtain other liver function parameter simultaneously, data can transfer to display simultaneously, printer, PC/browser is also stored in data storage or SD card.

With reference to Fig. 6, multi-wavelength liver reserve function detector detects the method for ICG concentration, and detecting step is:

1. start, start embedded system, enter liver reserve function and detect main interface;

2. set up patient files, 6 wavelength detecting parameters are set;

3. 6 wavelength image data, gather and terminate;

4. date processing, display parameters and curve, print examining report, data are saved to data base;

5. whether terminate or set up next patient files;

6. terminate.

The present invention uses the light of 6 different wave lengths to pass through tissue, not only consider that arterial pulse changes, also consider that venous pulsation changes and organizes the impact of pulsatile change, also consider the impact of scattering simultaneously, when after intravenous injection ICG, use the light of 6 different wave lengths by tissue, detect the light intensity signal of 6 different wave length emergent lights respectively, wherein arbitrary two kinds of different wave length λ _iand λ _jthe ratio of pulsating quantity of transillumination be:

${\mathrm{\&Phi;}}_{\mathrm{ij}}=\frac{{\mathrm{\&Delta;I}}_i/I_i}{{\mathrm{\&Delta;I}}_j/I_j}\&ap;\frac{{\mathrm{\&Delta;A}}_i}{{\mathrm{\&Delta;A}}_j}$

$=\frac{\sqrt{({\mathrm{\&epsiv;}}_a^i+{\mathrm{\&epsiv;}}_d^i{C}_d/C_{\mathrm{Hb}})({\mathrm{\&epsiv;}}_a^i+{\mathrm{\&epsiv;}}_d^i{C}_d/C_{\mathrm{Hb}}+F)}{C}_{\mathrm{Hb}}{\mathrm{\&Delta;D}}_a+\sqrt{({\mathrm{\&epsiv;}}_v^i+{\mathrm{\&epsiv;}}_d^i{C}_d/C_{\mathrm{Hb}})({\mathrm{\&epsiv;}}_v^i+{\mathrm{\&epsiv;}}_d^i{C}_d/C_{\mathrm{Hb}}+F)}{C}_{\mathrm{Hb}}{\mathrm{\&Delta;D}}_v+{\mathrm{\&Delta;A}}_s^i}{\sqrt{({\mathrm{\&epsiv;}}_a^j+{\mathrm{\&epsiv;}}_d^j{C}_d/C_{\mathrm{Hb}})({\mathrm{\&epsiv;}}_a^j+{\mathrm{\&epsiv;}}_d^j{C}_d/C_{\mathrm{Hb}}+F)}{C}_{\mathrm{Hb}}{\mathrm{\&Delta;D}}_a+\sqrt{({\mathrm{\&epsiv;}}_v^j+{\mathrm{\&epsiv;}}_d^j{C}_d/C_{\mathrm{Hb}})({\mathrm{\&epsiv;}}_v^j+{\mathrm{\&epsiv;}}_d^j{C}_d/C_{\mathrm{Hb}}+F)}{C}_{\mathrm{Hb}}{\mathrm{\&Delta;D}}_v+{\mathrm{\&Delta;A}}_s^j}$

$=\frac{\sqrt{({\mathrm{\&epsiv;}}_a^i+{\mathrm{\&epsiv;}}_d^{i}Z)({\mathrm{\&epsiv;}}_a^i+{\mathrm{\&epsiv;}}_d^{i}Z+F)}+\sqrt{({\mathrm{\&epsiv;}}_v^i+{\mathrm{\&epsiv;}}_d^{i}Z)({\mathrm{\&epsiv;}}_v^i+{\mathrm{\&epsiv;}}_d^{i}Z+F)V}+E_x^i}{\sqrt{({\mathrm{\&epsiv;}}_a^j+{\mathrm{\&epsiv;}}_d^{j}Z)({\mathrm{\&epsiv;}}_a^j+{\mathrm{\&epsiv;}}_d^{j}Z+F)}+\sqrt{({\mathrm{\&epsiv;}}_v^j+{\mathrm{\&epsiv;}}_d^{j}Z)({\mathrm{\&epsiv;}}_v^j+{\mathrm{\&epsiv;}}_d^{j}Z+F)}V+E_x^j}$

6 different wave lengths have 5 independently light intensity ratio equations, are solved: S by 5 independent equations _a, S _v, V, and C _dfive independently unknown quantitys.

Multi-wavelength liver reserve function detection method is specially:

The concentration that blood oxygen saturation is defined as Oxygenated blood Lactoferrin accounts for the ratio of total hemoglobin concentration, and what can be similar to represents with formula (1):

${\mathrm{SO}}_2=\frac{C_{O_2\mathrm{Hb}}}{C_{O_2\mathrm{Hb}}+C_{\mathrm{RHb}}}\&times;100\%---\left(1\right)$

In formula (1), point subrepresentation be the concentration of Oxygenated blood Lactoferrin in human body, what denominator represented is the total concentration containing oxygen and deoxidation two kinds of hemoglobin in human body, due in hemoglobin concentration, containing oxygen and deoxidation two kinds of hemoglobin concentration with account for the overwhelming majority, generally by both concentration be approximately equal to total hemoglobin concentration when therefore calculating.On clinical position, blood oxygen saturation is usually as the foundation whether oxygen supply passing judgment on patient respiratory and circulation is not enough.

Light transmittance T represents intensity I and the incident intensity I of transillumination _oratio, as shown in Equation (2).Light transmittance is larger, and the absorption of exponent confrontation incident illumination is fewer; On the contrary, light transmittance is less, then the absorption of exponent confrontation incident illumination is more.

$T=\frac{I}{I_o}---\left(2\right)$

The negative logarithm of light transmittance is called absorbance, represents with A, sees formula (3).Absorbance is larger, and the absorption of exponent confrontation incident illumination is more.

$A=-\mathrm{lgT}=\lg \frac{I_o}{I}---\left(3\right)$

Material is not only proportional with the thickness of material at the absorbance of certain single wavelength, and the concentration of solution also direct proportionality, and this law is called Lambert-Beer law.Lambert-Beer law the applicant is utilized to select the absorbance of given wavelength to obtain content of material and solution concentration easily by measuring.

Lambert-Beer law can represent with formula (4), and wherein, ε is molar absorption coefficient, and C is the concentration of solution, and D is the thickness of material.Can see from formula, the thickness of absorbance and material and the concentration of solution all direct proportionality.

$A=\lg \frac{I_o}{I}=\mathrm{\&epsiv;CD}---\left(4\right)$

Lambert-Beer law has three prerequisites as follows:

(1) incident illumination is monochromatic light;

(2) do not interact between each material of absorption process;

(3) effect of radiation and material is only limitted to absorption process, does not have scattering, fluorescence and photochemistry phenomenon.

Pulse spectrophotography is based upon on the basis of Lambert-Beer law.When a monochromic beam is through tissue, due to pulse effect, it is simultaneously by ripple component material and stationary components material absorbing, forms change in time and the transillumination not changing two kinds of component substances in time respectively.A current pulse cycle terminates, and when a rear pulse cycle does not also arrive, transillumination is the strongest, and reach peak value, light intensity is at this moment denoted as direct current light intensity I; Owing to also having the change of venous blood thickness and tissue thickness in pulse process except arterial blood varied in thickness, the at this moment change of transmitted light intensity is considered to be irradiated into that these varied in thickness materials cause; And when pulse volume reaches maximum, the transmitted light intensity that these change materials cause is the most weak.Transillumination time to time change in pulse process, the direct current light intensity transmitted light intensity deducted in pulse process obtains exchanging light intensity Δ I.

Because pulsation causes substance thickness changes delta D to cause being changed to of absorbance:

$\mathrm{\&Delta;A}=\lg \frac{I_0}{I-\mathrm{\&Delta;I}}-\lg \frac{I_0}{I}=-\lg \frac{I-\mathrm{\&Delta;I}}{I}=\mathrm{\&epsiv;C\&Delta;D}---\left(5\right)$

Because of in transillumination, the interchange light intensity Δ I that pulse causes will much smaller than direct current light intensity I, so:

$\mathrm{\&Delta;A}=\mathrm{\&epsiv;C\&Delta;}=-\mathrm{lgD}\frac{I-\mathrm{\&Delta;I}}{I}=-\lg (1-\frac{\mathrm{\&Delta;I}}{I})\&ap;\frac{\mathrm{\&Delta;I}}{I}---\left(6\right)$

In pulse process, the change of thickness is based on arterial blood varied in thickness, and the change of venous blood thickness and tissue thickness is relatively little.If only consider arterial blood varied in thickness and ignore the change of venous blood thickness and tissue thickness, so:

$\mathrm{\&Delta;A}={\mathrm{\&epsiv;}}_a{C}_{\mathrm{Hb}}{\mathrm{\&Delta;D}}_a\&ap;\frac{\mathrm{\&Delta;I}}{I}---\left(7\right)$

Wherein, ε _afor arterial blood specific absorbance, C _hbfor the concentration of hemoglobin, Δ D _afor arterial blood thickness changes values, as shown in Equation (8):

${\mathrm{\&epsiv;}}_a=S_a{\mathrm{\&epsiv;}}_o+(1-S_a){\mathrm{\&epsiv;}}_R---\left(8\right)$

Wherein, S _afor arterial oxygen saturation, ε _oand ε _rrepresent Oxygenated blood Lactoferrin O respectively ₂hb and deoxyhemoglobin RHb is at the specific absorbance of monochromatic af at wavelength lambda, and this formula is approximate on the basis that have ignored a small amount of Carbon monoxide haemoglobin contained in hemoglobin and metahemoglobin obtaining.

Therefore, when there being a HONGGUANG λ respectively ₁with an infrared light λ ₂, the pulsating quantity of absorbance is respectively Δ A ₁with Δ A ₂, the ratio of the pulsating quantity of the transillumination of two kinds of wavelength is as shown in Equation (9):

${\mathrm{\&Phi;}}_{12}=\frac{{\mathrm{\&Delta;I}}_1/I_1}{{\mathrm{\&Delta;I}}_2/I_2}\&ap;\frac{{\mathrm{\&Delta;A}}_1}{{\mathrm{\&Delta;A}}_2}=\frac{{\mathrm{\&epsiv;}}_a^1}{{\mathrm{\&epsiv;}}_a^2}=\frac{S_a{\mathrm{\&epsiv;}}_o^1+(1-S_a){\mathrm{\&epsiv;}}_R^1}{S_a{\mathrm{\&epsiv;}}_o^2+(1-S_a){\mathrm{\&epsiv;}}_R^2}---\left(9\right)$

Wherein arterial oxygen saturation is as shown in Equation (10):

$S_a=\frac{{\mathrm{\&Phi;\&epsiv;}}_R^2-{\mathrm{\&epsiv;}}_R^1}{\mathrm{\&Phi;}({\mathrm{\&epsiv;}}_R^2-{\mathrm{\&epsiv;}}_o^2)+{\mathrm{\&epsiv;}}_o^1-{\mathrm{\&epsiv;}}_R^1}---\left(10\right)$

In practical operation, infrared light λ ₂general selection wavelength makes with approximately equal, so formula (10) can be simplified to formula (11):

$S_a=a+\mathrm{b\&Phi;}---\left(11\right)$

If in pulse process, count arterial blood varied in thickness, venous blood varied in thickness and tissue thickness's change simultaneously, so:

$\mathrm{\&Delta;A}={\mathrm{\&epsiv;}}_a{C}_{\mathrm{Hb}}{\mathrm{\&Delta;D}}_a+{\mathrm{\&epsiv;}}_v{C}_{\mathrm{Hb}}{\mathrm{\&Delta;D}}_v+Z_t{\mathrm{\&Delta;D}}_t\&ap;\frac{\mathrm{\&Delta;I}}{I}---\left(12\right)$

Wherein: ε _afor arterial blood specific absorbance, Δ D _afor arterial blood thickness changes values, ε _vfor venous blood specific absorbance, Δ D _vfor venous blood thickness changes values, Δ D _tfor tissue thickness's changes values, Z _tit is a constant almost had nothing to do with incident wavelength.

The prerequisite that Lambert-Beer law is set up is that light only has absorption process in material, does not have scattering process.And in fact HONGGUANG and infrared light have stronger scattering phenomenon in organism or human body, ignore scattering process and can cause larger error.According to Schuster principle, introduce Scattering Factors, F is light scattering coefficient, and it is all a constant very on a large scale in hemoglobin concentration, so:

$\mathrm{\&Delta;A}=\sqrt{{\mathrm{\&epsiv;}}_a({\mathrm{\&epsiv;}}_a+F)}{C}_{\mathrm{Hb}}{\mathrm{\&Delta;D}}_a+\sqrt{{\mathrm{\&epsiv;}}_v({\mathrm{\&epsiv;}}_v+F)}{C}_{\mathrm{Hb}}{\mathrm{\&Delta;D}}_v+{\mathrm{\&Delta;A}}_s\&ap;\frac{\mathrm{\&Delta;I}}{I}---\left(13\right)$

Wherein: ε _a=S _aε _o+ (1-S _a) ε _r, ε _v=S _vε _o+ (1-S _v) ε _r, S _aand S _vrepresent arterial oxygen saturation and Svo2 respectively.Δ A _s=Z _aΔ D _a+ Z _tΔ D _t, Z here _ait is a constant almost had nothing to do with incident wavelength.

Two kinds of wavelength X _iand λ _jthe ratio of pulsating quantity of transillumination be:

${\mathrm{\&Phi;}}_{\mathrm{ij}}=\frac{{\mathrm{\&Delta;I}}_i/I_i}{{\mathrm{\&Delta;I}}_j/I_j}\&ap;\frac{{\mathrm{\&Delta;A}}_i}{{\mathrm{\&Delta;A}}_j}=\frac{\sqrt{{\mathrm{\&epsiv;}}_a^i({\mathrm{\&epsiv;}}_a^i+F)}{C}_{\mathrm{Hb}}{\mathrm{\&Delta;D}}_a+\sqrt{{\mathrm{\&epsiv;}}_v^i({\mathrm{\&epsiv;}}_v^i+F)}{C}_{\mathrm{Hb}}{\mathrm{\&Delta;D}}_v+{\mathrm{\&Delta;A}}_s^i}{\sqrt{{\mathrm{\&epsiv;}}_a^j({\mathrm{\&epsiv;}}_a^j+F)}{C}_{\mathrm{Hb}}{\mathrm{\&Delta;D}}_a+\sqrt{{\mathrm{\&epsiv;}}_v^j({\mathrm{\&epsiv;}}_v^j+F)}{C}_{\mathrm{Hb}}{\mathrm{\&Delta;D}}_v+A_s^j}$

$=\frac{\sqrt{{\mathrm{\&epsiv;}}_a^i({\mathrm{\&epsiv;}}_a^i+F)}+\sqrt{{\mathrm{\&epsiv;}}_v^i({\mathrm{\&epsiv;}}_v^i+F)}V+E_x^i}{\sqrt{{\mathrm{\&epsiv;}}_a^j({\mathrm{\&epsiv;}}_a^j+F)}+\sqrt{{\mathrm{\&epsiv;}}_v^j({\mathrm{\&epsiv;}}_v^j+F)}V+E_x^j}$

Wherein:

$V=\frac{{\mathrm{\&Delta;D}}_v}{{\mathrm{\&Delta;D}}_a}---\left(15\right)$

${\mathrm{\&epsiv;}}_a^i=S_a{\mathrm{\&epsiv;}}_O^i+(1-S_a){\mathrm{\&epsiv;}}_R^i---\left(16\right)$

${\mathrm{\&epsiv;}}_v^i=S_v{\mathrm{\&epsiv;}}_O^i+(1-S_v){\mathrm{\&epsiv;}}_R^i---\left(17\right)$

$E_x^i=\frac{{\mathrm{\&Delta;A}}_s^i}{C_{\mathrm{Hb}}{\mathrm{\&Delta;D}}_a}=\frac{Z_a{\mathrm{\&Delta;D}}_a+Z_t{\mathrm{\&Delta;D}}_t}{C_{\mathrm{Hb}}{\mathrm{\&Delta;D}}_a}=\frac{Z_a}{C_{\mathrm{Hb}}}+\frac{Z_t{\mathrm{\&Delta;D}}_t}{C_{\mathrm{Hb}}{\mathrm{\&Delta;D}}_a}---\left(18\right)$

Here with C _hband tissue, tremulous pulse varied in thickness has relation.

Experiment shows: wavelength for impact very little, therefore can represent: , A here _iand B _iconstant, like this can be by represent, namely only have an independent variable.

After ICG enters human body by intravenous injection, very fast with the hemoglobin speed that reacts.ICG to enter after blood hardly calm in skin also not by other tissue resorption, the overwhelming majority is drained by liver, and the ICG that vein injects after latter 20 minutes 97% is just discharged by liver.ICG absorbance curve is in blood surveyed at 800nm wavelength place, find that the absorbance of ICG in blood affects by its concentration, both present proportional relationship, the sodium chloride adding 0.9% afterwards in ICG solution reaches dilution effect, finds that this proportional relation of solution after dilution still exists.In different normal plasma, the coefficient of variation of the concentration of ICG is very little, therefore can think that the test of ICG is subject to pining down of density of plasma albumin hardly.Because ICG is only drained by liver, enter blood not with its hetero-organization generation chemical reaction, hemoglobin does not have a significant effect for the mensuration of ICG, and the concentration of ICG and absorbance linear.Spectrophotography can be utilized to calculate the concentration of ICG by the absorbance of the ICG surveyed, evaluate the reserve function of liver with this.

When after intravenous injection ICG, two kinds of wavelength X _iand λ _jthe ratio of pulsating quantity of transillumination be:

${\mathrm{\&Phi;}}_{\mathrm{ij}}=\frac{{\mathrm{\&Delta;I}}_i/I_i}{{\mathrm{\&Delta;I}}_j/I_j}\&ap;\frac{{\mathrm{\&Delta;A}}_i}{{\mathrm{\&Delta;A}}_j}$

$=\frac{\sqrt{({\mathrm{\&epsiv;}}_a^i+{\mathrm{\&epsiv;}}_d^i{C}_d/C_{\mathrm{Hb}})({\mathrm{\&epsiv;}}_a^i+{\mathrm{\&epsiv;}}_d^i{C}_d/C_{\mathrm{Hb}}+F)}{C}_{\mathrm{Hb}}{\mathrm{\&Delta;D}}_a+\sqrt{({\mathrm{\&epsiv;}}_v^i+{\mathrm{\&epsiv;}}_d^i{C}_d/C_{\mathrm{Hb}})({\mathrm{\&epsiv;}}_v^i+{\mathrm{\&epsiv;}}_d^i{C}_d/C_{\mathrm{Hb}}+F)}{C}_{\mathrm{Hb}}{\mathrm{\&Delta;D}}_v+{\mathrm{\&Delta;A}}_s^i}{\sqrt{({\mathrm{\&epsiv;}}_a^j+{\mathrm{\&epsiv;}}_d^j{C}_d/C_{\mathrm{Hb}})({\mathrm{\&epsiv;}}_a^j+{\mathrm{\&epsiv;}}_d^j{C}_d/C_{\mathrm{Hb}}+F)}{C}_{\mathrm{Hb}}{\mathrm{\&Delta;D}}_a+\sqrt{({\mathrm{\&epsiv;}}_v^j+{\mathrm{\&epsiv;}}_d^j{C}_d/C_{\mathrm{Hb}})({\mathrm{\&epsiv;}}_v^j+{\mathrm{\&epsiv;}}_d^j{C}_d/C_{\mathrm{Hb}}+F)}{C}_{\mathrm{Hb}}{\mathrm{\&Delta;D}}_v+{\mathrm{\&Delta;A}}_s^j}$

$=\frac{\sqrt{({\mathrm{\&epsiv;}}_a^i+{\mathrm{\&epsiv;}}_d^{i}Z)({\mathrm{\&epsiv;}}_a^i+{\mathrm{\&epsiv;}}_d^{i}Z+F)}+\sqrt{({\mathrm{\&epsiv;}}_v^i+{\mathrm{\&epsiv;}}_d^{i}Z)({\mathrm{\&epsiv;}}_v^i+{\mathrm{\&epsiv;}}_d^{i}Z+F)V}+E_x^i}{\sqrt{({\mathrm{\&epsiv;}}_a^j+{\mathrm{\&epsiv;}}_d^{j}Z)({\mathrm{\&epsiv;}}_a^j+{\mathrm{\&epsiv;}}_d^{j}Z+F)}+\sqrt{({\mathrm{\&epsiv;}}_v^j+{\mathrm{\&epsiv;}}_d^{j}Z)({\mathrm{\&epsiv;}}_v^j+{\mathrm{\&epsiv;}}_d^{j}Z+F)}V+E_x^j}---\left(19\right)$

Wherein: C _dthe concentration of ICG, Z=C _d/ C _hb, with two kinds of wavelength X respectively _iand λ _jlight by the specific absorbance of ICG.In formula (19), there is S _a, S _v, V, and C _dfive unknown quantitys, if the hepatic functional reserve tester adopting six wavelength, can list five independently equations by (19) formula, thus can solve S simultaneously _a, S _v, V, and C _dfive independently unknown quantity, wherein ICG concentration C _dnot by the impact of other unknown quantity.

Claims (6)

1. a multi-wavelength liver reserve function detector, is characterized in that: detector is made up of embedded microprocessor, light source driving circuit, multi-wave length illuminating light source, photodetector, signal processing circuit, liquid crystal display, data storage, PC/browser and printer; Wherein embedded microprocessor is connected with light source driving circuit, signal processing circuit, liquid crystal display, data storage, printer, PC/browser respectively; Multi-wave length illuminating light source is connected with light source driving circuit; Photodetector is connected with signal processing circuit;

Embedded microprocessor controls light source driving circuit, the LED timesharing of the multiple wavelength in light source driving circuit driving light source is luminous, photoelectric detector through tissue transillumination and convert the signal of telecommunication to, signal processing circuit by the signal of telecommunication first through one-level processing and amplifying, again the signal of telecommunication of different wave length is separated, then the A/D converter in embedded microprocessor is input to after carrying out filtering and secondary processing and amplifying respectively, A/D converter converts the signal of telecommunication of different wave length to digital signal, embedded microprocessor obtains ICG concentration value with process by analysis according to the signal of each wavelength, ICG curve, arterial oxygen saturation and Svo2, ICG concentration value, ICG curve, arterial oxygen saturation and Svo2 Simultaneous Transmission of Data are to display, printer, PC/browser, and be stored in data storage,

The LED of the multiple wavelength in described light source driving circuit driving light source is the LED of 6 different wave lengths, and the wave-length coverage of 6 LED is respectively λ ₁=650nm-680nm, λ ₂=700nm-730nm, λ ₃=750nm-780nm, λ ₄=790nm-810nm, λ ₅=900nm-920nm, λ ₆=930nm-950nm.

2. multi-wavelength liver reserve function detector as claimed in claim 1, is characterized in that: light source driving circuit is made up of pulse train circuit for generating and the drive circuit that is attached thereto.

3. multi-wavelength liver reserve function detector as claimed in claim 1, is characterized in that: the one-level amplifying circuit of signal processing circuit connects multichannel filtering circuit respectively through demultiplexing circuit, and multichannel filtering circuit connects multichannel second amplifying circuit respectively.

4. multi-wavelength liver reserve function detector as claimed in claim 2, it is characterized in that: the square-wave generator clocking of pulse train circuit for generating inputs to decoder, carry out frequency division by decoder and export 6 tunnel timesharing rectangular signals, then drive the LED of 6 different wave lengths luminous respectively by drive circuit.

5. detect the method for ICG concentration with multi-wavelength liver reserve function detector according to claim 1, it is characterized in that: detecting step is:

1. start, start embedded system, enter liver reserve function and detect main interface;

2. set up patient files, 6 wavelength detecting parameters are set;

3. 6 wavelength image data, gather and terminate;

4. date processing, display parameters and curve, print examining report, data are saved to data base;

5. whether terminate or set up next patient files;

6. terminate.

6. the method detecting ICG concentration with multi-wavelength liver reserve function detector as claimed in claim 5, it is characterized in that: the concrete grammar of described detection ICG concentration is, when after intravenous injection ICG, the light of 6 different wave lengths is used to pass through tissue, detect the light intensity signal of 6 different wave length emergent lights respectively, wherein any two kinds of different wave length λ _iand λ _jthe ratio of pulsating quantity of transillumination be:

${\mathrm{\&Phi;}}_{ij}=\frac{{\mathrm{\&Delta;I}}_i/I_i}{{\mathrm{\&Delta;I}}_j/I_j}\&ap;\frac{{\mathrm{\&Delta;A}}_i}{{\mathrm{\&Delta;A}}_j}=\frac{\sqrt{({\mathrm{\&epsiv;}}_a^i+{\mathrm{\&epsiv;}}_d^{i}Z)({\mathrm{\&epsiv;}}_a^i+{\mathrm{\&epsiv;}}_d^{i}Z+F)}+\sqrt{({\mathrm{\&epsiv;}}_v^i+{\mathrm{\&epsiv;}}_d^{i}Z)({\mathrm{\&epsiv;}}_v^i+{\mathrm{\&epsiv;}}_d^{i}Z+F)}V+E_x^i}{\sqrt{({\mathrm{\&epsiv;}}_a^j+{\mathrm{\&epsiv;}}_d^{j}Z)({\mathrm{\&epsiv;}}_a^j+{\mathrm{\&epsiv;}}_d^{j}Z+F)}+\sqrt{({\mathrm{\&epsiv;}}_v^j+{\mathrm{\&epsiv;}}_d^{j}Z)({\mathrm{\&epsiv;}}_v^j+{\mathrm{\&epsiv;}}_d^{j}Z+F)}V+E_x^j}$

6 different wave lengths have 5 independently light intensity ratio equations, are solved: S by 5 independent equations _a, S _v, V, and C _dfive independently unknown quantitys;

In formula: i and j represents the sequence number of any two different wave lengths in 6 wavelength respectively,

Φ _ijtwo kinds of wavelength X _iand λ _jthe ratio of pulsating quantity of transillumination

the change ratio of two kinds of wavelength absorbance,

ε _a, ε _vand ε _drepresent that wavelength is λ respectively _ior λ _jtime arterial blood specific absorbance, venous blood specific absorbance and light by the specific absorbance of ICG,

F is light scattering coefficient,

Z=C _d/ C _hb, C _hband C _dthe concentration of hemoglobin and ICG respectively,

Δ D _awith Δ D _varterial blood thickness changes values and venous blood thickness changes values respectively,

with be and hemoglobin concentration C _hband tissue, the relevant variable of tremulous pulse varied in thickness, a _iand B _iconstant, can be by represent, namely only have an independent variable;

ε _a=S _aε _o+ (1-S _a) ε _r, ε _v=S _vε _o+ (1-S _v) ε _r, S _aand S _vrepresent arterial oxygen saturation and Svo2 respectively, ε _oand ε _rrepresent Oxygenated blood Lactoferrin O respectively ₂hb and deoxyhemoglobin RHb is at the specific absorbance of monochromatic af at wavelength lambda.