CN109758162A - A kind of Optical devices and method detecting in-vivo tissue liquid glucose signals - Google Patents
A kind of Optical devices and method detecting in-vivo tissue liquid glucose signals Download PDFInfo
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- CN109758162A CN109758162A CN201910102703.8A CN201910102703A CN109758162A CN 109758162 A CN109758162 A CN 109758162A CN 201910102703 A CN201910102703 A CN 201910102703A CN 109758162 A CN109758162 A CN 109758162A
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- 230000003287 optical effect Effects 0.000 title claims abstract description 99
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Abstract
The invention discloses a kind of Optical devices and its detection method for detecting in-vivo tissue liquid glucose signals.Optical devices include monochromator, probe, excitation light source and analytical equipment, and probe includes shell and is arranged in the intracorporal collimation lens of shell, convergent lens and condenser lens, and the exploration hole of housing forward end is arranged in.Exploration hole aperture is less than 1mm, is centrally disposed on convergent lens main shaft, with the focal length for assembling optical center of lens distance L and convergent lensfFor 0.5mm≤f-L≤1.5mm.It motivates light source to issue the near infrared light of wavelength 600nm or more, excitation is formed to glucose in dermal layer of the skin tissue fluid, monochromator collects the characteristic signal generated after processing glucose excited target, analyzes to obtain glucose signals for analytical equipment.The present invention, which has, reduces or rejects the advantages of blood signal is interfered, directly, effectively, easily obtains interstitial fluid glucose signal during glucose signals are collected.
Description
Technical field
The present invention relates to a kind of Optical devices and method for detecting in-vivo tissue liquid glucose signals, belong to medical treatment detection skill
Art field.
Background technique
The abnormal carbohydrate metabolisms person such as diabetes or hyperglycemia needs frequently detection concentration of glucose level to cooperate medication at present
And diet, this is the key link for the treatment of diabetes, and it is diabetes that whether internal glucose level, which obtains being monitored and controlled in time,
The deciding factor for the treatment of.
The glucose to be detected is present in internal liquid environment in the form of glucose solution, hereinafter referred to as body fluid.
Concentration of glucose is detected to need first then to establish glucose signals intensity with algorithm with the glucose signals in instrument detection body fluid
With the relationship of concentration of glucose.
Common detection method is external detection, i.e., first turns the body fluid such as blood or tissue fluid using the method for extracting or permeating
It moves on in vitro, then it is detected again.
In view of the frequent feeling of pain of external detecting glucose signal and not convenient operation, and it can not achieve continuous survey
, there is the method for internal detection glucose signals in amount.
The body fluid for being used to detect concentration of glucose at present has vessel inner blood, subcutaneous tissue liquid, aqueous humor (tissue fluid in eyes
One kind).There are body fluid circulatory between blood-tissue liquid, concentration of glucose substantially reaches unanimity, however after intake sugar not
Concentration of glucose variation with body fluid has differences, relative to the concentration of glucose in blood, in some cases in tissue fluid
Concentration of glucose contacted with treating diabetes it is even closer, increasingly by medical field pay attention to.
Therefore, it is necessary to a better methods to overcome a series of above-mentioned disadvantages, and this method requirement: internal detection replaces external
Detection；Detect interstitial fluid glucose signal rather than blood glucose Sugar signal.
For United States Patent (USP) US6181957 using the aqueous humor of optical means detection eyes, aqueous humor is interior to be free of blood vessel, can be to avoid blood
The influence of liquid signal, however proposed method have safety the problem of.
The existing method for even penetrating skin detection concentration of glucose using skin, such as use up across ear-lobe or hand
Refer to, or with being needled into subcutaneously, however the tissue at these positions contains a large amount of blood vessels, and these methods are not all mentioned and how to be avoided
The interference of blood signal, even without recognizing dividing tissue liquid and blood.
Current method all ignores the feasibility and necessity of interstitial fluid glucose signal in detection corium.Blood in corium
It manages and is mainly enriched in the intersection of upper surface and epidermis and the intersection of lower surface and subcutaneous tissue, by protein inside skin corium
Fiber forms space structure, wherein being filled with tissue fluid, if it is possible to only collect the signal inside skin corium, so that it may have
Effect reduces the signal for carrying out autoblood, and safe and convenient.
Summary of the invention
The present invention is intended to provide a kind of Optical devices and method for detecting in-vivo tissue liquid glucose signals, by corium
The detection of interstitial fluid glucose signal obtains glucose information in layer, and reduces the influence for even avoiding blood signal.
The invention is realized by the following technical scheme:
A kind of Optical devices detecting in-vivo tissue liquid glucose signals, including monochromator, probe, excitation light source and analysis dress
It sets；The probe is connected by launching fiber with the excitation light source, and is connected by detection optical fiber with the monochromator；It is described
Monochromator is connected with the analytical equipment, and the probe includes shell and is arranged in the intracorporal collimation lens of shell, convergent lens
And condenser lens, launching fiber one end setting form signal transmitting terminal, the detection optical fiber on the housing rear end top
One end setting forms signal receiving end in the housing rear end lower part, and the convergent lens is arranged in shell front；Signal transmitting
Form transmitting optical path between end and the collimation lens and the convergent lens, and the convergent lens and the condenser lens and
Detection optical path is formed between signal receiving end；The housing forward end is provided with exploration hole, and the detection hole area is less than 1mm2；Institute
The exploration hole center of circle is stated to be arranged on the main shaft of the convergent lens, and the exploration hole center of circle to the convergent lens optical center away from
From the focal length that L is less than the convergent lensf, and 0.5mm≤f-L≤1.5mm。
One of technical solution is that the monochromator selects multiple-wavelength monochromator, and the probe further includes being arranged in shell
Narrow band filter, high-pass filter, reflecting mirror and dichroscope, the narrow band filter and reflecting mirror in body are successively set on
In the transmitting optical path of the collimation lens and the launching fiber opposite side, the reflecting mirror and incident ray are in 45 ° of arrangements；
The reflecting mirror and the dichroscope are in parallel arrangement；Dichroscope setting the convergent lens and condenser lens it
Between, the high-pass filter is arranged between the dichroscope and the condenser lens；The convergent lens, dichroscope,
Detection optical path is formed between high-pass filter and condenser lens；The detection optical path main shaft and the launching fiber and the transmitting
Input path main shaft between mirror is parallel.
Another technical solution is that the monochromator selects Single wavelength monochromator, and the convergent lens includes incident assembles
Lens and detection convergent lens, between the collimation lens and condenser lens and the incident convergent lens and detection assemble it is saturating
It is symmetrical set in the shell between mirror, the exploration hole center of circle is located on symmetry axis.
A kind of optical method detecting in-vivo tissue liquid glucose signals, including
Detected part is placed with the detection hole surface in shell；
The excitation optical signal that central wavelength lambda is issued by excitation light source, motivates optical signal to enter probe by incident optical, passes through
Collimation lens collimation, and make that the emitted optical path of optical signal is motivated to assemble by convergent lens, it passes through exploration hole and reaches detected part
Skin corium, in detected part dermis layer tissue liquid glucose generate optical excitation effect so that the grape in tissue fluid
Sugar generates feedback signal；
It returns to feedback signal by convergent lens, and is collimated via convergent lens, assembled by detection optical routing condenser lens
Enter monochromator detection to detection optical fiber to collect, and be transferred to analytical equipment and the feedback signal being collected into is analyzed and processed,
Obtain interstitial fluid glucose signal.
In above-mentioned technical proposal, the central wavelength lambda selects the near infrared band for being greater than 600nm.
When the monochromator select multiple-wavelength monochromator, it is described probe further include the narrow band filter being arranged in shell,
High-pass filter, reflecting mirror and dichroscope, the method also includes:
The excitation optical signal of central wavelength lambda enters probe by incident optical, by narrow-band-filter after being collimated by collimation lens
The light for the non-λ of wavelength that piece filtering excitation optical signal transmission process generates, it is then anti-again by reflecting mirror reflection and dichroscope
It penetrates, assembles the excitation optical signal of central wavelength lambda by convergent lens, the skin corium of detected part is reached across exploration hole, it is right
Glucose in detected part dermis layer tissue liquid generates optical excitation effect, so that the glucose in tissue fluid generates feedback letter
Number, feedback signal is the excitation optical signal of a series of Raman light of wavelength greater than λ and reflection；
It returns to feedback signal by convergent lens, and is collimated via convergent lens, transmitted by dichroscope, filter out big portion
Divide the excitation optical signal of reflection, excitation optical signal of remaining reflection is then filtered via high-pass filter, makes feedback signal only
Retain Raman light；Raman light converges to detection optical fiber by condenser lens and enters monochromator splitting collection, and is transferred to analytical equipment,
Fluorescence background is deducted by algorithm and restores raman spectral signal, identifies that wave number is located at 480cm-1~550cm-1The signal of range is strong
It spends to get interstitial fluid glucose signal is arrived.
In above-mentioned technical proposal, excitation light signal center wavelength X selects 785 ± 1nm.
When the monochromator selects Single wavelength monochromator, the convergent lens is assembled thoroughly including incident convergent lens and detection
Mirror, the method also includes:
The excitation optical signal of central wavelength lambda passes through incident convergent lens and assembles, and the skin corium of detected part is reached across exploration hole,
Optical excitation effect is generated to the glucose in detected part dermis layer tissue liquid, so that the glucose in tissue fluid generates feedback
Signal, feedback signal are the excitation optical signal cut down, and motivating the reduction of optical signal is by glucose absorption in tissue fluid
Excitation light semaphore；
It returns to feedback signal by detection convergent lens, and via detection convergent lens collimation, spy is converged to by condenser lens
It surveys optical fiber and enters monochromator detection collection, and be transferred to analytical equipment and residual excitation optical signal is recorded to the feedback signal being collected into
Power deducts human body amount of scattered light with incident excitation optical signal power difference to get interstitial fluid glucose signal is arrived.
In above-mentioned technical proposal, excitation light signal center wavelength X selects 946nm.
The present invention has the following advantages and beneficial effects: can obtain glucose signals in dermal tissue liquid, reduce even
The influence for avoiding blood signal, the signal detected use for various concentration of glucose analysis methods.
Detailed description of the invention
Fig. 1 is human skin tissue according to the present invention and detection principle schematic diagram.
Fig. 2 is the optics dress of the detection in-vivo tissue liquid glucose signals of one of embodiment according to the present invention
Set schematic diagram.
Fig. 3 is the Optical devices of the detection in-vivo tissue liquid glucose signals of another embodiment according to the present invention
Schematic diagram.
Fig. 4 is profile of optic fibre schematic diagram according to the present invention.
Fig. 5 is the interstitial fluid glucose signal graph that the detection of embodiment 1 obtains.
Fig. 6 is the interstitial fluid glucose signal graph that the detection of embodiment 2 obtains.
In figure: 1-monochromator；2-probes；21-shells；22-collimation lenses；23-convergent lenses；231-incident convergences are saturating
Mirror；232-detection convergent lenses；24-condenser lenses；25-exploration holes；26-narrow band filters；27-high-pass filters；28-reflections
Mirror；29-dichroscopes；3-excitation light sources；4-analytical equipments；5-launching fibers；6-detection optical fibers；7-epidermis；8-skin coriums；
9-subcutaneous tissues.
Specific embodiment
A specific embodiment of the invention and the course of work are further described with reference to the accompanying drawing.
The positional terms such as the upper, lower, left, right, front and rear in present specification be positional relationship based on the figure and
It establishes.Attached drawing is different, then corresponding positional relationship is also possible to change therewith, therefore cannot be interpreted as with this to protection model
The restriction enclosed.
A kind of Optical devices detecting in-vivo tissue liquid glucose signals, including monochromator 1, probe 2, excitation 3 and of light source
Analytical equipment 4.It can be used in detecting the dermis layer tissue liquid glucose signals of human skin, skin corium can be any position of body
The skin corium in skin is set, such as hand (foot) refers to, hand (foot) palm, hand (foot) wrist, four limbs, scalp, ear and subungual true
Cortex.
Probe 2 is connected by launching fiber 5 with excitation light source 3, and is connected by detection optical fiber 6 with monochromator 1.Monochromator
1 is connected with analytical equipment 4 by data line.
Probe 2 includes shell 21 and the collimation lens 22, convergent lens 23 and the condenser lens 24 that are arranged in shell 21.
After being with orientation where incident source, detected part is preceding, as front-rear direction.5 one end of launching fiber is arranged in 21 rear end of shell
Signal transmitting terminal is formed at top, and the setting of 6 one end of detection optical fiber forms signal receiving end, convergent lens 23 in 21 rear end lower of shell
It is arranged in 21 front of shell.Transmitting optical path is formed between signal transmitting terminal and collimation lens 22 and convergent lens 23, and is assembled saturating
Detection optical path is formed between mirror 23 and condenser lens 24 and signal receiving end.
21 front end of shell is provided with exploration hole 25, and 25 area of exploration hole is less than 1mm2；, preferably exploration hole 25 is less than for diameter
The circular hole of 1mm.25 center of circle of exploration hole is arranged on the main shaft of convergent lens 23, and 25 center of circle of exploration hole is to 23 optical center of convergent lens
Distance L be less than convergent lens 23 focal lengthf, and 0.5mm≤f-L≤1.5mm.This is because skin histology wraps as shown in Figure 1
Epidermis 7, skin corium 8 and subcutaneous tissue 9 are included, skin top layer is epidermis 7, is connected with skin corium 8, thickness is usually less than
It is 100 microns, very thin relative to corium, it readily penetrates through, is mainly the spatial network skeleton of azelon composition, group in corium 8
It knits liquid and is filled in and wherein contain only a small amount of blood vessel, dermis thickness is generally 2mm.When exploration hole 25 is close to skin, due to people
Body tissue is to the high-permeability of near infrared light, and excitation light will focus on the position of 0.5 ~ 1.5mm depth in human skin, to tissue fluid
Middle glucose generates illumination excitation.It is preferred thatfThe difference of-L is 1mm.
For one of technical solution as shown in Fig. 2, monochromator 1 selects multiple-wavelength monochromator at this time, probe 2 further includes setting
Narrow band filter 26, high-pass filter 27, reflecting mirror 28 and dichroscope 29 in shell 21, narrow band filter 26 and reflection
Mirror 28 is successively set in the transmitting optical path of collimation lens 22 and 5 opposite side of launching fiber, and reflecting mirror 28 is in incident ray
45 ° of arrangements；Reflecting mirror 28 and dichroscope 29 are in parallel arrangement；Dichroscope 29 is arranged in convergent lens 23 and condenser lens 24
Between, high-pass filter 27 is arranged between dichroscope 29 and condenser lens 24；Convergent lens 23, dichroscope 29, high pass
Detection optical path is formed between optical filter 27 and condenser lens 24；It detects between optical path main shaft and launching fiber 5 and transmitting mirror 28
Input path main shaft is parallel.
Another technical solution as shown in figure 3, at this time monochromator 1 select Single wavelength monochromator, convergent lens 23 include into
Convergent lens 231 and detection convergent lens 232 are penetrated, between collimation lens 22 and condenser lens 24 and incident convergent lens 231
It is symmetrical set in shell 21 between detection convergent lens 232,25 center of circle of exploration hole is located on symmetry axis.
In above two technical solution, the section of launching fiber 5 and detection optical fiber 6 arrangement can with as shown in figure 4, using
Such as the single hole arrangement of Fig. 4 a, or the porous array arrangement such as Fig. 4 b.
Embodiment 1: multiple-wavelength monochromator
Detected part is placed on 25 surface of exploration hole of shell 21.
Excitation light source 3 uses wavelength for the laser of 785nm.The excitation of central wavelength 785nm is issued by excitation light source 3
The excitation optical signal of optical signal, central wavelength 785nm enters probe 2 by incident optical 5, passes through after being collimated by collimation lens 22
The light for crossing the non-785nm of wavelength of 26 filtering excitation optical signal transmission process of narrow band filter generation, then passes through reflecting mirror 28
Reflection and dichroscope 29 reflect again, assemble the excitation optical signal of central wavelength 785nm by convergent lens 23, pass through detection
Hole 25 reaches the skin corium of detected part, generates optical excitation effect to the glucose in detected part dermis layer tissue liquid, makes
It obtains the glucose in tissue fluid and generates feedback signal, feedback signal is a series of Raman light of wavelength greater than 785nm and reflection
Motivate optical signal.Raman light is referred to as Raman shift with the difference of incentive optical wavelength.
It returns to feedback signal by convergent lens 23, and is collimated via convergent lens 23, transmitted by dichroscope 29,
The excitation optical signal largely reflected is filtered out, the excitation optical signal of remaining reflection is then filtered via high-pass filter 27,
Only allow optical signal of the wavelength greater than 785nm to pass through, feedback signal is made only to retain Raman light.Raman light is assembled by condenser lens 24
Enter the light splitting of monochromator 1 to detection optical fiber 6 to collect, which is multiple-wavelength monochromator, can extract a series of continuous waves
It grows and separately detects respective intensities.And it is transferred to analytical equipment 4, as the diagram in figure 5 shows, abscissa represents Raman position in figure
It moves, unit cm-1, the intensity of ordinate representation signal.Fig. 5 (a) represents the original spectrum for the wrist that this method measures, and spectrum is strong
Degree successively decreases from shortwave number to long wave number direction, this is because caused by the fluorescence that wrist generates under the excitation of 785nm light.Fluorescence
Intensity is much higher than the intensity of Raman signal, and Raman signal is overshadowed in wherein, though still it is observed that Raman peaks it is right at its
It is also difficult to than under, needs to deduct fluorescence background by algorithm to restore raman spectral signal.
Can be realized and deduct the algorithm of fluorescence background includes calculus of finite differences, Wavelet Transform etc..Wavelet Transform passes through to light
Spectrum signal carries out wavelet decomposition, obtains high and low frequency wavelet coefficient, then get rid of be considered as fluorescence part, then to surplus
Remaining part carries out wavelet decomposition reciprocal transformation, obtains the Raman spectrum of removal fluorescent component.
Fig. 5 (b) represents the fluorescent component deducted in original spectrum, the wrist Raman spectrum restored, the Raman spectrum
Be by glucose, what the Raman signal of protein and other human body components collectively constituted.Fig. 5 (c) represents glucose solution
Raman spectrum, it can be seen that Raman shift is located at 480cm-1~550cm-1Raman peak signature intensity highest in range, the face at peak
Product is also maximum, is the most strong Raman peaks of glucose, Raman shift is located at 1100cm-1~1150cm-1Raman peaks in range are Portugals
Time strong Raman peaks of grape sugar.Comparison diagram 5 (b) and Fig. 5 (c), it can be found that cover and other substance Raman spectrums by fluorescence
Interference under, the glucose Raman signal of part does not restore significantly, and Raman shift is located at 480cm-1~550cm-1
Most strong Raman peaks in range are obvious to be shown up, and as shown in dotted line frame 1 in Fig. 5, peak value is all 523cm-1。
It can also be observed that Raman shift is located at 1100cm-1~1150cm-1Time strong Raman peaks in range, such as institute in dotted line frame 2 in Fig. 5
Show, peak value is all 1129cm-1。
Usual blood Raman spectrum, which has, strong is located at 1565cm-1Neighbouring characteristic peak.And the spectrum that this method obtains exists
1500 cm-1To 1600cm-1All without spectral signal in range, can prove not carry out autoblood in spectrum that this method obtains
Signal, this method can influence to avoid blood signal to tissue fluid signal.
Embodiment 2: Single wavelength monochromator
Excitation light uses the laser of wavelength 946nm, this is because glucose solution has absorption to the light of wavelength 950nm or so
Effect, as shown in fig. 6, absorption spectrum (a) represents the near-infrared absorption spectrum of tissue in figure, absorption spectrum (b) represents Portugal
The near-infrared absorption spectrum of grape sugar aqueous solution, the two absorption peak having the same, peak is wider, and peak value is located at wavelength 950nm.
Wavelength is chosen close to the wavelength 946nm near glucose near-infrared absorption spectrum peak value, the sensitivity of equipment can be improved.
The excitation light for the wavelength 946nm that the excitation light source 29 of known power issues.Motivate optical signal by incident optical 5 into
Enter probe 2, collimated by collimation lens 22, and make that optical signal is motivated to pass through the incident convergence of convergent lens 231, passes through exploration hole 25
Reach the skin corium of detected part.After the glucose in tissue fluid is motivated by the illumination of wavelength 946nm, excitation light is generated
It partially absorbs, the number of uptake is influenced by the size of concentration of glucose in tissue fluid.Remaining excitation light passes through convergence
Lens 232 return, and collimate via detection convergent lens 232, converge to detection optical fiber 6 by condenser lens 24 and enter monochromator 1
(InGaAs detector), the monochromator are Single wavelength monochromator, can extract wavelength from the optical signal for reaching monochromator 1
The light of 946nm, and the optical signal to other wavelength that may reach monochromator 1, (such as environment light) are insensitive.Monochromator 1 is visited
The power of wavelength 946nm residue light is surveyed, and is transferred to the record of analytical equipment 4, which is by Portugal with the difference of the power of excitation light
Grape sugar absorbs and the amount of human body scattering light, and wherein the amount of human body scattering light is quantitative, by the amount of glucose absorption by glucose
Concentration determine, by analysis absorb number, can be obtained the information of concentration of glucose.
The foregoing is only a preferred embodiment of the present invention, is not intended to restrict the invention, for the skill of this field
For art personnel, the invention may be variously modified and varied.All within the spirits and principles of the present invention, made any to repair
Change, equivalent replacement, improvement etc., should all be included in the protection scope of the present invention.
Claims (9)
1. a kind of Optical devices for detecting in-vivo tissue liquid glucose signals, the Optical devices include monochromator (1), probe
(2), light source (3) and analytical equipment (4) are motivated；The probe (2) is connected by launching fiber (5) with the excitation light source (3),
And it is connected by detection optical fiber (6) with the monochromator (1)；The monochromator (1) is connected with the analytical equipment (4), described
Probe (2) includes collimation lens (22), convergent lens (23) and the condenser lens of shell (21) and setting in shell (21)
(24), launching fiber (5) one end setting forms signal transmitting terminal, the detection optical fiber in the shell (21) upper rear end
(6) one end setting forms signal receiving end in the shell (21) rear end lower, and the convergent lens (23) is arranged in shell
(21) front；Transmitting optical path, and institute are formed between signal transmitting terminal and the collimation lens (22) and the convergent lens (23)
It states and forms detection optical path between convergent lens (23) and the condenser lens (24) and signal receiving end；It is characterized in that, described
Shell (21) front end is provided with exploration hole (25), and exploration hole (25) area is less than 1mm2；Exploration hole (25) center of circle is set
It sets on the main shaft of the convergent lens (23), and the exploration hole (25) center of circle is to the distance of the convergent lens (23) optical center
L is less than the focal length of the convergent lens (23)f, and 0.5mm≤f-L≤1.5mm。
2. a kind of Optical devices for detecting in-vivo tissue liquid glucose signals according to claim 1, which is characterized in that institute
It states monochromator (1) and selects multiple-wavelength monochromator, the probe (2) further includes the setting narrow band filter inner in shell (21)
(26), high-pass filter (27), reflecting mirror (28) and dichroscope (29), the narrow band filter (26) and reflecting mirror (28) according to
Secondary setting is in the transmitting optical path of the collimation lens (22) and the launching fiber (5) opposite side, the reflecting mirror (28)
With incident ray in 45 ° of arrangements；The reflecting mirror (28) and the dichroscope (29) are in parallel arrangement；The dichroscope
(29) be arranged between the convergent lens (23) and condenser lens (24), the high-pass filter (27) be arranged described two to
Between Look mirror (29) and the condenser lens (24)；The convergent lens (23), dichroscope (29), high-pass filter (27) and
Detection optical path is formed between condenser lens (24)；The detection optical path main shaft and the launching fiber (5) and the transmitting mirror
(28) the input path main shaft between is parallel.
3. a kind of Optical devices for detecting in-vivo tissue liquid glucose signals according to claim 1, which is characterized in that institute
It states monochromator (1) and selects Single wavelength monochromator, the convergent lens (23) includes that incident convergent lens (231) and detection convergence are saturating
Mirror (232), between the collimation lens (22) and condenser lens (24) and the incident convergent lens (231) and detection convergence
It is symmetrical set in the shell (21) between lens (232), exploration hole (25) center of circle is located on symmetry axis.
4. a kind of optical method for detecting in-vivo tissue liquid glucose signals, uses Optical devices as described in claim 1,
It is characterized in that, which comprises
Detected part is placed on exploration hole (25) surface of shell (21)；
The excitation optical signal of central wavelength lambda is issued by excitation light source (3), excitation optical signal is entered by incident optical (5) to be visited
Head (2) is collimated by collimation lens (22), and makes that the emitted optical path of optical signal is motivated to assemble by convergent lens (23), is passed through
Exploration hole (25) reaches the skin corium of detected part, generates optical excitation to the glucose in detected part dermis layer tissue liquid and makees
With so that the glucose in tissue fluid generates feedback signal；
It returns to feedback signal by convergent lens (23), and is collimated via convergent lens (23), focused by detection optical routing
Lens (24) converge to detection optical fiber (6) and collect into monochromator (1) detection, and are transferred to analytical equipment (4) to what is be collected into
Feedback signal is analyzed and processed, and obtains interstitial fluid glucose signal.
5. a kind of optical method for detecting in-vivo tissue liquid glucose signals according to claim 4, which is characterized in that described
Central wavelength lambda selects the near infrared band for being greater than 600nm.
6. a kind of optical method for detecting in-vivo tissue liquid glucose signals according to claim 4, which is characterized in that described
Monochromator (1) select multiple-wavelength monochromator, the probe (2) further include be arranged the inner narrow band filter (26) of shell (21),
High-pass filter (27), reflecting mirror (28) and dichroscope (29), the method also includes:
The excitation optical signal of central wavelength lambda enters probe (2) by incident optical (5), passes through after being collimated by collimation lens (22)
The light for crossing the non-λ of wavelength of narrow band filter (26) filtering excitation optical signal transmission process generation, then passes through reflecting mirror (28)
Reflection and dichroscope (29) are reflected again, assemble the excitation optical signal of central wavelength lambda by convergent lens (23), pass through detection
Hole (25) reaches the skin corium of detected part, generates optical excitation effect to the glucose in detected part dermis layer tissue liquid,
So that the glucose in tissue fluid generates feedback signal, feedback signal is that a series of wavelength are greater than the Raman light of λ and swashing for reflection
Encourage optical signal；
It returns to feedback signal by convergent lens (23), and is collimated via convergent lens (23), it is saturating by dichroscope (29)
It penetrates, filters out the excitation optical signal largely reflected, the excitation light of remaining reflection is then filtered via high-pass filter (27)
Signal makes feedback signal only retain Raman light；Raman light converges to detection optical fiber (6) into monochromator by condenser lens (24)
(1) light splitting is collected, and is transferred to analytical equipment (4), is deducted fluorescence background by algorithm and is restored raman spectral signal, identifies wave
Numerical digit is in 480cm-1~550cm-1The signal strength of range to get arrive interstitial fluid glucose signal.
7. a kind of optical method for detecting in-vivo tissue liquid glucose signals according to claim 6, which is characterized in that described
Excitation light signal center wavelength X selects 785 ± 1nm.
8. a kind of optical method for detecting in-vivo tissue liquid glucose signals according to claim 4, which is characterized in that described
Monochromator (1) selects Single wavelength monochromator, and the convergent lens (23) includes incident convergent lens (231) and detection convergent lens
(232), the method also includes:
The excitation optical signal of central wavelength lambda passes through incident convergent lens (231) and assembles, and passes through exploration hole (25) and reaches detected part
Skin corium, in detected part dermis layer tissue liquid glucose generate optical excitation effect so that the grape in tissue fluid
Sugar generates feedback signal, and feedback signal is the excitation optical signal cut down, and motivating the reduction of optical signal is by Portugal in tissue fluid
The excitation light semaphore that grape sugar absorbs；
Return to feedback signal by detection convergent lens (232), and via detection convergent lens (232) collimation, it is saturating by focusing
Mirror (24) converges to detection optical fiber (6) and collects into monochromator (1) detection, and it is anti-to what is be collected into be transferred to analytical equipment (4)
Feedback signal record residual excitation optical signal power, with incident excitation optical signal power difference deduct human body amount of scattered light to get
To interstitial fluid glucose signal.
9. a kind of optical method for detecting in-vivo tissue liquid glucose signals according to claim 8, which is characterized in that described
Excitation light signal center wavelength X selects 946nm.
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