CA1239225A - Multiple wavelength light photometer for non-invasive monitoring - Google Patents
Multiple wavelength light photometer for non-invasive monitoringInfo
- Publication number
- CA1239225A CA1239225A CA000488142A CA488142A CA1239225A CA 1239225 A CA1239225 A CA 1239225A CA 000488142 A CA000488142 A CA 000488142A CA 488142 A CA488142 A CA 488142A CA 1239225 A CA1239225 A CA 1239225A
- Authority
- CA
- Canada
- Prior art keywords
- pulsed light
- light
- organ
- spectrophotometer
- light spectrophotometer
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired
Links
- 238000012544 monitoring process Methods 0.000 title claims abstract description 13
- 210000000056 organ Anatomy 0.000 claims abstract description 28
- 230000004060 metabolic process Effects 0.000 claims abstract description 4
- 230000005855 radiation Effects 0.000 claims description 12
- 230000000694 effects Effects 0.000 claims description 11
- 239000013307 optical fiber Substances 0.000 claims description 10
- 238000009792 diffusion process Methods 0.000 claims description 8
- 230000000644 propagated effect Effects 0.000 claims description 5
- 238000002798 spectrophotometry method Methods 0.000 claims description 5
- 239000011521 glass Substances 0.000 claims description 4
- 239000004033 plastic Substances 0.000 claims description 3
- 229920003023 plastic Polymers 0.000 claims description 3
- 229910052724 xenon Inorganic materials 0.000 claims description 3
- FHNFHKCVQCLJFQ-UHFFFAOYSA-N xenon atom Chemical compound [Xe] FHNFHKCVQCLJFQ-UHFFFAOYSA-N 0.000 claims description 3
- 239000007787 solid Substances 0.000 claims description 2
- 239000008280 blood Substances 0.000 abstract description 4
- 210000004369 blood Anatomy 0.000 abstract description 4
- 108010054147 Hemoglobins Proteins 0.000 description 9
- 102000001554 Hemoglobins Human genes 0.000 description 9
- 239000000835 fiber Substances 0.000 description 9
- QVGXLLKOCUKJST-UHFFFAOYSA-N atomic oxygen Chemical compound [O] QVGXLLKOCUKJST-UHFFFAOYSA-N 0.000 description 8
- 239000001301 oxygen Substances 0.000 description 7
- 229910052760 oxygen Inorganic materials 0.000 description 7
- 230000029058 respiratory gaseous exchange Effects 0.000 description 6
- 238000010586 diagram Methods 0.000 description 5
- 238000001727 in vivo Methods 0.000 description 4
- 239000000203 mixture Substances 0.000 description 4
- 102000000634 Cytochrome c oxidase subunit IV Human genes 0.000 description 3
- 108090000365 Cytochrome-c oxidases Proteins 0.000 description 3
- 206010021143 Hypoxia Diseases 0.000 description 3
- 208000008784 apnea Diseases 0.000 description 3
- 239000003990 capacitor Substances 0.000 description 3
- 238000012937 correction Methods 0.000 description 3
- 230000001146 hypoxic effect Effects 0.000 description 3
- 238000005259 measurement Methods 0.000 description 3
- 230000000241 respiratory effect Effects 0.000 description 3
- 102100030497 Cytochrome c Human genes 0.000 description 2
- 108010075031 Cytochromes c Proteins 0.000 description 2
- 238000010521 absorption reaction Methods 0.000 description 2
- 238000004364 calculation method Methods 0.000 description 2
- 230000002490 cerebral effect Effects 0.000 description 2
- 238000000034 method Methods 0.000 description 2
- 230000003287 optical effect Effects 0.000 description 2
- 238000006213 oxygenation reaction Methods 0.000 description 2
- 230000002093 peripheral effect Effects 0.000 description 2
- 238000005070 sampling Methods 0.000 description 2
- 238000003860 storage Methods 0.000 description 2
- 230000002792 vascular Effects 0.000 description 2
- SFNPDDSJBGRXLW-UHFFFAOYSA-N (3-methylsulfanylbutan-2-ylideneamino) n-methylcarbamate Chemical compound CNC(=O)ON=C(C)C(C)SC SFNPDDSJBGRXLW-UHFFFAOYSA-N 0.000 description 1
- 206010002091 Anaesthesia Diseases 0.000 description 1
- 241000557609 Cissa Species 0.000 description 1
- RYGMFSIKBFXOCR-UHFFFAOYSA-N Copper Chemical compound [Cu] RYGMFSIKBFXOCR-UHFFFAOYSA-N 0.000 description 1
- 102000004190 Enzymes Human genes 0.000 description 1
- 108090000790 Enzymes Proteins 0.000 description 1
- 102000004316 Oxidoreductases Human genes 0.000 description 1
- 108090000854 Oxidoreductases Proteins 0.000 description 1
- 108010064719 Oxyhemoglobins Proteins 0.000 description 1
- 206010036590 Premature baby Diseases 0.000 description 1
- 206010001053 acute respiratory failure Diseases 0.000 description 1
- VREFGVBLTWBCJP-UHFFFAOYSA-N alprazolam Chemical compound C12=CC(Cl)=CC=C2N2C(C)=NN=C2CN=C1C1=CC=CC=C1 VREFGVBLTWBCJP-UHFFFAOYSA-N 0.000 description 1
- 230000037005 anaesthesia Effects 0.000 description 1
- 239000012620 biological material Substances 0.000 description 1
- 210000004556 brain Anatomy 0.000 description 1
- 230000019522 cellular metabolic process Effects 0.000 description 1
- 210000003710 cerebral cortex Anatomy 0.000 description 1
- 230000001684 chronic effect Effects 0.000 description 1
- 229910052802 copper Inorganic materials 0.000 description 1
- 239000010949 copper Substances 0.000 description 1
- 238000001514 detection method Methods 0.000 description 1
- 238000011161 development Methods 0.000 description 1
- 230000018109 developmental process Effects 0.000 description 1
- 230000004927 fusion Effects 0.000 description 1
- 239000007789 gas Substances 0.000 description 1
- 150000003278 haem Chemical class 0.000 description 1
- 208000000122 hyperventilation Diseases 0.000 description 1
- 238000003384 imaging method Methods 0.000 description 1
- 230000036039 immunity Effects 0.000 description 1
- 238000011065 in-situ storage Methods 0.000 description 1
- 230000006698 induction Effects 0.000 description 1
- 238000013507 mapping Methods 0.000 description 1
- 239000000463 material Substances 0.000 description 1
- 230000002503 metabolic effect Effects 0.000 description 1
- 230000008811 mitochondrial respiratory chain Effects 0.000 description 1
- 238000007254 oxidation reaction Methods 0.000 description 1
- 238000012545 processing Methods 0.000 description 1
- 230000002226 simultaneous effect Effects 0.000 description 1
- 238000002560 therapeutic procedure Methods 0.000 description 1
- 238000007631 vascular surgery Methods 0.000 description 1
- 210000001835 viscera Anatomy 0.000 description 1
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
- G01N21/25—Colour; Spectral properties, i.e. comparison of effect of material on the light at two or more different wavelengths or wavelength bands
- G01N21/31—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry
- G01N21/314—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry with comparison of measurements at specific and non-specific wavelengths
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01J—MEASUREMENT OF INTENSITY, VELOCITY, SPECTRAL CONTENT, POLARISATION, PHASE OR PULSE CHARACTERISTICS OF INFRARED, VISIBLE OR ULTRAVIOLET LIGHT; COLORIMETRY; RADIATION PYROMETRY
- G01J1/00—Photometry, e.g. photographic exposure meter
- G01J1/10—Photometry, e.g. photographic exposure meter by comparison with reference light or electric value provisionally void
- G01J1/16—Photometry, e.g. photographic exposure meter by comparison with reference light or electric value provisionally void using electric radiation detectors
- G01J1/18—Photometry, e.g. photographic exposure meter by comparison with reference light or electric value provisionally void using electric radiation detectors using comparison with a reference electric value
- G01J2001/182—Photometry, e.g. photographic exposure meter by comparison with reference light or electric value provisionally void using electric radiation detectors using comparison with a reference electric value with SH sample and hold circuits
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01J—MEASUREMENT OF INTENSITY, VELOCITY, SPECTRAL CONTENT, POLARISATION, PHASE OR PULSE CHARACTERISTICS OF INFRARED, VISIBLE OR ULTRAVIOLET LIGHT; COLORIMETRY; RADIATION PYROMETRY
- G01J1/00—Photometry, e.g. photographic exposure meter
- G01J1/42—Photometry, e.g. photographic exposure meter using electric radiation detectors
- G01J1/44—Electric circuits
- G01J2001/4446—Type of detector
- G01J2001/4453—PMT
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
- G01N21/25—Colour; Spectral properties, i.e. comparison of effect of material on the light at two or more different wavelengths or wavelength bands
- G01N21/31—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry
- G01N2021/3129—Determining multicomponents by multiwavelength light
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N2201/00—Features of devices classified in G01N21/00
- G01N2201/06—Illumination; Optics
- G01N2201/069—Supply of sources
- G01N2201/0696—Pulsed
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N2201/00—Features of devices classified in G01N21/00
- G01N2201/08—Optical fibres; light guides
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N2201/00—Features of devices classified in G01N21/00
- G01N2201/12—Circuits of general importance; Signal processing
- G01N2201/126—Microprocessor processing
Abstract
ABSTRACT OF THE DISCLOSURE
A multiple wavelength pulsed light spectro-photometer for non-invasive monitoring and its use in measuring blood circulatory and local metabolism parameters in living organs.
A multiple wavelength pulsed light spectro-photometer for non-invasive monitoring and its use in measuring blood circulatory and local metabolism parameters in living organs.
Description
2~
DESCRIPTION
Sigrlificant developments in medical diagn~stics have been brought about in recent years by the introduction of non-invasive methodlcs9 Among these, near-infrared (I.R~) spectro~oopy and instruments have been utilized to characterize biological tissues in vivo.
I~Ro spectrophotometry rests upon the relative ; transpærency of biological materials to photon~ in t~e near I.R. ~700-900 nm). In situ photon transmis~ion through organs is sufficient to permit monitoring of absorptive changes in the tissues. In this ~pectral region, only some chromophores of great . function~l significance absorb light: the heme of : 15 he~oglobin whereby changes in local hematic volume : and equilibrium between oxyhemoglobin (HbO2) and hemoglobin (Hb) can be assessed, a~d ~he visible : copper of cytochromeo~idase (cyt a,a3), i.e. the terminal enzyme in the mitochondrial respiratory chain which cataly3es 95cjo cf the cell oxygen (2) ; input.
Since the mit'ochondrial respiratory chaln is the main gateway to utilizing the free energy obtai~ed in the variou~ metabolisms 9 in vivo 25 : e~aluation of the redox state of cyt a7a3 ~ay be ~; of great assistance in assessing t~e functional sta~e of cells in various physiopathological ituatio~s ~E~Dora, J. Neurochem. 42, 101-108t 1984;
rscin~a, D.YIilson, J. Memb. Biolvgy 70 9 1-14 7 ~ 1982; ~.F.Jobsi~, Adv~ Neurol. 26,299, 1979~.
~'2~:
Fairly aCcurate me~hod~ are known of measuring the le~el of oxygenation in the hemoglobin circulati~g through the vascular ~y3tem of surface tissues (Ta~atani et alD ~ ~n. Biomed. Eng. $,1, 1980). In general, however, such prior methods fail to provide quantitative result~ with internal organs owing to the difficulty encountered in evaluating the effects of light diffu~ionO
Jobsis, of Duke University, recently proposed to u~e this type of ~pectroscopy to characterize cell metabolism in vivo (~S Patent No. 4,218,645), and in particular, to a~ess the oxygenation level of cerebral tissues by measuring the I.R. absorption of cytochrome-c-oxida~e (F.F~Jobsis, Science, 198,1264, 1977)~
The spectrophotometer propo~ed by Jobsis comprises:
(A) some light sources which emit sequentially radiation within the range of 700 to 1,300 nm; (B) a fiber optic which tran~mits the light to an org~n to be monitored; (C)an optical fiberWhiCh picks.up the emerging radia~ion from the mo N tored organ; and ~D) a system for converting the radiatio~ to a readily analyzed ~ignal.
However, the ~pectrophotometer proposed by Job~i~
~: . 25 provide~ unacceptable quantitative results b~ca~e it ~-; take~ into ~o ac50unt the effect~ of light di~fusion, which are quite ~ignificant and may ~ary over time;
..
further, a~d more specific~1ly, light diffusion makes the optical path no~-rectllinear and Beer-~a~bert law does not apply.
:
Thus, the instrument i5 unable to correc-t the observed data due to scattering effects.
Now, we have developed a spectrophotometer, formi.ng the subject matter of this patent application, which can provide a quantitative and simultaneous assessment of the absorption due to cytochrome-c-oxidase and the two forms (oxygenated and non-oxygenated) of hemoglobin which are present in tissues in vivo, while taking into account the effects of light diffusion and of any variations thereof 1~ over time.
According to the present invention, there is provided a multiple wavelength pulsed light spectrophoto-meter for non-invasive monitoring, comprising:
(a) a light source emitting a light beam lncluding radiation in the near I.R. and consisting of a lamp powered by ~C-ti.med pulses;
(b) a means of conducting said light beam to an organ to be monitored (c) a means of conducting light from the monitored organ : (d) a detector for receiving said light and detecting at least four radiations at signiEicant wavelengths corresponding to physiological parameters to be measured, from all those which have been supplied from -the source and propagated through the organ;
(e) an amplifi.er for converting signals generated by said detector to readily analyzed continuous signals and correcting for variations due to fluctuations of -the source;
and (f) an acquisition system including a microprocessor adapted to permit instantaneous computation of the values of the detected physiological parameters taking into account the light diffusion effects.
According to the present invention, there is also l ~5 - 3a -provided a spectrophotometric method for measuring circula-tory and local metabolism parameters in living organs by non-invasive monitoring, comprising steps of:
(a) emitting a light beam including radiation in the near I.R. and consisting of a lamp powered by AC-timed pulses;
(b) conducting said light beam to an organ to be monitored;
(c) conducting light from the monitored organ;
~d) receiving said light and detecting at least four radiations at significant wavelengths corresponding to physiological parameters to be measured, from all those which have been supplied from the source and propagated through the organ;
(e) converting signals generated by said detector to readily analyzed continuous signals and correcting for variations due to fluctuations of the source; and (f) computing instantaneously the values of the detected physiological parameters taking into account the ~ 20 light diffusion effects.
:
DESCRIPTION OF THE DRAWIN~S
A better understanding of the invention may be had by reference to the detailed description which follows, taken in conjunction with the accompanying drawings, in which:
- Fig. 1 is a block diagram representing the fundamental parts of the apparatus object of the present invention - 30 - Fig. 2 is a detailed circuit diagram o~ the powering of the ~lash light source;
- Fig. 3 is showing the positions of -the light detectors;
DESCRIPTION
Sigrlificant developments in medical diagn~stics have been brought about in recent years by the introduction of non-invasive methodlcs9 Among these, near-infrared (I.R~) spectro~oopy and instruments have been utilized to characterize biological tissues in vivo.
I~Ro spectrophotometry rests upon the relative ; transpærency of biological materials to photon~ in t~e near I.R. ~700-900 nm). In situ photon transmis~ion through organs is sufficient to permit monitoring of absorptive changes in the tissues. In this ~pectral region, only some chromophores of great . function~l significance absorb light: the heme of : 15 he~oglobin whereby changes in local hematic volume : and equilibrium between oxyhemoglobin (HbO2) and hemoglobin (Hb) can be assessed, a~d ~he visible : copper of cytochromeo~idase (cyt a,a3), i.e. the terminal enzyme in the mitochondrial respiratory chain which cataly3es 95cjo cf the cell oxygen (2) ; input.
Since the mit'ochondrial respiratory chaln is the main gateway to utilizing the free energy obtai~ed in the variou~ metabolisms 9 in vivo 25 : e~aluation of the redox state of cyt a7a3 ~ay be ~; of great assistance in assessing t~e functional sta~e of cells in various physiopathological ituatio~s ~E~Dora, J. Neurochem. 42, 101-108t 1984;
rscin~a, D.YIilson, J. Memb. Biolvgy 70 9 1-14 7 ~ 1982; ~.F.Jobsi~, Adv~ Neurol. 26,299, 1979~.
~'2~:
Fairly aCcurate me~hod~ are known of measuring the le~el of oxygenation in the hemoglobin circulati~g through the vascular ~y3tem of surface tissues (Ta~atani et alD ~ ~n. Biomed. Eng. $,1, 1980). In general, however, such prior methods fail to provide quantitative result~ with internal organs owing to the difficulty encountered in evaluating the effects of light diffu~ionO
Jobsis, of Duke University, recently proposed to u~e this type of ~pectroscopy to characterize cell metabolism in vivo (~S Patent No. 4,218,645), and in particular, to a~ess the oxygenation level of cerebral tissues by measuring the I.R. absorption of cytochrome-c-oxida~e (F.F~Jobsis, Science, 198,1264, 1977)~
The spectrophotometer propo~ed by Jobsis comprises:
(A) some light sources which emit sequentially radiation within the range of 700 to 1,300 nm; (B) a fiber optic which tran~mits the light to an org~n to be monitored; (C)an optical fiberWhiCh picks.up the emerging radia~ion from the mo N tored organ; and ~D) a system for converting the radiatio~ to a readily analyzed ~ignal.
However, the ~pectrophotometer proposed by Job~i~
~: . 25 provide~ unacceptable quantitative results b~ca~e it ~-; take~ into ~o ac50unt the effect~ of light di~fusion, which are quite ~ignificant and may ~ary over time;
..
further, a~d more specific~1ly, light diffusion makes the optical path no~-rectllinear and Beer-~a~bert law does not apply.
:
Thus, the instrument i5 unable to correc-t the observed data due to scattering effects.
Now, we have developed a spectrophotometer, formi.ng the subject matter of this patent application, which can provide a quantitative and simultaneous assessment of the absorption due to cytochrome-c-oxidase and the two forms (oxygenated and non-oxygenated) of hemoglobin which are present in tissues in vivo, while taking into account the effects of light diffusion and of any variations thereof 1~ over time.
According to the present invention, there is provided a multiple wavelength pulsed light spectrophoto-meter for non-invasive monitoring, comprising:
(a) a light source emitting a light beam lncluding radiation in the near I.R. and consisting of a lamp powered by ~C-ti.med pulses;
(b) a means of conducting said light beam to an organ to be monitored (c) a means of conducting light from the monitored organ : (d) a detector for receiving said light and detecting at least four radiations at signiEicant wavelengths corresponding to physiological parameters to be measured, from all those which have been supplied from -the source and propagated through the organ;
(e) an amplifi.er for converting signals generated by said detector to readily analyzed continuous signals and correcting for variations due to fluctuations of -the source;
and (f) an acquisition system including a microprocessor adapted to permit instantaneous computation of the values of the detected physiological parameters taking into account the light diffusion effects.
According to the present invention, there is also l ~5 - 3a -provided a spectrophotometric method for measuring circula-tory and local metabolism parameters in living organs by non-invasive monitoring, comprising steps of:
(a) emitting a light beam including radiation in the near I.R. and consisting of a lamp powered by AC-timed pulses;
(b) conducting said light beam to an organ to be monitored;
(c) conducting light from the monitored organ;
~d) receiving said light and detecting at least four radiations at significant wavelengths corresponding to physiological parameters to be measured, from all those which have been supplied from the source and propagated through the organ;
(e) converting signals generated by said detector to readily analyzed continuous signals and correcting for variations due to fluctuations of the source; and (f) computing instantaneously the values of the detected physiological parameters taking into account the ~ 20 light diffusion effects.
:
DESCRIPTION OF THE DRAWIN~S
A better understanding of the invention may be had by reference to the detailed description which follows, taken in conjunction with the accompanying drawings, in which:
- Fig. 1 is a block diagram representing the fundamental parts of the apparatus object of the present invention - 30 - Fig. 2 is a detailed circuit diagram o~ the powering of the ~lash light source;
- Fig. 3 is showing the positions of -the light detectors;
- 3~ -- FigO 4 is a detailed circuit diagram of the amplifier system and of the sampling system of the signals for the computer;
- Fig. 5 is a block diagram of the computer system used to collect the signals and oE its interface with the light detectors through an analogic/digital converter;
: - Fig. 6 and 7 are showing some typical cuxves of /
oxygen saturation of hemoglobin, oxydation of the cytochrome-c-oxydase and of blood volume measured by rneans of the invention's apparatus in the encephalic region at different respiratory activities in comparison with oxygen level measured by a skin electrode;
- Fig. 8 is a pictorial view of the optical fibers disposition for a simultaneous monitoring of different regions of a same body section.
The most important applications of this type of instrumentation may regard the monitoring of the circulatory and metabolic conditions of the encephala of immature babies, patients who have undergone ne~lrosurgery interventions, interventions of vascular surgery to the carotids, and in general patients un~.er total anesthesia or being subjected to intensive therapy; further applications may involve monitoring of the peripheral vascular system and cases of chronic or acute respiratory insufficiency.
Accordingly, a first object of this patent ap?lication concerns a multiple wavelength pulsed light spectrophotometer for non-invasive monitoring, as illustra-ted by ~igure 1 herein, which comprises the following parts:
1. a light source emitting radiation in the near I.~., consisting of a lamp powered by A.C.~timed pulses;
2. a means of conducting the light to an organ ~' : ' to be monitored;
3. a mea~ of co~ducti~g the light from the monitored organ~
- Fig. 5 is a block diagram of the computer system used to collect the signals and oE its interface with the light detectors through an analogic/digital converter;
: - Fig. 6 and 7 are showing some typical cuxves of /
oxygen saturation of hemoglobin, oxydation of the cytochrome-c-oxydase and of blood volume measured by rneans of the invention's apparatus in the encephalic region at different respiratory activities in comparison with oxygen level measured by a skin electrode;
- Fig. 8 is a pictorial view of the optical fibers disposition for a simultaneous monitoring of different regions of a same body section.
The most important applications of this type of instrumentation may regard the monitoring of the circulatory and metabolic conditions of the encephala of immature babies, patients who have undergone ne~lrosurgery interventions, interventions of vascular surgery to the carotids, and in general patients un~.er total anesthesia or being subjected to intensive therapy; further applications may involve monitoring of the peripheral vascular system and cases of chronic or acute respiratory insufficiency.
Accordingly, a first object of this patent ap?lication concerns a multiple wavelength pulsed light spectrophotometer for non-invasive monitoring, as illustra-ted by ~igure 1 herein, which comprises the following parts:
1. a light source emitting radiation in the near I.~., consisting of a lamp powered by A.C.~timed pulses;
2. a means of conducting the light to an organ ~' : ' to be monitored;
3. a mea~ of co~ducti~g the light from the monitored organ~
4. a detector of at least four radiations ~ith significant wavelengths for the parameter~ to be measured9 from all those w~;ch have been ~upplied from the ~ource and propagated through the organ;
5. an amplifier for con~erting the radiation pulse signal to a readily a~alyzed continuous signal and correcting for variation~ due to fluctuations of the source; and
6. an acqui,qition sgstem including a micro-proces~or adapted to pe~it instanta~eous computation of the values of the detected physiological parameters taking into account the light diffusion effects~
: A particular embodiment of t~is invention will : be now deseribed by way of no~-limitative example.
~: ~
A circuit diagram is shown in Figure 2 of the circuitry for energizing a xenon flash lamp (Type EGeGFx200 or the like), Power for the' light flash is supplied by a capacitor CO charged to a voltage level V0. The capacitor is discharged through the lamp o~ recei~ing 2 5 a trigger pul~e .
.~".~ The triggering pulse is pro~ided by a control~.ed diode D ~ia a tranæformer ~ (Model FY604 ~ EGeG) driYen by a cloc~ C~ in synchro~iæation ~i~h the . mai~æ~ Each time ~hat a pulse reac~es the lamp~ the shaper F ~ill block the ~ucce~ive clock pul~e~ ~or ' ~ ~3~
~, a set time period which may be ~aried at will.
During the te~ts carried out thu~ ~ar9 thi~
time period was 125 ms and/vr 250 msO
The reference character M denotes a photodiode for mo~itoring the light from the lamp~ and P denotes the output preamplifier. The light from the lamp i~
directed to a fiber optic F0 by a glass len~ sy~tem 1,.
A viable variation of the foregoing scheme utili~es instead a high brilliance lamp which is DC powered through a conventional power supply (the lamp being a 75-200W xenon lamp of the Qsram XB0 Type); a chopper is placed in front of the fiber optic v~hich is rotated synchronously with the main~.
Of course, this choice of a light sourc~
involves a modified implementation of the electronic amplifying circuitry3 the duration of the light pulses being here longer than that of a light fla~h.
The light is conducted to the organ to be monitored by a flexible optical fiber of transparent glass and/or plastic material having a diameter in ; the 2 to 10 mm range. The light emerging from the ti~ue~ i~ picked up by another optical fiber generally of the same size. The optical fibers are ~-~. brought to rest on the tissue of the organ to be monitored BUC~ as to en~ure a good contact, ~ generally at a di~tan~e of a fe~ centimeter~ from eaoh other.
To thi~ aim, fvr monitoring an organ of an ; ::
i~dividu~l, the device di~closed in ~S Patents No~s 4,321~930 and 4~380,240 may be used to advantage~
Due to the high diffusion effect prevailing;
it is immaterial whether the two fibers are aligned or form an angle therebetween which may be o~ as much as 180~
Det Figure 3 illustrates the detector arrangeme~t.
The incoming light from the region being monitored and flo~ing through the ~tic~l fiber FO first branches out in two 9 and then illuminates the photocathodes of four photomultipliers PM1/~2,~3,~4 after goi~g through interference filters F1,~2,~3,F4 the front faces ~Yhereof also form an excellent mirror.
Lenses L1,L2,~3,~4 focus the light onto the ~- photocathode. The light path is indicated in dash lines.
The photomultipliers {R928 or R936 by Hammatsu), w~ich are particularl~ responsi~e in the region of the near ~ are supplied ~ith a ~oltage HV which may be ~aried or programmed in the 500 to 17100Y range through separate dividers.
~rom the p~otomultiplier anodes a signal is pic~ed up o~ resistors of relati~e low ~alue (C 3K Q) to maintain a good passband (> 1 ~lHz), and the 3ignal is amplified by pre~mpli~iers PA1rPA2lPA3,PA4 powered r~ by rechargeable batterie~ or bg a ~eparate power supply having a high immunity to noiset in order to _---~ a~oid eleGtromagnetic inductions from ~oltage dischargeG and comi~g o~er the mains. ~he batterie~
are recharged automatically. A different 9 simpler mou~t for the optic~ ia to be obtai~ed by using a four-le~ged fiber optic to illuminate the four photo~ul-tipliers separately. r~he interference filters employed have a mid-amplitude bandwidth rasging from 4 to 25 ~m (preferakl~ of 10 ~m) centered in between 700 and 950 nm and pre-ferably on 7~0,~00,8S0 and 900 ~m, respectively, (alternatively7 on 750~820,850 and 900 ~m, for example).
It would be poasible to increase the number of the channels up to five or six, or e~en above, to thereby e~hance the quantitative assessment of the scattering effects.
Sho~n in Figure 4 is an embodiment of the ~mpli~ier system and sampling eircuitry for acquisition to the computer.
The aignal~ from each of the channels, i.e~ t~at from the photodiode M of the light source and those from t~e preamplifiers PA1,PA2,PA3,PA4, are ampli~ied by a system of fast amplifier~ formed o~ two inverters H, the first of which also functions as a shaper to determi~e a fixed upgoing time (~ 2 ~s) by means of the integrating capacitor pro~rided o~ the feedback.
The two inverters are followed by a alower atage L and a sample-and-hold sampler SH~ The control signal to the sampli~ oircuit i9 ~uppl ied by a shaper F1 ~hich, in turn, ge~erates a trigger signal TR to _. co~trol the computer acquisition ~equence.
The individual channels are compared with the mo~itor in the differential stage D, ~o as to _ 9 _ ~limina~e signal fluctuations due to the souxoe oscillatio~s. T~e ~ignals Cl~C2,C3,C4 thu~ ob-tained and the trigger signal TR are supplied to the acquisition system.
Acq~isition S~stem Shown diagramatically in Figure 5 is a viable embodiment of the acquisition system for the instrument. A microprocessor A, 6502 from Apple II
is employed v~th a commercial ISAAC I/O syst~m I from Cyborg Co. capable of converting many analog signals sequentially and then passing them to the micro-processor.
The ISAAC sy~tem al~o allows analog signals to ~e passed to an external plotter PL -to provide plot B ' of the data obtained.
~he microprocessor is connected to two disk dri~ers D1 and D2, a printer S~, and to the display TY. The storage capacity of the microprocessor employed is of 48 kilobyte~. Al~o used is an additional 128 ~bytes high-speed storage card ~hich operate3 as a Yirtual disk. ~he same function~ m~y be performed, of course? practically by any other microprocessor : having comparable operating capabilitie~. The signal T~ ~rom the moni~or (indicated at ~ in Figure~ 2 and ; 25 4) initiate~ the acquisition ~equence. Once the data ~ are tran~ferred to the computer memorie~ it become~
,~. . .~
po ssible to di~play, either on line or ~ome time _ afterwardst the plots by calculati~g the value~ of ; th~ record~d p~y~iologic~l parameters~ such as the hematie volume, hemoglobin oxygen saturation, and ~23~
redox le~el of cytochrome-c-oxida~e9 through a~
algorithm which utilizes the insta~taneous value of the ~ignal at the four wavelengths.
The parameters o~ this calculation are obtained by an cpti~ization process of the ~alues calculated according to the theoretical model (D.V.Luebbers;
Advances in Exp. ~edicine and Biology, ~, 45-54, 1973) and the experimental data.
In addition to the signals from the channels C1-C4, se~eral other magnitudes from other instruments (~) are acquired.
It will be appreciated that various data processing programs may be utilized with the micro-proce~sor which allow some of the noise to be filtered out, spikes caused by instantaneous shift~ in the plots due to changes in the fiber optics-to-tissue contact to be detected and corrected, ~nd so forth, The in~trument just described affords the following adYantage~:
1~ pulse operation ma~es the ambient light background ~irtually negligible;
2. the monitor enables correction for any fluctuations in the source intensity;
3. the light measurement transmitted on at least four waYelengths enables computation of the hemoglobin ~,~, content of the tissue~ being ob6erved~ o~ its o~ygenation level, and of ~he oxyreduction state of ~ cytochrome-c oxida~e;
:~ 4. real time prvces~ing become~ ea~ible through a calculation proce~s which enable6 correction at :
any time instant of the ab~orption values for the ef~ect due to light diffu~ion;
5. the measurement stability is enhanced by t~e u~e of a ~eparate power supply for the preamplifiers a~d by synchronization o~ the source with the main~;
6~ the micropocessor pernLits the detection and correction of an~ instantaneous shifts in the plot~
due to variations in the contact between the fiber optics and tissue; and
: A particular embodiment of t~is invention will : be now deseribed by way of no~-limitative example.
~: ~
A circuit diagram is shown in Figure 2 of the circuitry for energizing a xenon flash lamp (Type EGeGFx200 or the like), Power for the' light flash is supplied by a capacitor CO charged to a voltage level V0. The capacitor is discharged through the lamp o~ recei~ing 2 5 a trigger pul~e .
.~".~ The triggering pulse is pro~ided by a control~.ed diode D ~ia a tranæformer ~ (Model FY604 ~ EGeG) driYen by a cloc~ C~ in synchro~iæation ~i~h the . mai~æ~ Each time ~hat a pulse reac~es the lamp~ the shaper F ~ill block the ~ucce~ive clock pul~e~ ~or ' ~ ~3~
~, a set time period which may be ~aried at will.
During the te~ts carried out thu~ ~ar9 thi~
time period was 125 ms and/vr 250 msO
The reference character M denotes a photodiode for mo~itoring the light from the lamp~ and P denotes the output preamplifier. The light from the lamp i~
directed to a fiber optic F0 by a glass len~ sy~tem 1,.
A viable variation of the foregoing scheme utili~es instead a high brilliance lamp which is DC powered through a conventional power supply (the lamp being a 75-200W xenon lamp of the Qsram XB0 Type); a chopper is placed in front of the fiber optic v~hich is rotated synchronously with the main~.
Of course, this choice of a light sourc~
involves a modified implementation of the electronic amplifying circuitry3 the duration of the light pulses being here longer than that of a light fla~h.
The light is conducted to the organ to be monitored by a flexible optical fiber of transparent glass and/or plastic material having a diameter in ; the 2 to 10 mm range. The light emerging from the ti~ue~ i~ picked up by another optical fiber generally of the same size. The optical fibers are ~-~. brought to rest on the tissue of the organ to be monitored BUC~ as to en~ure a good contact, ~ generally at a di~tan~e of a fe~ centimeter~ from eaoh other.
To thi~ aim, fvr monitoring an organ of an ; ::
i~dividu~l, the device di~closed in ~S Patents No~s 4,321~930 and 4~380,240 may be used to advantage~
Due to the high diffusion effect prevailing;
it is immaterial whether the two fibers are aligned or form an angle therebetween which may be o~ as much as 180~
Det Figure 3 illustrates the detector arrangeme~t.
The incoming light from the region being monitored and flo~ing through the ~tic~l fiber FO first branches out in two 9 and then illuminates the photocathodes of four photomultipliers PM1/~2,~3,~4 after goi~g through interference filters F1,~2,~3,F4 the front faces ~Yhereof also form an excellent mirror.
Lenses L1,L2,~3,~4 focus the light onto the ~- photocathode. The light path is indicated in dash lines.
The photomultipliers {R928 or R936 by Hammatsu), w~ich are particularl~ responsi~e in the region of the near ~ are supplied ~ith a ~oltage HV which may be ~aried or programmed in the 500 to 17100Y range through separate dividers.
~rom the p~otomultiplier anodes a signal is pic~ed up o~ resistors of relati~e low ~alue (C 3K Q) to maintain a good passband (> 1 ~lHz), and the 3ignal is amplified by pre~mpli~iers PA1rPA2lPA3,PA4 powered r~ by rechargeable batterie~ or bg a ~eparate power supply having a high immunity to noiset in order to _---~ a~oid eleGtromagnetic inductions from ~oltage dischargeG and comi~g o~er the mains. ~he batterie~
are recharged automatically. A different 9 simpler mou~t for the optic~ ia to be obtai~ed by using a four-le~ged fiber optic to illuminate the four photo~ul-tipliers separately. r~he interference filters employed have a mid-amplitude bandwidth rasging from 4 to 25 ~m (preferakl~ of 10 ~m) centered in between 700 and 950 nm and pre-ferably on 7~0,~00,8S0 and 900 ~m, respectively, (alternatively7 on 750~820,850 and 900 ~m, for example).
It would be poasible to increase the number of the channels up to five or six, or e~en above, to thereby e~hance the quantitative assessment of the scattering effects.
Sho~n in Figure 4 is an embodiment of the ~mpli~ier system and sampling eircuitry for acquisition to the computer.
The aignal~ from each of the channels, i.e~ t~at from the photodiode M of the light source and those from t~e preamplifiers PA1,PA2,PA3,PA4, are ampli~ied by a system of fast amplifier~ formed o~ two inverters H, the first of which also functions as a shaper to determi~e a fixed upgoing time (~ 2 ~s) by means of the integrating capacitor pro~rided o~ the feedback.
The two inverters are followed by a alower atage L and a sample-and-hold sampler SH~ The control signal to the sampli~ oircuit i9 ~uppl ied by a shaper F1 ~hich, in turn, ge~erates a trigger signal TR to _. co~trol the computer acquisition ~equence.
The individual channels are compared with the mo~itor in the differential stage D, ~o as to _ 9 _ ~limina~e signal fluctuations due to the souxoe oscillatio~s. T~e ~ignals Cl~C2,C3,C4 thu~ ob-tained and the trigger signal TR are supplied to the acquisition system.
Acq~isition S~stem Shown diagramatically in Figure 5 is a viable embodiment of the acquisition system for the instrument. A microprocessor A, 6502 from Apple II
is employed v~th a commercial ISAAC I/O syst~m I from Cyborg Co. capable of converting many analog signals sequentially and then passing them to the micro-processor.
The ISAAC sy~tem al~o allows analog signals to ~e passed to an external plotter PL -to provide plot B ' of the data obtained.
~he microprocessor is connected to two disk dri~ers D1 and D2, a printer S~, and to the display TY. The storage capacity of the microprocessor employed is of 48 kilobyte~. Al~o used is an additional 128 ~bytes high-speed storage card ~hich operate3 as a Yirtual disk. ~he same function~ m~y be performed, of course? practically by any other microprocessor : having comparable operating capabilitie~. The signal T~ ~rom the moni~or (indicated at ~ in Figure~ 2 and ; 25 4) initiate~ the acquisition ~equence. Once the data ~ are tran~ferred to the computer memorie~ it become~
,~. . .~
po ssible to di~play, either on line or ~ome time _ afterwardst the plots by calculati~g the value~ of ; th~ record~d p~y~iologic~l parameters~ such as the hematie volume, hemoglobin oxygen saturation, and ~23~
redox le~el of cytochrome-c-oxida~e9 through a~
algorithm which utilizes the insta~taneous value of the ~ignal at the four wavelengths.
The parameters o~ this calculation are obtained by an cpti~ization process of the ~alues calculated according to the theoretical model (D.V.Luebbers;
Advances in Exp. ~edicine and Biology, ~, 45-54, 1973) and the experimental data.
In addition to the signals from the channels C1-C4, se~eral other magnitudes from other instruments (~) are acquired.
It will be appreciated that various data processing programs may be utilized with the micro-proce~sor which allow some of the noise to be filtered out, spikes caused by instantaneous shift~ in the plots due to changes in the fiber optics-to-tissue contact to be detected and corrected, ~nd so forth, The in~trument just described affords the following adYantage~:
1~ pulse operation ma~es the ambient light background ~irtually negligible;
2. the monitor enables correction for any fluctuations in the source intensity;
3. the light measurement transmitted on at least four waYelengths enables computation of the hemoglobin ~,~, content of the tissue~ being ob6erved~ o~ its o~ygenation level, and of ~he oxyreduction state of ~ cytochrome-c oxida~e;
:~ 4. real time prvces~ing become~ ea~ible through a calculation proce~s which enable6 correction at :
any time instant of the ab~orption values for the ef~ect due to light diffu~ion;
5. the measurement stability is enhanced by t~e u~e of a ~eparate power supply for the preamplifiers a~d by synchronization o~ the source with the main~;
6~ the micropocessor pernLits the detection and correction of an~ instantaneous shifts in the plot~
due to variations in the contact between the fiber optics and tissue; and
7. it becomes possible to correlate the measure-me~ts taken by absoprtion in the near I.~. with those derived ~rom other instruments.
By way of exarnple Figures 6 a~d 7 are sho\, in,~;
the recorded plots ~or the aforesaid parameters as measured in the encephalon together with a measurement ; of the oxygen pressure at skin level taken with a transcutaneous electrode ~radiometer, ~odel TC~ 2).
Figure 6 shows a typical plot~obtained during change~ in the respiratory activity (hyperventilation-apnea). On the ab~cissa is the time in minutes On the ordinate, an mmHg scale relating to curve 1 is reproduced on the left.
Section A of the Figure corresponds to a condition of normal breathing, section B to a condition of hyperven~ilation, section G to a ` condition of apnea~ and section D again to a .~... .~
` condîtion of norm~l breathing.
The curve 2 is a measure of the hemoglobin sa*uration level9 ~he curYe 3 is a mea~ure o~ the cytochrome-c~oxidase o~ydation state, and the curYe `, ' ~:
2%~i 4 i~ a measure of the hematic ~olume.
The oxygen level in the arterial blood o the a~m ha~ been recorded for reference by means of a tran~cutaneous electrode ~Curve 1).
During the apnea, the hemoglobin ~aturatio~
level at arterial level drops from 95% down to abou-t 55~9 the oxireductive state of cytochrome-c-oxidase drops by about 155Jo from an estimated level of about 80p9 and the hematic volume increases to 12Cp from 10~.
It should be noted that the value of this parameter depends to sorne extent on the model asswned and the assumed values for the cerebral hematocri~, generally lower than the peripheral one (~l.E.Phelps et al., J. Appl. Physical 35, 275-280, 1983).
~i~ure 7 shows instead. a typical plot obtained duri~g in~alation of different gas mixtures ~air, pure ~-~ oxygen, hypoxic mixture~.
On the ab3cissa is the time in minute~.
On the ordinate, there is reproduced an mmHg scale relating to the curve 1~
In section A of the Figure, the condition is that of air breathing, in section B of breathing a hypoxic : ~ 25 mix~ure (2 10Cj~" N2 90Ck~ ~ ~d in section C ~he condition is that of breathing pure 2 The curve 2 i~ a measure o~ the oxidati~e ~tate of cytoohrom~-c--oxida~e ,~ the curve 3 is a measure OI
the ~emogloki~ saturàtion level~ and ~he ourve 4 i~
a measure of the hematic ~olume.
~3~
Here too, the level o 2 i~ the arterial blood o f th2 arm has been recorded for reference by mean~
of a transcutaneous electrode (Curve 1) b ~'~ile breathing the hypoxic mixture, the oxidatiYe state of cytochrome-c-oxidase does not vary appreciably, the saturatio~ level of hemoglobin decrea~e~ from 90~0 to about 650~9 and the hematic Yolume change~ from 10C~o to about 11~.
Based on the general ~cheme outlined above 9 a more complex instrumen~ation may be pro~ided to simultaneou~ly monitor different region~ of one and the ~ame organ.
The arrangement of theoptic~l fiber ~0 for such an instrument is shown in Figure 8 by way of e~ample.
Shown schematically at F~ i5 the ~ource of light, Ç
which may be embodied as in the preceding example~
ultiple leg fibera are used, and i~ each region ~he tr~n~mitted light is measured at at least four na~elengths.
The several detectors may be replaced ad~ntage-ously with a picture intensifier I (e.g. Thomso~-CSF
9403) coupled with a cluster of solid state siliGon detectors A.
The filter s~tem ~ ma~ be rep~aced with a si~gle fi1ter ~arying in the 750 to 900 nm.
he electric aig~als from the detector~ E ahould t~en be proce~ed b~ a ~y~tem of &mplifier~ ~imilar to the one diacussed hereinabove ~
more comple~ ins~rume~t like the one disclo~ed herein woula enable mapping of ~he metaboli~m and , ~
- 14 _ va~cular ~tate of cerebral cortex in keeping ~ith the most up-to date imaging methodics~
Also provided by this invent:ion is a spectrophotometric method for measuring circulatory and local meta~olism parameters in living organs by non-inYaSiVe monitoring, which utilizes the spectrophotometer described in the foregoing.
,6.. "
.
~'
By way of exarnple Figures 6 a~d 7 are sho\, in,~;
the recorded plots ~or the aforesaid parameters as measured in the encephalon together with a measurement ; of the oxygen pressure at skin level taken with a transcutaneous electrode ~radiometer, ~odel TC~ 2).
Figure 6 shows a typical plot~obtained during change~ in the respiratory activity (hyperventilation-apnea). On the ab~cissa is the time in minutes On the ordinate, an mmHg scale relating to curve 1 is reproduced on the left.
Section A of the Figure corresponds to a condition of normal breathing, section B to a condition of hyperven~ilation, section G to a ` condition of apnea~ and section D again to a .~... .~
` condîtion of norm~l breathing.
The curve 2 is a measure of the hemoglobin sa*uration level9 ~he curYe 3 is a mea~ure o~ the cytochrome-c~oxidase o~ydation state, and the curYe `, ' ~:
2%~i 4 i~ a measure of the hematic ~olume.
The oxygen level in the arterial blood o the a~m ha~ been recorded for reference by means of a tran~cutaneous electrode ~Curve 1).
During the apnea, the hemoglobin ~aturatio~
level at arterial level drops from 95% down to abou-t 55~9 the oxireductive state of cytochrome-c-oxidase drops by about 155Jo from an estimated level of about 80p9 and the hematic volume increases to 12Cp from 10~.
It should be noted that the value of this parameter depends to sorne extent on the model asswned and the assumed values for the cerebral hematocri~, generally lower than the peripheral one (~l.E.Phelps et al., J. Appl. Physical 35, 275-280, 1983).
~i~ure 7 shows instead. a typical plot obtained duri~g in~alation of different gas mixtures ~air, pure ~-~ oxygen, hypoxic mixture~.
On the ab3cissa is the time in minute~.
On the ordinate, there is reproduced an mmHg scale relating to the curve 1~
In section A of the Figure, the condition is that of air breathing, in section B of breathing a hypoxic : ~ 25 mix~ure (2 10Cj~" N2 90Ck~ ~ ~d in section C ~he condition is that of breathing pure 2 The curve 2 i~ a measure o~ the oxidati~e ~tate of cytoohrom~-c--oxida~e ,~ the curve 3 is a measure OI
the ~emogloki~ saturàtion level~ and ~he ourve 4 i~
a measure of the hematic ~olume.
~3~
Here too, the level o 2 i~ the arterial blood o f th2 arm has been recorded for reference by mean~
of a transcutaneous electrode (Curve 1) b ~'~ile breathing the hypoxic mixture, the oxidatiYe state of cytochrome-c-oxidase does not vary appreciably, the saturatio~ level of hemoglobin decrea~e~ from 90~0 to about 650~9 and the hematic Yolume change~ from 10C~o to about 11~.
Based on the general ~cheme outlined above 9 a more complex instrumen~ation may be pro~ided to simultaneou~ly monitor different region~ of one and the ~ame organ.
The arrangement of theoptic~l fiber ~0 for such an instrument is shown in Figure 8 by way of e~ample.
Shown schematically at F~ i5 the ~ource of light, Ç
which may be embodied as in the preceding example~
ultiple leg fibera are used, and i~ each region ~he tr~n~mitted light is measured at at least four na~elengths.
The several detectors may be replaced ad~ntage-ously with a picture intensifier I (e.g. Thomso~-CSF
9403) coupled with a cluster of solid state siliGon detectors A.
The filter s~tem ~ ma~ be rep~aced with a si~gle fi1ter ~arying in the 750 to 900 nm.
he electric aig~als from the detector~ E ahould t~en be proce~ed b~ a ~y~tem of &mplifier~ ~imilar to the one diacussed hereinabove ~
more comple~ ins~rume~t like the one disclo~ed herein woula enable mapping of ~he metaboli~m and , ~
- 14 _ va~cular ~tate of cerebral cortex in keeping ~ith the most up-to date imaging methodics~
Also provided by this invent:ion is a spectrophotometric method for measuring circulatory and local meta~olism parameters in living organs by non-inYaSiVe monitoring, which utilizes the spectrophotometer described in the foregoing.
,6.. "
.
~'
Claims (21)
1. A multiple wavelength pulsed light spectro-photometer for non-invasive monitoring, comprising:
(a) a light source emitting a light beam in-cluding radiation in the near I.R. and consisting of a lamp powered by AC-timed pulses;
(b) a means of conducting said light beam to an organ to be monitored;
(c) a means of conducting light from the monitored organ;
(d) a detector for receiving said light and detecting at least four radiations at significant wavelengths corresponding to physiological parameters to be measured, from all those which have been supplied from the source and propagated through the organ;
(e) an amplifier for converting signals generated by said detector to readily analyzed continuous signals and correcting for variations due to fluctuations of the source;
and (f) an acquisition system including a micropro-cessor adapted to permit instantaneous computation of the value of the detected physiological parameters taking into account the light diffusion effects.
(a) a light source emitting a light beam in-cluding radiation in the near I.R. and consisting of a lamp powered by AC-timed pulses;
(b) a means of conducting said light beam to an organ to be monitored;
(c) a means of conducting light from the monitored organ;
(d) a detector for receiving said light and detecting at least four radiations at significant wavelengths corresponding to physiological parameters to be measured, from all those which have been supplied from the source and propagated through the organ;
(e) an amplifier for converting signals generated by said detector to readily analyzed continuous signals and correcting for variations due to fluctuations of the source;
and (f) an acquisition system including a micropro-cessor adapted to permit instantaneous computation of the value of the detected physiological parameters taking into account the light diffusion effects.
2. A pulsed light spectrophotometer as in claim 1, wherein the source as recited under (a) comprises a xenon flash lamp.
3. A pulsed light spectrophotometer as in claim 1, wherein the conducting means as recited under (b) and (c) comprises a flexible optical fiber.
4. A pulsed light spectrophotometer according to claim 3, wherein said flexible optical fiber is made of transparent glass.
5. A pulsed light spectrophotometer according to claim 3, wherein said flexible optical fiber is made of plastics.
6. A pulsed light spectrophotometer according to claim 3, wherein said flexible optical fiber is made of transparent glass and plastics.
7. A pulsed light spectrophotometer as in claim 1, wherein said conducting means as recited under (b) and (c) comprises a multiple leg flexible optical fiber.
8. A pulsed light spectrophotometer as in claim 3, wherein said flexible optical fiber has a diameter in the 2 to 10 mm range.
9. A pulsed light spectrophotometer as in claim 1, wherein the light from the organ being monitored, after going through interference filters, illuminates the photoca-thode of at least four photomultipliers.
10. A pulsed light spectrophotometer as in claim 1, wherein the light from the organ being monitored illuminates the photocathode of a picture intensifier coupled with a cluster of solid state detectors.
11. A pulsed light spectrophotometer as in claim 9, wherein said photomultipliers are responsive in the near I.R. region.
12. A pulsed light spectrophotometer as in claim 9, wherein said interference filters have a mid-height bandwidth within the range of 4 to 25 nm centered in the 700 to 950 nm range.
13. A pulsed light spectrophotometer as in claim 9, wherein said interference filters have a mid-height bandwidth within the range of 4 to 25 nm centered at 750,800,850 and 900 nm, respectively.
14. A pulsed light spectrophotometer as in claim 9, wherein said interference filters have a mid-height bandwidth within the range of 4 to 25 nm centered at 750,820,850 and 900 nm, respectively.
15. A pulsed light spectrophotometer as in claim 9, wherein a single filter variable within the range of 750 to 900 nm is used.
16. A pulsed light spectrophotometer as in claim 9, wherein the signal from the photodiode and those from the preamplifiers are amplified through a system of high-speed amplifiers.
17. A pulsed light spectrophotometer as in claim 16, wherein said high-speed amplifier system comprises two inverters the first of which also functions as a shaper.
18. A pulsed light spectrophotometer as in claim 17, wherein said two . are followed by a slower stage and a sample-and-hold sampler.
19. A pulsed light spectrophotometer as in claim 1, wherein each signal converted by said amplifier is compared to a monitor in a differential stage.
20. A spectrophotometric method for measuring circulatory and local metabolism in living organs by non-invasive monitoring, comprising steps of:
(a) emitting a light beam including radiation in the near I.R. and consisting of a lamp powered by AC-timed pulses;
(b) conducting said light beam to an organ to be monitored;
(c) conducting light from the monitored organ;
(d) receiving said light and detecting at least four radiations at significant wavelengths corresponding to physiological parameters to be measured, from all those which have been supplied from the source and propagated through the organ;
(e) converting signals generated by said detector to readily analyzed continuous signals and correcting for variations due to fluctuations of the source; and (f) computing instantaneously the values of the detected physiological parameters taking into account the light diffusion effects.
(a) emitting a light beam including radiation in the near I.R. and consisting of a lamp powered by AC-timed pulses;
(b) conducting said light beam to an organ to be monitored;
(c) conducting light from the monitored organ;
(d) receiving said light and detecting at least four radiations at significant wavelengths corresponding to physiological parameters to be measured, from all those which have been supplied from the source and propagated through the organ;
(e) converting signals generated by said detector to readily analyzed continuous signals and correcting for variations due to fluctuations of the source; and (f) computing instantaneously the values of the detected physiological parameters taking into account the light diffusion effects.
21. A spectrophotometric method according to claim 20, wherein several regions of one organ are simul-tanously monitor.
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
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IT22247A/84 | 1984-08-07 | ||
IT8422247A IT1206462B (en) | 1984-08-07 | 1984-08-07 | MULTI-WAVE LENGTH PULSED LIGHT PHOTOMETER FOR NON-INVASIVE MONITORING. |
Publications (1)
Publication Number | Publication Date |
---|---|
CA1239225A true CA1239225A (en) | 1988-07-12 |
Family
ID=11193621
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
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CA000488142A Expired CA1239225A (en) | 1984-08-07 | 1985-08-06 | Multiple wavelength light photometer for non-invasive monitoring |
Country Status (11)
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US (1) | US5088493A (en) |
CA (1) | CA1239225A (en) |
DE (1) | DE3528369A1 (en) |
DK (1) | DK355085A (en) |
ES (1) | ES8700434A1 (en) |
FI (1) | FI853000L (en) |
FR (1) | FR2571491B1 (en) |
GB (1) | GB2162939B (en) |
IT (1) | IT1206462B (en) |
NO (1) | NO853080L (en) |
SE (1) | SE8503687L (en) |
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DE3734588A1 (en) * | 1987-10-13 | 1989-04-27 | Schmidt Werner Dr Rer Nat Habi | Recording photometer of high adaptability |
IT1213864B (en) * | 1987-12-23 | 1990-01-05 | Consiglio Nazionale Ricerche | METHOD OF DETECTION OF ENTEROGASTRIC REFLUX AND EQUIPMENT FOR THE IMPLEMENTATION OF THAT METHOD |
US5036853A (en) * | 1988-08-26 | 1991-08-06 | Polartechnics Ltd. | Physiological probe |
AU614660B2 (en) * | 1988-08-26 | 1991-09-05 | Polartechnics Limited | Physiological probe |
EP0358809A1 (en) * | 1988-09-15 | 1990-03-21 | Hellige GmbH | Spectrophotometer for monitoring a living organism |
US5873821A (en) * | 1992-05-18 | 1999-02-23 | Non-Invasive Technology, Inc. | Lateralization spectrophotometer |
US5119815A (en) * | 1988-12-21 | 1992-06-09 | Nim, Incorporated | Apparatus for determining the concentration of a tissue pigment of known absorbance, in vivo, using the decay characteristics of scintered electromagnetic radiation |
US5353799A (en) | 1991-01-22 | 1994-10-11 | Non Invasive Technology, Inc. | Examination of subjects using photon migration with high directionality techniques |
CN1012557B (en) * | 1990-03-17 | 1991-05-08 | 北京海淀龙兴医疗设备科技开发公司 | Detection imaging method of soft tissue and its apparatus |
US5441053A (en) * | 1991-05-03 | 1995-08-15 | University Of Kentucky Research Foundation | Apparatus and method for multiple wavelength of tissue |
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1984
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1985
- 1985-07-24 GB GB08518699A patent/GB2162939B/en not_active Expired
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- 1985-08-05 FI FI853000A patent/FI853000L/en not_active Application Discontinuation
- 1985-08-05 DK DK355085A patent/DK355085A/en not_active Application Discontinuation
- 1985-08-05 NO NO853080A patent/NO853080L/en unknown
- 1985-08-06 FR FR858512047A patent/FR2571491B1/en not_active Expired - Fee Related
- 1985-08-06 CA CA000488142A patent/CA1239225A/en not_active Expired
- 1985-08-06 ES ES545924A patent/ES8700434A1/en not_active Expired
- 1985-08-07 DE DE19853528369 patent/DE3528369A1/en not_active Withdrawn
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1988
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IT8422247A0 (en) | 1984-08-07 |
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NO853080L (en) | 1986-02-10 |
FI853000A0 (en) | 1985-08-05 |
GB2162939B (en) | 1988-09-28 |
DK355085A (en) | 1986-02-08 |
GB2162939A (en) | 1986-02-12 |
ES8700434A1 (en) | 1986-10-01 |
US5088493A (en) | 1992-02-18 |
IT1206462B (en) | 1989-04-27 |
FR2571491A1 (en) | 1986-04-11 |
ES545924A0 (en) | 1986-10-01 |
SE8503687D0 (en) | 1985-08-02 |
SE8503687L (en) | 1986-02-08 |
DK355085D0 (en) | 1985-08-05 |
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