CA1140773A - Apparatus for measuring pneusis function of bio-organ and textus - Google Patents
Apparatus for measuring pneusis function of bio-organ and textusInfo
- Publication number
- CA1140773A CA1140773A CA000346985A CA346985A CA1140773A CA 1140773 A CA1140773 A CA 1140773A CA 000346985 A CA000346985 A CA 000346985A CA 346985 A CA346985 A CA 346985A CA 1140773 A CA1140773 A CA 1140773A
- Authority
- CA
- Canada
- Prior art keywords
- light
- organ
- pneusis
- light source
- means adapted
- 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
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Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
Abstract
ABSTRACT OF THE DISCLOSURE
Apparatus for measuring pneusis function of bio-oxgan and textus is disclosed, wherein a portion to be diag-nosed is subject to interruption of oxygen supply in biospectroscopy. A reflection spectrum characteristic variation per time is measured to provide an information source. Such information is converted into an electrical signal to indicate the pneusis function.
Apparatus for measuring pneusis function of bio-oxgan and textus is disclosed, wherein a portion to be diag-nosed is subject to interruption of oxygen supply in biospectroscopy. A reflection spectrum characteristic variation per time is measured to provide an information source. Such information is converted into an electrical signal to indicate the pneusis function.
Description
1 BACKGROUND OF T~E ~N~ENTIO~
The present invention relates to apparatus for measuring pneusis function of a bio-organ and textus, and more particularly, to a type thereof which analyzes the variation with time of the reflection spectrum characteristlc in bio-spectrometry.
Conventional clinical diagnosis and medical ~esearch has involved merely the visual observatlon of the internal organ or textus. Recently, varlous parts of the internal organs have lQ been able to be directly observed with m~croscopy in accordance with the utilization of optical transm-ssion systems such as optical fibers employed, for example, ln gastro cameras, thus providing a substantial contr~but~.on to clinicai diagnosis~
However, such microscopy does not prov~de for objective and quan-titative diagnosis, since tt depends on t~e individual doctor' 5 skill and experience.
The ox~gen pneusis of a textus ma~ ~e e~amined by enucleation thereof or may be calculated as a pneusis of the overall organ by-comparison between veinous and artery ox~gen flow thereof. However, the organ and textus may be subjected to disease due to parasites during examination of the pneusis function thereof.
SUMU~ OF THE ~NVENTION
It is an object of the present invention to overcome the above-mentio~ned drawbacks and to provide a novel apparatus for measuring pneusis function of bio-organ ana textus~
Another object of this invention is to provide such an apparatus capable of measuring the pneUsis function while elimin-ating risks of disease due to parasites, Still another object of: this invention is to provide '773 1 such apparatus capable of ~inding out the initial abnormalities of the pneusis function of the internal organ and textus.
Still another object of thls invention is to provide such apparatus for ~inding out initial abnormalities of the pneusis function which'are not capable of being recognized with microscopic methods.
In accordan~e wtth the present invention, the internal organ and textus to be diagnosed ls subjected to interruption of oxygen supply ~for example, by pressurization), and the reflectin~
spectrum characteristic variation per time is measured. This variation permits determination of the pneus;~,s function of the internal organ and textus. Pressures utiI~ed in the pressurization may exceed maximum blood pressures~
Accordingly, in one of its aspects the present invention provides an apparatus for measuring the pneusis function of a bio-organ and textus, sald apparatus comprising:
(a) a light source adapted to emit light to the or~an to be diagnosed;
(b) transmission means adapted to receiye and transmit light reflected by sqid organ;
(cl control means adapted to control o~ygen ~upply to said organ;
~ d~ conversion means adapted to conYert said trans-mitted and reflected light from said organ to electrical signals;
(el, processing means adapted to calculate t~e resultant values of the pneusis function from said elec-trical signals; and (f~ display means adapted to display said resultant values.
~,:'" .
177;~ "
1 B~IEF DESCRIPTION OF THE ~R~INGS
Further objects and advantages of the invention will appear from the following description taken together with the accompanying drawing in which:
Fig . 1 iS a graphical representation showing diffused reflection spectrum varia~ion per time relative to the internal organ after interruption of the oxygen supply;
Fig. 2 is a graphical representation showing the relationship between time after pressurization and relative absorbance of deoxy hemoglobin and oxyhemoglobin;
Fig. 3 is a schematic view showing an apparatus for conducting a method of this invention;
Fig. 4 is a schematic view showing an apparatus for conducting a method of this inven~ion, wherein light splitting means and neighbouring members are illustrated in more detail, and Fig. 5 is a schem~atic view showing another embodiment of the apparatus for conducting a method of this invention.
DETAILED DESCRIPTION OF THE INVENTION
The present invention is based on a discovery with respect to reflection spectrum characteristic variation per time in a biospectroscopy, and the technical improvement is ascribed to the discovery. Fig. 1 shows a reflection characteristic of part of an internal organ or textus subjected to interruption of oxygen supplylthereto. The horizontal and vextical axis stand for wave length and reflection light absorbance, respectively.
An uppermost curvature A is obtained during oxygen supply to the internal organ, whereas the remaining curvatures B through I are obtained during interruption of oxygen supply to part of the organ. These curvatures show spectrum variation ' .
1 per time. As is apparent from the curvature A, two peaks of oxyhemoglobin (hereinafter simply re~erred to "oxy-Hb''~ are observed in blood flow in the organ. On the other hand, after interruption of the oxygen supply (after pressuriæation) relative absorbance is greatly reduced, and the spectropattern is greatly changed as sho~n in curvatures B to I.
Further, as shown in Fig. 2, decrease of the absorbance is terminated at equi-absorbance point between oxy-Hb and deoxy hemoglobin (hereinafter simply referred to "deoxy-Hb") for about l to 2 seconds after the pressurization. This point i~ at the wave length of ~l and ~2nm, for example, 569nm and 586nm, respect-ively. On the other hand, the decrease of the absorbance at the peak point (having wave length of ~3 for example 577nm) o~ the oxy-Hb still continues for about further a few seconds.
The absorbance decrease for about l to 2 seconds is considered to occur in accordance with the decrease of Hb amount.
The decrease of the Hb amount is attributed to the expulsion of the almost all of the blood in the local blood path due to pres-surization, since absorbances at equi-absorbance points ~lnm, ~ ~2nm between oxy-Hb and deoxy-Hb are simultaneously reduced.
On the other hand, the continuous absorbance reduction at the wave length of ~3nm is considered to occur by the con-vertion of oxy-Hb into deoxy-~ due to absorbance increase adjacent to bottom point having wave length of ~4 ~for example, 555nm~
of thè oxy-Hb. ,That is, local blood flow is completely blocked due to pressurization, and residual oxygen molecules are con-sumed due to pneusis of local cells, so that all of the Hb becomes deoxy-Hb.
Therefore, measurement of the variation characteristic per time concerning the convertion of oxy-Hb to deoxy-Hb, i.e.~
~ ~ cC
'~
1 the measuremen-t of the pneusis function can be made by measuring reflection spectrum at the equi-absorbance points ~ 2 of the oxy-Hb and deoxy-Hb, and at the characteristic point ~3 of either one of the oxy-Hb and deoxy-Hb.
According to the foregoing description~ peak point ~3 of the oxy-Hb is regarded as a characteristic point. However, it is also possible to conduct measurement at a bottom point of oxy~
Hb or at a peak or bottom point of deoxy-Hb.
One of the embodiments of an apparatus for measuring pneusis function according to the present invention is shown in Fig. 3, wherein a light source 1 such as a tungst~n-iodine lamp, a xenon lamp, and a mercury lamp emits various kind of light having different wave lengths from one another. Reference numeral 2-1 designates an optical fiber adapted to introduce light from the light source 1 into an internal organ to be examined.
Reference numeral 2-2 designates a second optical fiber adapted to introduce reflection light from the or~an into a light splitting means such as spectroscope 4. Further, a pressurization control portion 3 is provided in order to interrupt oxygen supply into ~ the organ. The pressurization ~orce be higher than the maximum blood pressure. The light source 1 and the optical fiber 2-1 are not requisite members in view of the measuring environment and reflection factor of the portion to be measured.
At the light splitting means 4, light having specific wave length i5 ,selected and is introduced into a photo-electric transducer 5, at which the light is converted into an electrical signal. The electrical signal is processed at a processing unit 6, and the pneusis function is indicated at an indicator 7.
According to an embodiment shown in Fig. 4, a plurality of optical fibers are formed as a fiber bundle 2~2. These .,;~;......................... .
7~3 1 fibers are divided into groups, for example, three groups coin-dicent with the numbers of wave length to be measured. Further, corresponding filters 4-1,4-2,4-~ having diferent transmission wave length ~ 2~ ~3 with one another are provided to receive respective portions of the light and split the light. The light thus splitted is converted into electrical signals by respective photoelectric transducers 5-1,5-2,5-3.
Another embodiment according to the present invention is shown in Fig. 5, wherein like parts and components are designated by the same reference numerals as those shown in the foregoing embodiments. In the embodiment shown in Fig. 5, light which has been split is irradiated toward a portion to be measured. Light sources 1-1,1-2,1-3 are positioned at different places with one another. Filters 4-1, 4-2, 4-3 are provided in order to split light having requiring wave length from the corresponding light sources. Further, a rotary mirror 8 is provided so as to selectively orient some of the light toward an optical fiber 2-1 adapted to introduce the light into the portion to be measured. The rotation of the rotary mirror 8 is controlled by a processing circuit 6. An optical fiber 2-2 is adapted to transmit the reflection light from the portion to be measured into a photoelectric transducer 5~
Reference numeral 7 designates an indicator for indicating the pneusis function. According to this embodiment, a pressurization member is omitted. I the operator can maintain constant pres surization, such member is not strictly required.
The optical fibers 2-1, 2-2 can be replaceable by other types of light transmission members. Further, the light splitting means can be selected from an in.erference filter, an interference mirror, an optical prism and a spectroscope.
' ~14~773 1 Furthermore, the photo-electric transducer may be an image-sensor array, a photo transistor, a photo-multiplier or solar battery.
According to the emboaiment shown in Fig. 3, the measurement can be made regardless of external diffused light, and therefore, it is unnecessary to conduct the measurement in a darkroom.
In view of the foregoing, according to the present invention, pneusis function of the internal organ and textus can bè measured without disease due to high parasite during inter-ruption of the oxygen supply into the organ, so that quantitative diagnosis as to the local pneusis function becomes possible.
Further, abnormalities of pneusis ~unction which ~aannot be obserbed by microscopy can be measured. Technically, since the reflection spectrum variation per time is measured as an infor-mation source, severe requirements as to the spectrum character-istic can be eliminated, to thus provide compact and simplified apparatus.
While the invention has been described in detail and with reference to specific embodiments thereof, it will be apparent to one skilled in the art that various changes and modifications can be made-therein without departing for the spirit and scope of the invention.
.~` -- .
. ~, ~`
.. .. . . . ..... . .. .. . . _ .. . . . . . . ... . . . . . .. .. . . . . . .
The present invention relates to apparatus for measuring pneusis function of a bio-organ and textus, and more particularly, to a type thereof which analyzes the variation with time of the reflection spectrum characteristlc in bio-spectrometry.
Conventional clinical diagnosis and medical ~esearch has involved merely the visual observatlon of the internal organ or textus. Recently, varlous parts of the internal organs have lQ been able to be directly observed with m~croscopy in accordance with the utilization of optical transm-ssion systems such as optical fibers employed, for example, ln gastro cameras, thus providing a substantial contr~but~.on to clinicai diagnosis~
However, such microscopy does not prov~de for objective and quan-titative diagnosis, since tt depends on t~e individual doctor' 5 skill and experience.
The ox~gen pneusis of a textus ma~ ~e e~amined by enucleation thereof or may be calculated as a pneusis of the overall organ by-comparison between veinous and artery ox~gen flow thereof. However, the organ and textus may be subjected to disease due to parasites during examination of the pneusis function thereof.
SUMU~ OF THE ~NVENTION
It is an object of the present invention to overcome the above-mentio~ned drawbacks and to provide a novel apparatus for measuring pneusis function of bio-organ ana textus~
Another object of this invention is to provide such an apparatus capable of measuring the pneUsis function while elimin-ating risks of disease due to parasites, Still another object of: this invention is to provide '773 1 such apparatus capable of ~inding out the initial abnormalities of the pneusis function of the internal organ and textus.
Still another object of thls invention is to provide such apparatus for ~inding out initial abnormalities of the pneusis function which'are not capable of being recognized with microscopic methods.
In accordan~e wtth the present invention, the internal organ and textus to be diagnosed ls subjected to interruption of oxygen supply ~for example, by pressurization), and the reflectin~
spectrum characteristic variation per time is measured. This variation permits determination of the pneus;~,s function of the internal organ and textus. Pressures utiI~ed in the pressurization may exceed maximum blood pressures~
Accordingly, in one of its aspects the present invention provides an apparatus for measuring the pneusis function of a bio-organ and textus, sald apparatus comprising:
(a) a light source adapted to emit light to the or~an to be diagnosed;
(b) transmission means adapted to receiye and transmit light reflected by sqid organ;
(cl control means adapted to control o~ygen ~upply to said organ;
~ d~ conversion means adapted to conYert said trans-mitted and reflected light from said organ to electrical signals;
(el, processing means adapted to calculate t~e resultant values of the pneusis function from said elec-trical signals; and (f~ display means adapted to display said resultant values.
~,:'" .
177;~ "
1 B~IEF DESCRIPTION OF THE ~R~INGS
Further objects and advantages of the invention will appear from the following description taken together with the accompanying drawing in which:
Fig . 1 iS a graphical representation showing diffused reflection spectrum varia~ion per time relative to the internal organ after interruption of the oxygen supply;
Fig. 2 is a graphical representation showing the relationship between time after pressurization and relative absorbance of deoxy hemoglobin and oxyhemoglobin;
Fig. 3 is a schematic view showing an apparatus for conducting a method of this invention;
Fig. 4 is a schematic view showing an apparatus for conducting a method of this inven~ion, wherein light splitting means and neighbouring members are illustrated in more detail, and Fig. 5 is a schem~atic view showing another embodiment of the apparatus for conducting a method of this invention.
DETAILED DESCRIPTION OF THE INVENTION
The present invention is based on a discovery with respect to reflection spectrum characteristic variation per time in a biospectroscopy, and the technical improvement is ascribed to the discovery. Fig. 1 shows a reflection characteristic of part of an internal organ or textus subjected to interruption of oxygen supplylthereto. The horizontal and vextical axis stand for wave length and reflection light absorbance, respectively.
An uppermost curvature A is obtained during oxygen supply to the internal organ, whereas the remaining curvatures B through I are obtained during interruption of oxygen supply to part of the organ. These curvatures show spectrum variation ' .
1 per time. As is apparent from the curvature A, two peaks of oxyhemoglobin (hereinafter simply re~erred to "oxy-Hb''~ are observed in blood flow in the organ. On the other hand, after interruption of the oxygen supply (after pressuriæation) relative absorbance is greatly reduced, and the spectropattern is greatly changed as sho~n in curvatures B to I.
Further, as shown in Fig. 2, decrease of the absorbance is terminated at equi-absorbance point between oxy-Hb and deoxy hemoglobin (hereinafter simply referred to "deoxy-Hb") for about l to 2 seconds after the pressurization. This point i~ at the wave length of ~l and ~2nm, for example, 569nm and 586nm, respect-ively. On the other hand, the decrease of the absorbance at the peak point (having wave length of ~3 for example 577nm) o~ the oxy-Hb still continues for about further a few seconds.
The absorbance decrease for about l to 2 seconds is considered to occur in accordance with the decrease of Hb amount.
The decrease of the Hb amount is attributed to the expulsion of the almost all of the blood in the local blood path due to pres-surization, since absorbances at equi-absorbance points ~lnm, ~ ~2nm between oxy-Hb and deoxy-Hb are simultaneously reduced.
On the other hand, the continuous absorbance reduction at the wave length of ~3nm is considered to occur by the con-vertion of oxy-Hb into deoxy-~ due to absorbance increase adjacent to bottom point having wave length of ~4 ~for example, 555nm~
of thè oxy-Hb. ,That is, local blood flow is completely blocked due to pressurization, and residual oxygen molecules are con-sumed due to pneusis of local cells, so that all of the Hb becomes deoxy-Hb.
Therefore, measurement of the variation characteristic per time concerning the convertion of oxy-Hb to deoxy-Hb, i.e.~
~ ~ cC
'~
1 the measuremen-t of the pneusis function can be made by measuring reflection spectrum at the equi-absorbance points ~ 2 of the oxy-Hb and deoxy-Hb, and at the characteristic point ~3 of either one of the oxy-Hb and deoxy-Hb.
According to the foregoing description~ peak point ~3 of the oxy-Hb is regarded as a characteristic point. However, it is also possible to conduct measurement at a bottom point of oxy~
Hb or at a peak or bottom point of deoxy-Hb.
One of the embodiments of an apparatus for measuring pneusis function according to the present invention is shown in Fig. 3, wherein a light source 1 such as a tungst~n-iodine lamp, a xenon lamp, and a mercury lamp emits various kind of light having different wave lengths from one another. Reference numeral 2-1 designates an optical fiber adapted to introduce light from the light source 1 into an internal organ to be examined.
Reference numeral 2-2 designates a second optical fiber adapted to introduce reflection light from the or~an into a light splitting means such as spectroscope 4. Further, a pressurization control portion 3 is provided in order to interrupt oxygen supply into ~ the organ. The pressurization ~orce be higher than the maximum blood pressure. The light source 1 and the optical fiber 2-1 are not requisite members in view of the measuring environment and reflection factor of the portion to be measured.
At the light splitting means 4, light having specific wave length i5 ,selected and is introduced into a photo-electric transducer 5, at which the light is converted into an electrical signal. The electrical signal is processed at a processing unit 6, and the pneusis function is indicated at an indicator 7.
According to an embodiment shown in Fig. 4, a plurality of optical fibers are formed as a fiber bundle 2~2. These .,;~;......................... .
7~3 1 fibers are divided into groups, for example, three groups coin-dicent with the numbers of wave length to be measured. Further, corresponding filters 4-1,4-2,4-~ having diferent transmission wave length ~ 2~ ~3 with one another are provided to receive respective portions of the light and split the light. The light thus splitted is converted into electrical signals by respective photoelectric transducers 5-1,5-2,5-3.
Another embodiment according to the present invention is shown in Fig. 5, wherein like parts and components are designated by the same reference numerals as those shown in the foregoing embodiments. In the embodiment shown in Fig. 5, light which has been split is irradiated toward a portion to be measured. Light sources 1-1,1-2,1-3 are positioned at different places with one another. Filters 4-1, 4-2, 4-3 are provided in order to split light having requiring wave length from the corresponding light sources. Further, a rotary mirror 8 is provided so as to selectively orient some of the light toward an optical fiber 2-1 adapted to introduce the light into the portion to be measured. The rotation of the rotary mirror 8 is controlled by a processing circuit 6. An optical fiber 2-2 is adapted to transmit the reflection light from the portion to be measured into a photoelectric transducer 5~
Reference numeral 7 designates an indicator for indicating the pneusis function. According to this embodiment, a pressurization member is omitted. I the operator can maintain constant pres surization, such member is not strictly required.
The optical fibers 2-1, 2-2 can be replaceable by other types of light transmission members. Further, the light splitting means can be selected from an in.erference filter, an interference mirror, an optical prism and a spectroscope.
' ~14~773 1 Furthermore, the photo-electric transducer may be an image-sensor array, a photo transistor, a photo-multiplier or solar battery.
According to the emboaiment shown in Fig. 3, the measurement can be made regardless of external diffused light, and therefore, it is unnecessary to conduct the measurement in a darkroom.
In view of the foregoing, according to the present invention, pneusis function of the internal organ and textus can bè measured without disease due to high parasite during inter-ruption of the oxygen supply into the organ, so that quantitative diagnosis as to the local pneusis function becomes possible.
Further, abnormalities of pneusis ~unction which ~aannot be obserbed by microscopy can be measured. Technically, since the reflection spectrum variation per time is measured as an infor-mation source, severe requirements as to the spectrum character-istic can be eliminated, to thus provide compact and simplified apparatus.
While the invention has been described in detail and with reference to specific embodiments thereof, it will be apparent to one skilled in the art that various changes and modifications can be made-therein without departing for the spirit and scope of the invention.
.~` -- .
. ~, ~`
.. .. . . . ..... . .. .. . . _ .. . . . . . . ... . . . . . .. .. . . . . . .
Claims (19)
1. An apparatus for measuring the pneusis function of a bio-organ and textus, said apparatus comprising:
(a) a light source adapted to emit light to the organ to be diagnosed;
(b) transmission means adapted to receive and transmit light reflected by said organ;
(c) control means adapted to control oxygen supply to said organ;
(d) conversion means adapted to convert said trans-mitted and reflected light from said organ to electrical signals;
(e) processing means adapted to calculate the resultant values of the pneusis function from said electrical signals; and (f) display means adapted to display said resultant values.
(a) a light source adapted to emit light to the organ to be diagnosed;
(b) transmission means adapted to receive and transmit light reflected by said organ;
(c) control means adapted to control oxygen supply to said organ;
(d) conversion means adapted to convert said trans-mitted and reflected light from said organ to electrical signals;
(e) processing means adapted to calculate the resultant values of the pneusis function from said electrical signals; and (f) display means adapted to display said resultant values.
2. An apparatus as claimed in claim 1 wherein said light source is selected from the group consisting of a tungsten-iodine lamp, a xenon lamp and a mercury lamp.
3. An apparatus as claimed in claim 1 wherein said light source emits light of differing wave lengths.
4. An apparatus as claimed in claim 1 wherein the light from said light source is transmitted to said organ by means of a first optical fiber.
5. An apparatus as claimed in claim 1 wherein said transmission means is a second optical fiber.
6. An apparatus as claimed in claim 1 wherein said transmission means is a second optical fiber which transmits said reflected light to a light splitting means.
7. An apparatus as claimed in claim 6 wherein said light splitting means is a spectroscope.
8. An apparatus as claimed in claim 1 wherein said control means is adapted to interrupt oxygen supply to said organ.
9. An apparatus as claimed in claim 1 wherein said con-version means-comprises selection means adapted to select one or more predetermined wave lengths of said transmitted reflected light, and a photo-electrical transducer adapted to convert said predetermined wave lengths to electrical signals.
10. An apparatus for measuring the pneusis function of a bio-organ and textus, said apparatus comprising:
(a) a light source adapted to emit light to the organ to be tested, said light source selected from the group con-sisting of a tungsten-iodine lamp, a xenon lamp and a mercury lamp, and adapted to emit light of differing wave length;
(b) a first optical fiber adapted to transmit light from said light source to said organ;
(c) a transmission means adapted to receive and trans-mit light reflected by said organ, said transmission means comprising a second optical fiber;
(d) light splitting means adapted to receive said light from said transmission means;
(e) control means adapted to interrupt oxygen supply to said organ;
(f) selection means adapted to receive said light from said light splitting means and -to select one or more pre-determined wave lengths of said light;
(g) a photo-electrical transducer adapted to convert said selected wave lengths to electrical signals;
10. An apparatus for measuring the pneusis function of a bio-organ and textus, said apparatus comprising:
(a) a light source adapted to emit light to the organ to be tested, said light source selected from the group con-sisting of a tungsten-iodine lamp, a xenon lamp and a mercury lamp, and adapted to emit light of differing wave length;
(b) a first optical fiber adapted to transmit light from said light source to said organ;
(c) a transmission means adapted to receive and trans-mit light reflected by said organ, said transmission means comprising a second optical fiber;
(d) light splitting means adapted to receive said light from said transmission means;
(e) control means adapted to interrupt oxygen supply to said organ;
(f) selection means adapted to receive said light from said light splitting means and -to select one or more pre-determined wave lengths of said light;
(g) a photo-electrical transducer adapted to convert said selected wave lengths to electrical signals;
Claim 10 continued....
(h) processing means adapted to calculate the resultant values of the pneusis function from said electrical signals; and (i) display means adapted to display said resultant values.
(h) processing means adapted to calculate the resultant values of the pneusis function from said electrical signals; and (i) display means adapted to display said resultant values.
11. An apparatus as claimed in claim 1 wherein said transmission means is a plurality of optical fibers formed as a fiber bundle.
12. An apparatus as claimed in claim 11 wherein said fiber bundle is divided into groups of fibers, each group coincident with a preselected wave length.
13. An apparatus as claimed in claim 11 further including a plurality of optical filters, each filter adapted to receive light from one group of fibers and to split said light.
14. An apparatus as claimed in claim 13 wherein said conversion means is a plurality of photo-electrical transducers, each transducer adapted to receive light from one filter and to convert said light to an electrical signal.
15. An apparatus for measuring the pneusis function of a bio-organ and textus, said apparatus comprising:
(a) a light source adapted to emit light to the organ to be tested, said light source selected from the group con-sisting of a tungsten-iodine lamp, a xenon lamp and a mercury lamp, and adapted to emit light of differing wave lengths;
(b) a first optical fiber adapted to transmit light from said light source to said organ;
(c) a transmission means adapted to receive and transmit light reflected by said organ, said transmission means
15. An apparatus for measuring the pneusis function of a bio-organ and textus, said apparatus comprising:
(a) a light source adapted to emit light to the organ to be tested, said light source selected from the group con-sisting of a tungsten-iodine lamp, a xenon lamp and a mercury lamp, and adapted to emit light of differing wave lengths;
(b) a first optical fiber adapted to transmit light from said light source to said organ;
(c) a transmission means adapted to receive and transmit light reflected by said organ, said transmission means
Claim 15 continued....
comprising a plurality of optical fibers formed as a fiber bundle, said fiber bundle being divided into groups of fibers, each group coincident with a preselected wave length;
(d) a plurality of optical filters, each filter adapted to receive light from one group of fibers and to split said light;
(e) control means adapted to interrupt oxygen supply to said organ;
(f) a plurality of photo-electrical transducers, each transducer adapted to receive light from one filter and to convert said light to an electrical signal;
(g) processing means adapted to calculate the resultant values of the pneusis function from said electrical signals; and (h) display means adapted to display said resultant values.
comprising a plurality of optical fibers formed as a fiber bundle, said fiber bundle being divided into groups of fibers, each group coincident with a preselected wave length;
(d) a plurality of optical filters, each filter adapted to receive light from one group of fibers and to split said light;
(e) control means adapted to interrupt oxygen supply to said organ;
(f) a plurality of photo-electrical transducers, each transducer adapted to receive light from one filter and to convert said light to an electrical signal;
(g) processing means adapted to calculate the resultant values of the pneusis function from said electrical signals; and (h) display means adapted to display said resultant values.
16. An apparatus as claimed in claim 1 wherein said light source is a plurality of light emitting means and a plurality of optical filters, each filter adapted to split light from one light emitting means into predetermined wave lengths.
17. An apparatus as claimed in claim 16 further including an orientation means adapted to orientate the light from at least one filter to the organ.
18. An apparatus as claimed in claim 6 wherein said light-splitting means is selected from the group consisting of an interference filter, an interference mirror, an optical prism and a spectroscope.
19. An apparatus as claimed in claim 9 or 14 wherein said photo-electrical transducer is selected from the group consist-ing of an image-sensor array, a photo transistor, a photo-multiplier and a solar battery.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP2718379A JPS55118738A (en) | 1979-03-07 | 1979-03-07 | Measuring device for breathing function of internal organ and tissue of living body |
| JP27183/79 | 1979-03-07 |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA1140773A true CA1140773A (en) | 1983-02-08 |
Family
ID=12213955
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA000346985A Expired CA1140773A (en) | 1979-03-07 | 1980-03-04 | Apparatus for measuring pneusis function of bio-organ and textus |
Country Status (6)
| Country | Link |
|---|---|
| US (1) | US4513751A (en) |
| JP (1) | JPS55118738A (en) |
| CA (1) | CA1140773A (en) |
| DE (1) | DE3008651C2 (en) |
| FR (1) | FR2450594B1 (en) |
| GB (1) | GB2049168B (en) |
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| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
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| DE3475467D1 (en) * | 1983-03-10 | 1989-01-12 | Shionogi & Co | Photoelectric brain scanner and its use |
| JPS60256443A (en) * | 1984-05-31 | 1985-12-18 | オムロン株式会社 | Image measuring apparatus |
| IT1206462B (en) * | 1984-08-07 | 1989-04-27 | Anic Spa | MULTI-WAVE LENGTH PULSED LIGHT PHOTOMETER FOR NON-INVASIVE MONITORING. |
| US4718417A (en) * | 1985-03-22 | 1988-01-12 | Massachusetts Institute Of Technology | Visible fluorescence spectral diagnostic for laser angiosurgery |
| US5318024A (en) * | 1985-03-22 | 1994-06-07 | Massachusetts Institute Of Technology | Laser endoscope for spectroscopic imaging |
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| US5104392A (en) * | 1985-03-22 | 1992-04-14 | Massachusetts Institute Of Technology | Laser spectro-optic imaging for diagnosis and treatment of diseased tissue |
| US5125404A (en) * | 1985-03-22 | 1992-06-30 | Massachusetts Institute Of Technology | Apparatus and method for obtaining spectrally resolved spatial images of tissue |
| US5199431A (en) * | 1985-03-22 | 1993-04-06 | Massachusetts Institute Of Technology | Optical needle for spectroscopic diagnosis |
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| US4836206A (en) * | 1987-02-25 | 1989-06-06 | The United States Of America As Represented By The Department Of Health And Human Services | Method and device for determining viability of intact teeth |
| DE3825352A1 (en) * | 1988-07-26 | 1990-02-01 | Kessler Manfred | METHOD AND DEVICE FOR DETERMINING LOCAL DYE CONCENTRATIONS AND SPREADING PARAMETERS IN ANIMAL AND HUMAN TISSUES |
| US5178142A (en) * | 1989-05-23 | 1993-01-12 | Vivascan Corporation | Electromagnetic method and apparatus to measure constituents of human or animal tissue |
| DE68902738T2 (en) * | 1989-05-23 | 1993-01-28 | Biosensors Technology Inc | METHOD FOR DETERMINING BY MEANS OF RADIATION ABSORPTION OF SUBSTANCES IN ABSORBENT AND SCATTERING MATRIX MATERIALS. |
| US5137023A (en) * | 1990-04-19 | 1992-08-11 | Worcester Polytechnic Institute | Method and apparatus for monitoring blood analytes noninvasively by pulsatile photoplethysmography |
| US5183042A (en) * | 1989-05-23 | 1993-02-02 | Vivascan Corporation | Electromagnetic method and apparatus to measure constituents of human or animal tissue |
| US5112124A (en) * | 1990-04-19 | 1992-05-12 | Worcester Polytechnic Institute | Method and apparatus for measuring the concentration of absorbing substances |
| US5127408A (en) * | 1990-09-14 | 1992-07-07 | Duke University | Apparatus for intravascularly measuring oxidative metabolism in body organs and tissues |
| US5277181A (en) * | 1991-12-12 | 1994-01-11 | Vivascan Corporation | Noninvasive measurement of hematocrit and hemoglobin content by differential optical analysis |
| AU2245092A (en) * | 1991-12-31 | 1993-07-28 | Vivascan Corporation | Blood constituent determination based on differential spectral analysis |
| US5497770A (en) * | 1994-01-14 | 1996-03-12 | The Regents Of The University Of California | Tissue viability monitor |
| US5865738A (en) * | 1993-12-10 | 1999-02-02 | Regents Of The University Of California | Tissue viability monitor |
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| US20070015981A1 (en) * | 2003-08-29 | 2007-01-18 | Benaron David A | Device and methods for the detection of locally-weighted tissue ischemia |
| US6711426B2 (en) * | 2002-04-09 | 2004-03-23 | Spectros Corporation | Spectroscopy illuminator with improved delivery efficiency for high optical density and reduced thermal load |
| US20080009689A1 (en) * | 2002-04-09 | 2008-01-10 | Benaron David A | Difference-weighted somatic spectroscopy |
| US7003337B2 (en) * | 2002-04-26 | 2006-02-21 | Vivascan Corporation | Non-invasive substance concentration measurement using and optical bridge |
| US8175666B2 (en) * | 2002-04-26 | 2012-05-08 | Grove Instruments, Inc. | Three diode optical bridge system |
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| US7536214B2 (en) * | 2005-10-26 | 2009-05-19 | Hutchinson Technology Incorporated | Dynamic StO2 measurements and analysis |
| WO2008113024A1 (en) * | 2007-03-14 | 2008-09-18 | Spectros Corporation | Metabolism-or biochemical-based anti-spoofing biometrics devices, systems, and methods |
| KR20220053934A (en) * | 2020-10-23 | 2022-05-02 | 삼성전자주식회사 | Optical apparatus and apparatus for estimating bio-information using the same |
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| US3068742A (en) * | 1959-06-15 | 1962-12-18 | American Optical Corp | Means for performing colorimetry |
| GB998472A (en) * | 1961-07-12 | 1965-07-14 | Honeywell Inc | Improved apparatus for measuring blood pressure and pulse rate |
| US3461856A (en) * | 1965-10-23 | 1969-08-19 | American Optical Corp | Oximeters |
| US3690769A (en) * | 1969-12-12 | 1972-09-12 | Olympus Optical Co | Endoscope with built-in oximeter |
| GB1325039A (en) * | 1970-10-07 | 1973-08-01 | Shaw R F | Oximeter and method for in vivo determination of oxygen saturatiion in blood |
| US3814081A (en) * | 1971-04-02 | 1974-06-04 | Olympus Optical Co | Optical measuring catheter |
| DE2122655A1 (en) * | 1971-05-07 | 1972-11-30 | Max Planck Gesellschaft | Optical absorption device for determining the concentration of a component of a substance mixture |
| JPS528632B2 (en) * | 1971-12-29 | 1977-03-10 | ||
| AU463065B2 (en) * | 1972-02-01 | 1975-07-17 | Oximetrix Inc. | Oximeter and method |
| US4029085A (en) * | 1976-03-26 | 1977-06-14 | Purdue Research Foundation | Method for determining bilirubin concentration from skin reflectance |
| US4114604A (en) * | 1976-10-18 | 1978-09-19 | Shaw Robert F | Catheter oximeter apparatus and method |
| DE2726606A1 (en) * | 1977-06-13 | 1978-12-21 | Max Planck Gesellschaft | MEDICAL SPECTRAL PHOTOMETER |
| US4201222A (en) * | 1977-08-31 | 1980-05-06 | Thomas Haase | Method and apparatus for in vivo measurement of blood gas partial pressures, blood pressure and blood pulse |
| US4222389A (en) * | 1977-10-18 | 1980-09-16 | Institute Of Applied Biology Special Cancer Research Project | Objective determination of the rate of oxygen utilization in peripheral tissue |
| US4170987A (en) * | 1977-11-28 | 1979-10-16 | California Institute Of Technology | Medical diagnosis system and method with multispectral imaging |
| US4261344A (en) * | 1979-09-24 | 1981-04-14 | Welch Allyn, Inc. | Color endoscope |
-
1979
- 1979-03-07 JP JP2718379A patent/JPS55118738A/en active Pending
-
1980
- 1980-03-04 CA CA000346985A patent/CA1140773A/en not_active Expired
- 1980-03-06 GB GB8007644A patent/GB2049168B/en not_active Expired
- 1980-03-06 DE DE3008651A patent/DE3008651C2/en not_active Expired
- 1980-03-07 FR FR8005218A patent/FR2450594B1/en not_active Expired
-
1983
- 1983-03-11 US US06/474,273 patent/US4513751A/en not_active Expired - Fee Related
Also Published As
| Publication number | Publication date |
|---|---|
| JPS55118738A (en) | 1980-09-11 |
| DE3008651C2 (en) | 1982-11-18 |
| GB2049168A (en) | 1980-12-17 |
| US4513751A (en) | 1985-04-30 |
| GB2049168B (en) | 1983-10-12 |
| DE3008651A1 (en) | 1980-10-16 |
| FR2450594A1 (en) | 1980-10-03 |
| FR2450594B1 (en) | 1985-09-27 |
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