CN114983404A - Method for realizing percutaneous partial pressure of oxygen tcpO2 and percutaneous partial pressure of carbon dioxide tcpCO2 by using optics - Google Patents
Method for realizing percutaneous partial pressure of oxygen tcpO2 and percutaneous partial pressure of carbon dioxide tcpCO2 by using optics Download PDFInfo
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- CN114983404A CN114983404A CN202210419371.8A CN202210419371A CN114983404A CN 114983404 A CN114983404 A CN 114983404A CN 202210419371 A CN202210419371 A CN 202210419371A CN 114983404 A CN114983404 A CN 114983404A
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- oxygen
- photosensitive element
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- CURLTUGMZLYLDI-UHFFFAOYSA-N Carbon dioxide Chemical compound O=C=O CURLTUGMZLYLDI-UHFFFAOYSA-N 0.000 title claims abstract description 62
- 238000000034 method Methods 0.000 title claims abstract description 37
- QVGXLLKOCUKJST-UHFFFAOYSA-N atomic oxygen Chemical compound [O] QVGXLLKOCUKJST-UHFFFAOYSA-N 0.000 title claims abstract description 31
- 229910002092 carbon dioxide Inorganic materials 0.000 title claims abstract description 31
- 239000001569 carbon dioxide Substances 0.000 title claims abstract description 31
- 229910052760 oxygen Inorganic materials 0.000 title claims abstract description 31
- 239000001301 oxygen Substances 0.000 title claims abstract description 31
- 239000007789 gas Substances 0.000 claims abstract description 51
- 230000002427 irreversible effect Effects 0.000 claims abstract description 13
- 239000000523 sample Substances 0.000 claims abstract description 9
- 239000008280 blood Substances 0.000 claims abstract description 7
- 210000004369 blood Anatomy 0.000 claims abstract description 7
- 238000011084 recovery Methods 0.000 claims abstract description 6
- 230000000451 tissue damage Effects 0.000 claims abstract description 6
- 231100000827 tissue damage Toxicity 0.000 claims abstract description 6
- 238000004364 calculation method Methods 0.000 claims abstract description 5
- 230000003595 spectral effect Effects 0.000 claims abstract description 5
- 238000002834 transmittance Methods 0.000 claims description 24
- 238000010521 absorption reaction Methods 0.000 claims description 16
- 230000008569 process Effects 0.000 claims description 14
- 238000005259 measurement Methods 0.000 claims description 11
- 230000003287 optical effect Effects 0.000 claims description 11
- 239000000126 substance Substances 0.000 claims description 10
- 238000004737 colorimetric analysis Methods 0.000 claims description 8
- 230000008859 change Effects 0.000 claims description 5
- 230000005670 electromagnetic radiation Effects 0.000 claims description 4
- 238000005286 illumination Methods 0.000 claims description 4
- 150000002500 ions Chemical class 0.000 claims description 4
- 230000031700 light absorption Effects 0.000 claims description 4
- 239000007788 liquid Substances 0.000 claims description 4
- 230000009467 reduction Effects 0.000 claims description 4
- 238000007493 shaping process Methods 0.000 claims description 4
- 239000007787 solid Substances 0.000 claims description 4
- 238000001228 spectrum Methods 0.000 claims description 4
- 230000003321 amplification Effects 0.000 claims description 3
- 201000010099 disease Diseases 0.000 claims description 3
- 208000037265 diseases, disorders, signs and symptoms Diseases 0.000 claims description 3
- 238000003199 nucleic acid amplification method Methods 0.000 claims description 3
- 238000001514 detection method Methods 0.000 claims description 2
- 238000001914 filtration Methods 0.000 claims 1
- 230000005518 electrochemistry Effects 0.000 abstract description 2
- 238000002848 electrochemical method Methods 0.000 description 5
- 238000002835 absorbance Methods 0.000 description 3
- 230000004048 modification Effects 0.000 description 2
- 238000012986 modification Methods 0.000 description 2
- 101000800556 Methanobrevibacter olleyae NAD(+) hydrolase TcpO Proteins 0.000 description 1
- 230000009286 beneficial effect Effects 0.000 description 1
- 206010012601 diabetes mellitus Diseases 0.000 description 1
- 238000010586 diagram Methods 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 238000005516 engineering process Methods 0.000 description 1
- 230000006872 improvement Effects 0.000 description 1
- 208000014674 injury Diseases 0.000 description 1
- 230000005855 radiation Effects 0.000 description 1
- GEVPIWPYWJZSPR-UHFFFAOYSA-N tcpo Chemical compound ClC1=CC(Cl)=CC(Cl)=C1OC(=O)C(=O)OC1=C(Cl)C=C(Cl)C=C1Cl GEVPIWPYWJZSPR-UHFFFAOYSA-N 0.000 description 1
- 230000008733 trauma Effects 0.000 description 1
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Classifications
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- 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
- A61B5/14551—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 for measuring blood gases
Abstract
A method for realizing percutaneous oxygen partial pressure tcpO2 and carbon dioxide partial pressure tcpCO2 by utilizing optics comprises a photosensitive element, wherein the photosensitive element detects gas concentration by adopting infrared and far infrared light in a certain spectral range, and the light penetrability is different under different concentrations, and after the photosensitive element captures the signal, the concentration value is converted into an electric signal through a unique encryption calculation mode, so that the actual gas concentration can be detected; this patent adopts the non-invasive collection mode, to the patient of specific state of illness, like skin tissue damage back irreversible, the irreversible condition of organizing to need to measure tissue recovery such as not cutting, blood gas content etc. provides the solution to in the electrochemistry method, avoided frequently changing sensor probe collection part.
Description
Technical Field
The invention relates to the field of gas measurement, in particular to a method for realizing percutaneous partial pressure of oxygen (tcpO 2) and percutaneous partial pressure of carbon dioxide (tcpCO 2) by using optics.
Background
Traditional blood gas measurements can only be invasive or non-invasive electrochemical measurements, which are irreversible to the trauma caused by a particular condition, such as diabetes. The noninvasive electrochemical measurement requires frequent replacement of chemical components of the measurement sensor, has certain operation difficulty and is frequent, and when the deviation of the measured value is large, the replacement of the chemical components or the sensor cannot be determined at first time.
To solve the above problems, a method for achieving the transcutaneous partial oxygen pressure tcpO2 and the transcutaneous partial carbon dioxide pressure tcpCO2 by using optics is proposed in the present application.
Disclosure of Invention
Object of the invention
In order to solve the technical problems in the background technology, the invention provides a method for realizing the percutaneous partial pressure of oxygen tcpO2 and the percutaneous partial pressure of carbon dioxide tcpCO2 by using optics, and the method has the characteristics of convenience in carrying and flexibility in use.
(II) technical scheme
In order to solve the technical problems, the invention provides a method for realizing a percutaneous oxygen partial pressure tcpO2 and a percutaneous carbon dioxide partial pressure tcpCO2 by utilizing optics, which comprises a photosensitive element, wherein the photosensitive element detects the gas concentration by adopting infrared and far infrared light in a certain spectral range, and after capturing the signals, the photosensitive element converts the concentration value into an electric signal in a unique encryption calculation mode so as to detect the actual gas concentration;
however, since the molecular volume and the bonding bond of the gas are different, the oxygen and the carbon dioxide have different light transmittances at the same concentration, and therefore, even in this case, it is impossible to avoid the overlapping region of the oxygen and the carbon dioxide at the same spectrum, and this can be avoided by setting the type of the gas to be measured before the measurement, and therefore, the beer-lambert law, english name: Beer-Lambert law, which is the fundamental law of light absorption, applies to all electromagnetic radiation and all light-absorbing substances, including gases, solids, liquids, molecules, atoms and ions, and the Beer-Lambert law is the quantitative basis for absorptiometry, colorimetry and photo-colorimetry;
the principle of beer-lambert law is as follows: when a monochromatic light irradiates the surface of an absorption medium, after the monochromatic light passes through a medium with a certain thickness, the intensity of the transmitted light is reduced because the medium absorbs a part of light energy, the greater the concentration of the absorption medium, the greater the thickness of the medium, the more remarkable the reduction of the light intensity is, and the formula relationship is as follows:
a: absorbance;
·I 0 : the intensity of the incident light;
·I t : the intensity of transmitted light;
t: transmittance, or transmittance;
k: the coefficient, which may be the absorption coefficient or the molar absorption coefficient;
l: the thickness of the absorption medium, typically in cm;
c: the concentration of the light-absorbing species can be in g/L or mol/L.
Preferably, when measuring gas by the principle of beer-lambert law, the light transmittance of the light source is different under different gas concentrations, some light is reflected back, and some light is completely blocked, so that the gas concentration can be measured by measuring the transmittance of the light.
Preferably, since the molecular structure of oxygen and the molecular structure of carbon dioxide are different, the molecular diameter of oxygen is about 0.346 nm, and the molecular diameter of carbon dioxide is about 0.35 to 0.51nm, the volume fraction and the light transmittance are different in the entire container when the amount of the substance is the same in the same container, and thus the types of the measurement gases can be distinguished.
Preferably, in the sensor probe, a small-scale laser emitting device and a photosensitive element are integrated, the optomaster emitting device adopts an IC circuit, the emitting wavelength can be changed by adjusting the emitting frequency and the power, the photosensitive element on the other side is sensitive to light, and the internal resistance value of the photosensitive element can be changed along with the change of slight illumination.
Preferably, the infrared receiving part completes the receiving, amplifying, detecting and shaping of the infrared signal and demodulates the remote control coded pulse; after the optical signal is collected, the infrared receiving needs to be demodulated firstly, and the demodulation process is carried out through an infrared receiving tube; the basic working process is as follows: when a modulation signal is received, outputting a high level, otherwise, outputting a low level, which is the inverse process of modulation; after being processed by the filter circuit, noise waves are filtered out, electric signals are acquired through the ADC acquisition circuit, the proportional relation between the gas concentration and the electric signals is calculated, and after relevant algorithms are compiled at a chip to process the acquired data, relevant gas concentration data are obtained.
Preferably, the method adopts a non-invasive acquisition mode, provides a solution for the patients with specific disease conditions, such as irreversible and irreversible skin tissue damage, operation and the like, which need to measure the tissue recovery condition, the blood gas content and the like, and avoids frequently replacing the acquisition part of the sensor probe by an electrochemical method.
The technical scheme of the invention has the following beneficial technical effects:
this patent adopts the non-invasive collection mode, to the patient of specific state of illness, like skin tissue damage back irreversible, the irreversible condition of organizing to need to measure tissue recovery such as not cutting, blood gas content etc. provides the solution to in the electrochemistry method, avoided frequently changing sensor probe collection part.
Drawings
Fig. 1 is a schematic diagram of the principle of the photosensitive device of the present invention.
Detailed Description
In order to make the objects, technical solutions and advantages of the present invention more apparent, the present invention will be described in further detail with reference to the accompanying drawings in conjunction with the following detailed description. It is to be understood that these descriptions are only illustrative and are not intended to limit the scope of the present invention. Moreover, in the following description, descriptions of well-known structures and techniques are omitted so as to not unnecessarily obscure the concepts of the present invention.
As shown in FIG. 1, a method for optically achieving transcutaneous partial pressure of oxygen tcpO2 and transcutaneous partial pressure of carbon dioxide tcpCO2 is provided, which comprises a light sensitive element, and is characterized in that: the photosensitive element detects the gas concentration by adopting infrared and far infrared light in a certain spectral range, and for different concentrations, the light penetrability is different, and after the photosensitive element captures the signal, the concentration value is converted into an electric signal through a unique encryption calculation mode, so that the actual gas concentration can be detected;
however, since the molecular volume and the bonding bond of the gas are different, the oxygen and the carbon dioxide have different light transmittances at the same concentration, and therefore, even in this case, it is impossible to avoid the overlapping region of the oxygen and the carbon dioxide at the same spectrum, and this can be avoided by setting the type of the gas to be measured before the measurement, and therefore, the beer-lambert law, english name: Beer-Lambert law, which is the basic law of light absorption, applies to all electromagnetic radiation and all light absorbing substances, including gases, solids, liquids, molecules, atoms and ions, and Beer-Lambert law is the quantitative basis for absorptiometry, colorimetry and photo-colorimetry;
the principle of beer-lambert law is as follows: when a monochromatic light irradiates the surface of an absorption medium, after the monochromatic light passes through a medium with a certain thickness, the intensity of the transmitted light is reduced because the medium absorbs a part of light energy, the greater the concentration of the absorption medium, the greater the thickness of the medium, the more remarkable the reduction of the light intensity is, and the formula relationship is as follows:
a: absorbance;
·I 0 : the intensity of the incident light;
·I t : the intensity of the transmitted light;
t: transmittance, or transmittance;
k: the coefficient, which may be an absorption coefficient or a molar absorption coefficient;
l: the thickness of the absorbing medium, typically in cm;
c: the concentration of the light-absorbing species may be in g/L or mol/L.
Further, when measuring gas by the principle of beer-lambert law, the light transmittance of light emitted from the light source is different under different gas concentrations, some light is reflected back, and some light is completely blocked, so that the gas concentration can be measured by measuring the transmittance of the light.
Furthermore, because the molecular structure of oxygen is different from that of carbon dioxide, the molecular diameter of oxygen is about 0.346 nm, and the molecular diameter of carbon dioxide is about 0.35-0.51 nm, the volume ratio and the light transmittance of the whole container are different when the amount of substances is the same in the same container, so that the types of the measurement gases can be distinguished.
Furthermore, in the sensor probe, a small-scale laser emission device and a photosensitive element are integrated, the optical emission device adopts an IC circuit, the emission wavelength can be changed by adjusting the emission frequency and the power, the photosensitive element on the other side is sensitive to light, and the internal resistance value of the photosensitive element can be changed along with the change of slight illumination.
Further, the infrared receiving part completes the receiving, amplification, detection and shaping of the infrared signals and demodulates the remote control coded pulses; after the optical signal is collected, the infrared receiving needs to be demodulated firstly, and the demodulation process is carried out by an infrared receiving tube; the basic working process is as follows: when a modulation signal is received, outputting a high level, otherwise, outputting a low level, which is the inverse process of modulation; after being processed by the filter circuit, noise waves are filtered out, electric signals are acquired through the ADC acquisition circuit, the proportional relation between the gas concentration and the electric signals is calculated, and after relevant algorithms are compiled at a chip to process the acquired data, relevant gas concentration data are obtained.
Furthermore, the method adopts a non-invasive acquisition mode, provides a solution for the patients with specific disease conditions, such as irreversible skin tissue damage, irreversible operation and the like, which need to measure the tissue recovery condition, blood gas content and the like, and avoids frequently replacing the acquisition part of the sensor probe by an electrochemical method.
The working principle of the invention is as follows: a method for realizing a percutaneous oxygen partial pressure tcpO2 and a percutaneous carbon dioxide partial pressure tcpCO2 by utilizing optics comprises a photosensitive element, wherein the photosensitive element detects gas concentration by adopting infrared and far infrared light in a certain spectral range, and the light penetrability is different under different concentrations, and after the photosensitive element captures the signal, the concentration value is converted into an electric signal through a unique encryption calculation mode, so that the actual gas concentration can be detected; however, since the molecular volume and the bonding bond of the gas are different, the oxygen and the carbon dioxide have different light transmittances at the same concentration, so that the oxygen and the carbon dioxide have overlapping regions in the same spectrum, and this can be avoided by setting the type of the gas to be measured before the measurement, and therefore, the beer-lambert law, english name: Beer-Lambert law, which is the basic law of light absorption, applies to all electromagnetic radiation and all light absorbing substances, including gases, solids, liquids, molecules, atoms and ions, and Beer-Lambert law is the quantitative basis for absorptiometry, colorimetry and photo-colorimetry; the principle of beer-lambert law is as follows: when a monochromatic light irradiates the surface of an absorption medium, after the monochromatic light passes through a medium with a certain thickness, the intensity of the transmitted light is reduced because the medium absorbs a part of light energy, the greater the concentration of the absorption medium, the greater the thickness of the medium, the more remarkable the reduction of the light intensity is, and the formula relationship is as follows:
a: absorbance;
·I 0 : intensity of lambda radiation;
·I t : the intensity of transmitted light;
t: transmittance, or transmittance;
k: the coefficient, which may be the absorption coefficient or the molar absorption coefficient;
l: the thickness of the absorption medium, typically in cm;
c: the concentration of the light-absorbing species can be in g/L or mol/L.
When measuring gas by the principle of beer-lambert law, the light transmittance of light emitted by a light source is different under different gas concentrations, some light is reflected back, and some light is completely shielded, so that the gas concentration can be measured by measuring the transmittance of the light. Because the molecular structure of oxygen is different from that of carbon dioxide, the molecular diameter of oxygen is about 0.346 nm, and the molecular diameter of carbon dioxide is about 0.35-0.51 nm, the volume ratio and the light transmittance in the whole container are different when the amount of substances is the same in the same container, so that the types of the measured gases can be distinguished. In the sensor probe, a small-scale laser emission device and a photosensitive element are integrated, the light emitting device adopts an IC circuit, the emission wavelength can be changed by adjusting the emission frequency and power, the photosensitive element on the other side is sensitive to light, and the internal resistance value can be changed along with the change of slight illumination. The infrared receiving part completes the receiving, amplification, demodulation and shaping of the infrared signal and demodulates the remote control coded pulse; after the optical signal is collected, the infrared receiving needs to be demodulated firstly, and the demodulation process is carried out through an infrared receiving tube; the basic working process is as follows: when a modulation signal is received, outputting a high level, otherwise, outputting a low level, which is the inverse process of modulation; the method adopts a non-invasive acquisition mode, provides a solution for patients with specific conditions, such as irreversible skin tissue damage, irreversible operation and the like, needing to measure tissue recovery conditions, blood gas content and the like, and aims at an electrochemical method, thereby avoiding frequent replacement of a sensor probe acquisition part.
It is to be understood that the above-described embodiments of the present invention are merely illustrative of or explaining the principles of the invention and are not to be construed as limiting the invention. Therefore, any modification, equivalent replacement, improvement and the like made without departing from the spirit and scope of the present invention should be included in the protection scope of the present invention. Further, it is intended that the appended claims cover all such variations and modifications as fall within the scope and boundaries of the appended claims or the equivalents of such scope and boundaries.
Claims (7)
1. A method for optically achieving a transcutaneous oxygen partial pressure tcpO2 and a transcutaneous carbon dioxide partial pressure tcpCO2, comprising a light sensitive element, wherein: the photosensitive element detects the gas concentration by adopting infrared and far infrared light in a certain spectral range, and for different concentrations, the light penetrability is different, and after the photosensitive element captures the signal, the concentration value is converted into an electric signal through a unique encryption calculation mode, so that the actual gas concentration can be detected;
since oxygen and carbon dioxide have different light transmittances at the same concentration because of different molecular volumes and bonds, it is impossible to avoid the overlapping region of oxygen and carbon dioxide in the same spectrum, but this can be avoided by setting the type of the measuring gas before measurement, and therefore, the beer-lambert law, english name: Beer-Lambert law, which is the basic law of light absorption, applies to all electromagnetic radiation and all light absorbing substances, including gases, solids, liquids, molecules, atoms and ions, and Beer-Lambert law is the quantitative basis for absorptiometry, colorimetry and photo-colorimetry;
the principle of beer-lambert law is as follows: when a monochromatic light irradiates the surface of an absorption medium, after the monochromatic light passes through a medium with a certain thickness, the intensity of the transmitted light is reduced because the medium absorbs a part of light energy, the greater the concentration of the absorption medium, the greater the thickness of the medium, the more remarkable the reduction of the light intensity is, and the formula relationship is as follows:
transmittance, or transmittance.
2. The method of claim 1, wherein said optical means is selected from the group consisting of tcpO2 transdermal oxygen partial pressure and tcpCO2 transdermal carbon dioxide partial pressure: when measuring gas by the principle of beer-lambert law, the light transmittance of the light source is different under different gas concentrations, some light is reflected back (fig. 1-2) and some light is completely blocked, so that the gas concentration can be measured by measuring the transmittance of the light.
3. The method of claim 2, wherein said optical means is used to achieve a transdermal oxygen partial pressure tcpO2 and transdermal carbon dioxide partial pressure tcpCO2, wherein said optical means comprises: since the molecular structure of oxygen is different from that of carbon dioxide, the molecular diameter of oxygen is about 0.346 nm, and the molecular diameter of carbon dioxide is about 0.35-0.51 nm, the volume ratio and the light transmittance in the whole container are different when the amount of the substance is the same in the same container, so that the types of the measurement gases can be distinguished (see fig. 1-3).
4. A method for optically achieving a transdermal partial pressure of oxygen tcpO2 and transdermal partial pressure of carbon dioxide tcpCO2 as recited in claim 3, wherein: in the sensor probe, a small-scale laser emitting device and a photosensitive element (as shown in fig. 1-1) are integrated, the optomaster emitting device adopts an IC circuit, the emitting wavelength can be changed by adjusting the emitting frequency and the power, the photosensitive element on the other side is sensitive to light, and the internal resistance value of the photosensitive element can be changed along with the change of the light and the slight illumination change of the photosensitive element.
5. The method of claim 4, wherein said optical means is used to achieve a transdermal oxygen partial pressure tcpO2 and transdermal carbon dioxide partial pressure tcpCO2, wherein said optical means comprises: the infrared receiving part completes the receiving of the infrared signal (as shown in figures 1-4); the modulation and demodulation part completes the amplification, detection and shaping of the infrared signals, and demodulates the remote control coded pulses, the infrared receiving needs to be demodulated firstly after the optical signals are collected, and the basic working process of the demodulation is as follows: when a modulation signal is received, a high level is output, otherwise, the output is a low level, and the process is the inverse process of modulation.
6. Clutter is filtered out after the data is processed by the filter circuit, an electric signal is acquired by the ADC acquisition circuit, a relevant algorithm is compiled at a chip by calculating the proportional relation between the gas concentration and the electric signal, and relevant gas concentration data are obtained after the data is processed by software and subjected to secondary filtering.
7. The method of claim 1, wherein said optical means is selected from the group consisting of tcpO2 transdermal oxygen partial pressure and tcpCO2 transdermal carbon dioxide partial pressure: the method adopts a non-invasive acquisition mode, provides a solution for patients with specific disease conditions, such as irreversible skin tissue damage, irreversible operation and the like, which need to measure tissue recovery conditions, blood gas content and the like, and the sensor can be continuously used for measurement without replacing parts.
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| Application Number | Priority Date | Filing Date | Title |
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| CN202210419371.8A CN114983404A (en) | 2022-04-21 | 2022-04-21 | Method for realizing percutaneous partial pressure of oxygen tcpO2 and percutaneous partial pressure of carbon dioxide tcpCO2 by using optics |
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| CN202210419371.8A CN114983404A (en) | 2022-04-21 | 2022-04-21 | Method for realizing percutaneous partial pressure of oxygen tcpO2 and percutaneous partial pressure of carbon dioxide tcpCO2 by using optics |
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Citations (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6802812B1 (en) * | 2001-07-27 | 2004-10-12 | Nostix Llc | Noninvasive optical sensor for measuring near infrared light absorbing analytes |
| KR20090034490A (en) * | 2007-10-04 | 2009-04-08 | 경북대학교 산학협력단 | Method of fabrication lif optical reaction chamber to detect transcuteneous pco2 and detecting system thereof |
| CN107529996A (en) * | 2015-04-30 | 2018-01-02 | 雷迪奥米特巴塞尔股份公司 | The non-invasive optical detecting of carbon dioxide partial pressure |
-
2022
- 2022-04-21 CN CN202210419371.8A patent/CN114983404A/en not_active Withdrawn
Patent Citations (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6802812B1 (en) * | 2001-07-27 | 2004-10-12 | Nostix Llc | Noninvasive optical sensor for measuring near infrared light absorbing analytes |
| KR20090034490A (en) * | 2007-10-04 | 2009-04-08 | 경북대학교 산학협력단 | Method of fabrication lif optical reaction chamber to detect transcuteneous pco2 and detecting system thereof |
| CN107529996A (en) * | 2015-04-30 | 2018-01-02 | 雷迪奥米特巴塞尔股份公司 | The non-invasive optical detecting of carbon dioxide partial pressure |
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