[go: up one dir, main page]

WO2014097965A1 - Dispositif de mesure de la saturation en oxygène et procédé de calcul de la saturation en oxygène - Google Patents

Dispositif de mesure de la saturation en oxygène et procédé de calcul de la saturation en oxygène Download PDF

Info

Publication number
WO2014097965A1
WO2014097965A1 PCT/JP2013/083363 JP2013083363W WO2014097965A1 WO 2014097965 A1 WO2014097965 A1 WO 2014097965A1 JP 2013083363 W JP2013083363 W JP 2013083363W WO 2014097965 A1 WO2014097965 A1 WO 2014097965A1
Authority
WO
WIPO (PCT)
Prior art keywords
light
oxygen saturation
living body
wavelength
calculation
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.)
Ceased
Application number
PCT/JP2013/083363
Other languages
English (en)
Japanese (ja)
Inventor
享志 渡辺
光春 三輪
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Hamamatsu Photonics KK
Original Assignee
Hamamatsu Photonics KK
Priority date (The priority date 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 date listed.)
Filing date
Publication date
Application filed by Hamamatsu Photonics KK filed Critical Hamamatsu Photonics KK
Publication of WO2014097965A1 publication Critical patent/WO2014097965A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

Links

Images

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 or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue
    • A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
    • A61B5/14551—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue using optical sensors, e.g. spectral photometrical oximeters for measuring blood gases

Definitions

  • the present invention relates to an oxygen saturation measuring device and an oxygen saturation calculating method.
  • SRS spatially resolved spectroscopy
  • TRS time-resolved spectroscopy
  • Phase modulation spectroscopy Phase modulation spectroscopy
  • PMS Modulation Spectroscopy
  • SRS Spatial resolution spectroscopy
  • Time-resolved spectroscopy Pulse light having an extremely short time width such as several picoseconds is incident on a living body, and a time-resolved waveform of light detected on the surface of the living body is detected by an ultrafast detector. After fitting the time response characteristics of the detected light so as to match the time response characteristics based on the light diffusion theory, the values of the absorption coefficient and equivalent scattering coefficient are obtained, and then the oxyhemoglobin concentration, deoxy The hemoglobin concentration is obtained, and the oxygen saturation is calculated from these.
  • TRS Time-resolved spectroscopy
  • Phase modulation spectroscopy Light modulated into a sinusoidal wave of about 100 MHz is incident on the living body, and each hemoglobin concentration and oxygen saturation is calculated from the phase change and amplitude change of the light detected on the living body surface.
  • Patent Document 1 describes a near-infrared noninvasive living body measuring apparatus.
  • the apparatus described in this document has the following configuration in order to measure the oxygen state in a deep part of a living body with high accuracy using near infrared rays. That is, this apparatus includes a light emitting element that irradiates while changing the intensity of near-infrared light having two wavelengths, and a light receiving element that is disposed at a certain distance from the light emitting element and receives transmitted light from the light. And a control unit that calculates the absorbance of each of the two wavelengths at the intensity and applies the absorbance to the Beer-Lambert rule to calculate the oxygen state of the living body.
  • Non-Patent Document 1 describes a method for non-invasively measuring the optical characteristics of a tissue using a time-resolving method.
  • time-resolved spectroscopy requires a light source that generates pulsed light of several picoseconds and a detector that can time-resolve detection signals with a time width of several picoseconds. This increases the cost of the device. Furthermore, since the calculation based on the light diffusion theory is performed, a burden on the arithmetic processing device is increased.
  • phase modulation spectroscopy requires a highly accurate phase detection technique in order to detect a change in the phase of the detection light, which increases the cost of the apparatus. Furthermore, the configuration of the apparatus becomes complicated in order to detect the phase change and amplitude change of the detection light.
  • spatially resolved spectroscopy uses continuous light (CW light) and does not require any special configuration for light detection, so it has a very simple configuration compared to the above two methods. Measurements can be taken.
  • Patent Document 1 In the device described in Patent Document 1, only one light incident position and one light detection position are provided, and the above-described problem is avoided. However, with the measuring method employed by this apparatus, it is difficult in principle to calculate the oxygen saturation with high accuracy (see Non-Patent Document 1, especially Equation 16. Even if the light amount is changed, the optical path length, That is, the depth information obtained does not change).
  • the present invention has been made in view of such problems, and has only one light incident position and one light detection position, and an oxygen saturation measuring apparatus and oxygen capable of accurately calculating oxygen saturation.
  • An object of the present invention is to provide a saturation calculation method.
  • an oxygen saturation measuring device is a device for measuring oxygen saturation in a living body, and is a first device having different wavelengths from one light incident position into a living body.
  • a light incident part for entering the light and the second light, a light detection part for detecting the light intensity of the first light and the second light propagated inside the living body at one light detection position, and a light detection part A calculation unit that calculates the in-vivo oxygen saturation by applying the attenuation of the first light and the second light in the living body obtained from the detection result of the detection result to Modified Beer-Lambert rule,
  • the optical path lengths of the first light and the second light in the living body are substantially equal to each other, and the sum of the absorption term and the scattering term by the light-absorbing substance other than the hemoglobin relating to the first light, and other than the hemoglobin relating to the second light
  • the sum of the absorption and scattering terms due to the light-absorbing material The oxygen saturation is calculated on the assumption that the ratio is
  • the oxygen saturation calculation method is a method for calculating oxygen saturation in an apparatus for measuring oxygen saturation in a living body, and has a wavelength different from each other in a living body from one light incident position.
  • the first light in the living body obtained by detecting the light intensities of the first light and the second light that are incident on the first light and the second light and propagated in the living body at one light detection position;
  • a calculation step of calculating the oxygen saturation in the living body by applying the dimming degree of the second light to the ModifiedModBeer-Lambert rule, and in the calculating step, the optical path lengths of the first light and the second light in the living body Are substantially equal to each other, and the ratio of the sum of the absorption term and the scattering term of the light-absorbing material other than hemoglobin with respect to the first light and the sum of the absorption term and the scattering term of the light-absorbing material other than the hemoglobin with respect to the second light But the first light reduction The oxygen saturation is calculated on the assumption that it is equal to the ratio of the ratio of
  • the calculation unit calculates the oxygen saturation of a living body calculated based on the assumption and the oxygen saturation of the living body in advance.
  • the following correction formula (1) based on the comparison with the measured results (However, SO 2 is the oxygen saturation calculated based on the assumption, SO 2 and corr are the corrected oxygen saturation, and a and b are real numbers), and the oxygen saturation calculated for other living bodies is corrected. It is good also as composition to do.
  • the oxygen saturation measuring device and the oxygen saturation calculating method include a calculation unit (or calculation step) and the following calculation formula (2):
  • SO 2 is the oxygen saturation calculated based on the assumption
  • ⁇ 1 is the wavelength of the first light
  • ⁇ 2 is the wavelength of the second light
  • ⁇ HbO2 ( ⁇ ) is the oxyhemoglobin of the light of the wavelength ⁇ .
  • ⁇ Hb ( ⁇ ) is the molar extinction coefficient of deoxyhemoglobin with respect to light of wavelength ⁇
  • OD ( ⁇ , t) is the attenuation of light with wavelength ⁇ at time t). It is good.
  • the oxygen saturation measuring apparatus and the oxygen saturation calculating method according to the present invention it is possible to calculate the oxygen saturation with high accuracy by using only one light incident position and one light detection position.
  • FIG. 1 is a block diagram illustrating a configuration of an oxygen saturation measuring apparatus according to an embodiment.
  • 2A is a plan view showing an external appearance of a probe included in the oxygen saturation measuring apparatus according to the embodiment, and FIG. 2B is a cross-sectional view taken along line II-II shown in FIG.
  • FIG. 3 is a diagram illustrating a state in which the probe is attached to the surface of the living body.
  • FIG. 4 is a diagram conceptually illustrating a method using a neutral density filter (ND filter) as an example of a method for calculating the coefficient K ( ⁇ ).
  • FIG. 5 is a diagram conceptually illustrating a method of monitoring the light intensity at the light incident portion as another example of the method for calculating the coefficient K ( ⁇ ).
  • ND filter neutral density filter
  • FIG. 6 is a flowchart illustrating an oxygen saturation calculation method according to an embodiment.
  • FIG. 7 is a graph showing the result of measuring the oxygen saturation at the right forehead by a breathing experiment as an example.
  • FIG. 8 is a graph showing the result of measuring the oxygen saturation at the right forehead by a breathing experiment as an example.
  • FIG. 1 is a block diagram showing a configuration of an oxygen saturation measuring apparatus according to an embodiment of the present invention.
  • FIG. 2A is a plan view showing the appearance of the probe 20 provided in the oxygen saturation measuring apparatus of the present embodiment
  • FIG. 2B is a cross-sectional view taken along the line II-II shown in FIG. It is sectional drawing along a line.
  • FIG. 3 is a diagram showing a state in which the probe 20 is mounted on the surface of the living body A.
  • the oxygen saturation measuring apparatus 1 ⁇ / b> A of this embodiment includes a main body 10 and a probe 20.
  • the oxygen saturation measuring apparatus 1A includes a first light (wavelength ⁇ 1 ) and a second light (wavelength ⁇ 2 ⁇ ⁇ ) from a probe 20 fixed to a part of a living body (for example, the head) at one light incident position.
  • 1 ) is a device that calculates hemoglobin oxygen saturation by detecting the intensity of light emitted from one light detection position in a living body. For example, near infrared light is used as the first light and the second light.
  • the probe 20 has a light incident part 21 and a light detection part 22.
  • the light incident part 21 and the light detection part 22 are arranged with an interval of, for example, about several centimeters, and are substantially integrated by a flexible black rubber holder 23.
  • the probe 20 can be fixed to the forehead portion having no hair, for example, with an adhesive tape, an elastic band, or the like.
  • the light incident part 21 enters the first light and the second light L ⁇ b> 1 and L ⁇ b> 2 from one light incident position P ⁇ b> 1 toward the living body A.
  • the light incident portion 21 includes a semiconductor light emitting element such as a light emitting diode (LED).
  • the light incident part 21 makes the first light and the second light L ⁇ b> 1 and L ⁇ b> 2 emitted from the semiconductor light emitting element incident substantially perpendicular to the surface of the living body A. Note that power for driving the semiconductor light emitting element is sent from the main body 10 via the cable 28.
  • the light detection unit 22 detects the light intensities of the first light and the second light L1 and L2 propagated inside the living body at one light detection position P2, and an electrical detection signal corresponding to the light intensity. Is generated.
  • the light detection unit 22 includes a semiconductor light receiving element such as a Si PIN photodiode, for example.
  • the light detection unit 22 may further include a preamplifier unit that integrates and amplifies the photocurrent output from the semiconductor light receiving element. Thereby, a weak signal can be detected with high sensitivity to generate a detection signal, and this signal can be transmitted to the main body 10 via the cable 28.
  • the main unit 10 includes a drive unit (driver) 11, a sample hold circuit 12, an A / D conversion circuit 13, a CPU 14, a display unit 15, a ROM 16, a RAM 17, and a data bus 18.
  • the drive unit 11 is configured by a circuit that drives the semiconductor light emitting element of the light incident unit 21.
  • the drive unit 11 is electrically connected to the data bus 18 and receives an instruction signal for instructing driving of the semiconductor light emitting element from the CPU 14 also electrically connected to the data bus 18.
  • the instruction signal includes information such as the light intensity and wavelength (for example, one of the wavelengths ⁇ 1 and ⁇ 2 ) of the light output from the semiconductor light emitting element.
  • the drive unit 11 drives the semiconductor light emitting element based on the instruction signal received from the CPU 14 and makes light enter the living body.
  • the configuration of the light incident part is not limited to that of the present embodiment, and the first light and the second light are sent from the light emitting element accommodated in the main body part 10 to the light incident part of the probe 20 through the optical fiber. It may be configured as follows.
  • the sample hold circuit 12 and the A / D conversion circuit 13 receive the detection signal transmitted from the probe 20 via the cable 28, hold (hold) it, convert it into a digital signal, and output it to the CPU 14.
  • the sample hold circuit 12 is electrically connected to the A / D conversion circuit 13 and outputs the held detection signal to the A / D conversion circuit 13.
  • the A / D conversion circuit 13 is means for converting the detection signal from an analog signal to a digital signal.
  • the A / D conversion circuit 13 converts the detection signal received from the sample hold circuit 12 into a digital signal.
  • the A / D conversion circuit 13 is electrically connected to the data bus 18 and outputs the converted detection signal to the CPU 14 via the data bus 18.
  • the CPU 14 is a calculation unit in the present embodiment, and calculates the oxygen saturation of hemoglobin contained in the living body based on the detection signal received from the A / D conversion circuit 13.
  • a calculation program for this purpose is stored in the ROM 16.
  • the CPU 14 sends time-series data indicating the calculated hemoglobin oxygen saturation to the display unit 15 via the data bus 18.
  • the display unit 15 is electrically connected to the data bus 18 and displays the result sent from the CPU 14 via the data bus 18.
  • the CPU 14 applies the dimming degree of the first light and the second light L1 and L2 in the living body obtained from the detection result of the light detection unit 22 to the ModifiederBeer-Lambert rule. Calculate oxygen saturation in the body.
  • Equation (3) the definition of each variable is as follows.
  • ⁇ 1 is 735 nm and ⁇ 2 is 850 nm.
  • the CPU 14 calculates the oxygen saturation based on the following assumption (approximation). First, it is assumed (approximate) that the optical path lengths of the first light and the second light L1 and L2 in the living body are equal to each other. This assumption is expressed by the following formula (7).
  • the ratio of the sum of the absorption term and the scattering term due to the light-absorbing substance other than hemoglobin relating to the first light L1 and the sum of the absorption term and the scattering term due to the light-absorbing substance other than the hemoglobin relating to the second light L2 is as follows: Assume that it is equal to the ratio of the dimming degree of the first light L1 and the dimming degree of the second light L2. This assumption (approximation) is expressed by the following mathematical formula (8).
  • the oxygen saturation SO 2 (t) is calculated using the following equation (9) from the equations (5) and (6) described above.
  • OD ( ⁇ , t) is obtained by the following formula (10).
  • ADC ( ⁇ , t) is the detected light intensity of the light of wavelength ⁇
  • ADC DARK (t) is a voltage-converted 12-bit A / D count value corresponding to the magnitude of the dark current
  • K ( ⁇ ) is a conversion coefficient for converting a value corresponding to the magnitude of the pulse driving forward current I Fin ( ⁇ ) of the semiconductor light emitting element into a 12-bit A / D count value.
  • the gain of the light detection unit 22 (for example, the gain of the first-stage transimpedance amplifier is 1.0 ⁇ 10 7 times and the gain of the next-stage programmable gain amplifier is 20 times) is unified to a constant value for a plurality of living bodies
  • the conversion The coefficient K ( ⁇ ) can be applied to the same value for a plurality of living bodies.
  • the detected light intensity ADC ( ⁇ , t) and the dark current equivalent value ADC DARK (t) show various values depending on the optical constants (absorption coefficient, equivalent scattering coefficient) of a plurality of living bodies. .
  • the corrected oxygen saturation SO 2, corr (t) may be calculated using the following equation (11) obtained by correcting the equation (9).
  • a and b are real numbers.
  • a in this formula (11) b is the equation (7) and (8) and calculated certain biological oxygen saturation SO 2 (t) based on the assumption of, in advance the biometric oxygen saturation SO 2 ( t) is a value obtained based on a comparison with the result of measurement by other means.
  • FIG. 4 is a diagram conceptually illustrating a method using a neutral density filter (ND filter) as an example of a method for calculating the coefficient K ( ⁇ ).
  • ND filter neutral density filter
  • the light incident part 21 and the light detection part 22 are disposed so as to face each other, and an ND filter 24 having a known transmittance is disposed therebetween.
  • the light emitted from the light incident part 21 passes through the ND filter 24 and is attenuated, and reaches the light detection part 22.
  • FIG. 4 a configuration having three LEDs 21 a to 21 c is shown as an example of the light incident portion 21.
  • LED21a and 21b emits light first light L1 having a wavelength lambda 1, and the wavelength lambda 2 of the second light L2, respectively.
  • the LED 21c emits third light L3 having a wavelength ⁇ 3 (for example, 810 nm) different from the wavelengths ⁇ 1 and ⁇ 2 .
  • the light detection unit 22 includes a semiconductor light receiving element such as a Si PIN photodiode, for example, and a transimpedance amplifier (TIA) 22b and a programmable gain amplifier (PGA) 22c provided in the subsequent stage.
  • FIG. 5 is a diagram conceptually showing a method of monitoring the intensity of the light L1 to L3 in the light incident part 21, as another example of the calculation method of the coefficient K ( ⁇ ).
  • monitoring units 25a to 25c are arranged in the vicinity of the LEDs 21a to 21c inside the light incident portion 21. These monitoring units 25a to 25c detect the light intensities of the lights L1 to L3 emitted by the LEDs 21a to 21c, respectively, and convert them into photocurrents. These photocurrents are converted into 12-bit A / D count values by TIAs 26a to 26c, PGAs 27a to 27c, and ADCs 28a to 28c provided in the light incident part 21 or the main body part 10, respectively. Thereby, conversion factors K ( ⁇ 1 ), K ( ⁇ 2 ), and K ( ⁇ 3 ) are obtained.
  • FIG. 6 is a flowchart showing an oxygen saturation calculation method according to this embodiment.
  • this oxygen saturation calculation method first, first light and second light L1, L2 having different wavelengths are incident on the living body A from one light incident position P1 (light incident step S11). Next, the light intensities of the first light and the second light L1, L2 propagated through the living body A are detected at one light detection position P2 (light detection step S12).
  • the oxygen saturation SO 2 (t) in the living body A is calculated (calculation step S13).
  • the oxygen saturation measuring apparatus 1A and the oxygen saturation calculating method of the present embodiment having the above configuration will be described.
  • the oxygen saturation measuring apparatus 1A and the oxygen saturation calculating method only one light incident position P1 and one light detection position P2 are provided. Therefore, compared to an apparatus that employs spatially resolved spectroscopy (SRS method) that provides a plurality of light detection positions, the contact state between the light detection unit 22 and the surface of the living body A can be suppressed from appearing in the measurement error, Since it is possible to avoid the influence of variation in the detection characteristics of the light detection unit 22 at the light detection position P2, more accurate measurement can be performed. Therefore, according to the oxygen saturation measuring apparatus 1A and the oxygen saturation calculating method of the present embodiment, the oxygen saturation can be calculated with high accuracy.
  • SRS method spatially resolved spectroscopy
  • the number of photodetectors can be reduced compared to an apparatus having a plurality of light detection positions, contributing to simplification and cost reduction of the apparatus. can do. Furthermore, compared with the apparatus described in Patent Document 1, it is not necessary to change the incident light intensity during measurement, so that the apparatus can be simplified and highly reproducible.
  • FIG.7 and FIG.8 is a graph which shows the result of having measured the oxygen saturation in the right forehead part by a breath-taking experiment as one Example of this embodiment.
  • the horizontal axis represents elapsed time (unit: seconds)
  • the vertical axis (left) represents light attenuation (arbitrary unit)
  • the vertical axis (right) represents oxygen saturation (unit). :%).
  • the following graphs G11 to G16 are shown.
  • Graph G11 Light attenuation graph at a wavelength of 735 nm
  • G12 Light attenuation graph at a wavelength of 810 nm
  • G13 Light attenuation graph at a wavelength of 850 nm
  • G14 Corrected arteriovenous mixed blood oxygen saturation graph G15 calculated by Equation (11) : Percutaneous arterial oxygen saturation graph G16 measured with a commercially available pulse oximeter: Arteriovenous blood oxygen saturation in the left forehead using another TRS device (MBL method)
  • the oxygen saturation measuring device and the oxygen saturation calculating method according to the present invention are not limited to the above-described embodiments, and various other modifications are possible.
  • the oxygen saturation measuring device is a device for measuring oxygen saturation in a living body, and is a light that enters first and second lights having different wavelengths from one light incident position into the living body.
  • a calculation unit that calculates the oxygen saturation in the living body by applying the second light attenuation to the Modified Beer-Lambert rule, and the calculation unit has optical path lengths of the first and second lights in the living body.
  • the ratio of the sum of the absorption term and the scattering term of the light-absorbing substance other than hemoglobin relating to the first light and the sum of the absorption term and the scattering term of the light-absorbing substance other than the hemoglobin relating to the second light are substantially equal to each other.
  • First light attenuation and second light attenuation Assuming that the ratio to the luminous intensity is approximately equal, the configuration for calculating the oxygen saturation is used.
  • the oxygen saturation is calculated inside the apparatus for measuring the oxygen saturation in the living body, and the wavelengths are different from each other in the living body from one light incident position.
  • the first and second lights incident on the living body are detected by detecting the light intensities of the first and second lights propagating in the living body at one light detection position.
  • the ratio of the sum of the absorption term and the scattering term of the light-absorbing substance other than hemoglobin relating to the first light and the sum of the absorption term and the scattering term of the light-absorbing substance other than the hemoglobin relating to the second light is Decrease degree and number
  • the configuration for calculating the oxygen saturation is used assuming that the ratio is equal to the ratio of the light attenuation of 2.
  • the present invention can be used as an oxygen saturation measuring apparatus and an oxygen saturation calculation method that can calculate the oxygen saturation with high accuracy by using only one light incident position and one light detection position.
  • SYMBOLS 1A Oxygen saturation measuring apparatus, 10 ... Main body part, 11 ... Drive part, 12 ... Sample hold circuit, 13 ... Conversion circuit, 14 ... CPU, 15 ... Display part, 16 ... ROM, 17 ... RAM, 18 ... Data bus , 20 ... probe, 21 ... light incident part, 22 ... light detection part, 23 ... holder, 24 ... ND filter, 28 ... cable, A ... biological body, P1 ... light incidence position, P2 ... light detection position.

Landscapes

  • Health & Medical Sciences (AREA)
  • Physics & Mathematics (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Biomedical Technology (AREA)
  • Medical Informatics (AREA)
  • Biophysics (AREA)
  • Pathology (AREA)
  • Engineering & Computer Science (AREA)
  • Spectroscopy & Molecular Physics (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Optics & Photonics (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)

Abstract

L'invention concerne un dispositif de mesure de la saturation en oxygène (1A) destiné à mesurer la saturation en oxygène dans un corps vivant, qui est équipé de : une unité d'injection de lumière (21) destinée à injecter une première lumière et une deuxième lumière de longueurs d'onde mutuellement différentes dans un corps vivant à partir d'une position d'injection de lumière unique ; une unité de détection de la lumière (22) destinée à détecter les intensités de lumière de la première et de la deuxième lumière qui se sont propagées à l'intérieur du corps vivant en une position de détection de lumière unique ; et une UC (14) destinée à utiliser les degrés de réduction dans la première et la deuxième lumière dans le corps vivant qui sont obtenus à partir des résultats de détection de l'unité de détection de la lumière (22) dans une loi modifiée de Beer-Lambert pour calculer la saturation en oxygène dans le corps vivant. On obtient ainsi un dispositif de mesure de la saturation en oxygène et un procédé de calcul de la saturation en oxygène, ne présentant qu'une seule position d'injection de lumière et qu'une seule position de détection de lumière et capable de calculer la saturation en oxygène avec une bonne précision.
PCT/JP2013/083363 2012-12-18 2013-12-12 Dispositif de mesure de la saturation en oxygène et procédé de calcul de la saturation en oxygène Ceased WO2014097965A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
JP2012-275744 2012-12-18
JP2012275744A JP6125821B2 (ja) 2012-12-18 2012-12-18 酸素飽和度測定装置及び酸素飽和度算出方法

Publications (1)

Publication Number Publication Date
WO2014097965A1 true WO2014097965A1 (fr) 2014-06-26

Family

ID=50978300

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/JP2013/083363 Ceased WO2014097965A1 (fr) 2012-12-18 2013-12-12 Dispositif de mesure de la saturation en oxygène et procédé de calcul de la saturation en oxygène

Country Status (2)

Country Link
JP (1) JP6125821B2 (fr)
WO (1) WO2014097965A1 (fr)

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN104856692A (zh) * 2015-03-31 2015-08-26 电子科技大学 一种混合静脉氧饱和度的光学无创检测方法

Families Citing this family (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20220015681A1 (en) 2018-11-11 2022-01-20 Biobeat Technologies Ltd. Wearable apparatus and method for monitoring medical properties
JP2021003299A (ja) 2019-06-26 2021-01-14 フェニックス電機株式会社 血中酸素飽和度の測定方法
US10813578B1 (en) 2019-12-26 2020-10-27 Biobeat Technologies Ltd. Sensor device for optical measurement of biological properties
JP6895557B1 (ja) * 2020-03-31 2021-06-30 浜松ホトニクス株式会社 透析システムおよび透析システム作動方法
KR102482459B1 (ko) * 2020-08-27 2022-12-29 (주)한국아이티에스 비침습적 당화혈색소 측정 시스템 및 방법
KR102500415B1 (ko) * 2022-01-05 2023-02-17 (주)한국아이티에스 2개의 파장을 이용한 비침습적 당화혈색소 및 혈당 측정 장치 및 방법

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2006280513A (ja) * 2005-03-31 2006-10-19 National Institute Of Information & Communication Technology 乗り物操縦者のモニター方法及びシステム
JP2007330381A (ja) * 2006-06-13 2007-12-27 Hitachi Medical Corp 生体光計測装置
WO2012066930A1 (fr) * 2010-11-16 2012-05-24 株式会社 日立メディコ Dispositif de mesure de lumière biologique et procédé de fonctionnement associé

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2006280513A (ja) * 2005-03-31 2006-10-19 National Institute Of Information & Communication Technology 乗り物操縦者のモニター方法及びシステム
JP2007330381A (ja) * 2006-06-13 2007-12-27 Hitachi Medical Corp 生体光計測装置
WO2012066930A1 (fr) * 2010-11-16 2012-05-24 株式会社 日立メディコ Dispositif de mesure de lumière biologique et procédé de fonctionnement associé

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN104856692A (zh) * 2015-03-31 2015-08-26 电子科技大学 一种混合静脉氧饱和度的光学无创检测方法

Also Published As

Publication number Publication date
JP6125821B2 (ja) 2017-05-10
JP2014117503A (ja) 2014-06-30

Similar Documents

Publication Publication Date Title
US20250090057A1 (en) Non-invasive optical physiological differential pathlength sensor
JP6125821B2 (ja) 酸素飽和度測定装置及び酸素飽和度算出方法
Fantini et al. Frequency-domain multichannel optical detector for noninvasive tissue spectroscopy and oximetry
US7884933B1 (en) Apparatus and method for determining analyte concentrations
US9380968B2 (en) Light absorption coefficient distribution estimation device, concentration measurement device, and method for controlling light absorption coefficient distribution estimation device
JP2008539968A (ja) 改良された分光測光による血液酸素化モニタリング方法
JP6878312B2 (ja) 光電式容積脈波記録法装置
US20050101850A1 (en) Optical device
US20090209836A1 (en) Optical Measuring Apparatus, Optical Measuring Method, and Storage Medium that Stores Optical Measuring Program
JP2005533609A5 (fr)
WO2006040841A1 (fr) Instrument de mesure non invasive de la glycemie
JP2003194714A (ja) 生体組織血液量測定装置
KR20190105422A (ko) 혈당 측정방법 및 이를 이용한 인체착용형 혈당 측정장치
KR20180010945A (ko) 주파수 도메인 기반의 다파장 생체신호 분석 장치 및 그 방법
JP5527658B2 (ja) 散乱吸収体測定方法及び装置
US20100076319A1 (en) Pathlength-Corrected Medical Spectroscopy
KR102166444B1 (ko) 근적외선을 이용한 비채혈식 혈당측정기 및 이를 이용한 혈당 측정 방법
US10422745B2 (en) Scattering absorber measurement device and scattering absorber measurement method
JP6043276B2 (ja) 散乱吸収体測定装置及び散乱吸収体測定方法
WO2019161336A1 (fr) Système et procédé pour une mesure optique de débit sanguin
EP3936035A1 (fr) Dispositif de mesure d'informations biologiques
ITBS20070161A1 (it) Metodo e strumento per la misura non invasiva dell'ossigenazione/saturazione di un tessuto biologico
JP6703841B2 (ja) パルスフォトメータ、および血中吸光物質濃度の算出方法
JP6741485B2 (ja) パルスフォトメータ、および血中吸光物質濃度の算出値の信頼性評価方法
JP3635331B2 (ja) 物質計測装置

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 13864986

Country of ref document: EP

Kind code of ref document: A1

NENP Non-entry into the national phase

Ref country code: DE

122 Ep: pct application non-entry in european phase

Ref document number: 13864986

Country of ref document: EP

Kind code of ref document: A1