WO2001082790A2 - Method for determining blood constituents - Google Patents
Method for determining blood constituents Download PDFInfo
- Publication number
- WO2001082790A2 WO2001082790A2 PCT/US2001/009446 US0109446W WO0182790A2 WO 2001082790 A2 WO2001082790 A2 WO 2001082790A2 US 0109446 W US0109446 W US 0109446W WO 0182790 A2 WO0182790 A2 WO 0182790A2
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- light
- range
- blood
- approximately
- patient
- Prior art date
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
- A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
- A61B5/6813—Specially adapted to be attached to a specific body part
- A61B5/6825—Hand
- A61B5/6826—Finger
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
- A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
- A61B5/683—Means for maintaining contact with the body
- A61B5/6838—Clamps or clips
Definitions
- the present invention relates to non-invasive pulse oximetry. More specifically, the present invention relates to a method for detecting the venous blood component in a pulse oximetry signal.
- Non-invasive photoelectric pulse oximetry for determining blood flow characteristics is well known in the art. Illustrative are the methods and apparatus described in U.S. Pat. Nos. RE 35,122; 5,193,543; 5,448,991; 4,407,290; and 3,704,706.
- Pulse oximeters typically measure and display various blood constituents and blood flow characteristics including, but not limited, to blood oxygen saturation of hemoglobin in arterial blood, the volume of individual blood pulsations supplying the flesh and the rate of blood pulsations corresponding to each heartbeat of the patient.
- the oximeters pass light through human or animal body tissue where blood perfuses the tissue such as a finger, an ear, the nasal septum or the scalp, and photoelectrically sense the absorption of light in the tissue. The amount of light absorbed is then used to calculate the amount of blood constituent being measured.
- Two lights having discrete frequencies in the range of -650-670 nanometers in the red range and -800-1000 nanometers in the infrared range are typically passed through the tissue.
- the light is absorbed by the blood in an amount representative of the amount of the blood constituent present in the blood.
- the amount of transmitted light passed through the tissue will vary in accordance with the changing amount of blood constituent in the tissue and the related light absorption.
- the output signal from the pulse oximeter which is sensitive to the arterial blood flow, contains a component that is waveform representative of the patient's blood gas saturation. This component is referred to as a "plethysmographic wave or waveform" (see curve P in Fig. 1).
- a problem generally associated with non-invasive pulse oximeters is that the plethysmograph signal (and the optically derived pulse rate) may be subject to irregular variants in the blood flow including, but not limited to, motion artifacts, that interfere with the detection of the blood constituents.
- a motion artifact is caused by the patient's muscle movement proximate to the oximeter sensor, for example, the patient's finger, ear or other body part to which the oximeter sensor is attached, and may cause spurious pulses that are similar to pulses caused by arterial blood flow. These spurious pulses, in turn, may cause the oximeter to process the artifact waveform and provide erroneous data. This problem is particularly significant with infants, fetuses, or patients that do not remain still during monitoring.
- the plethysmograph signal includes the blood oxygen saturation signals of the venous (i.e., non-pulsating) and arterial (i.e., pulsating) blood.
- the inability to reliably detect the venous blood component in the optical signal could, and in many instances will, result in erroneous data.
- a unique method and apparatus employs an "individualized', substantially noise free plethysmographic waveform as a reference signal.
- the noted reference is transmitted to a correlation canceler that provides a derived plethysmographic waveform that is substantially representative of the subject's true plethysmographic waveform.
- the method for determining the blood constituents of a patient in accordance with this invention comprises coupling an oximeter sensor arrangement to a tissue region of the patient; passing first and second lights through the patient's tissue region for a first period of time while the venous blood in the tissue region has a first volume and for a second period of time while the venous blood in the tissue region has a second volume, the first light being substantially in a red light range and the second light being substantially in an infrared light range; detecting a red light signal and an infrared light signal, the red and infrared signals having at least first and second frequencies; computing a first ratio of the red and infrared signals at the first frequency; computing a second ratio of the red and infrared signals at the second frequency; comparing the first and second ratios to determine a first blood constituent.
- FIGURE 1 is a graphical illustration of an r-wave portion of an electrocardiogram waveform and the related plethysmographic waveform
- FIGURE 2 is a graphical illustration of an r-wave portion of an electrocardiogram waveform and the related arterial blood pulse;
- FIGURE 3 is a schematic illustration of a prior art pulse oximeter apparatus
- FIGURES 4 and 5 are graphical illustrations of red and infrared optical signals ;
- FIGURES 6 A and 6B are schematic illustrations of a test subject showing the subject's positions during a test sequence according to the invention.
- FIGURE 7 is a graphical illustration of venous blood flow during a test sequence according to the invention.
- FIGURE is a further graphical illustration of red and infrared optical signals according to the invention.
- FIGURE 8 is graphical illustration of red and infrared optical signals acquired during a test sequence according to the invention.
- Fig. 1 there is shown a graphical illustration of an "r-wave” portion of an electrocardiogram (ECG) waveform (designated “r”) and the related plethysmographic waveform (designated “p”).
- ECG waveform comprises a complex waveform having several components that correspond to electrical heart activity.
- the QRS component relates to ventricular heart contraction.
- the r-wave portion of the QRS component is typically the steepest wave therein, having the largest amplitude and slope, and may be used for indicating the onset of cardiovascular activity.
- Correlating the occurrence of cardiovascular activity with the detection of arterial pulses typically occurs by measuring an ECG signal, detecting the occurrence of the r-wave portion of the ECG signal, determining the time delay by which an optical pulse in the detected optical signal follows the r-wave, and using the determined time delay between an r-wave and the following optical pulse to evaluate the waveform.
- FIG. 2 there is shown a graphical illustration of the arterial blood pressure (designated “P a ”) which is similarly follows the r-wave event by a determinable period of time.
- Fig. 3 there is shown a schematic illustration of one embodiment of a pulse oximeter apparatus 5 that can be employed within the scope of the invention.
- conventional pulse oximetry methods and apparatus typically employ two lights; a first light having a discrete frequently in the range of -650-670 nanometers in the red range and a second light having a discrete frequency in the range of -800-1000 nanometers.
- the lights are typically directed through a finger 4 via emitters 12, 14 and detected by a photo detector 16.
- Emitters 12 and 14 are driven by drive circuitry 18, which is in turn governed by control signal circuitry 20.
- Detector 16 is in communication with amplifier 22.
- the photo detector 16 provides an output signal S t that is transmitted to an amplifier 22.
- the amplified signal Si from amplifier 22 is then transmitted to demodulator 24, which is also synched to control signal circuitry 20.
- the output signal from the demodulator 24 would be a time multiplexed signal comprising (i) a background signal, (ii) the red light range signal and (iii) the infrared light range signal.
- the demodulator 24 which is employed in most pulse oximeter systems, removes any common mode signals present and splits the time multiplexed signal (Si) into two (2) channels, one representing the red voltage (or optical) signals (designated S 3 ) and the other representing the infrared voltage (or optical) signals (designated S 4 ). As illustrated in Fig. 3, the signal from the demodulator 24 is transmitted to analog-digital converter 26. The desired computations are performed on the output from the converter 26 by signal processor 28 and the results transmitted to display 30. Further details of the conventional pulse oximeter components, and related functions, are set forth in U.S. Pat. No. 4,934,372, which is incorporated by reference herein.
- the red signal S 3 includes motion artifacts or noise and the base red signal S, which comprises arterial blood (A B ) and venous blood (V ⁇ ) components.
- the infrared signal S 4 similarly includes noise and the base infrared signal S.
- the pulse oximeter apparatus 5 is designed correctly, such that the red and the infrared light pass through substantially the same tissue, the pulses in the plethysmographic waveform in the red channel, i.e., red voltage signal(s) S 3 , will be shaped identically to those in the infrared channel, i.e., infrared voltage signal(s) S . Only their size and the slowly-varying voltage on which they sit will be different, (see Fig. 5)
- the venous blood component V ⁇ can be distinguished from the arterial blood component VA in the following manner: Referring to Figs. 6A and 6B, in a first embodiment of the invention, the pulse oximeter 5 is operatively connected to a patient's finger 4. The patient's hand 3 (and, hence, finger 4) is then raised and held in a first position above the heart level (designated H) until substantially all of the venous (i.e., non-pulsating) blood is dissipated from or flows out of the finger 4. In a preferred embodiment, the hand 3 is held in the raised position for a first time period greater than 3 sec, more preferably, in the range of approximately 4.0 to 6.0 sec. During this first period of time, the red and infrared optical (or oximetry) signals are obtained.
- the patient's hand 3 is then lowered to a second position below the heart level (H) for a substantially equal time period (see Fig. 6B). During this second period of time, the red and infrared optical (or oximetry) signals are also obtained.
- FIG. 7 there is shown a graphical illustration of the venous blood flow during the above described test cycle.
- Fig. 1 when the finger 4 is in the second position, i.e., below the heart level (H), venous blood flows into the finger 4, designated V ⁇ ( i n) -
- V ⁇ ( ou t) When the finger is raised to the second position, venus blood dissipates from the finger A, designated V ⁇ ( ou t).
- the ratios of the low frequency (i.e., .08 to 0.12 Hz) and high frequency (i.e., 0.8 - 1.2 Hz) signals of S 3 ' (red) and S 4 ' (infrared) are then computed and compared (see Fig. 8).
- the ratio of the extended time period e.g., 10 sec
- the ratio of the extended time period can only be attributed to the venous blood component (V ⁇ ), since a period of 10 sec. could not be attributed to the heart rate.
- An oximeter sensor arrangement is coupled to a finger on patients A's left hand. The hand is raised over patient A's head and held for 4 sec. The hand is then lowered to Patient's A's side and held for 4 sec.
- Fig. 9 there is shown a representative modulation of red R and infrared I light for Patient A when both the venous concentration and arterial concentration are varying with time.
- the arterial blood concentration is varying at approximately 1 cycle/sec. and the venous blood concentration is varying at approximately 1 cycle/10 sec.
- the 1 cycle/sec. variation is due to the periodic changes in blood pressure attendant with each heart beat.
- the 1 cycle/10 sec. variation corresponds to the raising and lowering of the hand 3 above and below the heart level H within a 10.0 sec. period.
- the 1 cycle/sec. modulation has different amplitudes for red R and infrared I signals (i.e., "saw-tooth" shaped waveform).
- the 1 cycle/10 sec. modulation has the same amplitude for the red R and infrared I signals.
- the same ratio variations at low frequencies is indicative of a venous blood saturation of approximately 81%.
- the 2:1 amplitude variations (of the infrared to red signals) at 1 cycle/sec. is indicative of an arterial blood saturation of approximately 97%.
Abstract
Description
Claims
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
AU2001250960A AU2001250960A1 (en) | 2000-04-28 | 2001-03-26 | Method for determining blood constituents |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US20033200P | 2000-04-28 | 2000-04-28 | |
US60/200,332 | 2000-04-28 |
Publications (2)
Publication Number | Publication Date |
---|---|
WO2001082790A2 true WO2001082790A2 (en) | 2001-11-08 |
WO2001082790A3 WO2001082790A3 (en) | 2002-03-28 |
Family
ID=22741260
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/US2001/009446 WO2001082790A2 (en) | 2000-04-28 | 2001-03-26 | Method for determining blood constituents |
Country Status (3)
Country | Link |
---|---|
US (1) | US6480729B2 (en) |
AU (1) | AU2001250960A1 (en) |
WO (1) | WO2001082790A2 (en) |
Families Citing this family (111)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6018673A (en) | 1996-10-10 | 2000-01-25 | Nellcor Puritan Bennett Incorporated | Motion compatible sensor for non-invasive optical blood analysis |
US6675031B1 (en) | 1999-04-14 | 2004-01-06 | Mallinckrodt Inc. | Method and circuit for indicating quality and accuracy of physiological measurements |
US6748254B2 (en) | 2001-10-12 | 2004-06-08 | Nellcor Puritan Bennett Incorporated | Stacked adhesive optical sensor |
AU2003255745B2 (en) * | 2002-07-30 | 2007-03-22 | Medx Health Corporation | Method and apparatus for quantifying tissue histology |
GB0217570D0 (en) * | 2002-07-30 | 2002-09-11 | Univ Birmingham | Method and apparatus for quantifying material or object properties |
US7190986B1 (en) | 2002-10-18 | 2007-03-13 | Nellcor Puritan Bennett Inc. | Non-adhesive oximeter sensor for sensitive skin |
WO2004080300A1 (en) * | 2003-03-12 | 2004-09-23 | Yale University | Method of assesing blood volume using photoelectric plethysmography |
GB2413078C (en) * | 2004-01-08 | 2012-08-15 | Dialog Devices Ltd | A system or method for assessing a subject's pedalblood circulation. |
US8611977B2 (en) * | 2004-03-08 | 2013-12-17 | Covidien Lp | Method and apparatus for optical detection of mixed venous and arterial blood pulsation in tissue |
EP1860993B1 (en) | 2005-03-01 | 2019-01-23 | Masimo Laboratories, Inc. | Noninvasive multi-parameter patient monitor |
US7590439B2 (en) | 2005-08-08 | 2009-09-15 | Nellcor Puritan Bennett Llc | Bi-stable medical sensor and technique for using the same |
US7657294B2 (en) | 2005-08-08 | 2010-02-02 | Nellcor Puritan Bennett Llc | Compliant diaphragm medical sensor and technique for using the same |
US7657295B2 (en) | 2005-08-08 | 2010-02-02 | Nellcor Puritan Bennett Llc | Medical sensor and technique for using the same |
US20070060808A1 (en) | 2005-09-12 | 2007-03-15 | Carine Hoarau | Medical sensor for reducing motion artifacts and technique for using the same |
US8092379B2 (en) | 2005-09-29 | 2012-01-10 | Nellcor Puritan Bennett Llc | Method and system for determining when to reposition a physiological sensor |
US7869850B2 (en) | 2005-09-29 | 2011-01-11 | Nellcor Puritan Bennett Llc | Medical sensor for reducing motion artifacts and technique for using the same |
US7899510B2 (en) | 2005-09-29 | 2011-03-01 | Nellcor Puritan Bennett Llc | Medical sensor and technique for using the same |
US7904130B2 (en) | 2005-09-29 | 2011-03-08 | Nellcor Puritan Bennett Llc | Medical sensor and technique for using the same |
US7881762B2 (en) | 2005-09-30 | 2011-02-01 | Nellcor Puritan Bennett Llc | Clip-style medical sensor and technique for using the same |
US8233954B2 (en) | 2005-09-30 | 2012-07-31 | Nellcor Puritan Bennett Llc | Mucosal sensor for the assessment of tissue and blood constituents and technique for using the same |
US7555327B2 (en) | 2005-09-30 | 2009-06-30 | Nellcor Puritan Bennett Llc | Folding medical sensor and technique for using the same |
US7483731B2 (en) | 2005-09-30 | 2009-01-27 | Nellcor Puritan Bennett Llc | Medical sensor and technique for using the same |
US7486979B2 (en) | 2005-09-30 | 2009-02-03 | Nellcor Puritan Bennett Llc | Optically aligned pulse oximetry sensor and technique for using the same |
US8062221B2 (en) | 2005-09-30 | 2011-11-22 | Nellcor Puritan Bennett Llc | Sensor for tissue gas detection and technique for using the same |
US7215987B1 (en) | 2005-11-08 | 2007-05-08 | Woolsthorpe Technologies | Method and apparatus for processing signals reflecting physiological characteristics |
US7184809B1 (en) * | 2005-11-08 | 2007-02-27 | Woolsthorpe Technologies, Llc | Pulse amplitude indexing method and apparatus |
US8073518B2 (en) | 2006-05-02 | 2011-12-06 | Nellcor Puritan Bennett Llc | Clip-style medical sensor and technique for using the same |
US8145288B2 (en) | 2006-08-22 | 2012-03-27 | Nellcor Puritan Bennett Llc | Medical sensor for reducing signal artifacts and technique for using the same |
US8219170B2 (en) | 2006-09-20 | 2012-07-10 | Nellcor Puritan Bennett Llc | System and method for practicing spectrophotometry using light emitting nanostructure devices |
US8195264B2 (en) | 2006-09-22 | 2012-06-05 | Nellcor Puritan Bennett Llc | Medical sensor for reducing signal artifacts and technique for using the same |
US8175671B2 (en) | 2006-09-22 | 2012-05-08 | Nellcor Puritan Bennett Llc | Medical sensor for reducing signal artifacts and technique for using the same |
US8396527B2 (en) | 2006-09-22 | 2013-03-12 | Covidien Lp | Medical sensor for reducing signal artifacts and technique for using the same |
US7869849B2 (en) | 2006-09-26 | 2011-01-11 | Nellcor Puritan Bennett Llc | Opaque, electrically nonconductive region on a medical sensor |
US7574245B2 (en) | 2006-09-27 | 2009-08-11 | Nellcor Puritan Bennett Llc | Flexible medical sensor enclosure |
US8123695B2 (en) | 2006-09-27 | 2012-02-28 | Nellcor Puritan Bennett Llc | Method and apparatus for detection of venous pulsation |
US7890153B2 (en) | 2006-09-28 | 2011-02-15 | Nellcor Puritan Bennett Llc | System and method for mitigating interference in pulse oximetry |
US7796403B2 (en) | 2006-09-28 | 2010-09-14 | Nellcor Puritan Bennett Llc | Means for mechanical registration and mechanical-electrical coupling of a faraday shield to a photodetector and an electrical circuit |
US7680522B2 (en) | 2006-09-29 | 2010-03-16 | Nellcor Puritan Bennett Llc | Method and apparatus for detecting misapplied sensors |
US8175667B2 (en) | 2006-09-29 | 2012-05-08 | Nellcor Puritan Bennett Llc | Symmetric LED array for pulse oximetry |
US8068891B2 (en) | 2006-09-29 | 2011-11-29 | Nellcor Puritan Bennett Llc | Symmetric LED array for pulse oximetry |
US7684842B2 (en) | 2006-09-29 | 2010-03-23 | Nellcor Puritan Bennett Llc | System and method for preventing sensor misuse |
US7476131B2 (en) | 2006-09-29 | 2009-01-13 | Nellcor Puritan Bennett Llc | Device for reducing crosstalk |
CN101621958B (en) * | 2006-12-11 | 2011-05-18 | Cn体系药物技术有限公司 | Device for continuous, non-invasive measurement of arterial blood pressure and uses thereof |
US8265724B2 (en) | 2007-03-09 | 2012-09-11 | Nellcor Puritan Bennett Llc | Cancellation of light shunting |
US8280469B2 (en) | 2007-03-09 | 2012-10-02 | Nellcor Puritan Bennett Llc | Method for detection of aberrant tissue spectra |
US8221326B2 (en) | 2007-03-09 | 2012-07-17 | Nellcor Puritan Bennett Llc | Detection of oximetry sensor sites based on waveform characteristics |
US8109882B2 (en) | 2007-03-09 | 2012-02-07 | Nellcor Puritan Bennett Llc | System and method for venous pulsation detection using near infrared wavelengths |
US8229530B2 (en) | 2007-03-09 | 2012-07-24 | Nellcor Puritan Bennett Llc | System and method for detection of venous pulsation |
US7894869B2 (en) | 2007-03-09 | 2011-02-22 | Nellcor Puritan Bennett Llc | Multiple configuration medical sensor and technique for using the same |
EP2139383B1 (en) | 2007-03-27 | 2013-02-13 | Masimo Laboratories, Inc. | Multiple wavelength optical sensor |
US8374665B2 (en) | 2007-04-21 | 2013-02-12 | Cercacor Laboratories, Inc. | Tissue profile wellness monitor |
US8602997B2 (en) | 2007-06-12 | 2013-12-10 | Sotera Wireless, Inc. | Body-worn system for measuring continuous non-invasive blood pressure (cNIBP) |
US11330988B2 (en) | 2007-06-12 | 2022-05-17 | Sotera Wireless, Inc. | Body-worn system for measuring continuous non-invasive blood pressure (cNIBP) |
EP2162059B1 (en) | 2007-06-12 | 2021-01-13 | Sotera Wireless, Inc. | Vital sign monitor and method for measuring blood pressure using optical, electrical, and pressure waveforms |
US11607152B2 (en) | 2007-06-12 | 2023-03-21 | Sotera Wireless, Inc. | Optical sensors for use in vital sign monitoring |
US8352004B2 (en) | 2007-12-21 | 2013-01-08 | Covidien Lp | Medical sensor and technique for using the same |
US8346328B2 (en) | 2007-12-21 | 2013-01-01 | Covidien Lp | Medical sensor and technique for using the same |
US8366613B2 (en) | 2007-12-26 | 2013-02-05 | Covidien Lp | LED drive circuit for pulse oximetry and method for using same |
US8577434B2 (en) | 2007-12-27 | 2013-11-05 | Covidien Lp | Coaxial LED light sources |
US8442608B2 (en) | 2007-12-28 | 2013-05-14 | Covidien Lp | System and method for estimating physiological parameters by deconvolving artifacts |
US8452364B2 (en) | 2007-12-28 | 2013-05-28 | Covidien LLP | System and method for attaching a sensor to a patient's skin |
US8070508B2 (en) | 2007-12-31 | 2011-12-06 | Nellcor Puritan Bennett Llc | Method and apparatus for aligning and securing a cable strain relief |
US8092993B2 (en) | 2007-12-31 | 2012-01-10 | Nellcor Puritan Bennett Llc | Hydrogel thin film for use as a biosensor |
US8199007B2 (en) | 2007-12-31 | 2012-06-12 | Nellcor Puritan Bennett Llc | Flex circuit snap track for a biometric sensor |
US8897850B2 (en) | 2007-12-31 | 2014-11-25 | Covidien Lp | Sensor with integrated living hinge and spring |
US8437822B2 (en) | 2008-03-28 | 2013-05-07 | Covidien Lp | System and method for estimating blood analyte concentration |
US8112375B2 (en) | 2008-03-31 | 2012-02-07 | Nellcor Puritan Bennett Llc | Wavelength selection and outlier detection in reduced rank linear models |
US8071935B2 (en) | 2008-06-30 | 2011-12-06 | Nellcor Puritan Bennett Llc | Optical detector with an overmolded faraday shield |
US7880884B2 (en) | 2008-06-30 | 2011-02-01 | Nellcor Puritan Bennett Llc | System and method for coating and shielding electronic sensor components |
US7887345B2 (en) | 2008-06-30 | 2011-02-15 | Nellcor Puritan Bennett Llc | Single use connector for pulse oximetry sensors |
US8577431B2 (en) | 2008-07-03 | 2013-11-05 | Cercacor Laboratories, Inc. | Noise shielding for a noninvasive device |
US20100030040A1 (en) | 2008-08-04 | 2010-02-04 | Masimo Laboratories, Inc. | Multi-stream data collection system for noninvasive measurement of blood constituents |
US8364220B2 (en) | 2008-09-25 | 2013-01-29 | Covidien Lp | Medical sensor and technique for using the same |
US8423112B2 (en) | 2008-09-30 | 2013-04-16 | Covidien Lp | Medical sensor and technique for using the same |
US8417309B2 (en) | 2008-09-30 | 2013-04-09 | Covidien Lp | Medical sensor |
US8914088B2 (en) | 2008-09-30 | 2014-12-16 | Covidien Lp | Medical sensor and technique for using the same |
US8452366B2 (en) | 2009-03-16 | 2013-05-28 | Covidien Lp | Medical monitoring device with flexible circuitry |
US8221319B2 (en) | 2009-03-25 | 2012-07-17 | Nellcor Puritan Bennett Llc | Medical device for assessing intravascular blood volume and technique for using the same |
US8509869B2 (en) | 2009-05-15 | 2013-08-13 | Covidien Lp | Method and apparatus for detecting and analyzing variations in a physiologic parameter |
US8956294B2 (en) | 2009-05-20 | 2015-02-17 | Sotera Wireless, Inc. | Body-worn system for continuously monitoring a patients BP, HR, SpO2, RR, temperature, and motion; also describes specific monitors for apnea, ASY, VTAC, VFIB, and ‘bed sore’ index |
US11896350B2 (en) | 2009-05-20 | 2024-02-13 | Sotera Wireless, Inc. | Cable system for generating signals for detecting motion and measuring vital signs |
US8634891B2 (en) | 2009-05-20 | 2014-01-21 | Covidien Lp | Method and system for self regulation of sensor component contact pressure |
US10973414B2 (en) | 2009-05-20 | 2021-04-13 | Sotera Wireless, Inc. | Vital sign monitoring system featuring 3 accelerometers |
US9596999B2 (en) * | 2009-06-17 | 2017-03-21 | Sotera Wireless, Inc. | Body-worn pulse oximeter |
US8311601B2 (en) | 2009-06-30 | 2012-11-13 | Nellcor Puritan Bennett Llc | Reflectance and/or transmissive pulse oximeter |
US9010634B2 (en) | 2009-06-30 | 2015-04-21 | Covidien Lp | System and method for linking patient data to a patient and providing sensor quality assurance |
US8505821B2 (en) | 2009-06-30 | 2013-08-13 | Covidien Lp | System and method for providing sensor quality assurance |
US8636667B2 (en) | 2009-07-06 | 2014-01-28 | Nellcor Puritan Bennett Ireland | Systems and methods for processing physiological signals in wavelet space |
US8391941B2 (en) | 2009-07-17 | 2013-03-05 | Covidien Lp | System and method for memory switching for multiple configuration medical sensor |
US8417310B2 (en) | 2009-08-10 | 2013-04-09 | Covidien Lp | Digital switching in multi-site sensor |
US8428675B2 (en) | 2009-08-19 | 2013-04-23 | Covidien Lp | Nanofiber adhesives used in medical devices |
US20110066043A1 (en) * | 2009-09-14 | 2011-03-17 | Matt Banet | System for measuring vital signs during hemodialysis |
US11253169B2 (en) | 2009-09-14 | 2022-02-22 | Sotera Wireless, Inc. | Body-worn monitor for measuring respiration rate |
US10123722B2 (en) | 2009-09-14 | 2018-11-13 | Sotera Wireless, Inc. | Body-worn monitor for measuring respiration rate |
US10806351B2 (en) | 2009-09-15 | 2020-10-20 | Sotera Wireless, Inc. | Body-worn vital sign monitor |
US8527038B2 (en) * | 2009-09-15 | 2013-09-03 | Sotera Wireless, Inc. | Body-worn vital sign monitor |
US10420476B2 (en) | 2009-09-15 | 2019-09-24 | Sotera Wireless, Inc. | Body-worn vital sign monitor |
US9839381B1 (en) | 2009-11-24 | 2017-12-12 | Cercacor Laboratories, Inc. | Physiological measurement system with automatic wavelength adjustment |
GB2487882B (en) | 2009-12-04 | 2017-03-29 | Masimo Corp | Calibration for multi-stage physiological monitors |
US20110224564A1 (en) | 2010-03-10 | 2011-09-15 | Sotera Wireless, Inc. | Body-worn vital sign monitor |
US9173593B2 (en) | 2010-04-19 | 2015-11-03 | Sotera Wireless, Inc. | Body-worn monitor for measuring respiratory rate |
US9173594B2 (en) | 2010-04-19 | 2015-11-03 | Sotera Wireless, Inc. | Body-worn monitor for measuring respiratory rate |
US8979765B2 (en) | 2010-04-19 | 2015-03-17 | Sotera Wireless, Inc. | Body-worn monitor for measuring respiratory rate |
US8747330B2 (en) | 2010-04-19 | 2014-06-10 | Sotera Wireless, Inc. | Body-worn monitor for measuring respiratory rate |
US8888700B2 (en) | 2010-04-19 | 2014-11-18 | Sotera Wireless, Inc. | Body-worn monitor for measuring respiratory rate |
US9339209B2 (en) | 2010-04-19 | 2016-05-17 | Sotera Wireless, Inc. | Body-worn monitor for measuring respiratory rate |
US20140249432A1 (en) | 2010-12-28 | 2014-09-04 | Matt Banet | Body-worn system for continuous, noninvasive measurement of cardiac output, stroke volume, cardiac power, and blood pressure |
WO2012112891A1 (en) | 2011-02-18 | 2012-08-23 | Sotera Wireless, Inc. | Modular wrist-worn processor for patient monitoring |
US10357187B2 (en) | 2011-02-18 | 2019-07-23 | Sotera Wireless, Inc. | Optical sensor for measuring physiological properties |
US9888871B2 (en) | 2014-01-28 | 2018-02-13 | Covidien Lp | Methods and systems for determining a venous signal using a physiological monitor |
CN109602406A (en) * | 2019-01-31 | 2019-04-12 | 宁波市第二医院 | A kind of cardiovascular care equipment |
Citations (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5827181A (en) * | 1995-09-07 | 1998-10-27 | Hewlett-Packard Co. | Noninvasive blood chemistry measurement method and system |
US6002952A (en) * | 1997-04-14 | 1999-12-14 | Masimo Corporation | Signal processing apparatus and method |
US6067463A (en) * | 1999-01-05 | 2000-05-23 | Abbott Laboratories | Method and apparatus for non-invasively measuring the amount of glucose in blood |
US6094592A (en) * | 1998-05-26 | 2000-07-25 | Nellcor Puritan Bennett, Inc. | Methods and apparatus for estimating a physiological parameter using transforms |
Family Cites Families (16)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPS5725217B2 (en) | 1974-10-14 | 1982-05-28 | ||
US4167331A (en) | 1976-12-20 | 1979-09-11 | Hewlett-Packard Company | Multi-wavelength incremental absorbence oximeter |
JPS5524004A (en) | 1978-06-22 | 1980-02-20 | Minolta Camera Kk | Oxymeter |
US4407290A (en) | 1981-04-01 | 1983-10-04 | Biox Technology, Inc. | Blood constituent measuring device and method |
DE3381580D1 (en) | 1982-09-02 | 1990-06-28 | Nellcor Inc | DISPLAY DEVICE FOR PULSES AND OXYGEN CONTENT. |
EP0102816A3 (en) | 1982-09-02 | 1985-08-28 | Nellcor Incorporated | Pulse oximeter |
US4934372A (en) | 1985-04-01 | 1990-06-19 | Nellcor Incorporated | Method and apparatus for detecting optical pulses |
US5193543A (en) | 1986-12-12 | 1993-03-16 | Critikon, Inc. | Method and apparatus for measuring arterial blood constituents |
US4883055A (en) | 1988-03-11 | 1989-11-28 | Puritan-Bennett Corporation | Artificially induced blood pulse for use with a pulse oximeter |
US5078136A (en) | 1988-03-30 | 1992-01-07 | Nellcor Incorporated | Method and apparatus for calculating arterial oxygen saturation based plethysmographs including transients |
US5490505A (en) | 1991-03-07 | 1996-02-13 | Masimo Corporation | Signal processing apparatus |
US6222189B1 (en) * | 1992-07-15 | 2001-04-24 | Optix, Lp | Methods of enhancing optical signals by mechanical manipulation in non-invasive testing |
US5553615A (en) * | 1994-01-31 | 1996-09-10 | Minnesota Mining And Manufacturing Company | Method and apparatus for noninvasive prediction of hematocrit |
US5575284A (en) * | 1994-04-01 | 1996-11-19 | University Of South Florida | Portable pulse oximeter |
US5638816A (en) * | 1995-06-07 | 1997-06-17 | Masimo Corporation | Active pulse blood constituent monitoring |
US5784151A (en) * | 1996-12-03 | 1998-07-21 | Datrend Systems Inc. | Apparatus for testing a pulsed light oximeter |
-
2001
- 2001-03-26 US US09/817,667 patent/US6480729B2/en not_active Expired - Fee Related
- 2001-03-26 WO PCT/US2001/009446 patent/WO2001082790A2/en active Application Filing
- 2001-03-26 AU AU2001250960A patent/AU2001250960A1/en not_active Abandoned
Patent Citations (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5827181A (en) * | 1995-09-07 | 1998-10-27 | Hewlett-Packard Co. | Noninvasive blood chemistry measurement method and system |
US6002952A (en) * | 1997-04-14 | 1999-12-14 | Masimo Corporation | Signal processing apparatus and method |
US6094592A (en) * | 1998-05-26 | 2000-07-25 | Nellcor Puritan Bennett, Inc. | Methods and apparatus for estimating a physiological parameter using transforms |
US6067463A (en) * | 1999-01-05 | 2000-05-23 | Abbott Laboratories | Method and apparatus for non-invasively measuring the amount of glucose in blood |
Also Published As
Publication number | Publication date |
---|---|
WO2001082790A3 (en) | 2002-03-28 |
US6480729B2 (en) | 2002-11-12 |
AU2001250960A1 (en) | 2001-11-12 |
US20010037058A1 (en) | 2001-11-01 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US6480729B2 (en) | Method for determining blood constituents | |
US6594511B2 (en) | Method and apparatus for determining physiological characteristics | |
US5226417A (en) | Apparatus for the detection of motion transients | |
EP0217918B1 (en) | Method and apparatus for detecting optical pulses | |
US6997879B1 (en) | Methods and devices for reduction of motion-induced noise in optical vascular plethysmography | |
EP0904727B1 (en) | Pulse rate and heart rate coincidence detection for pulse oximetry | |
US4928692A (en) | Method and apparatus for detecting optical pulses | |
EP0335357B1 (en) | Improved method and apparatus for detecting optical pulses | |
US5111817A (en) | Noninvasive system and method for enhanced arterial oxygen saturation determination and arterial blood pressure monitoring | |
AU2002213271B2 (en) | A signal processing method and device for signal-to-noise improvement | |
EP0613652B1 (en) | Apparatus and method for non-invasive measurement of oxygen saturation | |
US7215987B1 (en) | Method and apparatus for processing signals reflecting physiological characteristics | |
US8611977B2 (en) | Method and apparatus for optical detection of mixed venous and arterial blood pulsation in tissue | |
US5860919A (en) | Active pulse blood constituent monitoring method | |
US6931268B1 (en) | Active pulse blood constituent monitoring | |
EP0951232B1 (en) | Motion compatible sensor for non-invasive optical blood analysis | |
US7738935B1 (en) | Methods and devices for reduction of motion-induced noise in pulse oximetry | |
EP0443267A1 (en) | Method and apparatus for continuous non-invasive blood pressure monitoring | |
EP2732759A1 (en) | System and method of measurement of systolic blood pressure | |
EP0512987A4 (en) | Enhanced arterial oxygen saturation determination and arterial blood pressure monitoring | |
Tanveejul et al. | A Study on the Subject and Location Specificity in Reflectance based SpO 2 Estimation using R-value based Calibration Curve | |
EP2073695A1 (en) | Method and apparatus for processing signals reflecting physiological characteristics | |
Rao et al. | A comparative analysis of reflective and transmissive PPG sensor in pulse acquisition system |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AK | Designated states |
Kind code of ref document: A2 Designated state(s): AL AM AT AU AZ BA BB BG BR BY CA CH CN CU CZ DE DK EE ES FI GB GE GH GM HR HU ID IL IS JP KE KG KP KR KZ LC LK LR LS LT LU LV MD MG MK MN MW MX NO NZ PL PT RO RU SD SE SG SI SK SL TJ TM TR TT UA UG US UZ VN YU ZW |
|
AL | Designated countries for regional patents |
Kind code of ref document: A2 Designated state(s): GH GM KE LS MW MZ SD SL SZ TZ UG ZW AM AZ BY KG KZ MD RU TJ TM AT BE CH CY DE DK ES FI FR GB GR IE IT LU MC NL PT SE TR BF BJ CF CG CI CM GA GN GW ML MR NE SN TD TG |
|
121 | Ep: the epo has been informed by wipo that ep was designated in this application | ||
DFPE | Request for preliminary examination filed prior to expiration of 19th month from priority date (pct application filed before 20040101) | ||
AK | Designated states |
Kind code of ref document: A3 Designated state(s): AL AM AT AU AZ BA BB BG BR BY CA CH CN CU CZ DE DK EE ES FI GB GE GH GM HR HU ID IL IS JP KE KG KP KR KZ LC LK LR LS LT LU LV MD MG MK MN MW MX NO NZ PL PT RO RU SD SE SG SI SK SL TJ TM TR TT UA UG US UZ VN YU ZW |
|
AL | Designated countries for regional patents |
Kind code of ref document: A3 Designated state(s): GH GM KE LS MW MZ SD SL SZ TZ UG ZW AM AZ BY KG KZ MD RU TJ TM AT BE CH CY DE DK ES FI FR GB GR IE IT LU MC NL PT SE TR BF BJ CF CG CI CM GA GN GW ML MR NE SN TD TG |
|
32PN | Ep: public notification in the ep bulletin as address of the adressee cannot be established |
Free format text: COMMUNICATION PURSUANT TO RULE 69(1) EPC (EPO FORM 1205A) SENT 140203 |
|
122 | Ep: pct application non-entry in european phase | ||
NENP | Non-entry into the national phase |
Ref country code: JP |