WO2007041330A1 - Medical sensor and technique for using the same - Google Patents
Medical sensor and technique for using the same Download PDFInfo
- Publication number
- WO2007041330A1 WO2007041330A1 PCT/US2006/038121 US2006038121W WO2007041330A1 WO 2007041330 A1 WO2007041330 A1 WO 2007041330A1 US 2006038121 W US2006038121 W US 2006038121W WO 2007041330 A1 WO2007041330 A1 WO 2007041330A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- sensor
- set forth
- pressure
- force
- sensitive structure
- Prior art date
Links
- 238000000034 method Methods 0.000 title claims description 30
- 230000033001 locomotion Effects 0.000 claims abstract description 41
- 238000005259 measurement Methods 0.000 claims abstract description 14
- 238000002106 pulse oximetry Methods 0.000 claims description 26
- 239000008280 blood Substances 0.000 claims description 16
- 210000004369 blood Anatomy 0.000 claims description 16
- 229910052760 oxygen Inorganic materials 0.000 claims description 16
- 239000001301 oxygen Substances 0.000 claims description 16
- QVGXLLKOCUKJST-UHFFFAOYSA-N atomic oxygen Chemical compound [O] QVGXLLKOCUKJST-UHFFFAOYSA-N 0.000 claims description 15
- 230000008859 change Effects 0.000 claims description 12
- 238000006073 displacement reaction Methods 0.000 claims description 7
- 239000000470 constituent Substances 0.000 claims description 6
- 238000010079 rubber tapping Methods 0.000 claims description 5
- 239000012223 aqueous fraction Substances 0.000 claims description 4
- 238000004519 manufacturing process Methods 0.000 claims description 4
- 238000012545 processing Methods 0.000 claims description 3
- 230000000007 visual effect Effects 0.000 claims description 3
- 238000006748 scratching Methods 0.000 claims description 2
- 230000002393 scratching effect Effects 0.000 claims description 2
- 230000005236 sound signal Effects 0.000 claims 1
- 230000002159 abnormal effect Effects 0.000 abstract 1
- 239000006260 foam Substances 0.000 description 9
- 230000004044 response Effects 0.000 description 7
- 230000005540 biological transmission Effects 0.000 description 5
- 239000002245 particle Substances 0.000 description 5
- 229920001971 elastomer Polymers 0.000 description 4
- 239000000463 material Substances 0.000 description 4
- 230000010349 pulsation Effects 0.000 description 4
- 108010054147 Hemoglobins Proteins 0.000 description 3
- 102000001554 Hemoglobins Human genes 0.000 description 3
- 238000007906 compression Methods 0.000 description 3
- 230000006835 compression Effects 0.000 description 3
- 230000000694 effects Effects 0.000 description 3
- 239000000806 elastomer Substances 0.000 description 3
- 210000001061 forehead Anatomy 0.000 description 3
- 239000011159 matrix material Substances 0.000 description 3
- 238000012544 monitoring process Methods 0.000 description 3
- 230000003287 optical effect Effects 0.000 description 3
- 229920000642 polymer Polymers 0.000 description 3
- 238000003825 pressing Methods 0.000 description 3
- 238000004458 analytical method Methods 0.000 description 2
- 230000008901 benefit Effects 0.000 description 2
- 238000013461 design Methods 0.000 description 2
- 238000011161 development Methods 0.000 description 2
- 239000003814 drug Substances 0.000 description 2
- 230000007246 mechanism Effects 0.000 description 2
- 238000012986 modification Methods 0.000 description 2
- 230000004048 modification Effects 0.000 description 2
- 239000013307 optical fiber Substances 0.000 description 2
- OKTJSMMVPCPJKN-UHFFFAOYSA-N Carbon Chemical compound [C] OKTJSMMVPCPJKN-UHFFFAOYSA-N 0.000 description 1
- 108010003320 Carboxyhemoglobin Proteins 0.000 description 1
- 108010061951 Methemoglobin Proteins 0.000 description 1
- 238000001069 Raman spectroscopy Methods 0.000 description 1
- BQCADISMDOOEFD-UHFFFAOYSA-N Silver Chemical compound [Ag] BQCADISMDOOEFD-UHFFFAOYSA-N 0.000 description 1
- 238000002083 X-ray spectrum Methods 0.000 description 1
- 238000010521 absorption reaction Methods 0.000 description 1
- 239000011157 advanced composite material Substances 0.000 description 1
- 238000003491 array Methods 0.000 description 1
- 230000017531 blood circulation Effects 0.000 description 1
- 238000009530 blood pressure measurement Methods 0.000 description 1
- 210000001124 body fluid Anatomy 0.000 description 1
- 239000010839 body fluid Substances 0.000 description 1
- 229910052799 carbon Inorganic materials 0.000 description 1
- 230000000747 cardiac effect Effects 0.000 description 1
- 238000004891 communication Methods 0.000 description 1
- 229920001940 conductive polymer Polymers 0.000 description 1
- 238000012937 correction Methods 0.000 description 1
- 239000000975 dye Substances 0.000 description 1
- 239000006263 elastomeric foam Substances 0.000 description 1
- 230000005670 electromagnetic radiation Effects 0.000 description 1
- 238000005516 engineering process Methods 0.000 description 1
- 239000000835 fiber Substances 0.000 description 1
- 210000004905 finger nail Anatomy 0.000 description 1
- 210000004904 fingernail bed Anatomy 0.000 description 1
- 238000009472 formulation Methods 0.000 description 1
- 230000005251 gamma ray Effects 0.000 description 1
- 230000003760 hair shine Effects 0.000 description 1
- 238000002329 infrared spectrum Methods 0.000 description 1
- 238000002044 microwave spectrum Methods 0.000 description 1
- 239000000203 mixture Substances 0.000 description 1
- 238000012806 monitoring device Methods 0.000 description 1
- 238000010895 photoacoustic effect Methods 0.000 description 1
- 238000011176 pooling Methods 0.000 description 1
- 230000009467 reduction Effects 0.000 description 1
- 238000005096 rolling process Methods 0.000 description 1
- 238000007650 screen-printing Methods 0.000 description 1
- 230000035945 sensitivity Effects 0.000 description 1
- 229910052709 silver Inorganic materials 0.000 description 1
- 239000004332 silver Substances 0.000 description 1
- 238000002798 spectrophotometry method Methods 0.000 description 1
- 238000002604 ultrasonography Methods 0.000 description 1
- 238000002211 ultraviolet spectrum Methods 0.000 description 1
- 238000001429 visible spectrum Methods 0.000 description 1
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 1
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/68—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
- A61B5/145—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
- A61B5/14552—Details of sensors specially adapted therefor
-
- 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 generally to medical devices and, more particularly, to sensors used for sensing physiological parameters of a patient.
- Pulse oximetry may be used to measure various blood flow characteristics, such as the blood-oxygen saturation of hemoglobin in arterial blood, the volume of individual blood pulsations supplying the tissue, and/or the rate of blood pulsations corresponding to each heartbeat of a patient.
- the "pulse" in pulse oximetry refers to the time varying amount of arterial blood in the tissue during each cardiac cycle.
- Pulse oximeters typically utilize a non-invasive sensor that transmits light through a patient's tissue and that photoelectrically detects the absorption and/or scattering of the transmitted light in such tissue. One or more of the above physiological characteristics may then be calculated based upon the amount of light absorbed or scattered. More specifically, the light passed through the tissue is typically selected to be of one or more wavelengths that may be absorbed or scattered by the blood in an amount correlative to the amount of the blood constituent present in the blood. The amount of light absorbed and/or scattered may then be used to estimate the amount of blood constituent in the tissue using various algorithms.
- Pulse oximetry readings depend on pulsation of blood through the tissue. Thus, any event that interferes with the ability of the sensor to detect that pulsation can cause variability in these measurements. Motion artifacts occur when a patient's movements cause interference in the signal detected by the sensor. Motion artifacts can also occur in response to forces acting on the sensor. For example, a patient may be jostled by healthcare workers in emergency room settings. The type location, amount, or duration of force acting on a sensor will determine the nature of the motion artifact.
- sensors are vulnerable to motion artifacts when the optical distance, or path length, orientation, or angle between a sensor's emitter and detector varies due to an undesired mechanical change in the conformation of the sensor while in use.
- the mechanical deformation of the sensor may be in the form of a compression of the sensor, causing a decrease in path length.
- a sensor may flex or move in a manner that increases the distance between an emitter and detector, resulting in an increase in path length.
- variability in the optical path length due to motion can cause motion artifacts and obscure the desired pulse oximetry signal.
- a sensor that includes: a sensor body; at least one sensing element disposed on the sensor body; and a pressure-sensitive structure associated with the sensor body, wherein the pressure-sensitive structure is adapted to provide a feedback related to a pressure applied to the sensor body.
- a pulse oximetry system that includes a pulse oximetry monitor and a pulse oximetry sensor adapted to be operatively coupled to the monitor.
- the sensor includes: a sensor body; at least one sensing element disposed on the sensor body; and a pressure-sensitive structure associated with the sensor body, wherein the pressure-sensitive structure is adapted to provide a feedback related to a pressure applied to the sensor body.
- a method of operating a sensor including: emitting light into a tissue with an emitter; detecting the light with a detector; measuring a physiological characteristic based on the detected light; detecting a force experienced by at least one of the emitter and the detector with a force-sensitive sensor; and triggering an alarm when the force is greater than a threshold value.
- a method of manufacturing a sensor that includes providing a sensor body on which at least one sensing element is disposed; and providing a pressure-sensitive structure disposed on the sensor body.
- a method that includes: acquiring pressure data and oxygen saturation data from a sensor; correlating the acquired pressure data to a set of reference artifact data; and determining if the oxygen saturation data comprises a motion artifact.
- Fig. IA illustrates a perspective view of an exemplary sensor featuring force-sensitive mesh regions
- Fig. IB illustrates a cross-sectional view of the sensor of Fig. IA applied to a patient digit
- Fig. 1C illustrates a perspective view of the tissue-contacting surface of the sensor of Fig. IA
- Fig. 2 illustrates a perspective view of the sensor of Fig. IA after deformation of the force-sensitive mesh caused by finger tapping
- Fig. 3 illustrates a perspective view of the sensor of Fig. IA after deformation of the force-sensitive mesh caused by finger squeezing at the joint;
- Fig. 4A illustrates a perspective view of an exemplary embodiment of a forehead sensor whereby the force-sensitive mesh is disposed in a region around the emitter and detector;
- Fig. 4B illustrates a perspective view of the sensor of Fig. 4A after deformation of the force-sensitive mesh caused by pressing the sensor against an object;
- Fig. 5A illustrates a cross-sectional view of an exemplary embodiment of a clip- style sensor with force-sensitive foam disposed on the tissue-contacting side of the sensor;
- Fig. 5B illustrates a cross-sectional view of the pulse oximetry sensor of Fig. 5A in which the force-sensitive foam compresses in response to finger motion;
- Fig. 6A illustrates a cross-sectional view of an exemplary embodiment of a sensor with a color-changing force-sensitive structure disposed on the sensor around the joint;
- Fig. 6B illustrates a cross-sectional view of the pulse oximetry sensor of Fig. 6A in which flexing at the joint causes the force-sensitive structure to change from colorless to red;
- Fig. 7 is a flow chart of the alarm trigger responsive to sensor output according to the present invention.
- Fig. 8 is a more detailed flow chart of step 82 from Fig. 7;
- Fig. 9 illustrates a pulse oximetry system coupled to a multi-parameter patient monitor and a sensor according to embodiments of the present invention.
- sensors for pulse oximetry or other applications utilizing spectrophotometry are provided that reduce motion artifacts by correcting for the effects of patient movement and outside forces.
- sensors are provided that include force-sensitive devices adapted to assess the pressure experienced by a sensor while in use.
- sensors as provided herein may notify a user that above-normal pressures are being exerted on a sensor, which may prompt relocation of the sensor to a tissue site that is less subject to motion artifacts.
- Motion artifacts in pulse oximetry are often generated by the movement of the sensor relative to the optically probed tissue, which is typically caused by patient movement or other forces acting on the sensor. Because pulse oximetry is often used in settings where it is difficult to prevent patient motion, it is desirable to provide a mechanism for reducing the effects of motion on the pulse oximetry measurement. For example, a squeezing motion by a patient may mechanically deform a sensor, causing the sensor's emitter and detector to temporarily change position relative to one another, resulting in a motion artifact. Similarly, outside forces, such as the mechanical force of an object pressing against a sensor, may also cause mechanical deformation of a sensor and movement of the sensing components.
- a squeezing motion by a finger may be assessed by a sensor 10 as provided herein.
- the squeezing may mechanically deform a force-sensitive region on a sensor body applied to the finger.
- the force of squeezing may be converted to an electrical signal that is sent to a monitor in order to assess the force experienced by the sensor and thus correct for the motion of the emitter relative to the detector.
- Figs. IA-C illustrate an exemplary bandage-style sensor 1OA adapted for use on a digit.
- the sensor 1OA has a force-sensitive structure 12 disposed on the sensor body 16 in a region corresponding to a fingertip region of a digit when the sensor 1OA is applied to a digit 18, as shown in Fig. IB.
- the sensor 1OA as depicted, also has a force-sensitive structure 14 disposed on the sensor body 16 in a region corresponding to a joint region of the digit 18.
- the force-sensitive sensors 12 and 14 may be disposed on the sensor body 16 on the surface 20 that does not contact the digit 18 during normal use. As shown in Fig.
- the force-sensitive sensors 12 and 14 may be disposed on the surface 20 of the sensor body 16 that opposes the tissue-contacting surface 22 upon which the emitter 24 and the detector 26 are disposed. In alternate embodiments, it is contemplated that the force-sensitive sensors 12 and 14 may be embedded in the sensor body 16 or disposed on the tissue-contacting surface 22.
- the force-sensitive sensors 12 and 14 have input and output leads 28 and 30 respectively, which may be embedded in the sensor body 16. It is contemplated that the leads 28 and 30 may be connected to a cable 36 that also connects to the electrical lead 32 of the emitter 24 and the electrical lead 34 of the detector 26. As depicted, the force-sensitive sensors 12 and 14 maybe flexible mesh-type arrays of multiple sensing elements, or maybe flexible circuits.
- the sensor 1OA may have additional force-sensitive sensors disposed on the sensor body 16. It may be advantageous to provide force-sensitive sensors on multiple sides of the sensor 1OA, as it is difficult to predict the types of motion that the sensor 1OA may experience.
- force-sensitive sensors may be distributed on the sensor body 16 in locations directly opposing each other across the digit 18. Such an arrangement may provide more complete information about a squeezing motion of the digit 18 at a joint, as a force-sensitive structure on the top of the digit 18 may experience a stretching force while a force-sensitive structure in the crease of the joint may experience a compression force.
- force-sensitive sensors may be disposed on the sensor body 16 in regions that correspond to the sides of the digit to provide information about the pressure experienced by the sensor body 16 during a rolling motion of the digit 18.
- Fig. 2 illustrates a perspective view of the sensor 1OA with an exemplary deformation pattern of the force-sensitive structure 12 in response to a finger- tapping or pressing motion.
- An x-axis 38 and a y-axis 40 correspond to the plane of the sensor body 16.
- a z-axis 42 corresponds to the direction of pressure from the tapping motion of the digit 18.
- the force-sensitive structure 12 is deformed such that certain portions of the mesh form a peak- like structure 19.
- the deformation in response to pressure may cause certain intersection points in the grid of the force-sensitive structure 12 to be pushed closer together.
- the force-sensitive structure 12 may convert the change in the distances into an electrical signal that is related to the pressure experienced by the sensor 1OA.
- Fig. 3 illustrates a perspective view of the sensor 1OA with an exemplary deformation pattern of the force-sensitive structure 14 in response to a finger squeezing motion.
- the z-axis 42 corresponds to the direction of pressure from a squeezing motion of the digit 18.
- the deformation in response to squeezing may cause certain intersection points in the grid of the force-sensitive structure 14 to be pushed closer together.
- the change in the distance between intersection points of the grid of the force-sensitive structure may be converted into an electrical signal.
- a force-sensitive structure may be disposed on a sensor body in a region corresponding to at least one of an emitter or a detector.
- Fig. 4A illustrates a reflectance-type sensor 1OB adapted for use on a patient's forehead.
- the sensor 1OB has a force-sensitive structure 44 disposed on a tissue-contacting surface 45 of the sensor body 50.
- the emitter 46 and the detector 48 are surrounded by the force- sensitive structure 44, which deforms in response to outside forces, thereby providing a measure of the outside forces acting upon the emitter 46 and the detector 48.
- Fig. 4B illustrates an exemplary deformation of the force-sensitive structure 44 as it may appear after a patient has pressed the sensor 1OB against a pillow or other object during normal wear.
- Force-sensitive sensors as described herein may be any appropriate sensor that is capable of converting a force applied to a sensor body into an electrical signal.
- the pressure or force-sensitive structure may take the form of a displacement sensor, hi one such embodiment, the pressure or force-sensitive structure may include a strain gauge or other mechanical displacement sensor.
- the displacement sensor may include a linear variable differential transformer, hi other embodiments, a force-sensitive structure may be a resistance-based sensor.
- Force-sensitive sensors e.g. sensors 12, 14, and 44 maybe disposed on the sensor body as electrodes, such as silver electrodes, printed as a matrix of intersecting rows and columns. An additional layer of semiconductive ink may provide an electrical resistance at each intersection on the matrix. Sandwiching these two layers together may create an array sensor.
- a force-sensitive structure When a force is applied, the change in resistance is measured. Changing the formulation of the ink may produce different sensitivity ranges. Additionally, varying the spacing between rows and columns may yield finer resolution, hi certain embodiments, a force-sensitive structure may have a spatial resolution, or sensor electrode spacing, of at least 0.0229 mm .
- An example of a resistance sensor that is appropriate for use with a sensor 10 according to the present techniques is Flexiforce® film or flexible circuits, available from Tekscan (South Boston, MA).
- Pressure measurements may also be made by using polymers that are force- sensitive resistor materials.
- Force-sensitive resistor materials such as those available from Interlink (Carptenteria, CA) and Advanced Composites Technology (Boston, MA) have a resistance variation under load.
- a force sensing resistor may be a piezoresistivity conductive polymer, which changes resistance in a predictable manner following application of force to its surface. It is normally supplied as a polymer sheet which has had the sensing film applied by screen printing.
- the sensing film typically includes both electrically conducting and non-conducting particles suspended in matrix. The particle sizes may be of the order of fraction of microns, and the particles may be formulated to reduce the temperature dependence, improve mechanical properties and increase surface durability.
- the pressure or force-sensitive structure may take the form of a capacitance sensor.
- the capacitance is inversely proportional to the distance between the electrodes of the sensor.
- An exemplary capacitance-based sensor, TactArray is available from Pressure Profile Systems (Los Angeles, CA).
- the capacitance sensor may be sensitive to forces or pressures from lpsi to 200psi.
- Figs. 5A-B illustrate a sensor 1 OC that includes an elastomeric foam that is sensitive to force.
- the force-sensitive foam 52 provides measurement of the resistance of a conductive elastomer or foam between two points.
- the force-sensitive foam may be a carbon doped rubber in which the resistance of the elastomer changes with the application of force, resulting from the deformation of the elastomer altering the particle density.
- the force- sensitive foam is disposed on the tissue-contacting surface 54 of the sensor body 56.
- Fig. 6A illustrates a sensor 1OD applied to a patient digit 60.
- the sensor 1OD includes a force-sensitive structure 62 disposed on the surface 64 of the sensor body 66 that does not contact the digit during normal use.
- the force-sensitive structure 62 is adapted to change color upon the application of force. As illustrated in Fig. 6B, upon squeezing of the digit 60 at the first joint, the force-sensitive structure 62 changes color from colorless to red as pressure increased in the area of the force-sensitive structure 62.
- the force-sensitive structure 62 may be Pressurex® film, available from Sensor Products Inc. (East Hanover, NJ), which increases in red color intensity in relation to the amount of force applied. A conscious patient may easily note the change in color and adjust his actions to prevent further movements that may be associated with motion artifacts and measurement errors.
- a sensor 10 as described herein may be used to provide information related to the pressure and forces experienced by the sensor 10 during use. Such information may be converted into an electrical signal and sent to a monitor or another appropriate device, as described in more detail below, for processing.
- the flow chart 68 depicted in Fig. 7 describes the downstream steps involved after step 70, which involves acquisition of the oxygen saturation data 74 from the sensor 10, and step 72, which involves acquisition of force or pressure data 76. In certain embodiments, it is envisioned that steps 70 and 72 may occur simultaneously.
- a processor compares the pressure data 76 against a pressure threshold.
- the raw pressure data 76 output from a force-sensitive structure as described herein is further acted upon by a processor, such as a processor in a pulse oximeter, to provide either a pressure map or a pressure value.
- a processor such as a processor in a pulse oximeter
- the map or value may then be compared to a predetermined threshold map or predetermined threshold value.
- the threshold value is generally envisioned to be a pressure value that is associated with an increase in motion artifacts.
- a threshold map may be an image which may be directly compared to a pressure map obtained from the force-sensitive structure. If, at a step 78, the pressure data 76 does not exceed a predetermined threshold value, the processor passes control to step 80. At step 80, the system goes into a default mode and a processor calculates an oxygen saturation value from the oxygen saturation data 74. The oxygen saturation value may then be displayed on a monitor.
- a notification is displayed to alert a user that the pressure experienced by a sensor 10 has increased beyond a critical threshold value.
- the notification may be an audio alarm, such as a warning sound, or a visual alarm, such as a text message or icon that is displayed on a monitor.
- a processor may act upon the oxygen saturation data 74 in order to correct for any influence of higher-than-normal pressures on the sensor 10. The corrected oxygen saturation value may then be displayed on the monitor.
- a processor may adjust an estimation of the path length between an emitter and a detector to account for any reduction in the path length due to tissue compression. In such an example, measured pressure would be inversely related to path length. The adjustment of the path length may result in a correction in the oxygen saturation.
- step 82 may be accomplished by correlating pressure data 76 to previously acquired or reference artifact data characteristic of different pressure events.
- the pressure data 76 exceeding a pre-defined threshold at step 78 is provided as input into a searchable machine-readable database of artifact data to determine if the pressure data 76 is characteristic of particular artifact events.
- the look-up database of artifact in step 104 may be acquired through measurements of various pressure profiles associated with artifact events to build a lookup database or table that correlates pressure data 76 with possible artifact/interference- related saturation data.
- the pressure data 76 may be compared to an artifact database in step 104 to determine if the pressure data 76 is characteristic of venous pooling under the fingertip during tapping or compartmentalization of blood in the finger during scratching.
- the oxygen saturation data 74 may then be corrected in light of the particular type of pressure experienced by the tissue.
- the database artifact/interference data obtained from step 104 that correlates with or is characteristic of the pressure data 76 is analyzed in frequency domain at step 106 using frequency transforms such as FFT (Fast Fourier Transform) and WT (Wavelet Transform). Additionally in step 106, frequency transforms are also applied to the acquired raw saturation data 74.
- FFT Fast Fourier Transform
- WT Widelet Transform
- a sensor 10 may include a second emitter and detector pair located in a different position on the sensor body than the first emitter and detector pair.
- a processor may note that pressure data 76 from the first emitter and detector pair exceeds a threshold pressure value.
- the processor may then pass control to the second emitter and detector pair, which may be located at a site that experiences pressures below the threshold pressure value.
- a sensor 10 may include an emitter and first detector located in a different position on the sensor body than a second detector.
- a processor may note that pressure data 76 from the first emitter and first detector exceeds a threshold pressure value, and the processor may pass control to the second detector.
- a sensor illustrated generically as a sensor 10, maybe used in conjunction with a pulse oximetry monitor 88, as illustrated in Fig. 9.
- the cable 90 of the sensor 10 may be coupled to the monitor 88 or it may be coupled to a transmission device (not shown) to facilitate wireless transmission between the sensor 10 and the monitor 88.
- the monitor 88 may be any suitable pulse oximeter, such as those available from Nellcor Puritan Bennett Inc.
- the monitor 88 may be coupled to a multi-parameter patient monitor 92 via a cable 94 connected to a sensor input port or via a cable 96 connected to a digital communication port.
- the sensor 10 includes an emitter 98 and a detector 100 that may be of any suitable type.
- the emitter 98 may be one or more light emitting diodes adapted to transmit one or more wavelengths of light in the red to infrared range
- the detector 100 may one or more photodetectors selected to receive light in the range or ranges emitted from the emitter 98.
- an emitter 98 may also be a laser diode or a vertical cavity surface emitting laser (VCSEL).
- An emitter 98 and detector 100 may also include optical fiber sensing elements.
- An emitter 98 may include a broadband or "white light" source, in which case the detector could include any of a variety of elements for selecting specific wavelengths, such as reflective or refractive elements or interferometers.
- a sensor 10 may sense light detected from the tissue is at a different wavelength from the light emitted into the tissue.
- Such sensors may be adapted to sense fluorescence, phosphorescence, Raman scattering, Rayleigh scattering and multi-photon events or photoacoustic effects.
- the oxygen saturation of the patient's arterial blood may be determined using two or more wavelengths of light, most commonly red and near infrared wavelengths.
- a tissue water fraction (or other body fluid related metric) or a concentration of one or more biochemical components in an aqueous environment may be measured using two or more wavelengths of light, most commonly near infrared wavelengths between about 1,000 nm to about 2,500 nm.
- the term "light” may refer to one or more of ultrasound, radio, microwave, millimeter wave, infrared, visible, ultraviolet, gamma ray or X-ray electromagnetic radiation, and may also include any wavelength within the radio, microwave, infrared, visible, ultraviolet, or X-ray spectra.
- the emitter 98 and the detector 100 maybe disposed on a sensor body 102, which may be made of any suitable material, such as plastic, foam, woven material, or paper. Alternatively, the emitter 98 and the detector 100 may be remotely located and optically coupled to the sensor 10 using optical fibers.
- the sensor 10 is coupled to a cable 90 that is responsible for transmitting electrical and/or optical signals to and from the emitter 98 and detector 100 of the sensor 10.
- the cable 90 may be permanently coupled to the sensor 10, or it may be removably coupled to the sensor 10 ⁇ the latter alternative being more useful and cost efficient in situations where the sensor 10 is disposable.
- the sensor 10 may be a "transmission type" sensor.
- Transmission type sensors include an emitter 98 and detector 100 that are typically placed on opposing sides of the sensor site. If the sensor site is a fingertip, for example, the sensor 10 is positioned over the patient's fingertip such that the emitter 98 and detector 100 lie on either side of the patient's nail bed. hi other words, the sensor 10 is positioned so that the emitter 98 is located on the patient's fingernail and the detector 100 is located 180° opposite the emitter 98 on the patient's finger pad.
- the emitter 98 shines one or more wavelengths of light through the patient's fingertip and the light received by the detector 100 is processed to determine various physiological characteristics of the patient, hi each of the embodiments discussed herein, it should be understood that the locations of the emitter 98 and the detector 100 may be exchanged.
- the detector 100 may be located at the top of the finger and the emitter 98 may be located underneath the finger. In either arrangement, the sensor 10 will perform in substantially the same manner.
- Reflectance type sensors also operate by emitting light into the tissue and detecting the light that is transmitted and scattered by the tissue.
- reflectance type sensors include an emitter 98 and detector 100 that are typically placed on the same side of the sensor site.
- a reflectance type sensor may be placed on a patient's fingertip or forehead such that the emitter 98 and detector 100 lie side-by-side.
- Reflectance type sensors detect light photons that are scattered back to the detector 100.
- a sensor 10 may also be a "transflectance" sensor, such as a sensor that may subtend a portion of a baby's heel.
Abstract
A sensor may be adapted to provide output to indicate when the sensor experiences abnormal forces or pressure. The forces may be outside forces, or the forces may be generated by patient motion. A sensor system as provided may also be adapted to correct for such forces when calculating measurements related to a physiological characteristic.
Description
MEDICAL SENSOR AND TECHNIQUE FOR USING THE SAME
BACKGROUND OF THE INVENTION
1. Field Of The Invention
The present invention relates generally to medical devices and, more particularly, to sensors used for sensing physiological parameters of a patient.
2. Description Of The Related Art
This section is intended to introduce the reader to various aspects of art that may be related to various aspects of the present invention, which are described and/or claimed below. This discussion is believed to be helpful in providing the reader with background information to facilitate a better understanding of the various aspects of the present invention. Accordingly, it should be understood that these statements are to be read in this light, and not as admissions of prior art.
In the field of medicine, doctors often desire to monitor certain physiological characteristics of their patients. Accordingly, a wide variety of devices have been developed for monitoring many such physiological characteristics. Such devices provide doctors and other healthcare personnel with the information they need to provide the best possible healthcare for their patients. As a result, such monitoring devices have become an indispensable part of modern medicine.
One technique for monitoring certain physiological characteristics of a patient is commonly referred to as pulse oximetry, and the devices built based upon pulse oximetry techniques are commonly referred to as pulse oximeters. Pulse oximetry may be used to measure various blood flow characteristics, such as the blood-oxygen saturation of hemoglobin in arterial blood, the volume of individual blood pulsations supplying the tissue, and/or the rate of blood pulsations corresponding to each heartbeat of a patient. In fact, the "pulse" in pulse oximetry refers to the time varying amount of arterial blood in the tissue during each cardiac cycle.
Pulse oximeters typically utilize a non-invasive sensor that transmits light through a patient's tissue and that photoelectrically detects the absorption and/or scattering of the transmitted light in such tissue. One or more of the above physiological characteristics may
then be calculated based upon the amount of light absorbed or scattered. More specifically, the light passed through the tissue is typically selected to be of one or more wavelengths that may be absorbed or scattered by the blood in an amount correlative to the amount of the blood constituent present in the blood. The amount of light absorbed and/or scattered may then be used to estimate the amount of blood constituent in the tissue using various algorithms.
Pulse oximetry readings depend on pulsation of blood through the tissue. Thus, any event that interferes with the ability of the sensor to detect that pulsation can cause variability in these measurements. Motion artifacts occur when a patient's movements cause interference in the signal detected by the sensor. Motion artifacts can also occur in response to forces acting on the sensor. For example, a patient may be jostled by healthcare workers in emergency room settings. The type location, amount, or duration of force acting on a sensor will determine the nature of the motion artifact.
Generally, sensors are vulnerable to motion artifacts when the optical distance, or path length, orientation, or angle between a sensor's emitter and detector varies due to an undesired mechanical change in the conformation of the sensor while in use. The mechanical deformation of the sensor may be in the form of a compression of the sensor, causing a decrease in path length. Alternately, a sensor may flex or move in a manner that increases the distance between an emitter and detector, resulting in an increase in path length. In any case, variability in the optical path length due to motion can cause motion artifacts and obscure the desired pulse oximetry signal.
SUMMARY
Certain aspects commensurate in scope with the originally claimed invention are set forth below. It should be understood that these aspects are presented merely to provide the reader with a brief summary of certain forms that the invention might take and that these aspects are not intended to limit the scope of the invention. Indeed, the invention may encompass a variety of aspects that may not be set forth below.
There is provided a sensor that includes: a sensor body; at least one sensing element disposed on the sensor body; and a pressure-sensitive structure associated with
the sensor body, wherein the pressure-sensitive structure is adapted to provide a feedback related to a pressure applied to the sensor body.
There is also provided a pulse oximetry system that includes a pulse oximetry monitor and a pulse oximetry sensor adapted to be operatively coupled to the monitor. The sensor includes: a sensor body; at least one sensing element disposed on the sensor body; and a pressure-sensitive structure associated with the sensor body, wherein the pressure-sensitive structure is adapted to provide a feedback related to a pressure applied to the sensor body.
There is also provided a method of operating a sensor including: emitting light into a tissue with an emitter; detecting the light with a detector; measuring a physiological characteristic based on the detected light; detecting a force experienced by at least one of the emitter and the detector with a force-sensitive sensor; and triggering an alarm when the force is greater than a threshold value.
There is also provided a method of manufacturing a sensor that includes providing a sensor body on which at least one sensing element is disposed; and providing a pressure-sensitive structure disposed on the sensor body.
There is also provided a method that includes: acquiring pressure data and oxygen saturation data from a sensor; correlating the acquired pressure data to a set of reference artifact data; and determining if the oxygen saturation data comprises a motion artifact.
BRIEF DESCRIPTION OF THE DRAWINGS
Advantages of the invention may become apparent upon reading the following detailed description and upon reference to the drawings in which:
Fig. IA illustrates a perspective view of an exemplary sensor featuring force- sensitive mesh regions;
Fig. IB illustrates a cross-sectional view of the sensor of Fig. IA applied to a patient digit;
Fig. 1C illustrates a perspective view of the tissue-contacting surface of the sensor of Fig. IA;
Fig. 2 illustrates a perspective view of the sensor of Fig. IA after deformation of the force-sensitive mesh caused by finger tapping;
Fig. 3 illustrates a perspective view of the sensor of Fig. IA after deformation of the force-sensitive mesh caused by finger squeezing at the joint;
Fig. 4A illustrates a perspective view of an exemplary embodiment of a forehead sensor whereby the force-sensitive mesh is disposed in a region around the emitter and detector;
Fig. 4B illustrates a perspective view of the sensor of Fig. 4A after deformation of the force-sensitive mesh caused by pressing the sensor against an object;
Fig. 5A illustrates a cross-sectional view of an exemplary embodiment of a clip- style sensor with force-sensitive foam disposed on the tissue-contacting side of the sensor;
Fig. 5B illustrates a cross-sectional view of the pulse oximetry sensor of Fig. 5A in which the force-sensitive foam compresses in response to finger motion;
Fig. 6A illustrates a cross-sectional view of an exemplary embodiment of a sensor with a color-changing force-sensitive structure disposed on the sensor around the joint;
Fig. 6B illustrates a cross-sectional view of the pulse oximetry sensor of Fig. 6A in which flexing at the joint causes the force-sensitive structure to change from colorless to red;
Fig. 7 is a flow chart of the alarm trigger responsive to sensor output according to the present invention;
Fig. 8 is a more detailed flow chart of step 82 from Fig. 7; and
Fig. 9 illustrates a pulse oximetry system coupled to a multi-parameter patient monitor and a sensor according to embodiments of the present invention.
DETAILED DESCRIPTION OF SPECIFIC EMBODIMENTS
One or more specific embodiments of the present invention will be described below. In an effort to provide a concise description of these embodiments, not all features of an actual implementation are described in the specification. It should be appreciated that in the development of any such actual implementation, as in any engineering or design project, numerous implementation-specific decisions must be made to achieve the developers' specific goals, such as compliance with system-related and business-related constraints, which may vary from one implementation to another. Moreover, it should be appreciated that such a development effort might be complex and time consuming, but
would nevertheless be a routine undertaking of design, fabrication, and manufacture for those of ordinary skill having the benefit of this disclosure.
In accordance with the present technique, sensors for pulse oximetry or other applications utilizing spectrophotometry are provided that reduce motion artifacts by correcting for the effects of patient movement and outside forces. For example, sensors are provided that include force-sensitive devices adapted to assess the pressure experienced by a sensor while in use. Further, sensors as provided herein may notify a user that above-normal pressures are being exerted on a sensor, which may prompt relocation of the sensor to a tissue site that is less subject to motion artifacts.
Motion artifacts in pulse oximetry are often generated by the movement of the sensor relative to the optically probed tissue, which is typically caused by patient movement or other forces acting on the sensor. Because pulse oximetry is often used in settings where it is difficult to prevent patient motion, it is desirable to provide a mechanism for reducing the effects of motion on the pulse oximetry measurement. For example, a squeezing motion by a patient may mechanically deform a sensor, causing the sensor's emitter and detector to temporarily change position relative to one another, resulting in a motion artifact. Similarly, outside forces, such as the mechanical force of an object pressing against a sensor, may also cause mechanical deformation of a sensor and movement of the sensing components.
It is desirable to account for the effect of forces on a sensor while in use by providing qualitative information indicating to a healthcare provider or other user that an event, such as a patient motion, is occurring that is likely to cause motion artifacts. In other embodiments, it is desirable to quantitatively assess the motion or force acting on a sensor in order to correct the sensor measurements accordingly. For example, a squeezing motion by a finger may be assessed by a sensor 10 as provided herein. The squeezing may mechanically deform a force-sensitive region on a sensor body applied to the finger. The force of squeezing may be converted to an electrical signal that is sent to a monitor in order to assess the force experienced by the sensor and thus correct for the motion of the emitter relative to the detector.
Figs. IA-C illustrate an exemplary bandage-style sensor 1OA adapted for use on a digit. The sensor 1OA has a force-sensitive structure 12 disposed on the sensor body 16 in
a region corresponding to a fingertip region of a digit when the sensor 1OA is applied to a digit 18, as shown in Fig. IB. The sensor 1OA, as depicted, also has a force-sensitive structure 14 disposed on the sensor body 16 in a region corresponding to a joint region of the digit 18. The force-sensitive sensors 12 and 14 may be disposed on the sensor body 16 on the surface 20 that does not contact the digit 18 during normal use. As shown in Fig. 1C, the force-sensitive sensors 12 and 14 may be disposed on the surface 20 of the sensor body 16 that opposes the tissue-contacting surface 22 upon which the emitter 24 and the detector 26 are disposed. In alternate embodiments, it is contemplated that the force-sensitive sensors 12 and 14 may be embedded in the sensor body 16 or disposed on the tissue-contacting surface 22.
The force-sensitive sensors 12 and 14 have input and output leads 28 and 30 respectively, which may be embedded in the sensor body 16. It is contemplated that the leads 28 and 30 may be connected to a cable 36 that also connects to the electrical lead 32 of the emitter 24 and the electrical lead 34 of the detector 26. As depicted, the force-sensitive sensors 12 and 14 maybe flexible mesh-type arrays of multiple sensing elements, or maybe flexible circuits.
In other embodiments, the sensor 1OA may have additional force-sensitive sensors disposed on the sensor body 16. It may be advantageous to provide force-sensitive sensors on multiple sides of the sensor 1OA, as it is difficult to predict the types of motion that the sensor 1OA may experience. For example, force-sensitive sensors may be distributed on the sensor body 16 in locations directly opposing each other across the digit 18. Such an arrangement may provide more complete information about a squeezing motion of the digit 18 at a joint, as a force-sensitive structure on the top of the digit 18 may experience a stretching force while a force-sensitive structure in the crease of the joint may experience a compression force. Further, force-sensitive sensors may be disposed on the sensor body 16 in regions that correspond to the sides of the digit to provide information about the pressure experienced by the sensor body 16 during a rolling motion of the digit 18.
More specifically, Fig. 2 illustrates a perspective view of the sensor 1OA with an exemplary deformation pattern of the force-sensitive structure 12 in response to a finger- tapping or pressing motion. An x-axis 38 and a y-axis 40 correspond to the plane of the
sensor body 16. A z-axis 42 corresponds to the direction of pressure from the tapping motion of the digit 18. As the digit 18 presses against the tip of the sensor body 16, the force-sensitive structure 12 is deformed such that certain portions of the mesh form a peak- like structure 19. The deformation in response to pressure may cause certain intersection points in the grid of the force-sensitive structure 12 to be pushed closer together. As the distances between the intersection points change, the force-sensitive structure 12 may convert the change in the distances into an electrical signal that is related to the pressure experienced by the sensor 1OA.
Similarly, Fig. 3 illustrates a perspective view of the sensor 1OA with an exemplary deformation pattern of the force-sensitive structure 14 in response to a finger squeezing motion. The z-axis 42 corresponds to the direction of pressure from a squeezing motion of the digit 18. As the digit 18 flexes at the joint, the force-sensitive structure 14 is deformed such that the mesh is compressed. The deformation in response to squeezing may cause certain intersection points in the grid of the force-sensitive structure 14 to be pushed closer together. As above, the change in the distance between intersection points of the grid of the force-sensitive structure may be converted into an electrical signal.
It is also contemplated that a force-sensitive structure may be disposed on a sensor body in a region corresponding to at least one of an emitter or a detector. Fig. 4A illustrates a reflectance-type sensor 1OB adapted for use on a patient's forehead. The sensor 1OB has a force-sensitive structure 44 disposed on a tissue-contacting surface 45 of the sensor body 50. The emitter 46 and the detector 48 are surrounded by the force- sensitive structure 44, which deforms in response to outside forces, thereby providing a measure of the outside forces acting upon the emitter 46 and the detector 48. Fig. 4B illustrates an exemplary deformation of the force-sensitive structure 44 as it may appear after a patient has pressed the sensor 1OB against a pillow or other object during normal wear.
Force-sensitive sensors as described herein may be any appropriate sensor that is capable of converting a force applied to a sensor body into an electrical signal. In certain embodiments, the pressure or force-sensitive structure may take the form of a displacement sensor, hi one such embodiment, the pressure or force-sensitive structure
may include a strain gauge or other mechanical displacement sensor. In another embodiment, the displacement sensor may include a linear variable differential transformer, hi other embodiments, a force-sensitive structure may be a resistance-based sensor. Force-sensitive sensors, e.g. sensors 12, 14, and 44 maybe disposed on the sensor body as electrodes, such as silver electrodes, printed as a matrix of intersecting rows and columns. An additional layer of semiconductive ink may provide an electrical resistance at each intersection on the matrix. Sandwiching these two layers together may create an array sensor. When a force is applied, the change in resistance is measured. Changing the formulation of the ink may produce different sensitivity ranges. Additionally, varying the spacing between rows and columns may yield finer resolution, hi certain embodiments, a force-sensitive structure may have a spatial resolution, or sensor electrode spacing, of at least 0.0229 mm . An example of a resistance sensor that is appropriate for use with a sensor 10 according to the present techniques is Flexiforce® film or flexible circuits, available from Tekscan (South Boston, MA).
Pressure measurements may also be made by using polymers that are force- sensitive resistor materials. Force-sensitive resistor materials, such as those available from Interlink (Carptenteria, CA) and Advanced Composites Technology (Boston, MA) have a resistance variation under load. A force sensing resistor may be a piezoresistivity conductive polymer, which changes resistance in a predictable manner following application of force to its surface. It is normally supplied as a polymer sheet which has had the sensing film applied by screen printing. The sensing film typically includes both electrically conducting and non-conducting particles suspended in matrix. The particle sizes may be of the order of fraction of microns, and the particles may be formulated to reduce the temperature dependence, improve mechanical properties and increase surface durability. Applying a force to the surface of the sensing film causes particles to touch the conducting electrodes, changing the resistance of the film. Such a polymer-based force- sensitive resistor may be advantageous as it utilizes a relatively simple interface and can operate satisfactorily in moderately hostile environments. hi certain embodiments, the pressure or force-sensitive structure may take the form of a capacitance sensor. In such sensors, the capacitance is inversely proportional to the distance between the electrodes of the sensor. An exemplary capacitance-based
sensor, TactArray, is available from Pressure Profile Systems (Los Angeles, CA). In certain embodiments, the capacitance sensor may be sensitive to forces or pressures from lpsi to 200psi.
In a specific embodiment, it may be advantageous to provide a mechanism for monitoring movement of a digit within a relatively rigid clip-style sensor. Figs. 5A-B illustrate a sensor 1 OC that includes an elastomeric foam that is sensitive to force. The force-sensitive foam 52 provides measurement of the resistance of a conductive elastomer or foam between two points. The force-sensitive foam may be a carbon doped rubber in which the resistance of the elastomer changes with the application of force, resulting from the deformation of the elastomer altering the particle density. As depicted, the force- sensitive foam is disposed on the tissue-contacting surface 54 of the sensor body 56. As the digit 58 moves within the sensor 1OC, the foam is compressed, resulting in a change in the resistance of the foam. The electrical signal generated by the movement of the digit may be further processed to correct for any motion artifacts caused by the movement of the digit relative to the sensor 1OC. m certain embodiments, it is envisioned that force or pressure data generated from the force-sensitive structures may be further processed to generate displays or other information related to a sensor 10 condition. However, as patients may not be familiar with the medical monitor icons and displays that may be used in conjunction with a sensor 10, in certain embodiments it may be advantageous to provide a sensor 10 with a force- sensitive signal that is easily identifiable by a patient. Fig. 6A illustrates a sensor 1OD applied to a patient digit 60. The sensor 1OD includes a force-sensitive structure 62 disposed on the surface 64 of the sensor body 66 that does not contact the digit during normal use. The force-sensitive structure 62 is adapted to change color upon the application of force. As illustrated in Fig. 6B, upon squeezing of the digit 60 at the first joint, the force-sensitive structure 62 changes color from colorless to red as pressure increased in the area of the force-sensitive structure 62. The force-sensitive structure 62 may be Pressurex® film, available from Sensor Products Inc. (East Hanover, NJ), which increases in red color intensity in relation to the amount of force applied. A conscious patient may easily note the change in color and adjust his actions to prevent further movements that may be associated with motion artifacts and measurement errors.
It is envisioned that a sensor 10 as described herein may be used to provide information related to the pressure and forces experienced by the sensor 10 during use. Such information may be converted into an electrical signal and sent to a monitor or another appropriate device, as described in more detail below, for processing. The flow chart 68 depicted in Fig. 7 describes the downstream steps involved after step 70, which involves acquisition of the oxygen saturation data 74 from the sensor 10, and step 72, which involves acquisition of force or pressure data 76. In certain embodiments, it is envisioned that steps 70 and 72 may occur simultaneously.
At a step 78, a processor compares the pressure data 76 against a pressure threshold. Generally, the raw pressure data 76 output from a force-sensitive structure as described herein is further acted upon by a processor, such as a processor in a pulse oximeter, to provide either a pressure map or a pressure value. As a sensor 10 may provide separate pressure outputs from multiple force-sensitive structures, it may be advantageous to provide a map of the pressure variations at different locations on the sensor body, hi other embodiments, it may be appropriate to provide a measure of the total pressure experienced by the sensor body, or the total pressure experienced at a single location, such as a fingertip location. The map or value may then be compared to a predetermined threshold map or predetermined threshold value. The threshold value is generally envisioned to be a pressure value that is associated with an increase in motion artifacts. A threshold map may be an image which may be directly compared to a pressure map obtained from the force-sensitive structure. If, at a step 78, the pressure data 76 does not exceed a predetermined threshold value, the processor passes control to step 80. At step 80, the system goes into a default mode and a processor calculates an oxygen saturation value from the oxygen saturation data 74. The oxygen saturation value may then be displayed on a monitor.
If, on the other hand, the pressure data 76 does exceed a threshold pressure value, the processor passes control to steps 82 and 84. In step 84, a notification is displayed to alert a user that the pressure experienced by a sensor 10 has increased beyond a critical threshold value. The notification may be an audio alarm, such as a warning sound, or a visual alarm, such as a text message or icon that is displayed on a monitor.
In step 82, a processor may act upon the oxygen saturation data 74 in order to correct for any influence of higher-than-normal pressures on the sensor 10. The corrected oxygen saturation value may then be displayed on the monitor. For example, a processor may adjust an estimation of the path length between an emitter and a detector to account for any reduction in the path length due to tissue compression. In such an example, measured pressure would be inversely related to path length. The adjustment of the path length may result in a correction in the oxygen saturation.
In another embodiment, shown in Fig. 8, step 82 may be accomplished by correlating pressure data 76 to previously acquired or reference artifact data characteristic of different pressure events. At step 104, the pressure data 76 exceeding a pre-defined threshold at step 78 is provided as input into a searchable machine-readable database of artifact data to determine if the pressure data 76 is characteristic of particular artifact events. The look-up database of artifact in step 104 may be acquired through measurements of various pressure profiles associated with artifact events to build a lookup database or table that correlates pressure data 76 with possible artifact/interference- related saturation data. For example, the pressure data 76 may be compared to an artifact database in step 104 to determine if the pressure data 76 is characteristic of venous pooling under the fingertip during tapping or compartmentalization of blood in the finger during scratching. The oxygen saturation data 74 may then be corrected in light of the particular type of pressure experienced by the tissue. The database artifact/interference data obtained from step 104 that correlates with or is characteristic of the pressure data 76 is analyzed in frequency domain at step 106 using frequency transforms such as FFT (Fast Fourier Transform) and WT (Wavelet Transform). Additionally in step 106, frequency transforms are also applied to the acquired raw saturation data 74. At certain frequencies where found artifacts/interferences are located, the artifacts/interferences may be removed from saturation data in the frequency domain. The resultant corrected frequency domain saturation data (with artifact/interference removed) may then be used to reconstruct the clean time domain saturation signal via inverse transforms such as inverse FFT and inverse wavelet transform at step 108. The reconstructed oxygen saturation data may then be displayed in step 86.
In another embodiment (not shown), a sensor 10 may include a second emitter and detector pair located in a different position on the sensor body than the first emitter and detector pair. At step 78, a processor may note that pressure data 76 from the first emitter and detector pair exceeds a threshold pressure value. The processor may then pass control to the second emitter and detector pair, which may be located at a site that experiences pressures below the threshold pressure value. In an alternate embodiment (not shown), a sensor 10 may include an emitter and first detector located in a different position on the sensor body than a second detector. At step 78, a processor may note that pressure data 76 from the first emitter and first detector exceeds a threshold pressure value, and the processor may pass control to the second detector.
A sensor, illustrated generically as a sensor 10, maybe used in conjunction with a pulse oximetry monitor 88, as illustrated in Fig. 9. It should be appreciated that the cable 90 of the sensor 10 may be coupled to the monitor 88 or it may be coupled to a transmission device (not shown) to facilitate wireless transmission between the sensor 10 and the monitor 88. The monitor 88 may be any suitable pulse oximeter, such as those available from Nellcor Puritan Bennett Inc. Furthermore, to upgrade conventional pulse oximetry provided by the monitor 88 to provide additional functions, the monitor 88 may be coupled to a multi-parameter patient monitor 92 via a cable 94 connected to a sensor input port or via a cable 96 connected to a digital communication port.
The sensor 10 includes an emitter 98 and a detector 100 that may be of any suitable type. For example, the emitter 98 may be one or more light emitting diodes adapted to transmit one or more wavelengths of light in the red to infrared range, and the detector 100 may one or more photodetectors selected to receive light in the range or ranges emitted from the emitter 98. Alternatively, an emitter 98 may also be a laser diode or a vertical cavity surface emitting laser (VCSEL). An emitter 98 and detector 100 may also include optical fiber sensing elements. An emitter 98 may include a broadband or "white light" source, in which case the detector could include any of a variety of elements for selecting specific wavelengths, such as reflective or refractive elements or interferometers. These kinds of emitters and/or detectors would typically be coupled to the rigid or rigidified sensor via fiber optics. Alternatively, a sensor 10 may sense light detected from the tissue is at a different wavelength from the light emitted into the tissue.
Such sensors may be adapted to sense fluorescence, phosphorescence, Raman scattering, Rayleigh scattering and multi-photon events or photoacoustic effects. For pulse oximetry applications using either transmission or reflectance type sensors the oxygen saturation of the patient's arterial blood may be determined using two or more wavelengths of light, most commonly red and near infrared wavelengths. Similarly, in other applications, a tissue water fraction (or other body fluid related metric) or a concentration of one or more biochemical components in an aqueous environment may be measured using two or more wavelengths of light, most commonly near infrared wavelengths between about 1,000 nm to about 2,500 nm. It should be understood that, as used herein, the term "light" may refer to one or more of ultrasound, radio, microwave, millimeter wave, infrared, visible, ultraviolet, gamma ray or X-ray electromagnetic radiation, and may also include any wavelength within the radio, microwave, infrared, visible, ultraviolet, or X-ray spectra.
The emitter 98 and the detector 100 maybe disposed on a sensor body 102, which may be made of any suitable material, such as plastic, foam, woven material, or paper. Alternatively, the emitter 98 and the detector 100 may be remotely located and optically coupled to the sensor 10 using optical fibers. In the depicted embodiments, the sensor 10 is coupled to a cable 90 that is responsible for transmitting electrical and/or optical signals to and from the emitter 98 and detector 100 of the sensor 10. The cable 90 may be permanently coupled to the sensor 10, or it may be removably coupled to the sensor 10 ~ the latter alternative being more useful and cost efficient in situations where the sensor 10 is disposable.
The sensor 10 may be a "transmission type" sensor. Transmission type sensors include an emitter 98 and detector 100 that are typically placed on opposing sides of the sensor site. If the sensor site is a fingertip, for example, the sensor 10 is positioned over the patient's fingertip such that the emitter 98 and detector 100 lie on either side of the patient's nail bed. hi other words, the sensor 10 is positioned so that the emitter 98 is located on the patient's fingernail and the detector 100 is located 180° opposite the emitter 98 on the patient's finger pad. During operation, the emitter 98 shines one or more wavelengths of light through the patient's fingertip and the light received by the detector 100 is processed to determine various physiological characteristics of the patient, hi each of the embodiments discussed herein, it should be understood that the locations of the
emitter 98 and the detector 100 may be exchanged. For example, the detector 100 may be located at the top of the finger and the emitter 98 may be located underneath the finger. In either arrangement, the sensor 10 will perform in substantially the same manner.
Reflectance type sensors also operate by emitting light into the tissue and detecting the light that is transmitted and scattered by the tissue. However, reflectance type sensors include an emitter 98 and detector 100 that are typically placed on the same side of the sensor site. For example, a reflectance type sensor may be placed on a patient's fingertip or forehead such that the emitter 98 and detector 100 lie side-by-side. Reflectance type sensors detect light photons that are scattered back to the detector 100. A sensor 10 may also be a "transflectance" sensor, such as a sensor that may subtend a portion of a baby's heel.
While the invention may be susceptible to various modifications and alternative forms, specific embodiments have been shown by way of example in the drawings and have been described in detail herein. However, it should be understood that the invention is not intended to be limited to the particular forms disclosed. Indeed, the present techniques may not only be applied to measurements of blood oxygen saturation, but these techniques may also be utilized for the measurement and/or analysis of other blood constituents. For example, using the same, different, or additional wavelengths, the present techniques may be utilized for the measurement and/or analysis of carboxyhemoglobin, met-hemoglobin, total hemoglobin, fractional hemoglobin, intravascular dyes, and/or water content. Rather, the invention is to cover all modifications, equivalents, and alternatives falling within the spirit and scope of the invention as defined by the following appended claims
Claims
1. A sensor comprising: a sensor body; at least one sensing element disposed on the sensor body; and a pressure-sensitive structure associated with the sensor body, wherein the pressure- sensitive structure is adapted to provide a feedback related to a pressure applied to the sensor body.
2. The sensor, as set forth in claim 1, wherein the sensor comprises at least one of a pulse oximetry sensor or a sensor for measuring a water fraction.
3. The sensor, as set forth in claim 1, wherein the sensing element comprises an emitter and a detector.
4. The sensor, as set forth in claim 3, wherein the emitter comprises at least one light emitting diode and the detector comprises at least one photodetector.
5. The sensor, as set forth in claim 1, wherein the feedback comprises an electrical signal.
6. The sensor, as set forth in claim 1, wherein the wherein the pressure- sensitive structure comprises a capacitance-based sensor or a resistance-based sensor.
7. The sensor, as set forth in claim 1 , wherein the wherein the pressure- sensitive structure comprises a displacement-based sensor.
8. The sensor, as set forth in claim 1, wherein the pressure-sensitive structure is conformable.
9. The sensor, as set forth in claim 1 , wherein the pressure-sensitive structure comprises an array of pressure sensors.
10. The sensor, as set forth in claim 1 , wherein the pressure-sensitive structure is disposed on the surface of the sensor body that does not contact a patient's tissue during normal use.
11. The sensor, as set forth in claim 1 , wherein the sensor comprises a bandage- type sensor.
12. A pulse oximetry system comprising: a pulse oximetry monitor; and a pulse oximetry sensor adapted to be operatively coupled to the monitor, the sensor comprising: a sensor body; at least one sensing element disposed on the sensor body; and a pressure-sensitive structure associated with the sensor body, wherein the pressure-sensitive structure is adapted to provide a feedback related to a pressure applied to the sensor body.
13. The system, as set forth in claim 12, wherein the sensor comprises at least one of a pulse oximetry sensor or a sensor for measuring a water fraction.
14. The system, as set forth in claim 12, wherein the sensing element comprises an emitter and a detector.
15. The system, as set forth in claim 14, wherein the emitter comprises at least one light emitting diode and the detector comprises at least one photodetector.
16. The system, as set forth in claim 12, wherein the feedback comprises an electrical signal.
17. The system, as set forth in claim 12, wherein the wherein the pressure- sensitive structure comprises a capacitance-based sensor or a resistance-based sensor.
18. The system, as set forth in claim 12, wherein the wherein the pressure- sensitive structure comprises a displacement-based sensor.
19. The system, as set forth in claim 12, wherein the pressure-sensitive structure is conformable.
20. The system, as set forth in claim 12, wherein the pressure-sensitive structure comprises an array of pressure sensors.
21. The system, as set forth in claim 12, wherein the pressure-sensitive structure is disposed on the surface of the sensor body that does not contact a patient's tissue during normal use.
22. The system, as set forth in claim 12, wherein the sensor comprises a bandage-type sensor.
23. The system, as set forth in claim 12, wherein the monitor is adapted to provide an indication related to the pressure feedback.
24. The system, as set forth in claim 23, wherein the indication comprises an alarm.
25. The system, as set forth in claim 24, wherein the alarm comprises at least one of a visual alarm or an audio alarm.
26. The system, as set forth in claim 24, wherein the indication comprises a corrected pulse oximetry measurement.
27. The system, as set forth in claim 12, comprising reference artifact data stored on a machine-readable medium.
28. The system, as set forth in claim 27, wherein the reference artifact data comprises clinical artifact data.
29. The system, as set forth in claim 12, wherein the system comprises a digital signal processing module.
30. A method comprising: emitting light into a tissue with an emitter; detecting the light with a detector; measuring a physiological characteristic based on the detected light; detecting a force experienced by at least one of the emitter and the detector with a force-sensitive sensor; and triggering an alarm when the force is greater than a threshold value.
31. The method, as set forth in claim 30, wherein detecting the force comprises detecting a change in capacitance or a change in resistance.
32. The method, as set forth in claim 30, wherein detecting the force comprises detecting displacement.
33. The method, as set forth in claim 30, wherein triggering the alarm comprises emitting an audio signal.
34. The method, as set forth in claim 30, wherein triggering the alarm comprises emitting a visual signal.
35. The method, as set forth in claim 30, comprising emitting light from a second emitter and detecting the light with a second detector when the force is greater than a threshold value.
36. The method, as set forth in claim 30, comprising detecting the light with a second detector when the force is greater than a threshold value.
37. The method, as set forth in claim 30, comprising correcting the measurement of the blood constituent when the force is greater than a threshold value.
38. The method, as set forth in claim 37, wherein correcting the measurement of the blood constituent comprises correcting the estimated path length between the emitter and the detector.
39. The method, as set forth in claim 37, wherein correcting the measurement of the blood constituent comprises comparing the force experienced by the emitter and the detector to a set of previously acquired force data.
40. The method, as set forth in claim 39, wherein the set of previously acquired force data comprises force data characteristic of scratching or tapping.
41. A method of manufacturing a sensor, comprising: providing a sensor body on which at least one sensing element is disposed; and providing a pressure-sensitive structure disposed on the sensor body.
42. The method, as set forth in claim 41, wherein the sensor comprises at least one of a pulse oximetry sensor or a sensor for measuring a water fraction.
43. The method, as set forth in claim 41 , wherein providing the sensing element comprises providing an emitter and a detector.
44. The method, as set forth in claim 43, wherein providing the emitter comprises providing one or more light emitting diodes and providing the detector comprises providing one or more photodetectors.
45. The method, as set forth in claim 41 , wherein providing the pressure- sensitive structure comprises providing a capacitance-based sensor or a resistance-based sensor.
46. The method, as set forth in claim 41 , wherein providing the pressure- sensitive structure comprises providing a displacement-based sensor.
47. A method comprising: acquiring pressure data and oxygen saturation data from a sensor; correlating the acquired pressure data to a set of reference artifact data; and determining if the oxygen saturation data comprises a motion artifact.
48. The method, as set forth in claim 47, wherein correlating the acquired pressure data with the reference artifact data comprises a look-up process that operates on the reference artifact data to generate input to a digital signal processing module.
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US11/240,682 US7483731B2 (en) | 2005-09-30 | 2005-09-30 | Medical sensor and technique for using the same |
US11/240,682 | 2005-09-30 |
Publications (1)
Publication Number | Publication Date |
---|---|
WO2007041330A1 true WO2007041330A1 (en) | 2007-04-12 |
Family
ID=37596198
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/US2006/038121 WO2007041330A1 (en) | 2005-09-30 | 2006-09-29 | Medical sensor and technique for using the same |
Country Status (3)
Country | Link |
---|---|
US (2) | US7483731B2 (en) |
TW (1) | TW200726443A (en) |
WO (1) | WO2007041330A1 (en) |
Cited By (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
GB2578120A (en) * | 2018-10-16 | 2020-04-22 | Medical Wireless Sensing Ltd | Movement sensing clamp |
Families Citing this family (92)
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 |
WO2004112448A2 (en) * | 2003-06-13 | 2004-12-23 | Semtech Corporation | Sensor for capacitive touch pad pointing device |
CN101912257B (en) * | 2003-10-09 | 2013-04-24 | 日本电信电话株式会社 | Living body information detection circuit and living body information measurement apparatus |
CA2584863A1 (en) * | 2004-11-09 | 2006-05-18 | Cybiocare Inc. | Method and apparatus for the reduction of spurious effects on physiological measurements |
US8002711B2 (en) * | 2005-03-18 | 2011-08-23 | Respironics, Inc. | Methods and devices for relieving stress |
US20070060808A1 (en) | 2005-09-12 | 2007-03-15 | Carine Hoarau | 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 |
US7869850B2 (en) | 2005-09-29 | 2011-01-11 | Nellcor Puritan Bennett Llc | Medical sensor for reducing motion artifacts 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 |
US7483731B2 (en) | 2005-09-30 | 2009-01-27 | Nellcor Puritan Bennett Llc | Medical sensor and technique for using the same |
US8073518B2 (en) | 2006-05-02 | 2011-12-06 | Nellcor Puritan Bennett Llc | Clip-style medical sensor and technique for using the same |
US10188348B2 (en) | 2006-06-05 | 2019-01-29 | Masimo Corporation | Parameter upgrade system |
US7845350B1 (en) * | 2006-08-03 | 2010-12-07 | Cleveland Medical Devices Inc. | Automatic continuous positive airway pressure treatment system with fast respiratory response |
US8145288B2 (en) | 2006-08-22 | 2012-03-27 | 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 |
US8190224B2 (en) | 2006-09-22 | 2012-05-29 | 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 |
US7680522B2 (en) * | 2006-09-29 | 2010-03-16 | Nellcor Puritan Bennett Llc | Method and apparatus for detecting misapplied sensors |
US7880626B2 (en) | 2006-10-12 | 2011-02-01 | Masimo Corporation | System and method for monitoring the life of a physiological sensor |
US7894869B2 (en) | 2007-03-09 | 2011-02-22 | Nellcor Puritan Bennett Llc | Multiple configuration medical sensor and technique for using the same |
US8116838B2 (en) * | 2007-11-27 | 2012-02-14 | Carnegie Mellon University | Medical device for diagnosing pressure ulcers |
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 |
EP2234535A1 (en) * | 2007-12-26 | 2010-10-06 | Nellcor Puritan Bennett LLC | Historical trend icons for physiological parameters |
WO2009086452A1 (en) * | 2007-12-26 | 2009-07-09 | Nellcor Puritan Bennett Llc | Pulse oximetry sensor with a pressure sensor |
US8766925B2 (en) * | 2008-02-28 | 2014-07-01 | New York University | Method and apparatus for providing input to a processor, and a sensor pad |
US20090281435A1 (en) * | 2008-05-07 | 2009-11-12 | Motorola, Inc. | Method and apparatus for robust heart rate sensing |
US8660799B2 (en) * | 2008-06-30 | 2014-02-25 | Nellcor Puritan Bennett Ireland | Processing and detecting baseline changes in signals |
US8257274B2 (en) | 2008-09-25 | 2012-09-04 | Nellcor Puritan Bennett Llc | Medical sensor and technique for using the same |
US8364220B2 (en) | 2008-09-25 | 2013-01-29 | Covidien Lp | Medical sensor and technique for using the same |
US20100081904A1 (en) * | 2008-09-30 | 2010-04-01 | Nellcor Puritan Bennett Llc | Device And Method For Securing A Medical Sensor to An Infant's Head |
EP2395907A4 (en) * | 2009-02-13 | 2015-04-22 | Hutchinson Technology | Portable sto2 spectrometer |
US8515515B2 (en) | 2009-03-25 | 2013-08-20 | Covidien Lp | Medical sensor with compressible light barrier and technique for using the same |
US8781548B2 (en) | 2009-03-31 | 2014-07-15 | Covidien Lp | Medical sensor with flexible components and technique for using the same |
US8571619B2 (en) | 2009-05-20 | 2013-10-29 | Masimo Corporation | Hemoglobin display and patient treatment |
US8634891B2 (en) | 2009-05-20 | 2014-01-21 | Covidien Lp | Method and system for self regulation of sensor component contact pressure |
US20110060224A1 (en) * | 2009-08-09 | 2011-03-10 | Tz Medical, Inc. | Non-invasive continuous doppler monitoring device for arterial blood flow to distal body parts |
US8494606B2 (en) * | 2009-08-19 | 2013-07-23 | Covidien Lp | Photoplethysmography with controlled application of sensor pressure |
US20110066042A1 (en) * | 2009-09-15 | 2011-03-17 | Texas Instruments Incorporated | Estimation of blood flow and hemodynamic parameters from a single chest-worn sensor, and other circuits, devices and processes |
US8798704B2 (en) * | 2009-09-24 | 2014-08-05 | Covidien Lp | Photoacoustic spectroscopy method and system to discern sepsis from shock |
US20110190612A1 (en) * | 2010-02-02 | 2011-08-04 | Nellcor Puritan Bennett Llc | Continous Light Emission Photoacoustic Spectroscopy |
US8391943B2 (en) | 2010-03-31 | 2013-03-05 | Covidien Lp | Multi-wavelength photon density wave system using an optical switch |
US8930145B2 (en) | 2010-07-28 | 2015-01-06 | Covidien Lp | Light focusing continuous wave photoacoustic spectroscopy and its applications to patient monitoring |
GB201014618D0 (en) * | 2010-09-03 | 2010-10-13 | Qinetiq Ltd | Respirtory protection equipment |
US9775545B2 (en) | 2010-09-28 | 2017-10-03 | Masimo Corporation | Magnetic electrical connector for patient monitors |
JP5710767B2 (en) | 2010-09-28 | 2015-04-30 | マシモ コーポレイション | Depth of consciousness monitor including oximeter |
US20120113411A1 (en) * | 2010-11-09 | 2012-05-10 | Nellcor Puritan Bennett Llc | Optical fiber sensors |
US8596147B2 (en) | 2010-11-30 | 2013-12-03 | Hallmark Cards, Incorporated | Non-rigid sensor for detecting deformation |
JP6151882B2 (en) | 2010-12-24 | 2017-06-21 | キヤノン株式会社 | Subject information acquisition apparatus and subject information acquisition method |
AU2012207287B2 (en) * | 2011-01-19 | 2015-12-17 | The Regents Of The University Of California | Apparatus, systems, and methods for tissue oximetry and perfusion imaging |
US9289177B2 (en) * | 2011-01-20 | 2016-03-22 | Nitto Denko Corporation | Sensing device, a method of preparing a sensing device and a personal mobile sensing system |
EP2665410B1 (en) | 2011-01-21 | 2017-08-30 | Worcester Polytechnic Institute | Physiological parameter monitoring with a mobile communication device |
TWI498106B (en) * | 2011-07-20 | 2015-09-01 | Crystalvue Medical Corp | Non-invasive detecting apparatus and operating method thereof |
US8852095B2 (en) | 2011-10-27 | 2014-10-07 | Covidien Lp | Headband for use with medical sensor |
US9138181B2 (en) | 2011-12-16 | 2015-09-22 | Covidien Lp | Medical sensor for use with headband |
EP2849635A4 (en) * | 2012-05-18 | 2016-01-20 | Univ Florida | PATIENT IN-TtHE-LOOP PARTICIPATORY CARE AND MONITORING |
JP6118512B2 (en) * | 2012-07-04 | 2017-04-19 | 株式会社日立製作所 | Biological light measurement device |
US10881310B2 (en) | 2012-08-25 | 2021-01-05 | The Board Of Trustees Of The Leland Stanford Junior University | Motion artifact mitigation methods and devices for pulse photoplethysmography |
US9177884B2 (en) | 2012-10-09 | 2015-11-03 | Avago Technologies General Ip (Singapore) Pte. Ltd. | Two-sided-access extended wafer-level ball grid array (eWLB) package, assembly and method |
US9380981B2 (en) | 2013-03-15 | 2016-07-05 | Covidien Lp | Photoacoustic monitoring technique with noise reduction |
WO2014186592A1 (en) * | 2013-05-16 | 2014-11-20 | Nch Healthcare System, Inc. | Pressure sensitive assemblies for limiting movements adverse to health or surgical recovery |
EP3021801B1 (en) * | 2013-07-18 | 2017-10-25 | Coloplast A/S | Touch mapping |
US9665213B2 (en) * | 2013-08-30 | 2017-05-30 | Maxim Integrated Products, Inc. | Detecting pressure exerted on a touch surface and providing feedback |
EP2898825A1 (en) * | 2014-01-22 | 2015-07-29 | ams AG | Portable device for optical heart rate measurement and method |
US20150245782A1 (en) * | 2014-02-28 | 2015-09-03 | Covidien Lp | Systems and methods for capacitance sensing in medical devices |
US9305908B2 (en) | 2014-03-14 | 2016-04-05 | Avago Technologies General Ip (Singapore) Pte. Ltd. | Methods for performing extended wafer-level packaging (eWLP) and eWLP devices made by the methods |
US9541503B2 (en) | 2014-03-14 | 2017-01-10 | Avago Technologies General Ip (Singapore) Pte. Ltd. | Compact systems, compact devices, and methods for sensing luminescent activity |
US9443835B2 (en) | 2014-03-14 | 2016-09-13 | Avago Technologies General Ip (Singapore) Pte. Ltd. | Methods for performing embedded wafer-level packaging (eWLP) and eWLP devices, packages and assemblies made by the methods |
WO2016057553A1 (en) | 2014-10-07 | 2016-04-14 | Masimo Corporation | Modular physiological sensors |
US9541717B2 (en) | 2015-01-30 | 2017-01-10 | Avago Technologies General IP (Singapore) Pta. Ltd. | Optoelectronic assembly incorporating an optical fiber alignment structure |
KR102092864B1 (en) * | 2015-08-31 | 2020-03-24 | 삼성전자주식회사 | A seonsor module and a motion assist apparatus comprising thereof |
US20190069785A1 (en) * | 2015-09-04 | 2019-03-07 | Footfalls And Heartbeats (Uk) Limited | Combined textile pressure and optic sensor |
JP2019514603A (en) | 2016-05-09 | 2019-06-06 | ベルン テクノロジー カンパニー リミテッドBelun Technology Company Limited | Wearable device for healthcare and method therefor |
US10391400B1 (en) | 2016-10-11 | 2019-08-27 | Valve Corporation | Electronic controller with hand retainer and finger motion sensing |
US10987573B2 (en) | 2016-10-11 | 2021-04-27 | Valve Corporation | Virtual reality hand gesture generation |
US10898797B2 (en) | 2016-10-11 | 2021-01-26 | Valve Corporation | Electronic controller with finger sensing and an adjustable hand retainer |
US10649583B1 (en) | 2016-10-11 | 2020-05-12 | Valve Corporation | Sensor fusion algorithms for a handheld controller that includes a force sensing resistor (FSR) |
US10888773B2 (en) * | 2016-10-11 | 2021-01-12 | Valve Corporation | Force sensing resistor (FSR) with polyimide substrate, systems, and methods thereof |
US11185763B2 (en) | 2016-10-11 | 2021-11-30 | Valve Corporation | Holding and releasing virtual objects |
US10691233B2 (en) | 2016-10-11 | 2020-06-23 | Valve Corporation | Sensor fusion algorithms for a handheld controller that includes a force sensing resistor (FSR) |
US11625898B2 (en) | 2016-10-11 | 2023-04-11 | Valve Corporation | Holding and releasing virtual objects |
US10549183B2 (en) | 2016-10-11 | 2020-02-04 | Valve Corporation | Electronic controller with a hand retainer, outer shell, and finger sensing |
US10307669B2 (en) | 2016-10-11 | 2019-06-04 | Valve Corporation | Electronic controller with finger sensing and an adjustable hand retainer |
KR101780264B1 (en) * | 2017-01-17 | 2017-10-11 | 한국표준과학연구원 | Apparatus for measuring photoplethysmograph and method of measuring photoplethysmo graph |
JP7143336B2 (en) | 2017-06-16 | 2022-09-28 | バルブ コーポレーション | Electronic controller with finger motion sensing |
US11864909B2 (en) | 2018-07-16 | 2024-01-09 | Bbi Medical Innovations, Llc | Perfusion and oxygenation measurement |
US10485094B1 (en) * | 2018-08-27 | 2019-11-19 | Tactotek Oy | Multilayer structure with embedded sensing functionalities and related method of manufacture |
USD950492S1 (en) * | 2019-05-20 | 2022-05-03 | Biointellisense, Inc. | Multi-lobe sensor |
WO2021126117A1 (en) * | 2019-12-18 | 2021-06-24 | Istanbul Medipol Universitesi | Pulse oximeter that is not affected from motion |
WO2021252611A1 (en) * | 2020-06-09 | 2021-12-16 | Joyson Safety Systems Acquisition Llc | System and method of touch sensing using physiological or biochemical sensors |
Citations (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5226417A (en) * | 1991-03-11 | 1993-07-13 | Nellcor, Inc. | Apparatus for the detection of motion transients |
EP1386578A1 (en) * | 2002-08-02 | 2004-02-04 | Samsung Electronics Co., Ltd. | Probe for measuring a biological signal and system incorporating the probe |
US20040034294A1 (en) * | 2002-08-16 | 2004-02-19 | Optical Sensors, Inc. | Pulse oximeter |
Family Cites Families (754)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3403555A (en) | 1966-07-18 | 1968-10-01 | Versaci | Flowmeter |
BE661207A (en) | 1968-05-13 | 1965-07-16 | ||
US3721813A (en) | 1971-02-01 | 1973-03-20 | Perkin Elmer Corp | Analytical instrument system |
WO2000078209A2 (en) | 1999-06-18 | 2000-12-28 | Masimo Corporation | Pulse oximeter probe-off detection system |
US4098772A (en) | 1976-03-11 | 1978-07-04 | The Upjohn Company | Thermoplastic polyurethanes prepared with small amounts of monohydric alcohols |
USD250275S (en) | 1976-07-19 | 1978-11-14 | Hewlett-Packard Company | Self-attaching probe for use in photoelectric monitoring of body extremities |
USD251387S (en) | 1977-02-07 | 1979-03-20 | Component Manufacturing Service, Inc. | Electrical connector for electrocardiogram monitoring |
US4281645A (en) | 1977-06-28 | 1981-08-04 | Duke University, Inc. | Method and apparatus for monitoring metabolism in body organs |
USD262488S (en) | 1979-10-24 | 1981-12-29 | Novatec, Inc. | Pulse rate monitor |
US4353372A (en) | 1980-02-11 | 1982-10-12 | Bunker Ramo Corporation | Medical cable set and electrode therefor |
US4334544A (en) | 1980-04-28 | 1982-06-15 | Amf Incorporated | Ear lobe clip with heart beat sensor |
US4350165A (en) | 1980-05-23 | 1982-09-21 | Trw Inc. | Medical electrode assembly |
NL8005145A (en) | 1980-09-12 | 1982-04-01 | Tno | DEVICE FOR INDIRECT, NON-INVASIVE, CONTINUOUS MEASUREMENT OF BLOOD PRESSURE. |
GB8416219D0 (en) | 1984-06-26 | 1984-08-01 | Antec Systems | Patient monitoring apparatus |
JPS58143243A (en) | 1982-02-19 | 1983-08-25 | Minolta Camera Co Ltd | Measuring apparatus for coloring matter in blood without taking out blood |
US4621643A (en) | 1982-09-02 | 1986-11-11 | Nellcor Incorporated | Calibrated optical oximeter probe |
US4770179A (en) | 1982-09-02 | 1988-09-13 | Nellcor Incorporated | Calibrated optical oximeter probe |
US4700708A (en) | 1982-09-02 | 1987-10-20 | Nellcor Incorporated | Calibrated optical oximeter probe |
US4653498A (en) | 1982-09-13 | 1987-03-31 | Nellcor Incorporated | Pulse oximeter monitor |
EP0127947B1 (en) | 1983-05-11 | 1990-08-29 | Nellcor Incorporated | Sensor having cutaneous conformance |
US4830014A (en) | 1983-05-11 | 1989-05-16 | Nellcor Incorporated | Sensor having cutaneous conformance |
US4938218A (en) | 1983-08-30 | 1990-07-03 | Nellcor Incorporated | Perinatal pulse oximetry sensor |
US5109849A (en) | 1983-08-30 | 1992-05-05 | Nellcor, Inc. | Perinatal pulse oximetry sensor |
US5140989A (en) | 1983-10-14 | 1992-08-25 | Somanetics Corporation | Examination instrument for optical-response diagnostic apparatus |
US5217013A (en) | 1983-10-14 | 1993-06-08 | Somanetics Corporation | Patient sensor for optical cerebral oximeter and the like |
US4603700A (en) | 1983-12-09 | 1986-08-05 | The Boc Group, Inc. | Probe monitoring system for oximeter |
DE3405444A1 (en) | 1984-02-15 | 1985-08-22 | Kraus, Werner, Dipl.-Ing., 8000 München | Pulse sensor |
US4714341A (en) | 1984-02-23 | 1987-12-22 | Minolta Camera Kabushiki Kaisha | Multi-wavelength oximeter having a means for disregarding a poor signal |
US4510551A (en) | 1984-05-21 | 1985-04-09 | Endeco Canada Limited | Portable memory module |
US4677528A (en) | 1984-05-31 | 1987-06-30 | Motorola, Inc. | Flexible printed circuit board having integrated circuit die or the like affixed thereto |
IT1206462B (en) | 1984-08-07 | 1989-04-27 | Anic Spa | MULTI-WAVE LENGTH PULSED LIGHT PHOTOMETER FOR NON-INVASIVE MONITORING. |
USRE35122E (en) | 1985-04-01 | 1995-12-19 | Nellcor Incorporated | Method and apparatus for detecting optical pulses |
US4911167A (en) | 1985-06-07 | 1990-03-27 | Nellcor Incorporated | Method and apparatus for detecting optical pulses |
US4802486A (en) | 1985-04-01 | 1989-02-07 | Nellcor Incorporated | Method and apparatus for detecting optical pulses |
US4934372A (en) | 1985-04-01 | 1990-06-19 | Nellcor Incorporated | Method and apparatus for detecting optical pulses |
US4928692A (en) | 1985-04-01 | 1990-05-29 | Goodman David E | Method and apparatus for detecting optical pulses |
DE3516338A1 (en) | 1985-05-07 | 1986-11-13 | Drägerwerk AG, 2400 Lübeck | Mounting for a measurement sensor |
US4685464A (en) | 1985-07-05 | 1987-08-11 | Nellcor Incorporated | Durable sensor for detecting optical pulses |
US4890619A (en) | 1986-04-15 | 1990-01-02 | Hatschek Rudolf A | System for the measurement of the content of a gas in blood, in particular the oxygen saturation of blood |
JPS6323645A (en) | 1986-05-27 | 1988-01-30 | 住友電気工業株式会社 | Reflection heating type oxymeter |
US4759369A (en) | 1986-07-07 | 1988-07-26 | Novametrix Medical Systems, Inc. | Pulse oximeter |
US4859056A (en) | 1986-08-18 | 1989-08-22 | Physio-Control Corporation | Multiple-pulse method and apparatus for use in oximetry |
US4913150A (en) | 1986-08-18 | 1990-04-03 | Physio-Control Corporation | Method and apparatus for the automatic calibration of signals employed in oximetry |
US4819646A (en) | 1986-08-18 | 1989-04-11 | Physio-Control Corporation | Feedback-controlled method and apparatus for processing signals used in oximetry |
US4869253A (en) | 1986-08-18 | 1989-09-26 | Physio-Control Corporation | Method and apparatus for indicating perfusion and oxygen saturation trends in oximetry |
US5259381A (en) | 1986-08-18 | 1993-11-09 | Physio-Control Corporation | Apparatus for the automatic calibration of signals employed in oximetry |
US4892101A (en) | 1986-08-18 | 1990-01-09 | Physio-Control Corporation | Method and apparatus for offsetting baseline portion of oximeter signal |
US4800495A (en) | 1986-08-18 | 1989-01-24 | Physio-Control Corporation | Method and apparatus for processing signals used in oximetry |
JPS6365845A (en) | 1986-09-05 | 1988-03-24 | ミノルタ株式会社 | Oximeter apparatus |
US4726382A (en) | 1986-09-17 | 1988-02-23 | The Boc Group, Inc. | Inflatable finger cuff |
US4824242A (en) | 1986-09-26 | 1989-04-25 | Sensormedics Corporation | Non-invasive oximeter and method |
US4714080A (en) | 1986-10-06 | 1987-12-22 | Nippon Colin Co., Ltd. | Method and apparatus for noninvasive monitoring of arterial blood oxygen saturation |
US4865038A (en) | 1986-10-09 | 1989-09-12 | Novametrix Medical Systems, Inc. | Sensor appliance for non-invasive monitoring |
JPS63111837A (en) | 1986-10-29 | 1988-05-17 | 日本光電工業株式会社 | Apparatus for measuring concentration of light absorbing substance in blood |
DE3639402A1 (en) | 1986-11-18 | 1988-05-19 | Siemens Ag | METHOD FOR THE PRODUCTION OF A MULTI-LAYERED CIRCUIT BOARD AND THE CIRCUIT BOARD PRODUCED THEREOF |
US5193543A (en) | 1986-12-12 | 1993-03-16 | Critikon, Inc. | Method and apparatus for measuring arterial blood constituents |
DE3703458A1 (en) | 1987-02-05 | 1988-08-18 | Hewlett Packard Gmbh | Medical oxygen saturation sensor using electromagnetic waves - has support segment for transmitter and receiver elements and clamping segment for fitting round patent |
US4776339A (en) | 1987-03-05 | 1988-10-11 | N.A.D., Inc. | Interlock for oxygen saturation monitor anesthesia apparatus |
US4880304A (en) | 1987-04-01 | 1989-11-14 | Nippon Colin Co., Ltd. | Optical sensor for pulse oximeter |
JPS63252239A (en) | 1987-04-09 | 1988-10-19 | Sumitomo Electric Ind Ltd | Reflection type oxymeter |
US4773422A (en) | 1987-04-30 | 1988-09-27 | Nonin Medical, Inc. | Single channel pulse oximeter |
USRE33643E (en) | 1987-04-30 | 1991-07-23 | Nonin Medical, Inc. | Pulse oximeter with circuit leakage and ambient light compensation |
JPS63277039A (en) | 1987-05-08 | 1988-11-15 | Hamamatsu Photonics Kk | Diagnostic apparatus |
JPS63275323A (en) | 1987-05-08 | 1988-11-14 | Hamamatsu Photonics Kk | Diagnostic apparatus |
US4722120A (en) | 1987-06-23 | 1988-02-02 | James Lu | Spring clip |
GB8719333D0 (en) | 1987-08-14 | 1987-09-23 | Swansea University College Of | Motion artefact rejection system |
US4805623A (en) | 1987-09-04 | 1989-02-21 | Vander Corporation | Spectrophotometric method for quantitatively determining the concentration of a dilute component in a light- or other radiation-scattering environment |
US4796636A (en) | 1987-09-10 | 1989-01-10 | Nippon Colin Co., Ltd. | Noninvasive reflectance oximeter |
US4819752A (en) | 1987-10-02 | 1989-04-11 | Datascope Corp. | Blood constituent measuring device and method |
US4848901A (en) | 1987-10-08 | 1989-07-18 | Critikon, Inc. | Pulse oximeter sensor control system |
US4825879A (en) | 1987-10-08 | 1989-05-02 | Critkon, Inc. | Pulse oximeter sensor |
US4807631A (en) | 1987-10-09 | 1989-02-28 | Critikon, Inc. | Pulse oximetry system |
US4807630A (en) | 1987-10-09 | 1989-02-28 | Advanced Medical Systems, Inc. | Apparatus and method for use in pulse oximeters |
US4859057A (en) | 1987-10-13 | 1989-08-22 | Lawrence Medical Systems, Inc. | Oximeter apparatus |
US4863265A (en) | 1987-10-16 | 1989-09-05 | Mine Safety Appliances Company | Apparatus and method for measuring blood constituents |
US4854699A (en) | 1987-11-02 | 1989-08-08 | Nippon Colin Co., Ltd. | Backscatter oximeter |
EP0315040B1 (en) | 1987-11-02 | 1993-01-27 | Sumitomo Electric Industries Limited | Bio-photosensor |
US4781195A (en) | 1987-12-02 | 1988-11-01 | The Boc Group, Inc. | Blood monitoring apparatus and methods with amplifier input dark current correction |
US4846183A (en) | 1987-12-02 | 1989-07-11 | The Boc Group, Inc. | Blood parameter monitoring apparatus and methods |
US4800885A (en) | 1987-12-02 | 1989-01-31 | The Boc Group, Inc. | Blood constituent monitoring apparatus and methods with frequency division multiplexing |
US4927264A (en) | 1987-12-02 | 1990-05-22 | Omron Tateisi Electronics Co. | Non-invasive measuring method and apparatus of blood constituents |
US4960126A (en) | 1988-01-15 | 1990-10-02 | Criticare Systems, Inc. | ECG synchronized pulse oximeter |
US4883353A (en) | 1988-02-11 | 1989-11-28 | Puritan-Bennett Corporation | Pulse oximeter |
US4883055A (en) | 1988-03-11 | 1989-11-28 | Puritan-Bennett Corporation | Artificially induced blood pulse for use with a pulse oximeter |
DE3809084C2 (en) | 1988-03-18 | 1999-01-28 | Nicolay Gmbh | Sensor for the non-invasive measurement of the pulse frequency and / or the oxygen saturation of the blood and method for its production |
DE3810411A1 (en) | 1988-03-26 | 1989-10-12 | Nicolay Gmbh | DEVICE FOR FIXING A SENSOR, IN PARTICULAR A SENSOR FOR OXIMETRIC MEASUREMENTS |
US5078136A (en) | 1988-03-30 | 1992-01-07 | Nellcor Incorporated | Method and apparatus for calculating arterial oxygen saturation based plethysmographs including transients |
US4869254A (en) | 1988-03-30 | 1989-09-26 | Nellcor Incorporated | Method and apparatus for calculating arterial oxygen saturation |
US4964408A (en) | 1988-04-29 | 1990-10-23 | Thor Technology Corporation | Oximeter sensor assembly with integral cable |
US5041187A (en) | 1988-04-29 | 1991-08-20 | Thor Technology Corporation | Oximeter sensor assembly with integral cable and method of forming the same |
US5069213A (en) | 1988-04-29 | 1991-12-03 | Thor Technology Corporation | Oximeter sensor assembly with integral cable and encoder |
JPH06169902A (en) | 1988-05-05 | 1994-06-21 | Sentinel Monitoring Inc | Pulse type non-invasion type oxymeter and technology for measuring it |
EP0341327B1 (en) | 1988-05-09 | 1993-09-15 | Hewlett-Packard GmbH | A method for processing signals, particularly for oximetric measurements on living human tissue |
US5361758A (en) | 1988-06-09 | 1994-11-08 | Cme Telemetrix Inc. | Method and device for measuring concentration levels of blood constituents non-invasively |
US4948248A (en) | 1988-07-22 | 1990-08-14 | Invivo Research Inc. | Blood constituent measuring device and method |
US4825872A (en) | 1988-08-05 | 1989-05-02 | Critikon, Inc. | Finger sensor for pulse oximetry system |
JPH0288041A (en) | 1988-09-24 | 1990-03-28 | Misawahoomu Sogo Kenkyusho:Kk | Finger tip pulse wave sensor |
US5099842A (en) | 1988-10-28 | 1992-03-31 | Nellcor Incorporated | Perinatal pulse oximetry probe |
US5873821A (en) | 1992-05-18 | 1999-02-23 | Non-Invasive Technology, Inc. | Lateralization spectrophotometer |
US5564417A (en) | 1991-01-24 | 1996-10-15 | Non-Invasive Technology, Inc. | Pathlength corrected oximeter and the like |
USH1039H (en) | 1988-11-14 | 1992-04-07 | The United States Of America As Represented By The Secretary Of The Air Force | Intrusion-free physiological condition monitoring |
EP0374668A3 (en) | 1988-12-16 | 1992-02-05 | A.W. Faber - Castell GmbH & Co. | Fluorescent marking fluid |
JPH02164341A (en) | 1988-12-19 | 1990-06-25 | Nippon Koden Corp | Hemoglobin concentration measuring device |
US5353799A (en) | 1991-01-22 | 1994-10-11 | Non Invasive Technology, Inc. | Examination of subjects using photon migration with high directionality techniques |
US5119815A (en) | 1988-12-21 | 1992-06-09 | Nim, Incorporated | Apparatus for determining the concentration of a tissue pigment of known absorbance, in vivo, using the decay characteristics of scintered electromagnetic radiation |
US5553614A (en) | 1988-12-21 | 1996-09-10 | Non-Invasive Technology, Inc. | Examination of biological tissue using frequency domain spectroscopy |
US5111817A (en) | 1988-12-29 | 1992-05-12 | Medical Physics, Inc. | Noninvasive system and method for enhanced arterial oxygen saturation determination and arterial blood pressure monitoring |
US5028787A (en) | 1989-01-19 | 1991-07-02 | Futrex, Inc. | Non-invasive measurement of blood glucose |
US5365066A (en) | 1989-01-19 | 1994-11-15 | Futrex, Inc. | Low cost means for increasing measurement sensitivity in LED/IRED near-infrared instruments |
US5086229A (en) | 1989-01-19 | 1992-02-04 | Futrex, Inc. | Non-invasive measurement of blood glucose |
US5218207A (en) | 1989-01-19 | 1993-06-08 | Futrex, Inc. | Using led harmonic wavelengths for near-infrared quantitative |
FI82366C (en) | 1989-02-06 | 1991-03-11 | Instrumentarium Oy | MAETNING AV BLODETS SAMMANSAETTNING. |
US5596986A (en) | 1989-03-17 | 1997-01-28 | Scico, Inc. | Blood oximeter |
US5902235A (en) | 1989-03-29 | 1999-05-11 | Somanetics Corporation | Optical cerebral oximeter |
USD326715S (en) | 1989-04-18 | 1992-06-02 | Hewlett-Packard Company | Medical sensors for measuring oxygen saturation or the like |
DE3912993C2 (en) | 1989-04-20 | 1998-01-29 | Nicolay Gmbh | Optoelectronic sensor for generating electrical signals based on physiological values |
US5040539A (en) | 1989-05-12 | 1991-08-20 | The United States Of America | Pulse oximeter for diagnosis of dental pulp pathology |
JP2766317B2 (en) | 1989-06-22 | 1998-06-18 | コーリン電子株式会社 | Pulse oximeter |
JPH0315502U (en) | 1989-06-28 | 1991-02-15 | ||
US5090410A (en) | 1989-06-28 | 1992-02-25 | Datascope Investment Corp. | Fastener for attaching sensor to the body |
US5299120A (en) | 1989-09-15 | 1994-03-29 | Hewlett-Packard Company | Method for digitally processing signals containing information regarding arterial blood flow |
US5058588A (en) | 1989-09-19 | 1991-10-22 | Hewlett-Packard Company | Oximeter and medical sensor therefor |
US5483646A (en) | 1989-09-29 | 1996-01-09 | Kabushiki Kaisha Toshiba | Memory access control method and system for realizing the same |
US5007423A (en) | 1989-10-04 | 1991-04-16 | Nippon Colin Company Ltd. | Oximeter sensor temperature control |
US5216598A (en) | 1989-10-04 | 1993-06-01 | Colin Electronics Co., Ltd. | System for correction of trends associated with pulse wave forms in oximeters |
US5203329A (en) | 1989-10-05 | 1993-04-20 | Colin Electronics Co., Ltd. | Noninvasive reflectance oximeter sensor providing controlled minimum optical detection depth |
US5094239A (en) | 1989-10-05 | 1992-03-10 | Colin Electronics Co., Ltd. | Composite signal implementation for acquiring oximetry signals |
US5190038A (en) | 1989-11-01 | 1993-03-02 | Novametrix Medical Systems, Inc. | Pulse oximeter with improved accuracy and response time |
DE3938759A1 (en) | 1989-11-23 | 1991-05-29 | Philips Patentverwaltung | NON-INVASIVE OXIMETER ARRANGEMENT |
US5224478A (en) | 1989-11-25 | 1993-07-06 | Colin Electronics Co., Ltd. | Reflecting-type oxymeter probe |
KR100213554B1 (en) | 1989-11-28 | 1999-08-02 | 제이슨 오토 가도시 | Fetal probe |
US5080098A (en) | 1989-12-18 | 1992-01-14 | Sentinel Monitoring, Inc. | Non-invasive sensor |
DK0613653T3 (en) | 1990-02-15 | 1996-12-02 | Hewlett Packard Gmbh | Method for calculating oxygen saturation |
US5152296A (en) | 1990-03-01 | 1992-10-06 | Hewlett-Packard Company | Dual-finger vital signs monitor |
US5104623A (en) | 1990-04-03 | 1992-04-14 | Minnesota Mining And Manufacturing Company | Apparatus and assembly for use in optically sensing a compositional blood parameter |
US5066859A (en) | 1990-05-18 | 1991-11-19 | Karkar Maurice N | Hematocrit and oxygen saturation blood analyzer |
GB9011887D0 (en) | 1990-05-26 | 1990-07-18 | Le Fit Ltd | Pulse responsive device |
WO1991018549A1 (en) | 1990-05-29 | 1991-12-12 | Yue Samuel K | Fetal probe apparatus |
US5239185A (en) | 1990-06-22 | 1993-08-24 | Hitachi, Ltd. | Method and equipment for measuring absorptance of light scattering materials using plural wavelengths of light |
IE77034B1 (en) | 1990-06-27 | 1997-11-19 | Futrex Inc | Non-invasive masurement of blood glucose |
US5259761A (en) | 1990-08-06 | 1993-11-09 | Jenifer M. Schnettler | Tooth vitality probe and process |
ATE175558T1 (en) | 1990-08-22 | 1999-01-15 | Nellcor Puritan Bennett Inc | FETAL PULSE OXYGEN METER |
US5158082A (en) | 1990-08-23 | 1992-10-27 | Spacelabs, Inc. | Apparatus for heating tissue with a photoplethysmograph sensor |
WO1992003965A1 (en) | 1990-08-29 | 1992-03-19 | Cadell Theodore E | Finger receptor |
US5170786A (en) | 1990-09-28 | 1992-12-15 | Novametrix Medical Systems, Inc. | Reusable probe system |
US5055671A (en) | 1990-10-03 | 1991-10-08 | Spacelabs, Inc. | Apparatus for detecting transducer movement using a first and second light detector |
US6681128B2 (en) | 1990-10-06 | 2004-01-20 | Hema Metrics, Inc. | System for noninvasive hematocrit monitoring |
US5372136A (en) | 1990-10-06 | 1994-12-13 | Noninvasive Medical Technology Corporation | System and method for noninvasive hematocrit monitoring |
US6266546B1 (en) | 1990-10-06 | 2001-07-24 | In-Line Diagnostics Corporation | System for noninvasive hematocrit monitoring |
US5209230A (en) | 1990-10-19 | 1993-05-11 | Nellcor Incorporated | Adhesive pulse oximeter sensor with reusable portion |
US6263221B1 (en) | 1991-01-24 | 2001-07-17 | Non-Invasive Technology | Quantitative analyses of biological tissue using phase modulation spectroscopy |
US5193542A (en) | 1991-01-28 | 1993-03-16 | Missanelli John S | Peripartum oximetric monitoring apparatus |
US5291884A (en) | 1991-02-07 | 1994-03-08 | Minnesota Mining And Manufacturing Company | Apparatus for measuring a blood parameter |
JPH0614922B2 (en) | 1991-02-15 | 1994-03-02 | 日本光電工業株式会社 | Calibration test equipment for pulse oximeter |
US5125403A (en) | 1991-02-20 | 1992-06-30 | Culp Joel B | Device and method for engagement of an oximeter probe |
US5154175A (en) | 1991-03-04 | 1992-10-13 | Gunther Ted J | Intrauterine fetal EKG-oximetry cable apparatus |
US5343818A (en) | 1991-03-05 | 1994-09-06 | Sensormedics Corp. | Photoplethysmographics using energy-reducing waveform shaping |
US5349952A (en) | 1991-03-05 | 1994-09-27 | Sensormedics Corp. | Photoplethysmographics using phase-division multiplexing |
US5349953A (en) | 1991-03-05 | 1994-09-27 | Sensormedics, Corp. | Photoplethysmographics using component-amplitude-division multiplexing |
US5490505A (en) | 1991-03-07 | 1996-02-13 | Masimo Corporation | Signal processing apparatus |
US5632272A (en) | 1991-03-07 | 1997-05-27 | Masimo Corporation | Signal processing apparatus |
US5267566A (en) | 1991-03-07 | 1993-12-07 | Maged Choucair | Apparatus and method for blood pressure monitoring |
EP0930045A3 (en) | 1991-03-07 | 1999-10-27 | Masimo Corporation | Signal processing apparatus and method for an oximeter |
MX9702434A (en) | 1991-03-07 | 1998-05-31 | Masimo Corp | Signal processing apparatus. |
US5237994A (en) | 1991-03-12 | 1993-08-24 | Square One Technology | Integrated lead frame pulse oximetry sensor |
US6541756B2 (en) | 1991-03-21 | 2003-04-01 | Masimo Corporation | Shielded optical probe having an electrical connector |
US5638818A (en) | 1991-03-21 | 1997-06-17 | Masimo Corporation | Low noise optical probe |
US5995855A (en) | 1998-02-11 | 1999-11-30 | Masimo Corporation | Pulse oximetry sensor adapter |
US5645440A (en) | 1995-10-16 | 1997-07-08 | Masimo Corporation | Patient cable connector |
US6580086B1 (en) | 1999-08-26 | 2003-06-17 | Masimo Corporation | Shielded optical probe and method |
DE4138702A1 (en) | 1991-03-22 | 1992-09-24 | Madaus Medizin Elektronik | METHOD AND DEVICE FOR THE DIAGNOSIS AND QUANTITATIVE ANALYSIS OF APNOE AND FOR THE SIMULTANEOUS DETERMINATION OF OTHER DISEASES |
US5273036A (en) | 1991-04-03 | 1993-12-28 | Ppg Industries, Inc. | Apparatus and method for monitoring respiration |
US5218962A (en) | 1991-04-15 | 1993-06-15 | Nellcor Incorporated | Multiple region pulse oximetry probe and oximeter |
US5247932A (en) | 1991-04-15 | 1993-09-28 | Nellcor Incorporated | Sensor for intrauterine use |
US5313940A (en) | 1991-05-15 | 1994-05-24 | Nihon Kohden Corporation | Photo-electric pulse wave measuring probe |
DE69214391T2 (en) | 1991-06-19 | 1997-05-15 | Endotronics Inc | Cell culture apparatus |
US5402777A (en) | 1991-06-28 | 1995-04-04 | Alza Corporation | Methods and devices for facilitated non-invasive oxygen monitoring |
US5267563A (en) | 1991-06-28 | 1993-12-07 | Nellcor Incorporated | Oximeter sensor with perfusion enhancing |
EP0522674B1 (en) | 1991-07-12 | 1998-11-11 | Mark R. Robinson | Oximeter for reliable clinical determination of blood oxygen saturation in a fetus |
US5413100A (en) | 1991-07-17 | 1995-05-09 | Effets Biologiques Exercice | Non-invasive method for the in vivo determination of the oxygen saturation rate of arterial blood, and device for carrying out the method |
US5351685A (en) | 1991-08-05 | 1994-10-04 | Nellcor Incorporated | Condensed oximeter system with noise reduction software |
EP0527703B1 (en) | 1991-08-12 | 1995-06-28 | AVL Medical Instruments AG | Device for measuring at least one gaseous concentration level in particular the oxygen concentration level in blood |
US5368025A (en) | 1991-08-22 | 1994-11-29 | Sensor Devices, Inc. | Non-invasive oximeter probe |
US5429129A (en) | 1991-08-22 | 1995-07-04 | Sensor Devices, Inc. | Apparatus for determining spectral absorption by a specific substance in a fluid |
US5217012A (en) | 1991-08-22 | 1993-06-08 | Sensor Devices Inc. | Noninvasive oximeter probe |
JP3124073B2 (en) | 1991-08-27 | 2001-01-15 | 日本コーリン株式会社 | Blood oxygen saturation monitor |
US5246003A (en) | 1991-08-28 | 1993-09-21 | Nellcor Incorporated | Disposable pulse oximeter sensor |
US5934277A (en) | 1991-09-03 | 1999-08-10 | Datex-Ohmeda, Inc. | System for pulse oximetry SpO2 determination |
US6714803B1 (en) | 1991-09-03 | 2004-03-30 | Datex-Ohmeda, Inc. | Pulse oximetry SpO2 determination |
US5247931A (en) | 1991-09-16 | 1993-09-28 | Mine Safety Appliances Company | Diagnostic sensor clasp utilizing a slot, pivot and spring hinge mechanism |
US5213099A (en) | 1991-09-30 | 1993-05-25 | The United States Of America As Represented By The Secretary Of The Air Force | Ear canal pulse/oxygen saturation measuring device |
JP3115374B2 (en) | 1991-10-11 | 2000-12-04 | テルモ株式会社 | Patient monitoring system |
US5249576A (en) | 1991-10-24 | 1993-10-05 | Boc Health Care, Inc. | Universal pulse oximeter probe |
US5311865A (en) | 1991-11-07 | 1994-05-17 | Mayeux Charles D | Plastic finger oximetry probe holder |
US5253645A (en) | 1991-12-13 | 1993-10-19 | Critikon, Inc. | Method of producing an audible alarm in a blood pressure and pulse oximeter monitor |
JPH0569784U (en) | 1991-12-28 | 1993-09-21 | センチュリーメディカル株式会社 | Display device in medical equipment |
DE69117964T2 (en) | 1991-12-30 | 1996-07-25 | Hamamatsu Photonics Kk | Diagnostic device |
FR2685865B1 (en) | 1992-01-08 | 1998-04-10 | Distr App Medicaux Off | OPTICAL SENSOR, PARTICULARLY FOR MEASURING THE OXYGEN SATURATION RATE IN ARTERIAL BLOOD. |
DE69215204T2 (en) | 1992-01-29 | 1997-03-13 | Hewlett Packard Gmbh | Process and system for monitoring vital functions |
US5385143A (en) | 1992-02-06 | 1995-01-31 | Nihon Kohden Corporation | Apparatus for measuring predetermined data of living tissue |
US5297548A (en) | 1992-02-07 | 1994-03-29 | Ohmeda Inc. | Arterial blood monitoring probe |
US5246002A (en) | 1992-02-11 | 1993-09-21 | Physio-Control Corporation | Noise insensitive pulse transmittance oximeter |
DE4210102C2 (en) | 1992-03-27 | 1999-02-25 | Rall Gerhard | Device for optically determining parameters of perfused tissue |
US5263244A (en) | 1992-04-17 | 1993-11-23 | Gould Inc. | Method of making a flexible printed circuit sensor assembly for detecting optical pulses |
JP3170866B2 (en) | 1992-04-24 | 2001-05-28 | 株式会社ノーリツ | 1 can 2 circuit type instant heating type heat exchanger |
DE69211986T2 (en) | 1992-05-15 | 1996-10-31 | Hewlett Packard Gmbh | Medical sensor |
JP3091929B2 (en) | 1992-05-28 | 2000-09-25 | 日本光電工業株式会社 | Pulse oximeter |
JP3165983B2 (en) | 1992-06-15 | 2001-05-14 | 日本光電工業株式会社 | Light emitting element driving device for pulse oximeter |
US5377675A (en) | 1992-06-24 | 1995-01-03 | Nellcor, Inc. | Method and apparatus for improved fetus contact with fetal probe |
US5355880A (en) | 1992-07-06 | 1994-10-18 | Sandia Corporation | Reliable noninvasive measurement of blood gases |
JP3116252B2 (en) | 1992-07-09 | 2000-12-11 | 日本光電工業株式会社 | Pulse oximeter |
US6222189B1 (en) | 1992-07-15 | 2001-04-24 | Optix, Lp | Methods of enhancing optical signals by mechanical manipulation in non-invasive testing |
US6411832B1 (en) | 1992-07-15 | 2002-06-25 | Optix Lp | Method of improving reproducibility of non-invasive measurements |
US5425360A (en) | 1992-07-24 | 1995-06-20 | Sensormedics Corporation | Molded pulse oximeter sensor |
US6223064B1 (en) | 1992-08-19 | 2001-04-24 | Lawrence A. Lynn | Microprocessor system for the simplified diagnosis of sleep apnea |
US6609016B1 (en) | 1997-07-14 | 2003-08-19 | Lawrence A. Lynn | Medical microprocessor system and method for providing a ventilation indexed oximetry value |
US6342039B1 (en) | 1992-08-19 | 2002-01-29 | Lawrence A. Lynn | Microprocessor system for the simplified diagnosis of sleep apnea |
US20050062609A9 (en) | 1992-08-19 | 2005-03-24 | Lynn Lawrence A. | Pulse oximetry relational alarm system for early recognition of instability and catastrophic occurrences |
US5680857A (en) | 1992-08-28 | 1997-10-28 | Spacelabs Medical, Inc. | Alignment guide system for transmissive pulse oximetry sensors |
US5348003A (en) | 1992-09-03 | 1994-09-20 | Sirraya, Inc. | Method and apparatus for chemical analysis |
JP2547840Y2 (en) | 1992-09-25 | 1997-09-17 | 日本光電工業株式会社 | Oximeter probe |
US5323776A (en) | 1992-10-15 | 1994-06-28 | Picker International, Inc. | MRI compatible pulse oximetry system |
US5329922A (en) | 1992-10-19 | 1994-07-19 | Atlee Iii John L | Oximetric esophageal probe |
US5368224A (en) | 1992-10-23 | 1994-11-29 | Nellcor Incorporated | Method for reducing ambient noise effects in electronic monitoring instruments |
EP0690692A4 (en) | 1992-12-01 | 1999-02-10 | Somanetics Corp | Patient sensor for optical cerebral oximeters |
US5287853A (en) | 1992-12-11 | 1994-02-22 | Hewlett-Packard Company | Adapter cable for connecting a pulsoximetry sensor unit to a medical measuring device |
US5551423A (en) | 1993-01-26 | 1996-09-03 | Nihon Kohden Corporation | Pulse oximeter probe |
DE4304693C2 (en) | 1993-02-16 | 2002-02-21 | Gerhard Rall | Sensor device for measuring vital parameters of a fetus during childbirth |
JP2586392Y2 (en) | 1993-03-15 | 1998-12-02 | 日本光電工業株式会社 | Probe for pulse oximeter |
US5687719A (en) | 1993-03-25 | 1997-11-18 | Ikuo Sato | Pulse oximeter probe |
US5520177A (en) | 1993-03-26 | 1996-05-28 | Nihon Kohden Corporation | Oximeter probe |
US5368026A (en) | 1993-03-26 | 1994-11-29 | Nellcor Incorporated | Oximeter with motion detection for alarm modification |
US5348004A (en) | 1993-03-31 | 1994-09-20 | Nellcor Incorporated | Electronic processor for pulse oximeter |
US5676141A (en) | 1993-03-31 | 1997-10-14 | Nellcor Puritan Bennett Incorporated | Electronic processor for pulse oximeters |
US5497771A (en) | 1993-04-02 | 1996-03-12 | Mipm Mammendorfer Institut Fuer Physik Und Medizin Gmbh | Apparatus for measuring the oxygen saturation of fetuses during childbirth |
US5521851A (en) | 1993-04-26 | 1996-05-28 | Nihon Kohden Corporation | Noise reduction method and apparatus |
US5339810A (en) | 1993-05-03 | 1994-08-23 | Marquette Electronics, Inc. | Pulse oximetry sensor |
US5494043A (en) | 1993-05-04 | 1996-02-27 | Vital Insite, Inc. | Arterial sensor |
US5348005A (en) | 1993-05-07 | 1994-09-20 | Bio-Tek Instruments, Inc. | Simulation for pulse oximeter |
EP0699047A4 (en) | 1993-05-20 | 1998-06-24 | Somanetics Corp | Improved electro-optical sensor for spectrophotometric medical devices |
AU6942494A (en) | 1993-05-21 | 1994-12-20 | Nims, Inc. | Discriminating between valid and artifactual pulse waveforms |
AU7080594A (en) | 1993-05-28 | 1994-12-20 | Somanetics Corporation | Method and apparatus for spectrophotometric cerebral oximetry |
JP3310390B2 (en) | 1993-06-10 | 2002-08-05 | 浜松ホトニクス株式会社 | Method and apparatus for measuring concentration of light absorbing substance in scattering medium |
US5452717A (en) | 1993-07-14 | 1995-09-26 | Masimo Corporation | Finger-cot probe |
US5337744A (en) | 1993-07-14 | 1994-08-16 | Masimo Corporation | Low noise finger cot probe |
US5425362A (en) | 1993-07-30 | 1995-06-20 | Criticare | Fetal sensor device |
DE4329898A1 (en) | 1993-09-04 | 1995-04-06 | Marcus Dr Besson | Wireless medical diagnostic and monitoring device |
EP0641543A1 (en) | 1993-09-07 | 1995-03-08 | Ohmeda Inc. | Heat-sealed neo-natal medical monitoring probe |
US5511546A (en) | 1993-09-20 | 1996-04-30 | Hon; Edward H. | Finger apparatus for measuring continuous cutaneous blood pressure and electrocardiogram electrode |
JP3345481B2 (en) | 1993-09-22 | 2002-11-18 | 興和株式会社 | Pulse wave spectrometer |
JP3387171B2 (en) | 1993-09-28 | 2003-03-17 | セイコーエプソン株式会社 | Pulse wave detection device and exercise intensity measurement device |
US5485847A (en) | 1993-10-08 | 1996-01-23 | Nellcor Puritan Bennett Incorporated | Pulse oximeter using a virtual trigger for heart rate synchronization |
US5411023A (en) | 1993-11-24 | 1995-05-02 | The Shielding Corporation | Optical sensor system |
US5417207A (en) | 1993-12-06 | 1995-05-23 | Sensor Devices, Inc. | Apparatus for the invasive use of oximeter probes |
JP2605584Y2 (en) | 1993-12-07 | 2000-07-24 | 日本光電工業株式会社 | Multi sensor |
JP3125079B2 (en) | 1993-12-07 | 2001-01-15 | 日本光電工業株式会社 | Pulse oximeter |
JP3116259B2 (en) | 1993-12-07 | 2000-12-11 | 日本光電工業株式会社 | Probe for pulse oximeter |
EP0658331B1 (en) | 1993-12-11 | 1996-10-02 | Hewlett-Packard GmbH | A method for detecting an irregular state in a non-invasive pulse oximeter system |
US5438986A (en) | 1993-12-14 | 1995-08-08 | Criticare Systems, Inc. | Optical sensor |
US5730124A (en) | 1993-12-14 | 1998-03-24 | Mochida Pharmaceutical Co., Ltd. | Medical measurement apparatus |
US5411024A (en) | 1993-12-15 | 1995-05-02 | Corometrics Medical Systems, Inc. | Fetal pulse oximetry sensor |
US5492118A (en) | 1993-12-16 | 1996-02-20 | Board Of Trustees Of The University Of Illinois | Determining material concentrations in tissues |
US5560355A (en) | 1993-12-17 | 1996-10-01 | Nellcor Puritan Bennett Incorporated | Medical sensor with amplitude independent output |
US5645059A (en) | 1993-12-17 | 1997-07-08 | Nellcor Incorporated | Medical sensor with modulated encoding scheme |
JP3238813B2 (en) | 1993-12-20 | 2001-12-17 | テルモ株式会社 | Pulse oximeter |
JP3464697B2 (en) | 1993-12-21 | 2003-11-10 | 興和株式会社 | Oxygen saturation meter |
US5507286A (en) | 1993-12-23 | 1996-04-16 | Medical Taping Systems, Inc. | Method and apparatus for improving the durability of a sensor |
US5553615A (en) | 1994-01-31 | 1996-09-10 | Minnesota Mining And Manufacturing Company | Method and apparatus for noninvasive prediction of hematocrit |
US5437275A (en) | 1994-02-02 | 1995-08-01 | Biochem International Inc. | Pulse oximetry sensor |
US5632273A (en) | 1994-02-04 | 1997-05-27 | Hamamatsu Photonics K.K. | Method and means for measurement of biochemical components |
US5995859A (en) | 1994-02-14 | 1999-11-30 | Nihon Kohden Corporation | Method and apparatus for accurately measuring the saturated oxygen in arterial blood by substantially eliminating noise from the measurement signal |
US5830135A (en) | 1994-03-31 | 1998-11-03 | Bosque; Elena M. | Fuzzy logic alarm system for pulse oximeters |
US5421329A (en) | 1994-04-01 | 1995-06-06 | Nellcor, Inc. | Pulse oximeter sensor optimized for low saturation |
US5575284A (en) | 1994-04-01 | 1996-11-19 | University Of South Florida | Portable pulse oximeter |
US6662033B2 (en) | 1994-04-01 | 2003-12-09 | Nellcor Incorporated | Pulse oximeter and sensor optimized for low saturation |
JP3364819B2 (en) | 1994-04-28 | 2003-01-08 | 日本光電工業株式会社 | Blood absorption substance concentration measurement device |
US5402779A (en) | 1994-04-29 | 1995-04-04 | Chen; William X. | Method for the non-invasive detection of an intravascular injection of an anesthetic by the use of an indicator dye |
US5491299A (en) | 1994-06-03 | 1996-02-13 | Siemens Medical Systems, Inc. | Flexible multi-parameter cable |
US5490523A (en) | 1994-06-29 | 1996-02-13 | Nonin Medical Inc. | Finger clip pulse oximeter |
US5912656A (en) | 1994-07-01 | 1999-06-15 | Ohmeda Inc. | Device for producing a display from monitored data |
DE4423597C1 (en) | 1994-07-06 | 1995-08-10 | Hewlett Packard Gmbh | Pulsoximetric ear sensor |
US5664270A (en) | 1994-07-19 | 1997-09-09 | Kinetic Concepts, Inc. | Patient interface system |
DE4429758A1 (en) | 1994-08-22 | 1996-02-29 | Buschmann Johannes | Method for validating devices for photometry of living tissue and device for carrying out the method |
DE4429845C1 (en) | 1994-08-23 | 1995-10-19 | Hewlett Packard Gmbh | Pulse oximeter with flexible strap for attachment to hand or foot |
US5697367A (en) | 1994-10-14 | 1997-12-16 | Somanetics Corporation | Specially grounded sensor for clinical spectrophotometric procedures |
US5503148A (en) | 1994-11-01 | 1996-04-02 | Ohmeda Inc. | System for pulse oximetry SPO2 determination |
DE4442260C2 (en) | 1994-11-28 | 2000-06-08 | Mipm Mammendorfer Inst Fuer Ph | Method and arrangement for the non-invasive in vivo determination of oxygen saturation |
DE4442855B4 (en) | 1994-12-01 | 2004-04-01 | Gerhard Dipl.-Ing. Rall | Use of a pulse oximetry sensor device |
US5505199A (en) | 1994-12-01 | 1996-04-09 | Kim; Bill H. | Sudden infant death syndrome monitor |
US5676139A (en) | 1994-12-14 | 1997-10-14 | Ohmeda Inc. | Spring clip probe housing |
US5673692A (en) | 1995-02-03 | 1997-10-07 | Biosignals Ltd. Co. | Single site, multi-variable patient monitor |
US5692503A (en) | 1995-03-10 | 1997-12-02 | Kuenstner; J. Todd | Method for noninvasive (in-vivo) total hemoglobin, oxyhemogolobin, deoxyhemoglobin, carboxyhemoglobin and methemoglobin concentration determination |
US5524617A (en) | 1995-03-14 | 1996-06-11 | Nellcor, Incorporated | Isolated layer pulse oximetry |
US5619992A (en) | 1995-04-06 | 1997-04-15 | Guthrie; Robert B. | Methods and apparatus for inhibiting contamination of reusable pulse oximetry sensors |
US5617852A (en) | 1995-04-06 | 1997-04-08 | Macgregor; Alastair R. | Method and apparatus for non-invasively determining blood analytes |
US5774213A (en) | 1995-04-21 | 1998-06-30 | Trebino; Rick P. | Techniques for measuring difference of an optical property at two wavelengths by modulating two sources to have opposite-phase components at a common frequency |
JP3326580B2 (en) | 1995-05-08 | 2002-09-24 | 日本光電工業株式会社 | Biological tissue transmitted light sensor |
US5662105A (en) | 1995-05-17 | 1997-09-02 | Spacelabs Medical, Inc. | System and method for the extractment of physiological signals |
US7035697B1 (en) | 1995-05-30 | 2006-04-25 | Roy-G-Biv Corporation | Access control systems and methods for motion control |
US5851178A (en) | 1995-06-02 | 1998-12-22 | Ohmeda Inc. | Instrumented laser diode probe connector |
US5760910A (en) | 1995-06-07 | 1998-06-02 | Masimo Corporation | Optical filter for spectroscopic measurement and method of producing the optical filter |
US5758644A (en) | 1995-06-07 | 1998-06-02 | Masimo Corporation | Manual and automatic probe calibration |
US5743262A (en) | 1995-06-07 | 1998-04-28 | Masimo Corporation | Blood glucose monitoring system |
US5638816A (en) | 1995-06-07 | 1997-06-17 | Masimo Corporation | Active pulse blood constituent monitoring |
EP0957747B1 (en) | 1995-06-09 | 2004-02-25 | Cybro Medical Ltd. | Sensor, method and device for optical blood oximetry |
US5645060A (en) | 1995-06-14 | 1997-07-08 | Nellcor Puritan Bennett Incorporated | Method and apparatus for removing artifact and noise from pulse oximetry |
US5685301A (en) | 1995-06-16 | 1997-11-11 | Ohmeda Inc. | Apparatus for precise determination of operating characteristics of optical devices contained in a monitoring probe |
US5829439A (en) | 1995-06-28 | 1998-11-03 | Hitachi Medical Corporation | Needle-like ultrasonic probe for ultrasonic diagnosis apparatus, method of producing same, and ultrasonic diagnosis apparatus using same |
US6055447A (en) | 1995-07-06 | 2000-04-25 | Institute Of Critical Care Medicine | Patient CO2 Measurement |
US5558096A (en) | 1995-07-21 | 1996-09-24 | Biochem International, Inc. | Blood pulse detection method using autocorrelation |
EP0955865B1 (en) | 1995-07-21 | 2005-09-28 | Respironics, Inc. | Apparatus for diode laser pulse oximetry using multifiber optical cables and disposable fiber optic probes |
US6095974A (en) | 1995-07-21 | 2000-08-01 | Respironics, Inc. | Disposable fiber optic probe |
GB9515649D0 (en) | 1995-07-31 | 1995-09-27 | Johnson & Johnson Medical | Surface sensor device |
US5853364A (en) | 1995-08-07 | 1998-12-29 | Nellcor Puritan Bennett, Inc. | Method and apparatus for estimating physiological parameters using model-based adaptive filtering |
FI111214B (en) | 1995-08-17 | 2003-06-30 | Tunturipyoerae Oy | Giver |
US5800348A (en) | 1995-08-31 | 1998-09-01 | Hewlett-Packard Company | Apparatus and method for medical monitoring, in particular pulse oximeter |
GB9518094D0 (en) * | 1995-09-05 | 1995-11-08 | Cardionics Ltd | Heart monitoring apparatus |
US5629992A (en) | 1995-09-14 | 1997-05-13 | Bell Communications Research, Inc. | Passband flattening of integrated optical filters |
DE19537646C2 (en) | 1995-10-10 | 1998-09-17 | Hewlett Packard Gmbh | Method and device for detecting falsified measurement values in pulse oximetry for measuring oxygen saturation |
USD393830S (en) | 1995-10-16 | 1998-04-28 | Masimo Corporation | Patient cable connector |
CA2235772C (en) | 1995-10-23 | 2002-12-31 | Cytometrics, Inc. | Method and apparatus for reflected imaging analysis |
US5626140A (en) | 1995-11-01 | 1997-05-06 | Spacelabs Medical, Inc. | System and method of multi-sensor fusion of physiological measurements |
DE19541605C2 (en) | 1995-11-08 | 1999-06-24 | Hewlett Packard Co | Sensor and method for performing medical measurements, in particular pulse oximetric measurements, on the human finger |
US5839439A (en) | 1995-11-13 | 1998-11-24 | Nellcor Puritan Bennett Incorporated | Oximeter sensor with rigid inner housing and pliable overmold |
US5660567A (en) | 1995-11-14 | 1997-08-26 | Nellcor Puritan Bennett Incorporated | Medical sensor connector with removable encoding device |
US5588427A (en) | 1995-11-20 | 1996-12-31 | Spacelabs Medical, Inc. | Enhancement of physiological signals using fractal analysis |
US5724967A (en) | 1995-11-21 | 1998-03-10 | Nellcor Puritan Bennett Incorporated | Noise reduction apparatus for low level analog signals |
US5995856A (en) | 1995-11-22 | 1999-11-30 | Nellcor, Incorporated | Non-contact optical monitoring of physiological parameters |
US6041247A (en) | 1995-11-29 | 2000-03-21 | Instrumentarium Corp | Non-invasive optical measuring sensor and measuring method |
US5810724A (en) | 1995-12-01 | 1998-09-22 | Nellcor Puritan Bennett Incorporated | Reusable sensor accessory containing a conformable spring activated rubber sleeved clip |
US6226540B1 (en) | 1995-12-13 | 2001-05-01 | Peter Bernreuter | Measuring process for blood gas analysis sensors |
US5922607A (en) | 1995-12-13 | 1999-07-13 | Bernreuter; Peter | Measuring process for blood gas analysis sensors |
US20020014533A1 (en) | 1995-12-18 | 2002-02-07 | Xiaxun Zhu | Automated object dimensioning system employing contour tracing, vertice detection, and forner point detection and reduction methods on 2-d range data maps |
US5807247A (en) | 1995-12-20 | 1998-09-15 | Nellcor Puritan Bennett Incorporated | Method and apparatus for facilitating compatibility between pulse oximeters and sensor probes |
US5818985A (en) | 1995-12-20 | 1998-10-06 | Nellcor Puritan Bennett Incorporated | Optical oximeter probe adapter |
AUPN740796A0 (en) | 1996-01-04 | 1996-01-25 | Circuitry Systems Limited | Biomedical data collection apparatus |
US5891026A (en) | 1996-01-29 | 1999-04-06 | Ntc Technology Inc. | Extended life disposable pulse oximetry sensor and method of making |
SE9600322L (en) | 1996-01-30 | 1997-07-31 | Hoek Instr Ab | Sensor for pulse oximetry with fiber optic signal transmission |
US5746697A (en) | 1996-02-09 | 1998-05-05 | Nellcor Puritan Bennett Incorporated | Medical diagnostic apparatus with sleep mode |
US5797841A (en) | 1996-03-05 | 1998-08-25 | Nellcor Puritan Bennett Incorporated | Shunt barrier in pulse oximeter sensor |
US6253097B1 (en) | 1996-03-06 | 2001-06-26 | Datex-Ohmeda, Inc. | Noninvasive medical monitoring instrument using surface emitting laser devices |
JP3245042B2 (en) | 1996-03-11 | 2002-01-07 | 沖電気工業株式会社 | Tuning oscillation circuit |
DE59704665D1 (en) | 1996-04-01 | 2001-10-25 | Linde Medical Sensors Ag Basel | DETECTION OF INTERFERENCE SIGNALS IN PULSOXYMETRIC MEASUREMENT |
US5790729A (en) | 1996-04-10 | 1998-08-04 | Ohmeda Inc. | Photoplethysmographic instrument having an integrated multimode optical coupler device |
US5766127A (en) | 1996-04-15 | 1998-06-16 | Ohmeda Inc. | Method and apparatus for improved photoplethysmographic perfusion-index monitoring |
US5692505A (en) | 1996-04-25 | 1997-12-02 | Fouts; James Michael | Data processing systems and methods for pulse oximeters |
US5919133A (en) | 1996-04-26 | 1999-07-06 | Ohmeda Inc. | Conformal wrap for pulse oximeter sensor |
US5913819A (en) | 1996-04-26 | 1999-06-22 | Datex-Ohmeda, Inc. | Injection molded, heat-sealed housing and half-etched lead frame for oximeter sensor |
WO1997042903A1 (en) | 1996-05-15 | 1997-11-20 | Nellcor Puritan Bennett Incorporated | Semi-reusable sensor with disposable sleeve |
US5807248A (en) | 1996-05-15 | 1998-09-15 | Ohmeda Inc. | Medical monitoring probe with modular device housing |
US5752914A (en) | 1996-05-28 | 1998-05-19 | Nellcor Puritan Bennett Incorporated | Continuous mesh EMI shield for pulse oximetry sensor |
FI962448A (en) | 1996-06-12 | 1997-12-13 | Instrumentarium Oy | Method, apparatus and sensor for the determination of fractional oxygen saturation |
US5890929A (en) | 1996-06-19 | 1999-04-06 | Masimo Corporation | Shielded medical connector |
US6027452A (en) | 1996-06-26 | 2000-02-22 | Vital Insite, Inc. | Rapid non-invasive blood pressure measuring device |
US5879294A (en) | 1996-06-28 | 1999-03-09 | Hutchinson Technology Inc. | Tissue chromophore measurement system |
US5842981A (en) | 1996-07-17 | 1998-12-01 | Criticare Systems, Inc. | Direct to digital oximeter |
US6163715A (en) | 1996-07-17 | 2000-12-19 | Criticare Systems, Inc. | Direct to digital oximeter and method for calculating oxygenation levels |
ATE346539T1 (en) | 1996-07-19 | 2006-12-15 | Daedalus I Llc | DEVICE FOR THE BLOODLESS DETERMINATION OF BLOOD VALUES |
DE59707228D1 (en) | 1996-07-26 | 2002-06-13 | Linde Medical Sensors Ag Basel | METHOD FOR THE NON-INVASIVE DETERMINATION OF OXYGEN SATURATION IN BLOODED TISSUE |
US5916155A (en) | 1996-07-30 | 1999-06-29 | Nellcor Puritan Bennett Incorporated | Fetal sensor with securing balloons remote from optics |
US5842982A (en) | 1996-08-07 | 1998-12-01 | Nellcor Puritan Bennett Incorporated | Infant neonatal pulse oximeter sensor |
US5813980A (en) | 1996-08-13 | 1998-09-29 | Nellcor Puritan Bennett Incorporated | Fetal pulse oximetry sensor with remote securing mechanism |
US5776058A (en) | 1996-08-13 | 1998-07-07 | Nellcor Puritan Bennett Incorporated | Pressure-attached presenting part fetal pulse oximetry sensor |
US5823952A (en) | 1996-08-14 | 1998-10-20 | Nellcor Incorporated | Pulse oximeter sensor with differential slip coefficient |
JP3844815B2 (en) | 1996-08-30 | 2006-11-15 | 浜松ホトニクス株式会社 | Method and apparatus for measuring absorption information of scatterers |
US5727547A (en) | 1996-09-04 | 1998-03-17 | Nellcor Puritan Bennett Incorporated | Presenting part fetal oximeter sensor with securing mechanism for providing tension to scalp attachment |
US5871442A (en) | 1996-09-10 | 1999-02-16 | International Diagnostics Technologies, Inc. | Photonic molecular probe |
EP0875199B1 (en) | 1996-09-10 | 2004-03-10 | Seiko Epson Corporation | Organism state measuring device and relaxation state indicator device |
US5782756A (en) | 1996-09-19 | 1998-07-21 | Nellcor Puritan Bennett Incorporated | Method and apparatus for in vivo blood constituent analysis |
US5782758A (en) | 1996-09-23 | 1998-07-21 | Ohmeda Inc. | Method and apparatus for identifying the presence of noise in a time division multiplexed oximeter |
US5891022A (en) | 1996-09-25 | 1999-04-06 | Ohmeda Inc. | Apparatus for performing multiwavelength photoplethysmography |
DE19640807A1 (en) | 1996-10-02 | 1997-09-18 | Siemens Ag | Noninvasive optical detection of oxygen supply to e.g. brain or liver |
JPH10108846A (en) | 1996-10-03 | 1998-04-28 | Nippon Koden Corp | Holder for organic signal detector |
US5851179A (en) | 1996-10-10 | 1998-12-22 | Nellcor Puritan Bennett Incorporated | Pulse oximeter sensor with articulating head |
US6018673A (en) | 1996-10-10 | 2000-01-25 | Nellcor Puritan Bennett Incorporated | Motion compatible sensor for non-invasive optical blood analysis |
US5800349A (en) | 1996-10-15 | 1998-09-01 | Nonin Medical, Inc. | Offset pulse oximeter sensor |
US5964701A (en) | 1996-10-24 | 1999-10-12 | Massachusetts Institute Of Technology | Patient monitoring finger ring sensor |
US5817008A (en) | 1996-10-31 | 1998-10-06 | Spacelabs Medical, Inc. | Conformal pulse oximetry sensor and monitor |
US5830136A (en) | 1996-10-31 | 1998-11-03 | Nellcor Puritan Bennett Incorporated | Gel pad optical sensor |
US5830137A (en) | 1996-11-18 | 1998-11-03 | University Of South Florida | Green light pulse oximeter |
DE19647877C2 (en) | 1996-11-19 | 2000-06-15 | Univ Ilmenau Tech | Method and circuit arrangement for determining the oxygen saturation in the blood |
US5810723A (en) | 1996-12-05 | 1998-09-22 | Essential Medical Devices | Non-invasive carboxyhemoglobin analyer |
US6397093B1 (en) | 1996-12-05 | 2002-05-28 | Essential Medical Devices, Inc. | Non-invasive carboxyhemoglobin analyzer |
US5921921A (en) | 1996-12-18 | 1999-07-13 | Nellcor Puritan-Bennett | Pulse oximeter with sigma-delta converter |
US5842979A (en) | 1997-02-14 | 1998-12-01 | Ohmeda Inc. | Method and apparatus for improved photoplethysmographic monitoring of oxyhemoglobin, deoxyhemoglobin, carboxyhemoglobin and methemoglobin |
US6159147A (en) | 1997-02-28 | 2000-12-12 | Qrs Diagnostics, Llc | Personal computer card for collection of real-time biological data |
US6712762B1 (en) | 1997-02-28 | 2004-03-30 | Ors Diagnostic, Llc | Personal computer card for collection of real-time biological data |
US5827179A (en) | 1997-02-28 | 1998-10-27 | Qrs Diagnostic, Llc | Personal computer card for collection for real-time biological data |
US6113541A (en) | 1997-03-07 | 2000-09-05 | Agilent Technologies, Inc. | Noninvasive blood chemistry measurement method and system |
US5954644A (en) | 1997-03-24 | 1999-09-21 | Ohmeda Inc. | Method for ambient light subtraction in a photoplethysmographic measurement instrument |
DE19880369C1 (en) | 1997-03-25 | 2002-08-08 | Siemens Ag | Method and device for the non-invasive in vivo determination of blood substances |
US5817010A (en) | 1997-03-25 | 1998-10-06 | Ohmeda Inc. | Disposable sensor holder |
US5827182A (en) | 1997-03-31 | 1998-10-27 | Ohmeda Inc. | Multiple LED sets in oximetry sensors |
US6195575B1 (en) | 1997-04-02 | 2001-02-27 | Nellcor Puritan Bennett Incorporated | Fetal sensor which self-inflates using capillary force |
US5891024A (en) | 1997-04-09 | 1999-04-06 | Ohmeda Inc. | Two stage calibration and analyte measurement scheme for spectrophotomeric analysis |
DE69704264T2 (en) | 1997-04-12 | 2001-06-28 | Agilent Technologies Inc | Method and device for the non-invasive determination of the concentration of a component |
EP0870466B1 (en) | 1997-04-12 | 1999-06-02 | Hewlett-Packard Company | Method and apparatus for determining the concentration of a component |
US6229856B1 (en) | 1997-04-14 | 2001-05-08 | Masimo Corporation | Method and apparatus for demodulating signals in a pulse oximetry system |
US6002952A (en) | 1997-04-14 | 1999-12-14 | Masimo Corporation | Signal processing apparatus and method |
US5919134A (en) | 1997-04-14 | 1999-07-06 | Masimo Corp. | Method and apparatus for demodulating signals in a pulse oximetry system |
EP0872210B1 (en) | 1997-04-18 | 2006-01-04 | Koninklijke Philips Electronics N.V. | Intermittent measuring of arterial oxygen saturation of hemoglobin |
AUPO676397A0 (en) | 1997-05-13 | 1997-06-05 | Dunlop, Colin | Method and apparatus for monitoring haemodynamic function |
IL121079A0 (en) | 1997-06-15 | 1997-11-20 | Spo Medical Equipment Ltd | Physiological stress detector device and method |
CN1309341C (en) | 1997-06-17 | 2007-04-11 | 里普朗尼克股份有限公司 | Fetal oximetry system and sensor |
WO1999000053A1 (en) | 1997-06-27 | 1999-01-07 | Toa Medical Electronics Co., Ltd. | Living body inspecting apparatus and noninvasive blood analyzer using the same |
US6532958B1 (en) * | 1997-07-25 | 2003-03-18 | Minnesota Innovative Technologies & Instruments Corporation | Automated control and conservation of supplemental respiratory oxygen |
US5924985A (en) | 1997-07-29 | 1999-07-20 | Ohmeda Inc. | Patient probe disconnect alarm |
US6343223B1 (en) | 1997-07-30 | 2002-01-29 | Mallinckrodt Inc. | Oximeter sensor with offset emitters and detector and heating device |
US6466808B1 (en) | 1999-11-22 | 2002-10-15 | Mallinckrodt Inc. | Single device for both heating and temperature measurement in an oximeter sensor |
US6115621A (en) | 1997-07-30 | 2000-09-05 | Nellcor Puritan Bennett Incorporated | Oximetry sensor with offset emitters and detector |
US5924982A (en) | 1997-07-30 | 1999-07-20 | Nellcor Puritan Bennett Incorporated | Oximeter sensor with user-modifiable color surface |
US6018674A (en) | 1997-08-11 | 2000-01-25 | Datex-Ohmeda, Inc. | Fast-turnoff photodiodes with switched-gain preamplifiers in photoplethysmographic measurement instruments |
FI973454A (en) | 1997-08-22 | 1999-02-23 | Instrumentarium Oy | A resilient device in a measuring sensor for observing the properties of living tissue |
GB9717858D0 (en) | 1997-08-23 | 1997-10-29 | Electrode Company Ltd | The Electrode Company Ltd |
CN1242693A (en) | 1997-08-26 | 2000-01-26 | 精工爱普生株式会社 | Measuring, sensing and diagnosing apparatus and method relating to wave pulse, cardiac function, and motion intensity |
US6198951B1 (en) | 1997-09-05 | 2001-03-06 | Seiko Epson Corporation | Reflection photodetector and biological information measuring instrument |
GB2329015B (en) | 1997-09-05 | 2002-02-13 | Samsung Electronics Co Ltd | Method and device for noninvasive measurement of concentrations of blood components |
US5865736A (en) | 1997-09-30 | 1999-02-02 | Nellcor Puritan Bennett, Inc. | Method and apparatus for nuisance alarm reductions |
US5960610A (en) | 1997-10-01 | 1999-10-05 | Nellcor Puritan Bennett Incorporated | Method of curving a fetal sensor |
US5971930A (en) | 1997-10-17 | 1999-10-26 | Siemens Medical Systems, Inc. | Method and apparatus for removing artifact from physiological signals |
US5987343A (en) | 1997-11-07 | 1999-11-16 | Datascope Investment Corp. | Method for storing pulse oximetry sensor characteristics |
US5995858A (en) | 1997-11-07 | 1999-11-30 | Datascope Investment Corp. | Pulse oximeter |
US6035223A (en) | 1997-11-19 | 2000-03-07 | Nellcor Puritan Bennett Inc. | Method and apparatus for determining the state of an oximetry sensor |
AU1608099A (en) | 1997-11-26 | 1999-06-15 | Somanetics Corporation | Method and apparatus for monitoring fetal cerebral oxygenation during childbirth |
US5983122A (en) | 1997-12-12 | 1999-11-09 | Ohmeda Inc. | Apparatus and method for improved photoplethysmographic monitoring of multiple hemoglobin species using emitters having optimized center wavelengths |
JP3853053B2 (en) | 1997-12-17 | 2006-12-06 | 松下電器産業株式会社 | Biological information measuring device |
EP0864293B1 (en) | 1997-12-22 | 1999-08-04 | Hewlett-Packard Company | Telemetry system, in particular for medical purposes |
JP3567319B2 (en) | 1997-12-26 | 2004-09-22 | 日本光電工業株式会社 | Probe for pulse oximeter |
US6184521B1 (en) | 1998-01-06 | 2001-02-06 | Masimo Corporation | Photodiode detector with integrated noise shielding |
EP1054626A1 (en) * | 1998-01-13 | 2000-11-29 | Urometrics, Inc. | Devices and methods for monitoring female arousal |
US6400973B1 (en) | 1998-01-20 | 2002-06-04 | Bowden's Automated Products, Inc. | Arterial blood flow simulator |
US6179159B1 (en) | 1998-01-26 | 2001-01-30 | Mariruth D. Gurley | Communicable disease barrier digit cover and dispensing package therefor |
US5978693A (en) | 1998-02-02 | 1999-11-02 | E.P. Limited | Apparatus and method for reduction of motion artifact |
ATE416668T1 (en) | 1998-02-05 | 2008-12-15 | Hema Metrics Inc | METHOD AND DEVICE FOR NON-INVASIVE OBSERVATION OF BLOOD COMPONENTS |
US6014576A (en) | 1998-02-27 | 2000-01-11 | Datex-Ohmeda, Inc. | Segmented photoplethysmographic sensor with universal probe-end |
JPH11244267A (en) | 1998-03-03 | 1999-09-14 | Fuji Photo Film Co Ltd | Blood component concentration measuring device |
US6525386B1 (en) | 1998-03-10 | 2003-02-25 | Masimo Corporation | Non-protruding optoelectronic lens |
US5924980A (en) | 1998-03-11 | 1999-07-20 | Siemens Corporate Research, Inc. | Method and apparatus for adaptively reducing the level of noise in an acquired signal |
US6165005A (en) | 1998-03-19 | 2000-12-26 | Masimo Corporation | Patient cable sensor switch |
US5997343A (en) | 1998-03-19 | 1999-12-07 | Masimo Corporation | Patient cable sensor switch |
US6078833A (en) | 1998-03-25 | 2000-06-20 | I.S.S. (Usa) Inc. | Self referencing photosensor |
US5991648A (en) | 1998-03-30 | 1999-11-23 | Palco Labs, Inc. | Adjustable pulse oximetry sensor for pediatric use |
US6047201A (en) | 1998-04-02 | 2000-04-04 | Jackson, Iii; William H. | Infant blood oxygen monitor and SIDS warning device |
EP0988521A1 (en) | 1998-04-14 | 2000-03-29 | Instrumentarium Corporation | Sensor assembly and method for measuring nitrogen dioxide |
US5916154A (en) | 1998-04-22 | 1999-06-29 | Nellcor Puritan Bennett | Method of enhancing performance in pulse oximetry via electrical stimulation |
US6064899A (en) | 1998-04-23 | 2000-05-16 | Nellcor Puritan Bennett Incorporated | Fiber optic oximeter connector with element indicating wavelength shift |
US6094592A (en) * | 1998-05-26 | 2000-07-25 | Nellcor Puritan Bennett, Inc. | Methods and apparatus for estimating a physiological parameter using transforms |
US5891021A (en) | 1998-06-03 | 1999-04-06 | Perdue Holdings, Inc. | Partially rigid-partially flexible electro-optical sensor for fingertip transillumination |
ATE521277T1 (en) | 1998-06-03 | 2011-09-15 | Masimo Corp | STEREO PULSE OXIMETER |
DE69800355T2 (en) | 1998-06-05 | 2001-03-01 | Hewlett Packard Co | Pulse rate and heart rate matching detection for pulse oximetry |
IL124787A0 (en) | 1998-06-07 | 1999-01-26 | Itamar Medical C M 1997 Ltd | Pressure applicator devices particularly useful for non-invasive detection of medical conditions |
US5920263A (en) | 1998-06-11 | 1999-07-06 | Ohmeda, Inc. | De-escalation of alarm priorities in medical devices |
IL124965A (en) | 1998-06-17 | 2002-08-14 | Orsense Ltd | Non-invasive method of optical measurements for determining concentration of a substance in blood |
US5999834A (en) | 1998-06-18 | 1999-12-07 | Ntc Technology, Inc. | Disposable adhesive wrap for use with reusable pulse oximetry sensor and method of making |
WO2000009004A2 (en) | 1998-08-13 | 2000-02-24 | Whitland Research Limited | Optical device |
US6285896B1 (en) | 1998-07-13 | 2001-09-04 | Masimo Corporation | Fetal pulse oximetry sensor |
US6671526B1 (en) | 1998-07-17 | 2003-12-30 | Nihon Kohden Corporation | Probe and apparatus for determining concentration of light-absorbing materials in living tissue |
JP2000083933A (en) | 1998-07-17 | 2000-03-28 | Nippon Koden Corp | Instrument for measuring concentration of light absorptive material in vital tissue |
US6430513B1 (en) | 1998-09-04 | 2002-08-06 | Perkinelmer Instruments Llc | Monitoring constituents of an animal organ using statistical correlation |
EP1109487A1 (en) | 1998-09-09 | 2001-06-27 | U.S. Army Institute of Surgical Research | Nasopharyngeal airway with reflectance pulse oximeter sensor |
US20020028990A1 (en) | 1998-09-09 | 2002-03-07 | Shepherd John M. | Device and method for monitoring arterial oxygen saturation |
CA2355337A1 (en) | 1998-09-09 | 2000-03-16 | U.S. Army Institute Of Surgical Research | Method for monitoring arterial oxygen saturation |
US6253098B1 (en) | 1998-09-09 | 2001-06-26 | The United States Of America As Represented By The Secretary Of The Army | Disposable pulse oximeter assembly and protective cover therefor |
US6393310B1 (en) | 1998-09-09 | 2002-05-21 | J. Todd Kuenstner | Methods and systems for clinical analyte determination by visible and infrared spectroscopy |
US6256524B1 (en) | 1998-09-09 | 2001-07-03 | The United States Of America As Represented By The Secretary Of The Army | Pulse oximeter sensor combined with a combination oropharyngeal airway and bite block |
EP1113750A1 (en) | 1998-09-18 | 2001-07-11 | U.S. Army Institute of Surgical Research | Self-piercing pulse oximeter sensor assembly |
US6064898A (en) | 1998-09-21 | 2000-05-16 | Essential Medical Devices | Non-invasive blood component analyzer |
CA2345633A1 (en) | 1998-09-29 | 2000-04-06 | Mallinckrodt Inc. | Multiple-code oximeter calibration element |
US6298252B1 (en) | 1998-09-29 | 2001-10-02 | Mallinckrodt, Inc. | Oximeter sensor with encoder connected to detector |
WO2000018290A1 (en) | 1998-09-29 | 2000-04-06 | Mallinckrodt Inc. | Oximeter sensor with encoded temperature characteristic |
ES2402233T7 (en) | 1998-10-13 | 2015-04-23 | Covidien Lp | Non-invasive multichannel tissue oximeter |
US6519487B1 (en) | 1998-10-15 | 2003-02-11 | Sensidyne, Inc. | Reusable pulse oximeter probe and disposable bandage apparatus |
US6684091B2 (en) | 1998-10-15 | 2004-01-27 | Sensidyne, Inc. | Reusable pulse oximeter probe and disposable bandage method |
US6343224B1 (en) | 1998-10-15 | 2002-01-29 | Sensidyne, Inc. | Reusable pulse oximeter probe and disposable bandage apparatus |
US6144868A (en) | 1998-10-15 | 2000-11-07 | Sensidyne, Inc. | Reusable pulse oximeter probe and disposable bandage apparatus |
US6519486B1 (en) * | 1998-10-15 | 2003-02-11 | Ntc Technology Inc. | Method, apparatus and system for removing motion artifacts from measurements of bodily parameters |
US6721585B1 (en) | 1998-10-15 | 2004-04-13 | Sensidyne, Inc. | Universal modular pulse oximeter probe for use with reusable and disposable patient attachment devices |
US6321100B1 (en) | 1999-07-13 | 2001-11-20 | Sensidyne, Inc. | Reusable pulse oximeter probe with disposable liner |
US6393311B1 (en) * | 1998-10-15 | 2002-05-21 | Ntc Technology Inc. | Method, apparatus and system for removing motion artifacts from measurements of bodily parameters |
US6006120A (en) | 1998-10-22 | 1999-12-21 | Palco Labs, Inc. | Cordless Pulse oximeter |
US6261236B1 (en) | 1998-10-26 | 2001-07-17 | Valentin Grimblatov | Bioresonance feedback method and apparatus |
US6061584A (en) | 1998-10-28 | 2000-05-09 | Lovejoy; David A. | Pulse oximetry sensor |
US6438396B1 (en) | 1998-11-05 | 2002-08-20 | Cytometrics, Inc. | Method and apparatus for providing high contrast imaging |
US6144444A (en) | 1998-11-06 | 2000-11-07 | Medtronic Avecor Cardiovascular, Inc. | Apparatus and method to determine blood parameters |
US7006855B1 (en) | 1998-11-16 | 2006-02-28 | S.P.O. Medical Equipment Ltd. | Sensor for radiance based diagnostics |
US6463311B1 (en) | 1998-12-30 | 2002-10-08 | Masimo Corporation | Plethysmograph pulse recognition processor |
US6684090B2 (en) | 1999-01-07 | 2004-01-27 | Masimo Corporation | Pulse oximetry data confidence indicator |
US6606511B1 (en) | 1999-01-07 | 2003-08-12 | Masimo Corporation | Pulse oximetry pulse indicator |
US6280381B1 (en) | 1999-07-22 | 2001-08-28 | Instrumentation Metrics, Inc. | Intelligent system for noninvasive blood analyte prediction |
JP4986324B2 (en) | 1999-01-25 | 2012-07-25 | マシモ・コーポレイション | General purpose / upgrade pulse oximeter |
US20020140675A1 (en) | 1999-01-25 | 2002-10-03 | Ali Ammar Al | System and method for altering a display mode based on a gravity-responsive sensor |
US6770028B1 (en) | 1999-01-25 | 2004-08-03 | Masimo Corporation | Dual-mode pulse oximeter |
US6658276B2 (en) | 1999-01-25 | 2003-12-02 | Masimo Corporation | Pulse oximeter user interface |
US6438399B1 (en) | 1999-02-16 | 2002-08-20 | The Children's Hospital Of Philadelphia | Multi-wavelength frequency domain near-infrared cerebral oximeter |
DE60041577D1 (en) | 1999-03-08 | 2009-04-02 | Nellcor Puritan Bennett Llc | PROCESS AND CIRCUIT FOR STORAGE AND READY |
IL129790A0 (en) | 1999-03-09 | 2000-02-29 | Orsense Ltd | A device for enhancement of blood-related signals |
US6360114B1 (en) | 1999-03-25 | 2002-03-19 | Masimo Corporation | Pulse oximeter probe-off detector |
US6308089B1 (en) | 1999-04-14 | 2001-10-23 | O.B. Scientific, Inc. | Limited use medical probe |
US6675031B1 (en) | 1999-04-14 | 2004-01-06 | Mallinckrodt Inc. | Method and circuit for indicating quality and accuracy of physiological measurements |
US6402690B1 (en) | 1999-04-23 | 2002-06-11 | Massachusetts Institute Of Technology | Isolating ring sensor design |
US6226539B1 (en) | 1999-05-26 | 2001-05-01 | Mallinckrodt, Inc. | Pulse oximeter having a low power led drive |
JP4495378B2 (en) | 1999-06-10 | 2010-07-07 | コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ | Quality indicators for measurement signals, especially medical measurement signals from oxygen saturation measurements |
EP1200905B1 (en) | 1999-06-10 | 2016-08-24 | Koninklijke Philips N.V. | Recognition of a useful signal in a measurement signal |
JP4495379B2 (en) | 1999-06-10 | 2010-07-07 | コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ | Noise suppression for measurement signals with periodic effective signals |
US6587704B1 (en) | 1999-06-16 | 2003-07-01 | Orsense Ltd. | Method for non-invasive optical measurements of blood parameters |
US20030018243A1 (en) | 1999-07-07 | 2003-01-23 | Gerhardt Thomas J. | Selectively plated sensor |
JP2001017404A (en) | 1999-07-09 | 2001-01-23 | Koike Medical:Kk | Medical measuring device |
US6760609B2 (en) | 1999-07-14 | 2004-07-06 | Providence Health System - Oregon | Adaptive calibration pulsed oximetry method and device |
WO2001003577A1 (en) | 1999-07-14 | 2001-01-18 | Providence Health System - Oregon | Adaptive calibration pulsed oximetry method and device |
US6512937B2 (en) | 1999-07-22 | 2003-01-28 | Sensys Medical, Inc. | Multi-tier method of developing localized calibration models for non-invasive blood analyte prediction |
WO2001010295A1 (en) | 1999-08-06 | 2001-02-15 | The Board Of Regents Of The University Of Texas System | Optoacoustic monitoring of blood oxygenation |
US6515273B2 (en) | 1999-08-26 | 2003-02-04 | Masimo Corporation | System for indicating the expiration of the useful operating life of a pulse oximetry sensor |
US6608562B1 (en) | 1999-08-31 | 2003-08-19 | Denso Corporation | Vital signal detecting apparatus |
WO2001017426A1 (en) | 1999-09-10 | 2001-03-15 | Gorski Stephen H | Oximeter sensor with functional liner |
JP3627214B2 (en) | 1999-09-13 | 2005-03-09 | 日本光電工業株式会社 | Blood absorption substance measuring device |
US6708049B1 (en) | 1999-09-28 | 2004-03-16 | Nellcor Puritan Bennett Incorporated | Sensor with signature of data relating to sensor |
US6213952B1 (en) | 1999-09-28 | 2001-04-10 | Orsense Ltd. | Optical device for non-invasive measurement of blood related signals utilizing a finger holder |
US6339715B1 (en) | 1999-09-30 | 2002-01-15 | Ob Scientific | Method and apparatus for processing a physiological signal |
MXPA02003412A (en) | 1999-10-07 | 2004-09-10 | K Mills Alexander | Method and apparatus for non invasive continuous determination of physiological parameters of a patient s blood. |
US6400971B1 (en) | 1999-10-12 | 2002-06-04 | Orsense Ltd. | Optical device for non-invasive measurement of blood-related signals and a finger holder therefor |
US7359741B2 (en) | 1999-11-15 | 2008-04-15 | Spo Medical Equipment Ltd. | Sensor and radiance based diagnostics |
US6665551B1 (en) | 1999-11-19 | 2003-12-16 | Nihon Kohden Corporation | Current driving system of light emitting diode |
CA2290083A1 (en) | 1999-11-19 | 2001-05-19 | Linde Medical Sensors Ag. | Device for the combined measurement of the arterial oxygen saturation and the transcutaneous co2 partial pressure of an ear lobe |
DE60045876D1 (en) | 1999-11-22 | 2011-06-01 | Mallinckrodt Inc | Pulse oximeter sensor with a wider band |
JP2001149349A (en) | 1999-11-26 | 2001-06-05 | Nippon Koden Corp | Sensor for living body |
US6542764B1 (en) | 1999-12-01 | 2003-04-01 | Masimo Corporation | Pulse oximeter monitor for expressing the urgency of the patient's condition |
US6950687B2 (en) | 1999-12-09 | 2005-09-27 | Masimo Corporation | Isolation and communication element for a resposable pulse oximetry sensor |
US6671531B2 (en) | 1999-12-09 | 2003-12-30 | Masimo Corporation | Sensor wrap including foldable applicator |
US6377829B1 (en) | 1999-12-09 | 2002-04-23 | Masimo Corporation | Resposable pulse oximetry sensor |
US7204250B1 (en) | 1999-12-16 | 2007-04-17 | Compumedics Limited | Bio-mask |
US6397092B1 (en) | 1999-12-17 | 2002-05-28 | Datex-Ohmeda, Inc. | Oversampling pulse oximeter |
US6363269B1 (en) | 1999-12-17 | 2002-03-26 | Datex-Ohmeda, Inc. | Synchronized modulation/demodulation method and apparatus for frequency division multiplexed spectrophotometric system |
US6408198B1 (en) | 1999-12-17 | 2002-06-18 | Datex-Ohmeda, Inc. | Method and system for improving photoplethysmographic analyte measurements by de-weighting motion-contaminated data |
US6360113B1 (en) | 1999-12-17 | 2002-03-19 | Datex-Ohmeda, Inc. | Photoplethysmographic instrument |
US6381479B1 (en) | 1999-12-17 | 2002-04-30 | Date-Ohmeda, Inc. | Pulse oximeter with improved DC and low frequency rejection |
US6152754A (en) | 1999-12-21 | 2000-11-28 | Masimo Corporation | Circuit board based cable connector |
AU1678800A (en) | 1999-12-22 | 2001-07-03 | Orsense Ltd. | A method of optical measurements for determining various parameters of the patient's blood |
US6419671B1 (en) | 1999-12-23 | 2002-07-16 | Visx, Incorporated | Optical feedback system for vision correction |
US6594513B1 (en) | 2000-01-12 | 2003-07-15 | Paul D. Jobsis | Method and apparatus for determining oxygen saturation of blood in body organs |
US7198778B2 (en) | 2000-01-18 | 2007-04-03 | Mallinckrodt Inc. | Tumor-targeted optical contrast agents |
US6564088B1 (en) | 2000-01-21 | 2003-05-13 | University Of Massachusetts | Probe for localized tissue spectroscopy |
US7047055B2 (en) | 2000-01-28 | 2006-05-16 | The General Hospital Corporation | Fetal pulse oximetry |
US6816266B2 (en) | 2000-02-08 | 2004-11-09 | Deepak Varshneya | Fiber optic interferometric vital sign monitor for use in magnetic resonance imaging, confined care facilities and in-hospital |
CN100506143C (en) | 2000-02-10 | 2009-07-01 | 德雷格医疗系统公司 | Method and apparatus for detecting physiological parameter |
AU2001236874B8 (en) | 2000-02-11 | 2004-05-27 | Government Of The United States Of America As Represented By The Secretary Of The Army | Pacifier pulse oximeter sensor |
US6385821B1 (en) | 2000-02-17 | 2002-05-14 | Udt Sensors, Inc. | Apparatus for securing an oximeter probe to a patient |
IL135077A0 (en) | 2000-03-15 | 2001-05-20 | Orsense Ltd | A probe for use in non-invasive measurements of blood related parameters |
US6538721B2 (en) | 2000-03-24 | 2003-03-25 | Nikon Corporation | Scanning exposure apparatus |
US6594511B2 (en) | 2000-03-29 | 2003-07-15 | Robert T. Stone | Method and apparatus for determining physiological characteristics |
US6453183B1 (en) | 2000-04-10 | 2002-09-17 | Stephen D. Walker | Cerebral oxygenation monitor |
EP2684514B1 (en) | 2000-04-17 | 2018-10-24 | Covidien LP | Pulse oximeter sensor with piece-wise function |
US6699199B2 (en) | 2000-04-18 | 2004-03-02 | Massachusetts Institute Of Technology | Photoplethysmograph signal-to-noise line enhancement |
AU2001250960A1 (en) | 2000-04-28 | 2001-11-12 | Kinderlife Instruments, Inc. | Method for determining blood constituents |
WO2001084107A2 (en) | 2000-05-02 | 2001-11-08 | Cas Medical Systems, Inc. | Method for non-invasive spectrophotometric blood oxygenation monitoring |
US6449501B1 (en) | 2000-05-26 | 2002-09-10 | Ob Scientific, Inc. | Pulse oximeter with signal sonification |
US6554788B1 (en) | 2000-06-02 | 2003-04-29 | Cobe Cardiovascular, Inc. | Hematocrit sampling system |
US6430525B1 (en) | 2000-06-05 | 2002-08-06 | Masimo Corporation | Variable mode averager |
US6510331B1 (en) | 2000-06-05 | 2003-01-21 | Glenn Williams | Switching device for multi-sensor array |
GB0014855D0 (en) | 2000-06-16 | 2000-08-09 | Isis Innovation | Combining measurements from different sensors |
GB0014854D0 (en) | 2000-06-16 | 2000-08-09 | Isis Innovation | System and method for acquiring data |
US6470199B1 (en) | 2000-06-21 | 2002-10-22 | Masimo Corporation | Elastic sock for positioning an optical probe |
DE10030862B4 (en) | 2000-06-23 | 2006-02-09 | Nicolay Verwaltungs-Gmbh | Device for fixing a medical measuring device, in particular a pulse oximetry sensor, and use of such a device |
US6697656B1 (en) | 2000-06-27 | 2004-02-24 | Masimo Corporation | Pulse oximetry sensor compatible with multiple pulse oximetry systems |
US6597931B1 (en) | 2000-09-18 | 2003-07-22 | Photonify Technologies, Inc. | System and method for absolute oxygen saturation |
US6587703B2 (en) | 2000-09-18 | 2003-07-01 | Photonify Technologies, Inc. | System and method for measuring absolute oxygen saturation |
US6889153B2 (en) | 2001-08-09 | 2005-05-03 | Thomas Dietiker | System and method for a self-calibrating non-invasive sensor |
US6640116B2 (en) | 2000-08-18 | 2003-10-28 | Masimo Corporation | Optical spectroscopy pathlength measurement system |
US6719686B2 (en) | 2000-08-30 | 2004-04-13 | Mallinckrodt, Inc. | Fetal probe having an optical imaging device |
US6553241B2 (en) | 2000-08-31 | 2003-04-22 | Mallinckrodt Inc. | Oximeter sensor with digital memory encoding sensor expiration data |
US6591123B2 (en) | 2000-08-31 | 2003-07-08 | Mallinckrodt Inc. | Oximeter sensor with digital memory recording sensor data |
US6628975B1 (en) | 2000-08-31 | 2003-09-30 | Mallinckrodt Inc. | Oximeter sensor with digital memory storing data |
US6606510B2 (en) | 2000-08-31 | 2003-08-12 | Mallinckrodt Inc. | Oximeter sensor with digital memory encoding patient data |
US6600940B1 (en) | 2000-08-31 | 2003-07-29 | Mallinckrodt Inc. | Oximeter sensor with digital memory |
US6571113B1 (en) | 2000-09-21 | 2003-05-27 | Mallinckrodt, Inc. | Oximeter sensor adapter with coding element |
US6490466B1 (en) | 2000-09-21 | 2002-12-03 | Mallinckrodt Inc. | Interconnect circuit between non-compatible oximeter and sensor |
JP3845776B2 (en) | 2000-09-22 | 2006-11-15 | 日本光電工業株式会社 | Absorbent concentration measuring device in blood |
US6434408B1 (en) | 2000-09-29 | 2002-08-13 | Datex-Ohmeda, Inc. | Pulse oximetry method and system with improved motion correction |
US6505060B1 (en) | 2000-09-29 | 2003-01-07 | Datex-Ohmeda, Inc. | Method and apparatus for determining pulse oximetry differential values |
IL138884A (en) | 2000-10-05 | 2006-07-05 | Conmed Corp | Pulse oximeter and a method of its operation |
US6819950B2 (en) | 2000-10-06 | 2004-11-16 | Alexander K. Mills | Method for noninvasive continuous determination of physiologic characteristics |
US6519484B1 (en) | 2000-11-01 | 2003-02-11 | Ge Medical Systems Information Technologies, Inc. | Pulse oximetry sensor |
US6466809B1 (en) | 2000-11-02 | 2002-10-15 | Datex-Ohmeda, Inc. | Oximeter sensor having laminated housing with flat patient interface surface |
US6967652B1 (en) | 2000-11-13 | 2005-11-22 | Ge Medical Systems Information Technologies, Inc. | Method and apparatus for displaying physiological patient data |
US6560470B1 (en) | 2000-11-15 | 2003-05-06 | Datex-Ohmeda, Inc. | Electrical lockout photoplethysmographic measurement system |
US6505133B1 (en) | 2000-11-15 | 2003-01-07 | Datex-Ohmeda, Inc. | Simultaneous signal attenuation measurements utilizing code division multiplexing |
US6594512B2 (en) | 2000-11-21 | 2003-07-15 | Siemens Medical Solutions Usa, Inc. | Method and apparatus for estimating a physiological parameter from a physiological signal |
US6760610B2 (en) | 2000-11-23 | 2004-07-06 | Sentec Ag | Sensor and method for measurement of physiological parameters |
US20020068859A1 (en) | 2000-12-01 | 2002-06-06 | Knopp Christina A. | Laser diode drive scheme for noise reduction in photoplethysmographic measurements |
US6760607B2 (en) | 2000-12-29 | 2004-07-06 | Masimo Corporation | Ribbon cable substrate pulse oximetry sensor |
US6985763B2 (en) | 2001-01-19 | 2006-01-10 | Tufts University | Method for measuring venous oxygen saturation |
US6501974B2 (en) | 2001-01-22 | 2002-12-31 | Datex-Ohmeda, Inc. | Compensation of human variability in pulse oximetry |
US6510329B2 (en) | 2001-01-24 | 2003-01-21 | Datex-Ohmeda, Inc. | Detection of sensor off conditions in a pulse oximeter |
US6618602B2 (en) | 2001-03-08 | 2003-09-09 | Palco Labs, Inc. | Method and apparatus for simultaneously determining a patient's identification and blood oxygen saturation |
US20020133067A1 (en) | 2001-03-15 | 2002-09-19 | Jackson William H. | New born and premature infant SIDS warning device |
US6591122B2 (en) | 2001-03-16 | 2003-07-08 | Nellcor Puritan Bennett Incorporated | Device and method for monitoring body fluid and electrolyte disorders |
US6556852B1 (en) | 2001-03-27 | 2003-04-29 | I-Medik, Inc. | Earpiece with sensors to measure/monitor multiple physiological variables |
JP2002303576A (en) | 2001-04-05 | 2002-10-18 | Nippon Colin Co Ltd | Oxygen saturation measuring device |
GR1003802B (en) | 2001-04-17 | 2002-02-08 | Micrel �.�.�. ������� ��������� ��������������� ��������� | Tele-medicine system |
KR100612827B1 (en) | 2001-04-19 | 2006-08-14 | 삼성전자주식회사 | Method and apparatus for noninvasively measuring hemoglobin concentration and oxygen saturation |
US20050043599A1 (en) | 2001-04-19 | 2005-02-24 | O'mara Sean T. | Pulse oximetry device and method |
US6505061B2 (en) | 2001-04-20 | 2003-01-07 | Datex-Ohmeda, Inc. | Pulse oximetry sensor with improved appendage cushion |
US20020156354A1 (en) | 2001-04-20 | 2002-10-24 | Larson Eric Russell | Pulse oximetry sensor with improved spring |
JP2004532526A (en) | 2001-05-03 | 2004-10-21 | マシモ・コーポレイション | Flex circuit shield optical sensor and method of manufacturing the flex circuit shield optical sensor |
ATE348566T1 (en) | 2001-05-03 | 2007-01-15 | Instrumentarium Corp | PULSE OXIMETER |
DE60221841T2 (en) | 2001-06-20 | 2008-05-15 | Purdue Research Foundation, West Lafayette | PRESSURE CUFF WITH BODY LIGHTING FOR USE IN THE OPTICAL NON-INVASIVE MEASUREMENT OF BLOOD PARAMETERS |
US6801802B2 (en) | 2001-06-29 | 2004-10-05 | Ge Medical Systems Information Technologies, Inc. | System and method for selecting physiological data from a plurality of physiological data sources |
US6850787B2 (en) | 2001-06-29 | 2005-02-01 | Masimo Laboratories, Inc. | Signal component processor |
US6697658B2 (en) | 2001-07-02 | 2004-02-24 | Masimo Corporation | Low power pulse oximeter |
US6731967B1 (en) | 2001-07-16 | 2004-05-04 | Pacesetter, Inc. | Methods and devices for vascular plethysmography via modulation of source intensity |
US6754516B2 (en) | 2001-07-19 | 2004-06-22 | Nellcor Puritan Bennett Incorporated | Nuisance alarm reductions in a physiological monitor |
DE10136355A1 (en) | 2001-07-26 | 2003-02-13 | Niels Rahe-Meyer | Device for monitoring vital parameters of an animal or human body consists of a portable bag with sensors, analysis electronics and visual and audible output means as well as interfaces for connection to other devices |
US6802812B1 (en) | 2001-07-27 | 2004-10-12 | Nostix Llc | Noninvasive optical sensor for measuring near infrared light absorbing analytes |
USD455834S1 (en) | 2001-08-29 | 2002-04-16 | Bci, Inc. | Finger oximeter |
US6654621B2 (en) | 2001-08-29 | 2003-11-25 | Bci, Inc. | Finger oximeter with finger grip suspension system |
US6668183B2 (en) | 2001-09-11 | 2003-12-23 | Datex-Ohmeda, Inc. | Diode detection circuit |
IL145445A (en) | 2001-09-13 | 2006-12-31 | Conmed Corp | Signal processing method and device for signal-to-noise improvement |
US6671532B1 (en) | 2001-09-17 | 2003-12-30 | Respironics Novametrix, Inc. | Pulse oximetry sensor and dispensing method |
GB0123395D0 (en) | 2001-09-28 | 2001-11-21 | Isis Innovation | Locating features ina photoplethysmograph signal |
US6697655B2 (en) | 2001-10-05 | 2004-02-24 | Mortara Instrument, Inc. | Low power pulse oximeter |
US6697653B2 (en) | 2001-10-10 | 2004-02-24 | Datex-Ohmeda, Inc. | Reduced wire count voltage drop sense |
US6564077B2 (en) | 2001-10-10 | 2003-05-13 | Mortara Instrument, Inc. | Method and apparatus for pulse oximetry |
US20030073890A1 (en) | 2001-10-10 | 2003-04-17 | Hanna D. Alan | Plethysmographic signal processing method and system |
US20030073889A1 (en) | 2001-10-11 | 2003-04-17 | Keilbach Kevin A. | Monitoring led wavelength shift in photoplethysmography |
US6773397B2 (en) | 2001-10-11 | 2004-08-10 | Draeger Medical Systems, Inc. | System for processing signal data representing physiological parameters |
US6840904B2 (en) | 2001-10-11 | 2005-01-11 | Jason Goldberg | Medical monitoring device and system |
US6748254B2 (en) | 2001-10-12 | 2004-06-08 | Nellcor Puritan Bennett Incorporated | Stacked adhesive optical sensor |
US7248910B2 (en) | 2001-10-22 | 2007-07-24 | Cardiodigital Limited | Physiological parameter monitoring system and sensor assembly for same |
US6839579B1 (en) | 2001-11-02 | 2005-01-04 | Nellcor Puritan Bennett Incorporated | Temperature indicating oximetry sensor |
US6701170B2 (en) | 2001-11-02 | 2004-03-02 | Nellcor Puritan Bennett Incorporated | Blind source separation of pulse oximetry signals |
JP4174648B2 (en) | 2001-11-12 | 2008-11-05 | ロート製薬株式会社 | Aqueous composition |
JP3709836B2 (en) | 2001-11-20 | 2005-10-26 | コニカミノルタセンシング株式会社 | Blood component measuring device |
US20030100840A1 (en) | 2001-11-28 | 2003-05-29 | Nihon Kohden Corporation | Pulse photometry probe |
US6839580B2 (en) | 2001-12-06 | 2005-01-04 | Ric Investments, Inc. | Adaptive calibration for pulse oximetry |
US6780158B2 (en) | 2001-12-14 | 2004-08-24 | Nihon Kohden Corporation | Signal processing method and pulse wave signal processing method |
US6934570B2 (en) | 2002-01-08 | 2005-08-23 | Masimo Corporation | Physiological sensor combination |
US6668182B2 (en) | 2002-01-10 | 2003-12-23 | Northeast Monitoring | Pulse oxymetry data processing |
US6822564B2 (en) | 2002-01-24 | 2004-11-23 | Masimo Corporation | Parallel measurement alarm processor |
DE60315596T2 (en) | 2002-01-31 | 2008-05-15 | Loughborough University Enterprises Ltd., Loughborough | VENOUS PULSE OXIMETRY |
US7020507B2 (en) | 2002-01-31 | 2006-03-28 | Dolphin Medical, Inc. | Separating motion from cardiac signals using second order derivative of the photo-plethysmogram and fast fourier transforms |
US6882874B2 (en) | 2002-02-15 | 2005-04-19 | Datex-Ohmeda, Inc. | Compensation of human variability in pulse oximetry |
US6805673B2 (en) | 2002-02-22 | 2004-10-19 | Datex-Ohmeda, Inc. | Monitoring mayer wave effects based on a photoplethysmographic signal |
US20040039273A1 (en) | 2002-02-22 | 2004-02-26 | Terry Alvin Mark | Cepstral domain pulse oximetry |
US6709402B2 (en) | 2002-02-22 | 2004-03-23 | Datex-Ohmeda, Inc. | Apparatus and method for monitoring respiration with a pulse oximeter |
JP2005518238A (en) | 2002-02-22 | 2005-06-23 | デイテックス−オーメダ インコーポレイテッド | Cepstrum region pulse oximeter |
US6702752B2 (en) | 2002-02-22 | 2004-03-09 | Datex-Ohmeda, Inc. | Monitoring respiration based on plethysmographic heart rate signal |
US20050177034A1 (en) | 2002-03-01 | 2005-08-11 | Terry Beaumont | Ear canal sensing device |
US20030171662A1 (en) | 2002-03-07 | 2003-09-11 | O'connor Michael William | Non-adhesive flexible electro-optical sensor for fingertip trans-illumination |
US6863652B2 (en) | 2002-03-13 | 2005-03-08 | Draeger Medical Systems, Inc. | Power conserving adaptive control system for generating signal in portable medical devices |
KR100455289B1 (en) | 2002-03-16 | 2004-11-08 | 삼성전자주식회사 | Method of diagnosing using a ray and apparatus thereof |
JP4188844B2 (en) | 2002-03-21 | 2008-12-03 | デイテックス−オーメダ インコーポレイテッド | Newborn boot wrap |
US6647279B2 (en) | 2002-03-22 | 2003-11-11 | Jonas Alexander Pologe | Hybrid optical delivery system for photoplethysmography |
US6850788B2 (en) | 2002-03-25 | 2005-02-01 | Masimo Corporation | Physiological measurement communications adapter |
KR100462182B1 (en) * | 2002-04-15 | 2004-12-16 | 삼성전자주식회사 | Apparatus and method for detecting heart beat using ppg |
US7892183B2 (en) | 2002-04-19 | 2011-02-22 | Pelikan Technologies, Inc. | Method and apparatus for body fluid sampling and analyte sensing |
US20030212316A1 (en) | 2002-05-10 | 2003-11-13 | Leiden Jeffrey M. | Method and apparatus for determining blood parameters and vital signs of a patient |
US6711425B1 (en) | 2002-05-28 | 2004-03-23 | Ob Scientific, Inc. | Pulse oximeter with calibration stabilization |
US8996090B2 (en) | 2002-06-03 | 2015-03-31 | Exostat Medical, Inc. | Noninvasive detection of a physiologic parameter within a body tissue of a patient |
US7024235B2 (en) | 2002-06-20 | 2006-04-04 | University Of Florida Research Foundation, Inc. | Specially configured nasal pulse oximeter/photoplethysmography probes, and combined nasal probe/cannula, selectively with sampler for capnography, and covering sleeves for same |
US6909912B2 (en) | 2002-06-20 | 2005-06-21 | University Of Florida | Non-invasive perfusion monitor and system, specially configured oximeter probes, methods of using same, and covers for probes |
US6865407B2 (en) | 2002-07-11 | 2005-03-08 | Optical Sensors, Inc. | Calibration technique for non-invasive medical devices |
US6999809B2 (en) | 2002-07-16 | 2006-02-14 | Edwards Lifesciences Corporation | Central venous catheter having a soft tip and fiber optics |
US7072701B2 (en) | 2002-07-26 | 2006-07-04 | Cas Medical Systems, Inc. | Method for spectrophotometric blood oxygenation monitoring |
US6850789B2 (en) | 2002-07-29 | 2005-02-01 | Welch Allyn, Inc. | Combination SPO2/temperature measuring apparatus |
US7096054B2 (en) | 2002-08-01 | 2006-08-22 | Masimo Corporation | Low noise optical housing |
US7133711B2 (en) | 2002-08-07 | 2006-11-07 | Orsense, Ltd. | Method and system for decomposition of multiple channel signals |
US6825619B2 (en) | 2002-08-08 | 2004-11-30 | Datex-Ohmeda, Inc. | Feedback-controlled LED switching |
US6707257B2 (en) | 2002-08-08 | 2004-03-16 | Datex-Ohmeda, Inc. | Ferrite stabilized LED drive |
US6720734B2 (en) | 2002-08-08 | 2004-04-13 | Datex-Ohmeda, Inc. | Oximeter with nulled op-amp current feedback |
US6879850B2 (en) | 2002-08-16 | 2005-04-12 | Optical Sensors Incorporated | Pulse oximeter with motion detection |
US6745061B1 (en) | 2002-08-21 | 2004-06-01 | Datex-Ohmeda, Inc. | Disposable oximetry sensor |
US6643531B1 (en) | 2002-08-22 | 2003-11-04 | Bci, Inc. | Combination fingerprint and oximetry device |
US6912413B2 (en) | 2002-09-13 | 2005-06-28 | Ge Healthcare Finland Oy | Pulse oximeter |
US7341559B2 (en) | 2002-09-14 | 2008-03-11 | Masimo Corporation | Pulse oximetry ear sensor |
US7142901B2 (en) | 2002-09-25 | 2006-11-28 | Masimo Corporation | Parameter compensated physiological monitor |
US20040186358A1 (en) | 2002-09-25 | 2004-09-23 | Bart Chernow | Monitoring system containing a hospital bed with integrated display |
US7289837B2 (en) | 2002-10-01 | 2007-10-30 | Nellcor Puritan Bennett Incorpoated | Forehead sensor placement |
US7096052B2 (en) | 2002-10-04 | 2006-08-22 | Masimo Corporation | Optical probe including predetermined emission wavelength based on patient type |
US6731962B1 (en) | 2002-10-31 | 2004-05-04 | Smiths Medical Pm Inc | Finger oximeter with remote telecommunications capabilities and system therefor |
JP4352315B2 (en) | 2002-10-31 | 2009-10-28 | 日本光電工業株式会社 | Signal processing method / apparatus and pulse photometer using the same |
WO2004047631A2 (en) | 2002-11-22 | 2004-06-10 | Masimo Laboratories, Inc. | Blood parameter measurement system |
JP4489385B2 (en) | 2002-12-12 | 2010-06-23 | 株式会社日立メディコ | Measuring probe and biological light measuring device |
US6947781B2 (en) | 2002-12-13 | 2005-09-20 | Massachusetts Institute Of Technology | Vibratory venous and arterial oximetry sensor |
US6754515B1 (en) | 2002-12-17 | 2004-06-22 | Kestrel Labs, Inc. | Stabilization of noisy optical sources in photoplethysmography |
KR100499139B1 (en) | 2003-01-07 | 2005-07-04 | 삼성전자주식회사 | Method of removing abnormal data and blood constituent analysing system using spectroscopy employing the same |
US7006856B2 (en) | 2003-01-10 | 2006-02-28 | Nellcor Puritan Bennett Incorporated | Signal quality metrics design for qualifying data for a physiological monitor |
US7016715B2 (en) | 2003-01-13 | 2006-03-21 | Nellcorpuritan Bennett Incorporated | Selection of preset filter parameters based on signal quality |
US7225006B2 (en) | 2003-01-23 | 2007-05-29 | Masimo Corporation | Attachment and optical probe |
US6920345B2 (en) | 2003-01-24 | 2005-07-19 | Masimo Corporation | Optical sensor including disposable and reusable elements |
US7272426B2 (en) | 2003-02-05 | 2007-09-18 | Koninklijke Philips Electronics N.V. | Finger medical sensor |
ATE521279T1 (en) | 2003-02-27 | 2011-09-15 | Nellcor Puritan Bennett Ie | METHOD AND DEVICE FOR EVALUATION AND PROCESSING PHOTOPLETHYSMOGRAPHIC SIGNALS BY WAVE TRANSFORMATION ANALYSIS |
US6968221B2 (en) | 2003-03-14 | 2005-11-22 | Futrex, Inc. | Low-cost method and apparatus for non-invasively measuring blood glucose levels |
US20040215244A1 (en) | 2003-04-23 | 2004-10-28 | Marcovecchio Alan F. | Processing pulse signal in conjunction with ECG signal to detect pulse in external defibrillation |
KR100571811B1 (en) | 2003-05-09 | 2006-04-17 | 삼성전자주식회사 | Ear type measurement apparatus for bio signal |
US6993372B2 (en) | 2003-06-03 | 2006-01-31 | Orsense Ltd. | Method and system for use in non-invasive optical measurements of blood parameters |
US6992772B2 (en) | 2003-06-19 | 2006-01-31 | Optix Lp | Method and apparatus for optical sampling to reduce interfering variances |
US6954664B2 (en) | 2003-06-20 | 2005-10-11 | Smiths Medical Pm, Inc. | Oximetry simulator |
US7047056B2 (en) | 2003-06-25 | 2006-05-16 | Nellcor Puritan Bennett Incorporated | Hat-based oximeter sensor |
US7025728B2 (en) | 2003-06-30 | 2006-04-11 | Nihon Kohden Corporation | Method for reducing noise, and pulse photometer using the method |
US7003338B2 (en) | 2003-07-08 | 2006-02-21 | Masimo Corporation | Method and apparatus for reducing coupling between signals |
DE10334542A1 (en) | 2003-07-29 | 2005-02-17 | Pav Patentverwertung Kg | Brewing device with elastic element for holding down the coffee pad |
US7263396B2 (en) | 2003-08-08 | 2007-08-28 | Cardiodigital Limited | Ear sensor assembly |
JP4685014B2 (en) | 2003-08-20 | 2011-05-18 | コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ | System and method for detecting signal artifacts |
US7107088B2 (en) | 2003-08-25 | 2006-09-12 | Sarnoff Corporation | Pulse oximetry methods and apparatus for use within an auditory canal |
US6931269B2 (en) | 2003-08-27 | 2005-08-16 | Datex-Ohmeda, Inc. | Multi-domain motion estimation and plethysmographic recognition using fuzzy neural-nets |
US20050049468A1 (en) | 2003-09-03 | 2005-03-03 | Sven-Erik Carlson | Increasing the performance of an optical pulsoximeter |
CA2481857A1 (en) | 2003-09-19 | 2005-03-19 | Nir Diagnostics Inc. | Near infrared risk assessment of diseases |
US20050075550A1 (en) | 2003-10-03 | 2005-04-07 | Lindekugel Eric W. | Quick-clip sensor holder |
US7254434B2 (en) | 2003-10-14 | 2007-08-07 | Masimo Corporation | Variable pressure reusable sensor |
TWI250867B (en) | 2003-10-22 | 2006-03-11 | Surewin Technology Corp | Pulse wave analysis device |
US20050113704A1 (en) | 2003-11-26 | 2005-05-26 | Lawson Corey J. | Patient monitoring system that incorporates memory into patient parameter cables |
DE20318882U1 (en) | 2003-12-03 | 2004-03-11 | Drewes, Susanne | Pulse-oximetry sensor suitable for new-born includes flexible, conformed, hygienic material embedding circuitry for disinfection and reuse |
US7305262B2 (en) | 2003-12-11 | 2007-12-04 | Ge Medical Systems Information Technologies, Inc. | Apparatus and method for acquiring oximetry and electrocardiogram signals |
US7280858B2 (en) | 2004-01-05 | 2007-10-09 | Masimo Corporation | Pulse oximetry sensor |
JP2005200031A (en) | 2004-01-13 | 2005-07-28 | Showa Kiki Kogyo Co Ltd | Pos communication failure preventive device |
US7162288B2 (en) | 2004-02-25 | 2007-01-09 | Nellcor Purtain Bennett Incorporated | Techniques for detecting heart pulses and reducing power consumption in sensors |
US20050197548A1 (en) | 2004-03-05 | 2005-09-08 | Elekon Industries Usa, Inc. | Disposable/reusable flexible sensor |
JP4191642B2 (en) | 2004-04-02 | 2008-12-03 | 三菱電機株式会社 | Transflective liquid crystal display device and manufacturing method thereof |
US20050228300A1 (en) | 2004-04-07 | 2005-10-13 | Triage Data Networks | Cuffless blood-pressure monitor and accompanying wireless mobile device |
US7179228B2 (en) | 2004-04-07 | 2007-02-20 | Triage Wireless, Inc. | Cuffless system for measuring blood pressure |
US20050228248A1 (en) | 2004-04-07 | 2005-10-13 | Thomas Dietiker | Clip-type sensor having integrated biasing and cushioning means |
US7238159B2 (en) | 2004-04-07 | 2007-07-03 | Triage Wireless, Inc. | Device, system and method for monitoring vital signs |
US20070208269A1 (en) | 2004-05-18 | 2007-09-06 | Mumford John R | Mask assembly, system and method for determining the occurrence of respiratory events using frontal electrode array |
US7575005B2 (en) | 2004-05-18 | 2009-08-18 | Excel-Tech Ltd. | Mask assembly with integrated sensors |
US7263393B2 (en) | 2004-06-07 | 2007-08-28 | Healing Rhythms, Llc. | Biofeedback ring sensors |
EP1781162A1 (en) | 2004-07-09 | 2007-05-09 | Tadiran Spectralink Ltd. | Wearable device, system and method for measuring vital parameters |
US7438687B2 (en) | 2004-08-14 | 2008-10-21 | Nova Technology Corporation | Patient monitoring system with blood pressure measurement capacity |
US7683759B2 (en) | 2004-10-06 | 2010-03-23 | Martis Ip Holdings, Llc | Patient identification system |
US20060084878A1 (en) | 2004-10-18 | 2006-04-20 | Triage Wireless, Inc. | Personal computer-based vital signs monitor |
WO2006134421A2 (en) | 2004-11-05 | 2006-12-21 | Envitec-Wismar Gmbh | Apparatus for improved pulse oximetry measurement |
US7359742B2 (en) | 2004-11-12 | 2008-04-15 | Nonin Medical, Inc. | Sensor assembly |
US7658716B2 (en) | 2004-12-07 | 2010-02-09 | Triage Wireless, Inc. | Vital signs monitor using an optical ear-based module |
US7392074B2 (en) | 2005-01-21 | 2008-06-24 | Nonin Medical, Inc. | Sensor system with memory and method of using same |
JP2006204742A (en) | 2005-01-31 | 2006-08-10 | Konica Minolta Sensing Inc | Method and system for evaluating sleep, its operation program, pulse oxymeter, and system for supporting sleep |
US7236881B2 (en) | 2005-02-07 | 2007-06-26 | International Business Machines Corporation | Method and apparatus for end-to-end travel time estimation using dynamic traffic data |
US7596398B2 (en) | 2005-03-01 | 2009-09-29 | Masimo Laboratories, Inc. | Multiple wavelength sensor attachment |
US7548771B2 (en) | 2005-03-31 | 2009-06-16 | Nellcor Puritan Bennett Llc | Pulse oximetry sensor and technique for using the same on a distal region of a patient's digit |
KR100716824B1 (en) | 2005-04-28 | 2007-05-09 | 삼성전기주식회사 | Printed circuit board with embedded capacitors using hybrid materials, and manufacturing process thereof |
US7657294B2 (en) | 2005-08-08 | 2010-02-02 | Nellcor Puritan Bennett Llc | Compliant diaphragm medical sensor and technique for using the same |
US7590439B2 (en) | 2005-08-08 | 2009-09-15 | Nellcor Puritan Bennett Llc | Bi-stable medical sensor and technique for using the same |
JP3116255U (en) | 2005-08-30 | 2005-12-02 | モリト株式会社 | Eggplant ring and key holder using the same |
JP3116260U (en) | 2005-08-30 | 2005-12-02 | マーテック株式会社 | Swivel hanger |
US20070060808A1 (en) | 2005-09-12 | 2007-03-15 | Carine Hoarau | Medical sensor for reducing motion artifacts and technique for using the same |
JP4779017B2 (en) | 2005-09-21 | 2011-09-21 | 章民 ▲楊▼ | Electronics |
US7904130B2 (en) | 2005-09-29 | 2011-03-08 | Nellcor Puritan Bennett Llc | Medical sensor and technique for using the same |
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 |
US7483731B2 (en) | 2005-09-30 | 2009-01-27 | 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 |
US8073518B2 (en) | 2006-05-02 | 2011-12-06 | Nellcor Puritan Bennett Llc | Clip-style medical sensor and technique for using the same |
US7477924B2 (en) | 2006-05-02 | 2009-01-13 | Nellcor Puritan Bennett Llc | Medical sensor and technique for using the same |
US7522948B2 (en) | 2006-05-02 | 2009-04-21 | Nellcor Puritan Bennett Llc | Medical sensor and technique for using the same |
JP3134144U (en) | 2006-11-13 | 2007-08-09 | ▲寛▼重 小林 | Article-mounted lid and Western-style toilet equipped with article-mounted lid |
JP5049624B2 (en) | 2007-03-26 | 2012-10-17 | 株式会社東芝 | Metal fine particle dispersed film and method for producing metal fine particle dispersed film |
JP5049625B2 (en) | 2007-03-27 | 2012-10-17 | キヤノン株式会社 | Structure manufacturing method and structure manufacturing apparatus using the same |
-
2005
- 2005-09-30 US US11/240,682 patent/US7483731B2/en active Active
-
2006
- 2006-09-29 WO PCT/US2006/038121 patent/WO2007041330A1/en active Application Filing
- 2006-09-29 TW TW095136259A patent/TW200726443A/en unknown
-
2009
- 2009-01-05 US US12/348,742 patent/US8352009B2/en active Active
Patent Citations (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5226417A (en) * | 1991-03-11 | 1993-07-13 | Nellcor, Inc. | Apparatus for the detection of motion transients |
EP1386578A1 (en) * | 2002-08-02 | 2004-02-04 | Samsung Electronics Co., Ltd. | Probe for measuring a biological signal and system incorporating the probe |
US20040034294A1 (en) * | 2002-08-16 | 2004-02-19 | Optical Sensors, Inc. | Pulse oximeter |
Cited By (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
GB2578120A (en) * | 2018-10-16 | 2020-04-22 | Medical Wireless Sensing Ltd | Movement sensing clamp |
GB2578120B (en) * | 2018-10-16 | 2021-06-16 | Medical Wireless Sensing Ltd | Movement sensing clamp |
Also Published As
Publication number | Publication date |
---|---|
US8352009B2 (en) | 2013-01-08 |
US20070078316A1 (en) | 2007-04-05 |
US20090118598A1 (en) | 2009-05-07 |
TW200726443A (en) | 2007-07-16 |
US7483731B2 (en) | 2009-01-27 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US7483731B2 (en) | Medical sensor and technique for using the same | |
US8364220B2 (en) | Medical sensor and technique for using the same | |
US8805463B2 (en) | Medical sensor with compressible light barrier and technique for using the same | |
US8190224B2 (en) | Medical sensor for reducing signal artifacts and technique for using the same | |
US8175671B2 (en) | Medical sensor for reducing signal artifacts and technique for using the same | |
US8396527B2 (en) | Medical sensor for reducing signal artifacts and technique for using the same | |
US8311601B2 (en) | Reflectance and/or transmissive pulse oximeter | |
US7894869B2 (en) | Multiple configuration medical sensor and technique for using the same | |
US8352004B2 (en) | Medical sensor and technique for using the same | |
US8145288B2 (en) | Medical sensor for reducing signal artifacts and technique for using the same | |
US7477924B2 (en) | Medical sensor and technique for using the same | |
US20110124991A1 (en) | System and method for mitigating interference in pulse oximetry | |
KR101033472B1 (en) | Method and shape of sensor module for photo-plethysmogram measurement without motion artifact | |
US20090163783A1 (en) | Medical sensor and technique for using the same | |
US20230039857A1 (en) | Improved ppg measurement | |
JP2016067916A (en) | Sensor and biological signal measurement system | |
TW201347735A (en) | Blood parameter measuring device and method for measuring blood parameter |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
121 | Ep: the epo has been informed by wipo that ep was designated in this application | ||
NENP | Non-entry into the national phase |
Ref country code: DE |
|
122 | Ep: pct application non-entry in european phase |
Ref document number: 06815823 Country of ref document: EP Kind code of ref document: A1 |