US20090076345A1 - Adherent Device with Multiple Physiological Sensors - Google Patents

Adherent Device with Multiple Physiological Sensors Download PDF

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Publication number
US20090076345A1
US20090076345A1 US12209288 US20928808A US2009076345A1 US 20090076345 A1 US20090076345 A1 US 20090076345A1 US 12209288 US12209288 US 12209288 US 20928808 A US20928808 A US 20928808A US 2009076345 A1 US2009076345 A1 US 2009076345A1
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Prior art keywords
patient
signal
patch
electrocardiogram
electrodes
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Abandoned
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US12209288
Inventor
Yatheendhar D. Manicka
Badri Amurthur
Mark J. Bly
Kristofer J. James
Imad Libbus
Scott T. Mazar
Jerry S. Wang
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Medtronic Monitoring Inc
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Medtronic Monitoring Inc
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Abstract

An adherent device to monitor a patient comprises an adhesive patch to adhere to a skin of the patient. At least four electrodes are connected to the patch and capable of electrically coupling to the patient. Impedance circuitry is coupled to the at least four electrodes to measure a hydration signal of the patient. Electrocardiogram circuitry is coupled to at least two of the at least four electrodes to measure an electrocardiogram signal of the patient. An accelerometer can be mechanically coupled to the adhesive patch to generate a signal in response to at least one of an activity or a position of the patient.

Description

    CROSS-REFERENCES TO RELATED APPLICATIONS
  • The present application claims the benefit under 35 USC 119(e) of U.S. Provisional Application No. 60/972,537 and 60/972,629 both filed Sep. 14, 2007, and 61/055,645 and 61/055,666 both filed May 23, 2008; the full disclosures of which are incorporated herein by reference in their entirety.
  • The subject matter of the present application is related to the following applications: 60/972,512; 60/972,329; 60/972,354; 60/972,616; 60/972,363; 60/972,343; 60/972,581; 60/972,316; 60/972,333; 60/972,359; 60/972,336; 60/972,340 all of which were filed on Sep. 14, 2007; 61/046,196 filed Apr. 18, 2008; 61/047,875 filed Apr. 25, 2008; 61/055,656 and 61/055,662 both filed May 23, 2008; and 61/079,746 filed Jul. 10, 2008. The following applications are being filed concurrently with the present application, on Sep. 12, 2008: Attorney Docket Nos. 026843-000110US entitled “Multi-Sensor Patient Monitor to Detect Impending Cardiac Decompensation Prediction”; 026843-000410US entitled “Injectable Device for Physiological Monitoring”; 026843-000510US entitled “Delivery System for Injectable Physiological Monitoring System”; 026843-000620US entitled “Adherent Device for Cardiac Rhythm Management”; 026843-000710US entitled “Adherent Device for Respiratory Monitoring”; 026843-0008110US entitled “Adherent Athletic Monitor”; 026843-000910US entitled “Adherent Emergency Monitor”; 026843-001320US entitled “Adherent Device with Physiological Sensors”; 026843-001410US entitled “Medical Device Automatic Start-up upon Contact to Patient Tissue”; 026843-001900US entitled “System and Methods for Wireless Body Fluid Monitoring”; 026843-002010US entitled “Adherent Cardiac Monitor with Advanced Sensing Capabilities”; 026843-002410US entitled “Adherent Device for Sleep Disordered Breathing”; 026843-002710US entitled “Dynamic Pairing of Patients to Data Collection Gateways”; 026843-003010US entitled “Adherent Multi-Sensor Device with Implantable Device Communications Capabilities”; 026843-003110US entitled “Data Collection in a Multi-Sensor Patient Monitor”; 026843-003210US entitled “Adherent Multi-Sensor Device with Empathic Monitoring”; 026843-003310US entitled “Energy Management for Adherent Patient Monitor”; and 026843-003410US entitled “Tracking and Security for Adherent Patient Monitor.”
  • BACKGROUND OF THE INVENTION
  • 1. Field of the Invention
  • The present invention relates to patient monitoring. Although embodiments make specific reference to monitoring impedance and electrocardiogram signals with an adherent patch, the system methods and device described herein may be applicable to many applications in which physiological monitoring is used, for example wireless physiological monitoring for extended periods.
  • Patients are often treated for diseases and/or conditions associated with a compromised status of the patient, for example a compromised physiologic status. In some instances, a patient may report symptoms that require diagnosis to determine the underlying cause. For example, a patient may report fainting or dizziness that requires diagnosis, in which long term monitoring of the patient can provide useful information as to the physiologic status of the patient. In some instances a patient may have suffered a heart attack and require care and/or monitoring after release from the hospital. One example of a device to provide long term monitoring of a patient is the Holter monitor, or ambulatory electrocardiography device.
  • In addition to measuring heart signals with electrocardiograms, known physiologic measurements include impedance measurements. For example, transthoracic impedance measurements can be used to measure hydration and respiration. Although transthoracic measurements can be useful, such measurements may use electrodes that are positioned across the midline of the patient, and may be somewhat uncomfortable and/or cumbersome for the patient to wear.
  • Work in relation to embodiments of the present invention suggests that known methods and apparatus for long term monitoring of patients may be less than ideal. At least some of the known devices may not collect the right kinds of data to treat patients optimally. For example, although successful at detecting and storing electrocardiogram signals, devices such as the Holter monitor can be somewhat bulky and may not collect all of the kinds of data that would be ideal to diagnose and/or treat a patient. In at least some instances, devices that are worn by the patient may be somewhat uncomfortable, which may lead to patients not wearing the devices and not complying with direction from the health care provider, such that data collected may be less than ideal. Although implantable devices may be used in some instances, many of these devices can be invasive and/or costly, and may suffer at least some of the shortcomings of known wearable devices.
  • Therefore, a need exists for improved patient monitoring. Ideally, such improved patient monitoring would avoid at least some of the short-comings of the present methods and devices.
  • 2. Description of Background Art
  • The following U.S. patents and Publications may describe relevant background art: U.S. Pat. Nos. 3,370,459; 3,805,769; 3,845,757; 3,972,329; 4,121,573; 4,141,366; 4,838,273; 4,955,381; 4,981,139; 5,080,099; 5,353,793; 5,511,553; 5,544,661; 5,558,638; 5,724,025; 5,772,586; 5,862,802; 6,047,203; 6,117,077; 6,129,744; 6,225,901; 6,385,473; 6,416,471; 6,454,707; 6,527,711; 6,527,729; 6,551,252; 6,595,927; 6,595,929; 6,605,038; 6,645,153; 6,795,722; 6,821,249; 6,980,851; 7,020,508; 7,054,679; 7,153,262; 2003/0092975; 2005/0113703; 2005/0131288; 2006/0010090; 2006/0031102; 2006/0089679; 2006/0155183; 2006/122474; 2006/0224051; 2006/0264730; 2007/0021678; and 2007/0038038.
  • BRIEF SUMMARY OF THE INVENTION
  • The present invention relates to patient monitoring. Although embodiments make specific reference to monitoring impedance and electrocardiogram signals with an adherent patch, the system methods and device described herein may be applicable to any application in which physiological monitoring is used, for example wireless physiological monitoring for extended periods.
  • In a first aspect, embodiments of the present invention provide an adherent device to monitor a patient. The device comprises an adhesive patch to adhere to a skin of the patient. At least four electrodes are connected to the patch and capable of electrically coupling to the patient. Impedance circuitry can be coupled to the at least four electrodes to measure a hydration signal of the patient. Electrocardiogram circuitry can be coupled to at least two of the at least four electrodes to measure an electrocardiogram signal of the patient. An accelerometer can be mechanically coupled, for exampled adhered or affixed, to the adhesive patch to generate an accelerometer signal in response to at least one of an activity or a position of the patient. Work in relation to embodiments of the present invention suggests accelerometer signals can improve patient diagnosis, and can be especially useful when used with other signals, such as electrocardiogram signals and impedance signals for hydration and respiration. Mechanically coupling the accelerometer to the electrodes for measuring impedance and hydration may also improve the quality and/or usefulness of the impedance and/or electrocardiogram signals. For example, mechanical coupling of the accelerometer to the electrodes and to the skin of the patient can improve the reliability, quality and/or accuracy of the accelerometer measurements, as the electrode signals can indicate the quality of mechanical coupling of the patch to the patient so as to indicate that the device is connected to the patient and that the accelerometer signals are valid. In some embodiments, the adherent device may comprise a dimension across that is no more than about 8 inches, such that the device can be comfortably worn by at least some patients for an extended period to permit collection of the electrocardiogram, impedance and accelerometer signals for extended periods.
  • In many embodiments, the adhesive patch is mechanically coupled to the at least four electrodes, the impedance circuitry, the electrocardiogram circuitry and the accelerometer, such that the patch is capable of supporting the at least four electrodes, the impedance circuitry, the electrocardiogram circuitry and the accelerometer when the adherent patch is adhered to the skin of the patient.
  • In many embodiments, a wireless communication circuitry is coupled to the impedance circuitry, the electrocardiogram circuitry and the accelerometer to transmit to a remote center with a communication protocol at least one of the hydration signal, the electrocardiogram signal or the accelerometer signal. The wireless communication circuitry can be configured to transmit the hydration signal, the electrocardiogram signal and the accelerometer signal to the remote center with a single wireless hop from the wireless communication circuitry to an intermediate device. In specific embodiments, the communication protocol can comprise at least one of Bluetooth, Zigbee, WiFi, WiMax, IR, a cellular protocol, amplitude modulation or frequency modulation. In many embodiments, the intermediate device comprises a data collection system to collect and/or store data from the wireless transmitter, and the data collection system can be configured to communicate periodically with the remote center with wireless communication and/or wired communication. The communications protocol may comprise a two way protocol such that the remote center is capable of issuing commands to control data collection
  • The adherent device may comprise many sensors configured to measure many different signals. In many embodiments, the accelerometer comprises at least one of a piezoelectric accelerometer, capacitive accelerometer or electromechanical accelerometer and wherein the accelerometer comprises a 3-axis accelerometer to measure at least one of an inclination, a position, an orientation or acceleration of the patient in three dimensions. The impedance circuitry can be adapted to measure extracellular fluid of the patient with at least one frequency within a range from about 0.5 kHz to about 200 kHz., and the impedance circuitry is configured to determine a respiration of the patient. The device may comprise a microphone to detect an audio signal from within the patient, and the audio signal may comprise a heart sound with an S3 heart sound and/or a respiratory sound with rales and/or crackles. The device may comprise a temperature sensor to measure a temperature of the patient. Work in relation to embodiments of the present invention suggest that patient temperature may effect impedance measurements, such that the impedance measurements can be corrected with the temperature measurement.
  • In many embodiments, the adherent device comprises a processor comprising a tangible medium, and the processor is configured to control a collection and transmission of data from the impedance circuitry, the electrocardiogram circuitry and the accelerometer. The adherent device may comprise a real time clock and a frequency generator.
  • In another aspect, embodiments of the present invention provide a method of monitoring a patient. An adhesive patch is adhered to a skin of the patient to couple at least four electrodes to the skin of the patient. A hydration signal of the patient is measured with impedance circuitry coupled to the at least four electrodes. An electrocardiogram signal of the patient is measured with electrocardiogram circuitry coupled to at least two of the at least four electrodes. A signal from an accelerometer is measured in response to at least one of an activity or a position of the patient.
  • In many embodiments, the adhesive patch supports the at least four electrodes, the impedance circuitry, the electrocardiogram circuitry and the accelerometer when the adherent patch is adhered to the skin of the patient.
  • In another aspect, embodiments of the present invention provide an adherent device to monitor a patient. The adherent device comprises an adhesive patch to adhere to a skin of the patient. At least four electrodes are affixed to the patch and capable of electrically coupling to the patient. A maximum dimension across the at least 4 electrodes may comprise no more that about eight inches, such that the at least four electrodes are capable of adhering to either a left side or a right side of the patient. Impedance circuitry may be coupled to the at least four electrodes to measure hydration of the patient. Electrocardiogram circuitry may be coupled to at least two of the at least four electrodes to measure an electrocardiogram of the patient.
  • In many embodiments, the maximum distance across the at least four electrodes comprises no more than about six inches. The device comprises a maximum dimension across no more than about 8 inches, and the patch is capable of measuring the electrocardiogram and the impedance from a left side or a right side of the patient.
  • In another aspect, an adherent device to monitor a patient for an extended period is provided. The device comprises a breathable tape comprising an adhesive coating to adhere the breathable tape to a skin of the patient, such that tape and device may be comfortable when worn by the patient. The breathable tape may comprise a porous material, for example a porous fabric, to allow transmission of water vapor while the device is worn by the patient. At least one electrode is affixed to the breathable tape and capable of electrically coupling to a skin of the patient. At least one gel can be disposed over a contact surface of the at least one electrode to electrically connect the electrode to the skin. A printed circuit board, for example, a flex printed circuit board, can be connected to the breathable tape to support the printed circuit board with the breathable tape when the tape is adhered to the patient. Electronic components may be electrically connected to the printed circuit board and coupled to the at least one electrode to measure physiologic signals of the patient. A breathable cover, which may be water resistant, can be disposed over the circuit board and electronic components and connected to at least one of the electronics components, the printed circuit board or the breathable tape.
  • In many embodiments, an electronics housing is adhered to at least one of the electronics circuitry or the printed circuit board, such that the electronics housing is disposed between the cover and the electronics components.
  • In many embodiments, a gel cover is positioned over a breathable tape to inhibit a flow of the gel through the breathable tape. The printed circuit board, for example a flex printed circuit board, may be located over the gel cover such that the gel cover is disposed between the breathable tape and the printed circuit board.
  • In many embodiments, the breathable tape comprises a first porosity, and the gel cover comprises a breathable tape with a second porosity, in which the second porosity is less than the first porosity to inhibit flow of the gel through the breathable tape. In specific embodiments, the breathable tape comprises a tricot-knit polyester fabric backing with an acrylate adhesive coating, and the gel cover comprises a polyurethane, non-woven backing with an acrylate adhesive coating.
  • In many embodiments, the breathable tape, the adhesive coating, the at least one electrode and gel coating are separable from the printed circuit board, electronic components, and water resistant housing and cover, such that the printed circuit board, electronic components, water resistant housing and water proof cover are reusable.
  • In many embodiments, the at least one electrode extends through at least one aperture in the breathable tape. In some embodiments, the at least one electrode is configured to electrically couple to the printed circuit board through the breathable tape.
  • In another aspect, embodiments of the present invention provide a method of monitoring a patient for an extended period. An electronics module is attached to a first adherent patch component of a plurality of adherent patch components. The first adherent patch component is adhered to a skin of the patient. The electronics module is removed from the first adherent patch component. The electronics module is attached to a second patch component of the plurality of patch components after the first adherent patch component has been removed.
  • In many embodiments, the electronics module is removed from the second adherent patch component, and the electronics module is attached to a third patch component of the plurality of patch components after the second adherent patch component has been removed.
  • In many embodiments, impedance signals are measured when the third adherent patch component is adhered to the patient.
  • In another aspect, embodiments of the present invention provide a system to monitor a patient for an extended period. The system comprise a plurality of adherent patch components. An electronics module may be adapted to couple to each of the plurality of patch components for sequential measurements from each of the patch components.
  • In many embodiments, each of the plurality of adherent patch components comprises, a breathable tape with an adhesive coating to adhere the breathable tape to a skin of the patient, and at least one electrode affixed to the breathable tape.
  • In many embodiments, the electronics module comprises a printed circuit board configured to connect electrically to the at least one electrode to measure physiologic signals of the patient, electronic components electrically connected to the printed circuit board, and a housing adhered to at least one of the electronics module or the printed circuit board.
  • In another aspect, embodiments of the present invention provide a method of monitoring a patient for an extended period of time. A first adherent patch is adhered on a first side of the patient, in which the first adherent patch comprises first electrodes to measure at least one of an electrocardiogram or an impedance. The at least one of the electrocardiogram or the impedance is measured from the first side of the patient for a first period of time. The first patch is removed from the first side of the patient. A second adherent patch is placed on a second side of the patient, in which the second adherent patch comprises second electrodes to measure the at least one of the electrocardiogram or the impedance. The at least one of the electrocardiogram or the impedance is measured from the second side of the patient for a second period of time after the first patch has been removed.
  • In many embodiments, the first side comprises at least one of a left side or a right side of the patient, and the second side is opposite the first side.
  • In many embodiments, the second patch is removed from the second side of the patient, and a third adherent patch is placed on the first side of the patient, in which the third patch comprises third electrodes to measure the at least one of the electrocardiogram or the impedance. The at least one of the electrocardiogram or the impedance is measured from the first side of the patient for a third period of time after the second patch has been removed.
  • In many embodiments, the third patch is removed from the first side of the patient. A fourth adherent patch is placed on the second side of the patient, in which the fourth patch comprising fourth electrodes to measure the at least one of the electrocardiogram or the impedance. The at least one of the electrocardiogram or the impedance is measured from the second side of the patient for a fourth period of time after the third patch has been removed.
  • In specific embodiments, each of the first period of time, the second period of time, the third period of time and the fourth period of time comprises at least about 1 week.
  • In another aspect, embodiments of the present invention provide a method of monitoring a patient for an extended period of time. A first adherent patch is placed on a skin location on a first side of the patient, in which the first adherent patch comprises first electrodes to measure at least one of an electrocardiogram or an impedance. The at least one of the electrocardiogram or the impedance is measured from the first adherent patch on the first skin location for a first period of time. The first patch is removed from the first skin location. A second adherent patch is placed on a second skin location on a second side of the patient, in which the second adherent patch comprises second electrodes to measure the at least one of the electrocardiogram or the impedance. The at least one of the electrocardiogram or the impedance is measured from the second skin location for a second period of time after the first patch has been removed.
  • In many embodiments, the first skin location heals during the second period of time.
  • In another aspect, embodiments of the present invention provide an adherent device to monitor a patient. The device comprises an adhesive patch to adhere to a skin of the patient. At least four electrodes are mechanically coupled to the patch and capable of electrically coupling to the patient. The at least four electrodes may comprise at least two force electrodes and at least two sense electrodes. Impedance circuitry may be electrically coupled to the at least two force electrodes to force an electrical current and to the at least two sense electrodes to measure a hydration signal of the patient. Electrocardiogram circuitry can be coupled to the at least two force electrodes to measure an electrocardiogram signal of the patient.
  • In many embodiments, the adherent device comprises electrical switches connected to the at least two force electrodes to isolate the at least two force electrodes from the impedance circuitry when the electrocardiogram circuitry measures the electrocardiogram. In specific embodiments, a processor an be configured to control the impedance circuitry and the electrocardiogram circuitry so as to time division multiplex collection the hydration signal and the electrocardiogram signal. The processor may be configured to decouple the at least two force electrodes from the impedance circuitry when the electrocardiogram circuitry measures the electrocardiogram signal.
  • In many embodiments, the at least four electrodes comprise no more than four electrodes.
  • In some embodiments, the at least two force electrodes comprise outer electrodes and the at least two sense electrodes comprise inner electrodes.
  • In some embodiments, the at least two force electrodes comprise inner electrodes and the at least two sense electrodes comprise outer electrodes.
  • In another aspect, embodiments of the present invention provide a method of monitoring a patient. An adhesive patch is adhered to a skin of the patient so as to couple at least four electrodes to the skin of the patient, in which the at least four electrodes comprise at least two force electrodes and at least two sense electrodes. A hydration signal of the patient is measured with impedance circuitry electrically coupled to the at least two force electrodes and to the at least two sense electrodes, such that the at least two force electrodes force an electrical current between the at least two force electrodes. An electrocardiogram signal of the patient is measured with electrocardiogram circuitry coupled to the at least two force electrodes.
  • In many embodiments, electrical switches connected to the at least two force electrodes can be opened to isolate the at least two force electrodes from the impedance circuitry when the electrocardiogram circuitry measures the electrocardiogram.
  • In many embodiments, the hydration signal and the electrocardiogram signal can be time division multiplexed.
  • In another aspect, embodiments of the present inventions provide an adherent device to monitor a patient. The device comprises an adhesive patch and at least two electrodes connected to the patch. The device also comprises circuitry coupled to at least two electrodes to measure at least two of an electrocardiogram signal, a respiration signal of the patient or an activity signal of the patient, and a processor system. The adhesive patch can adhere to a skin of the patient. The electrodes are capable of electrically coupling to the patient. The processor system comprises a tangible medium configured to trigger an alarm in response to the at least two of the electrocardiogram signal, the respiration signal or the activity signal.
  • In many embodiments, the processor system comprises a first processor and a second processor. The first processor may comprise a tangible medium attached to the adherent patch. The second processor may comprise a tangible medium at a remote center.
  • In many embodiments, the processor system is configured to combine at least two of the electrocardiogram signal, the respiration signal or the activity signal, the purpose of which may be to detect an impending cardiac decompensation. Combining may comprise at least one of adding, subtracting, multiplying, scaling, or dividing the at least two of the electrocardiogram signal, the hydration signal, the respiration signal, or the activity signal. In some embodiments, the at least two of the electrocardiogram signal, the respiration signal, or the activity signal can be combined with at least one of a weighted combination, a tiered combination, or a logic gated combination, a time weighted combination or a rate of change.
  • In many embodiments, the processor system is configured to continuously monitor, store in tangible media, and transmit to a remote center at least two of the electrocardiogram signal, the respiration signal or the activity signal when the alarm is triggered.
  • In many embodiments, the processor system is configured to trigger the alarm and alert the patient and/or the physician in response to an adverse cardiac event.
  • In many embodiments, the processor system is configured to calculate and report a patient risk of sudden cardiac death to at least one of a remote center or a physician.
  • In many embodiments, the processor system is configured to detect at least one of a T-wave alternans, a pulsus alternans, an autonomic imbalance, a heart rate variability in response to at least two of the electrocardiogram signal, the respiration signal or the activity signal.
  • In many embodiments, the processor system is configured to loop record at least two of the electrocardiogram signal, the respiration signal or the activity signal for diagnosis of an unexplained syncope and/or arrhythmia when the alarm is triggered.
  • In many embodiments, the processor system is configured to detect an event comprising at least one of an atrial fibrillation in response to the electrocardiogram signal or an acute myocardial infarction in response to an ST segment elevation of the electrocardiogram signal.
  • In many embodiments, the processor system is configured to monitor a high risk patient post myocardial infarction with at least two of the electrocardiogram signal, the respiration signal or the activity signal.
  • In many embodiments, the processor system is configured to continuously monitor a bradycardia of the patient at risk for sudden death, the electrocardiogram signal comprising at least one of a Brugada Syndrome with an ST elevation and a short QT interval or long-QT interval.
  • In many embodiments, the processor system is configured to monitor the electrocardiogram signal and an alert at least one of a patient, a remote center a physician, emergency responder, or family/caregiver in response to an adverse event.
  • In many embodiments, the processor system is configured to determine a tiered response to at least two of the electrocardiogram signal, the respiration signal or the activity signal.
  • In some embodiments, the tiered response may comprise a first tier to contact an emergency responder in response to an immediate life threatening event, a second tier to contact a physician in response to an event that requires medical care, a third tier to contact a family member and/or care giver, and a fourth tier to contact the center.
  • In some embodiments, the immediate life threatening event comprises at least one of a sustained ventricular tachycardia, a sustained ventricular fibrillation, an asystole, an arrhythmia with no respiration or an arrhythmia with no patient movement.
  • In some embodiments, the event that requires medical care comprises an atrial fibrillation that is not immediately life threatening.
  • In some embodiments, the wireless communication circuitry is configured to transmit at least two of the electrocardiogram signal, the respiration signal or the activity signal with a single wireless hop from the wireless communication circuitry to an intermediate device.
  • In another aspect, embodiments of the present invention provides a method of monitoring a patient. An adhesive patch is adhered to a skin of the patient so as to couple at least two electrodes to the skin of the patient. Circuitry coupled to the at least two electrodes measures at least two of an electrocardiogram signal of the patient, a respiration signal of the patient or an activity signal of the patient. An alarm may be triggered by a processor system in response to the at least two of the electrocardiogram signal, the respiration signal or the activity signal with the processor system comprising a tangible medium.
  • In many embodiments, the processor system comprises a first processor and a second processor. The first processor comprises a tangible medium attached to the adherent patch and the second processor comprises a tangible medium at a remote center.
  • In many embodiments, at least two of the electrocardiogram signal, the respiration signal, or the activity signal are combined, which may be to detect am impending cardiac decompensation. In some embodiments, combining may comprise at least one of adding, subtracting, multiplying, scaling or dividing the at least two of the electrocardiogram signal, the hydration signal, the respiration signal or the activity signal. In some embodiments, the at least two of the electrocardiogram signal, the respiration signal, or the activity signal can be combined with at least one of a weighted combination, a tiered combination, or a logic gated combination, a time weighted combination or a rate of change.
  • In many embodiments, at least two of the electrocardiogram signal, the respiration signal, or the activity signal are continuously monitored, stored, and/or transmitted to a remote center.
  • In many embodiments, the alarm is triggered and the patient and/or the physician is alerted in response to an adverse cardiac event.
  • In many embodiments, a patient risk of sudden cardiac death is calculated and/or reported to at least one of a remote center or a physician.
  • In many embodiments, at least one of a T-wave alternans, a pulsus alternans, an autonomic imbalance, a heart rate variability in response to the at least two of the electrocardiogram signal, the respiration signal or the activity signal is detected.
  • In many embodiments, the at least two of the electrocardiogram signal, the respiration signal or the activity signal is loop recorded when the alarm is triggered.
  • In many embodiments, an event comprising at least one of an atrial fibrillation in response to the electrocardiogram signal or an acute myocardial infarction in response to an ST segment elevation of the electrocardiogram signal is detected.
  • In many embodiments, a high risk patent post myocardial infarction is monitored with the at least two of the electrocardiogram signal, the respiration signal or the activity signal.
  • In many embodiments, a bradycardia of the patient at risk for sudden death, the electrocardiogram signal comprising at least one of a Brugada Syndrome with an ST elevation and a short QT interval or long-QT interval are continuously monitored.
  • In many embodiments, the electrocardiogram signal is monitored and/or at least one of a patient, a remote center, a physician, emergency responder, or family/caregiver is alerted in response to an adverse event.
  • In many embodiments, a tiered response to the at least two of the electrocardiogram signal, the respiration signal or the activity signal is determined.
  • In many embodiments, the tiered response comprises a first tier to contact an emergency responder in response to an immediate life threatening event, a second tier to contact a physician in response to an event that requires medical care, a third tier to contact a family member and/or care giver, and a fourth tier to contact the center.
  • In many embodiments, the immediate life threatening event comprises at least one of a sustained ventricular tachycardia, a sustained ventricular fibrillation, an asystole, an arrhythmia with no respiration or an arrhythmia with no patient movement.
  • In many embodiments, the event that requires medical care comprises an atrial fibrillation that is not immediately life threatening.
  • In some embodiments, wireless communication circuitry transmits the at least two of the electrocardiogram signal, the respiration signal or the activity signal with a single wireless hop from the wireless communication circuitry to an intermediate device.
  • BRIEF DESCRIPTION OF THE DRAWINGS
  • FIG. 1A shows a patient and a monitoring system comprising an adherent device, according to embodiments of the present invention;
  • FIG. 1B shows a bottom view of the adherent device as in FIG. 1A comprising an adherent patch;
  • FIG. 1C shows a top view of the adherent patch, as in FIG. 1B;
  • FIG. 1D shows a printed circuit boards and electronic components over the adherent patch, as in FIG. 1C;
  • FIG. 1D1 shows an equivalent circuit that can be used to determine optimal frequencies for determining patient hydration, according to embodiments of the present invention;
  • FIG. 1E shows batteries positioned over the printed circuit board and electronic components as in FIG. 1D;
  • FIG. 1F shows a top view of an electronics housing and a breathable cover over the batteries, electronic components and printed circuit board as in FIG. 1E;
  • FIG. 1G shows a side view of the adherent device as in FIGS. 1A to 1F;
  • FIG. 1H shown a bottom isometric view of the adherent device as in FIGS. 1A to 1G;
  • FIGS. 1I and 1J show a side cross-sectional view and an exploded view, respectively, of the adherent device as in FIGS. 1A to 1H;
  • FIG. 1K shows at least one electrode configured to electrically couple to a skin of the patient through a breathable tape, according to embodiments of the present invention;
  • FIGS. 2A to 2C show a system to monitor a patient for an extended period comprising a reusable electronic component and a plurality of disposable patch components, according to embodiments of the present invention;
  • FIG. 2D shows a method of using the system as in FIGS. 2A to 2C;
  • FIGS. 3A to 3D show a method of monitoring a patient for an extended period with an adherent patch with adherent patches alternatively adhered to the right side or the left side of the patient;
  • FIG. 4A shows an adherent device to measure an impedance signal and an electrocardiogram signal, according to embodiments of the present invention;
  • FIG. 4B shows a method of measuring the impedance signal and the electrocardiogram signal, according to embodiments of the present invention;
  • FIG. 5A shows a method for monitoring a patient and responding to a signal event; and
  • FIGS. 6A and 6B show clinical data measured with an adherent patch device.
  • DETAILED DESCRIPTION OF THE INVENTION
  • Embodiments of the present invention relate to patient monitoring. Although embodiments make specific reference to monitoring impedance and electrocardiogram signals with an adherent patch, the system methods and device described herein may be applicable to any application in which physiological monitoring is used, for example wireless physiological monitoring for extended periods.
  • Decompensation is failure of the heart to maintain adequate blood circulation. Although the heart can maintain at least some pumping of blood, the quantity is inadequate to maintain healthy tissues. Several symptoms can result from decompensation including pulmonary congestion, breathlessness, faintness, cardiac palpitation, edema of the extremities, and enlargement of the liver. Cardiac decompensation can result in slow or sudden death. Sudden Cardiac Arrest (hereinafter “SCA”), also referred to as sudden cardiac death, is an abrupt loss of cardiac pumping function that can be caused by a ventricular arrhythmia, for example ventricular tachycardia and/or ventricular fibrillation. Although decompensation and SCA can be related in that patients with decompensation are also at an increased risk for SCA, decompensation is primarily a mechanical dysfunction caused by inadequate blood flow, and SCA is primarily an electrical dysfunction caused by inadequate and/or inappropriate electrical signals of the heart.
  • In many embodiments, the adherent devices described herein may be used for 90 day monitoring, or more, and may comprise completely disposable components and/or reusable components, and can provide reliable data acquisition and transfer. In many embodiments, the patch is configured for patient comfort, such that the adherent patch can be worn and/or tolerated by the patient for extended periods, for example 90 days or more. The patch may be worn continuously for at least seven days, for example 14 days, and then replaced with another patch. Adherent devices with comfortable patches that can be worn for extended periods and in which patches can be replaced and the electronics modules reused are described in U.S. patent application Nos. 60/972,537, entitled “Adherent Device with Multiple Physiological Sensors”; and 60/972,629, entitled “Adherent Device with Multiple Physiological Sensors”, both filed on Sep. 14, 2007, the full disclosures of which have been previously incorporated herein by reference. In many embodiments, the adherent patch comprises a tape, which comprises a material, preferably breathable, with an adhesive, such that trauma to the patient skin can be minimized while the patch is worn for the extended period. The printed circuit board may comprise a flex printed circuit board that can flex with the patient to provide improved patient comfort.
  • FIG. 1A shows a patient P and a monitoring system 10. Patient P comprises a midline M, a first side S1, for example a right side, and a second side S2, for example a left side. Monitoring system 10 comprises an adherent device 100. Adherent device 100 can be adhered to a patient P at many locations, for example thorax T of patient P. In many embodiments, the adherent device may adhere to one side of the patient, from which side data can be collected. Work in relation with embodiments of the present invention suggests that location on a side of the patient can provide comfort for the patient while the device is adhered to the patient.
  • Monitoring system 10 includes components to transmit data to a remote center 106. Remote center 106 can be located in a different building from the patient, for example in the same town as the patient, and can be located as far from the patient as a separate continent from the patient, for example the patient located on a first continent and the remote center located on a second continent. Adherent device 100 can communicate wirelessly to an intermediate device 102, for example with a single wireless hop from the adherent device on the patient to the intermediate device. Intermediate device 102 can communicate with remote center 106 in many ways, for example with an internet connection and/or with a cellular connection. In many embodiments, monitoring system 10 comprises a distributed processing system with at least one processor comprising a tangible medium of device 100, at least one processor 102P of intermediate device 102, and at least one processor 106P at remote center 106, each of which processors can be in electronic communication with the other processors. At least one processor 102P comprises a tangible medium 102T, and at least one processor 106P comprises a tangible medium 106T. Remote processor 106P may comprise a backend server located at the remote center. Remote center 106 can be in communication with a health care provider 108A with a communication system 107A, such as the Internet, an intranet, phone lines, wireless and/or satellite phone. Health care provider 108A, for example a family member, can be in communication with patient P with a communication, for example with a two way communication system, as indicated by arrow 109A, for example by cell phone, email, landline. Remote center 106 can be in communication with a health care professional, for example a physician 108B, with a communication system 107B, such as the Internet, an intranet, phone lines, wireless and/or satellite phone. Physician 108B can be in communication with patient P with a communication, for example with a two way communication system, as indicated by arrow 109B, for example by cell phone, email, landline. Remote center 106 can be in communication with an emergency responder 108C, for example a 911 operator and/or paramedic, with a communication system 107C, such as the Internet, an intranet, phone lines, wireless and/or satellite phone. Emergency responder 108C can travel to the patient as indicated by arrow 109C. Thus, in many embodiments, monitoring system 10 comprises a closed loop system in which patient care can be monitored and implemented from the remote center in response to signals from the adherent device.
  • In many embodiments, the adherent device may continuously monitor physiological parameters, communicate wirelessly with a remote center, and provide alerts when necessary. The system may comprise an adherent patch, which attaches to the patient's thorax and contains sensing electrodes, battery, memory, logic, and wireless communication capabilities. In some embodiments, the patch can communicate with the remote center, via the intermediate device in the patient's home. In some embodiments, remote center 106 receives the patient data and applies a patient evaluation algorithm, for example the prediction algorithm to predict cardiac decompensation. In some embodiments, the algorithm may comprise an algorithm to predict impending cardiac decompensation is described in U.S. patent application No. 60/972,512, the full disclosure of which has been previously incorporated herein by reference. When a flag is raised, the center may communicate with the patient, hospital, nurse, and/or physician to allow for therapeutic intervention, for example to prevent decompensation.
  • The adherent device may be affixed and/or adhered to the body in many ways. For example, with at least one of the following an adhesive tape, a constant-force spring, suspenders around shoulders, a screw-in microneedle electrode, a pre-shaped electronics module to shape fabric to a thorax, a pinch onto roll of skin, or transcutaneous anchoring. Patch and/or device replacement may occur with a keyed patch (e.g. two-part patch), an outline or anatomical mark, a low-adhesive guide (place guide|remove old patch|place new patch|remove guide), or a keyed attachment for chatter reduction. The patch and/or device may comprise an adhesiveless embodiment (e.g. chest strap), and/or a low-irritation adhesive for sensitive skin. The adherent patch and/or device can comprise many shapes, for example at least one of a dogbone, an hourglass, an oblong, a circular or an oval shape.
  • In many embodiments, the adherent device may comprise a reusable electronics module with replaceable patches, and each of the replaceable patches may include a battery. The module may collect cumulative data for approximately 90 days and/or the entire adherent component (electronics+patch) may be disposable. In a completely disposable embodiment, a “baton” mechanism may be used for data transfer and retention, for example baton transfer may include baseline information. In some embodiments, the device may have a rechargeable module, and may use dual battery and/or electronics modules, wherein one module 101A can be recharged using a charging station 103 while the other module 101B is placed on the adherent patch with connectors. In some embodiments, the intermediate device 102 may comprise the charging module, data transfer, storage and/or transmission, such that one of the electronics modules can be placed in the intermediate device for charging and/or data transfer while the other electronics module is worn by the patient.
  • System 10 can perform the following functions: initiation, programming, measuring, storing, analyzing, communicating, predicting, and displaying. The adherent device may contain a subset of the following physiological sensors: bioimpedance, respiration, respiration rate variability, heart rate (ave, min, max), heart rhythm, hear rate variability (HRV), heart rate turbulence (HRT), heart sounds (e.g. S3), respiratory sounds, blood pressure, activity, posture, wake/sleep, orthopnea, temperature/heat flux, and weight. The activity sensor may comprise one or more of the following: ball switch, accelerometer, minute ventilation, HR, bioimpedance noise, skin temperature/heat flux, BP, muscle noise, posture.
  • The adherent device can wirelessly communicate with remote center 106. The communication may occur directly (via a cellular or Wi-Fi network), or indirectly through intermediate device 102. Intermediate device 102 may consist of multiple devices, which can communicate wired or wirelessly to relay data to remote center 106.
  • In many embodiments, instructions are transmitted from remote site 106 to a processor supported with the adherent patch on the patient, and the processor supported with the patient can receive updated instructions for the patient treatment and/or monitoring, for example while worn by the patient.
  • FIG. 1B shows a bottom view of adherent device 100 as in FIG. 1A comprising an adherent patch 110. Adherent patch 110 comprises a first side, or a lower side 110A, that is oriented toward the skin of the patient when placed on the patient. In many embodiments, adherent patch 110 comprises a tape 110T which is a material, preferably breathable, with an adhesive 116A. Patient side 110A comprises adhesive 116A to adhere the patch 110 and adherent device 100 to patient P. Electrodes 112A, 112B, 112C and 112D are affixed to adherent patch 110. In many embodiments, at least four electrodes are attached to the patch, for example six electrodes. In some embodiments the patch comprises two electrodes, for example two electrodes to measure the electrocardiogram (ECG) of the patient. Gel 114A, gel 114B, gel 114C and gel 114D can each be positioned over electrodes 112A, 112B, 112C and 112D, respectively, to provide electrical conductivity between the electrodes and the skin of the patient. In many embodiments, the electrodes can be affixed to the patch 110, for example with known methods and structures such as rivets, adhesive, stitches, etc. In many embodiments, patch 110 comprises a breathable material to permit air and/or vapor to flow to and from the surface of the skin.
  • FIG. 1C shows a top view of the adherent patch 100, as in FIG. 1B. Adherent patch 100 comprises a second side, or upper side 110B. In many embodiments, electrodes 112A, 112B, 112C and 112D extend from lower side 110A through adherent patch 110 to upper side 110B. An adhesive 116B can be applied to upper side 110B to adhere structures, for example a breathable cover, to the patch such that the patch can support the electronics and other structures when the patch is adhered to the patient. The PCB may comprise completely flex PCB, rigid PCB, rigid PCB combined flex PCB and/or rigid PCB boards connected by cable.
  • FIG. 1D shows a printed circuit boards and electronic components over adherent patch 110, as in FIGS. 1A to 1C. In some embodiments, a printed circuit board (PCB), for example flex printed circuit board 120, may be connected to electrodes 112A, 112B, 112C and 112D with connectors 122A, 122B, 122C and 122D. Flex printed circuit board 120 can include traces 123A, 123B, 123C and 123D that extend to connectors 122A, 122B, 122C and 122D, respectively, on the flex PCB. Connectors 122A, 122B, 122C and 122D can be positioned on flex printed circuit board 120 in alignment with electrodes 112A, 112B, 112C and 112D so as to electrically couple the flex PCB with the electrodes. In some embodiments, connectors 122A, 122B, 122C and 122D may comprise insulated wires and/or a film with conductive ink that provide strain relief between the PCB and the electrodes. For example, connectors 122A, 122B, 122C and 122D may comprise a flexible polyester film coated with conductive silver ink. In some embodiments, additional PCB's, for example rigid PCB's 120A, 120B, 120C and 120D, can be connected to flex printed circuit board 120. Electronic components 130 can be connected to flex printed circuit board 120 and/or mounted thereon. In some embodiments, electronic components 130 can be mounted on the additional PCB's.
  • Electronic components 130 comprise components to take physiologic measurements, transmit data to remote center 106 and receive commands from remote center 106. In many embodiments, electronics components 130 may comprise known low power circuitry, for example complementary metal oxide semiconductor (CMOS) circuitry components. Electronics components 130 comprise an activity sensor and activity circuitry 134, impedance circuitry 136 and electrocardiogram circuitry, for example ECG circuitry 136. In some embodiments, electronics circuitry 130 may comprise a microphone and microphone circuitry 142 to detect an audio signal from within the patient, and the audio signal may comprise a heart sound and/or a respiratory sound, for example an S3 heart sound and a respiratory sound with rales and/or crackles.
  • Electronics circuitry 130 may comprise a temperature sensor, for example a thermistor in contact with the skin of the patient, and temperature sensor circuitry 144 to measure a temperature of the patient, for example a temperature of the skin of the patient. A temperature sensor may be used to determine the sleep and wake state of the patient. The temperature of the patient can decrease as the patient goes to sleep and increase when the patient wakes up.
  • Work in relation to embodiments of the present invention suggests that skin temperature may effect impedance and/or hydration measurements, and that skin temperature measurements may be used to correct impedance and/or hydration measurements. In some embodiments, increase in skin temperature or heat flux can be associated with increased vaso-dilation near the skin surface, such that measured impedance measurement decreased, even through the hydration of the patient in deeper tissues under the skin remains substantially unchanged. Thus, use of the temperature sensor can allow for correction of the hydration signals to more accurately assess the hydration, for example extra cellular hydration, of deeper tissues of the patient, for example deeper tissues in the thorax.
  • Electronics circuitry 130 may comprise a processor 146. Processor 146 comprises a tangible medium, for example read only memory (ROM), electrically erasable programmable read only memory (EEPROM) and/or random access memory (RAM). Electronic circuitry 130 may comprise real time clock and frequency generator circuitry 148. In some embodiments, processor 136 may comprise the frequency generator and real time clock. The processor can be configured to control a collection and transmission of data from the impedance circuitry electrocardiogram circuitry and the accelerometer. In many embodiments, device 100 comprise a distributed processor system, for example with multiple processors on device 100.
  • In many embodiments, electronics components 130 comprise wireless communications circuitry 132 to communicate with remote center 106. The wireless communication circuitry can be coupled to the impedance circuitry, the electrocardiogram circuitry and the accelerometer to transmit to a remote center with a communication protocol at least one of the hydration signal, the electrocardiogram signal or the inclination signal. In specific embodiments, wireless communication circuitry is configured to transmit the hydration signal, the electrocardiogram signal and the inclination signal to the remote center with a single wireless hop, for example from wireless communication circuitry 132 to intermediate device 102. The communication protocol comprises at least one of Bluetooth, Zigbee, WiFi, WiMax, IR, amplitude modulation or frequency modulation. In many embodiments, the communications protocol comprises a two way protocol such that the remote center is capable of issuing commands to control data collection.
  • Intermediate device 102 may comprise a data collection system to collect and store data from the wireless transmitter. The data collection system can be configured to communicate periodically with the remote center. The data collection system can transmit data in response to commands from remote center 106 and/or in response to commands from the adherent device.
  • Activity sensor and activity circuitry 134 can comprise many known activity sensors and circuitry. In many embodiments, the accelerometer comprises at least one of a piezoelectric accelerometer, capacitive accelerometer or electromechanical accelerometer. The accelerometer may comprises a 3-axis accelerometer to measure at least one of an inclination, a position, an orientation or acceleration of the patient in three dimensions. Work in relation to embodiments of the present invention suggests that three dimensional orientation of the patient and associated positions, for example sitting, standing, lying down, can be very useful when combined with data from other sensors, for example ECG data and/or hydration data.
  • Impedance circuitry 136 can generate both hydration data and respiration data. In many embodiments, impedance circuitry 136 is electrically connected to electrodes 112A, 112B, 112C and 112D in a four pole configuration, such that electrodes 112A and 112D comprise outer electrodes that are driven with a current and comprise force electrodes that force the current through the tissue. The current delivered between electrodes 112A and 112D generates a measurable voltage between electrodes 112B and 112C, such that electrodes 112B and 112C comprise inner, sense, electrodes that sense and/or measure the voltage in response to the current from the force electrodes. In some embodiments, electrodes 112B and 112C may comprise force electrodes and electrodes 112A and 112B may comprise sense electrodes. The voltage measured by the sense electrodes can be used to measure the impedance of the patient and determine the respiration rate and/or hydration of the patient.
  • FIG. 1D1 shows an equivalent circuit 152 that can be used to determine optimal frequencies for measuring patient hydration. Work in relation to embodiments of the present invention indicates that the frequency of the current and/or voltage at the force electrodes can be selected so as to provide impedance signals related to the extracellular and/or intracellular hydration of the patient tissue. Equivalent circuit 152 comprises an intracellular resistance 156, or R(ICW) in series with a capacitor 154, and an extracellular resistance 158, or R(ECW). Extracellular resistance 158 is in parallel with intracellular resistance 156 and capacitor 154 related to capacitance of cell membranes. In many embodiments, impedances can be measured and provide useful information over a wide range of frequencies, for example from about 0.5 kHz to about 200 KHz. Work in relation to embodiments of the present invention suggests that extracellular resistance 158 can be significantly related extracellular fluid and to cardiac decompensation, and that extracellular resistance 158 and extracellular fluid can be effectively measured with frequencies in a range from about 0.5 kHz to about 20 kHz, for example from about 1 kHz to about 10 kHz. In some embodiments, a single frequency can be used to determine the extracellular resistance and/or fluid. As sample frequencies increase from about 10 kHz to about 20 kHz, capacitance related to cell membranes decrease the impedance, such that the intracellular fluid contributes to the impedance and/or hydration measurements. Thus, many embodiments of the present invention measure hydration with frequencies from about 0.5 kHz to about 20 kHz to determine patient hydration.
  • In many embodiments, impedance circuitry 136 can be configured to determine respiration of the patient. In specific embodiments, the impedance circuitry can measure the hydration at 25 Hz intervals, for example at 25 Hz intervals using impedance measurements with a frequency from about 0.5 kHz to about 20 kHz.
  • ECG circuitry 138 can generate electrocardiogram signals and data from two or more of electrodes 112A, 112B, 112C and 112D in many ways. In some embodiments, ECG circuitry 138 is connected to inner electrodes 112B and 122C, which may comprise sense electrodes of the impedance circuitry as described above. In some embodiments, ECG circuitry 138 can be connected to electrodes 112A and 112D so as to increase spacing of the electrodes. The inner electrodes may be positioned near the outer electrodes to increase the voltage of the ECG signal measured by ECG circuitry 138. In many embodiments, the ECG circuitry may measure the ECG signal from electrodes 112A and 112D when current is not passed through electrodes 112A and 112D, for example with switches as described in U.S. App. No. 60/972,527, the full disclosure of which has been previously incorporated herein by reference.
  • FIG. 1E shows batteries 150 positioned over the flex printed circuit board and electronic components as in FIG. 1D. Batteries 150 may comprise rechargeable batteries that can be removed and/or recharged. In some embodiments, batteries 150 can be removed from the adherent patch and recharged and/or replaced.
  • FIG. 1F shows a top view of a cover 162 over the batteries, electronic components and flex printed circuit board as in FIGS. 1A to 1E. In many embodiments, an electronics housing 160 may be disposed under cover 162 to protect the electronic components, and in some embodiments electronics housing 160 may comprise an encapsulant over the electronic components and PCB. In some embodiments, cover 162 can be adhered to adherent patch 110 with an adhesive 164 on an underside of cover 162. In many embodiments, electronics housing 160 may comprise a water proof material, for example a sealant adhesive such as epoxy or silicone coated over the electronics components and/or PCB. In some embodiments, electronics housing 160 may comprise metal and/or plastic. Metal or plastic may be potted with a material such as epoxy or silicone.
  • Cover 162 may comprise many known biocompatible cover, casing and/or housing materials, such as elastomers, for example silicone. The elastomer may be fenestrated to improve breathability. In some embodiments, cover 162 may comprise many known breathable materials, for example polyester, polyamide, and/or elastane (Spandex™). The breathable fabric may be coated to make it water resistant, waterproof, and/or to aid in wicking moisture away from the patch.
  • FIG. 1G shows a side view of adherent device 100 as in FIGS. 1A to 1F. Adherent device 100 comprises a maximum dimension, for example a length 170 from about 4 to 10 inches (from about 100 mm to about 250 mm), for example from about 6 to 8 inches (from about 150 mm to about 200 mm). In some embodiments, length 170 may be no more than about 6 inches (no more than about 150 mm). Adherent device 100 comprises a thickness 172. Thickness 172 may comprise a maximum thickness along a profile of the device. Thickness 172 can be from about 0.2 inches to about 0.4 inches (from about 5 mm to about 10 mm), for example about 0.3 inches (about 7.5 mm).
  • FIG. 1H shown a bottom isometric view of adherent device 100 as in FIGS. 1A to 1G. Adherent device 100 comprises a width 174, for example a maximum width along a width profile of adherent device 100. Width 174 can be from about 2 to about 4 inches (from about 50 mm to 100 mm), for example about 3 inches (about 75 mm).
  • FIGS. 1I and 1J show a side cross-sectional view and an exploded view, respectively, of adherent device 100 as in FIGS. 1A to 1H. Device 100 comprises several layers. Gel 114A, or gel layer, is positioned on electrode 112A to provide electrical conductivity between the electrode and the skin. Electrode 112A may comprise an electrode layer. Adherent patch 110 may comprise a layer of breathable tape 110T, for example a known breathable tape, such as tricot-knit polyester fabric. An adhesive 116A, for example a layer of acrylate pressure sensitive adhesive, can be disposed on underside 110A of adherent patch 110.
  • A gel cover 180, or gel cover layer, for example a polyurethane non-woven tape, can be positioned over patch 110 comprising the breathable tape. A PCB layer, for example flex printed circuit board 120, or flex PCB layer, can be positioned over gel cover 180 with electronic components 130 connected and/or mounted to flex printed circuit board 120, for example mounted on flex PCB so as to comprise an electronics layer disposed on the flex PCB layer. In many embodiments, the adherent device may comprise a segmented inner component, for example the PCB may be segmented to provide at least some flexibility. In many embodiments, the electronics layer may be encapsulated in electronics housing 160 which may comprise a waterproof material, for example silicone or epoxy. In many embodiments, the electrodes are connected to the PCB with a flex connection, for example trace 123A of flex printed circuit board 120, so as to provide strain relive between the electrodes 112A, 112B, 112C and 112D and the PCB.
  • Gel cover 180 can inhibit flow of gel 114A and liquid. In many embodiments, gel cover 180 can inhibit gel 114A from seeping through breathable tape 110T to maintain gel integrity over time. Gel cover 180 can also keep external moisture, for example liquid water, from penetrating though the gel cover into gel 114A while allowing moisture vapor from the gel, for example moisture vapor from the skin, to transmit through the gel cover.
  • In many embodiments, cover 162 can encase the flex PCB and/or electronics and can be adhered to at least one of the electronics, the flex PCB or adherent patch 110, so as to protect at least the electronics components and the PCB. Cover 162 can attach to adherent patch 110 with adhesive 1116B. Cover 162 can comprise many known biocompatible cover materials, for example silicone. Cover 162 can comprise an outer polymer cover to provide smooth contour without limiting flexibility. In many embodiments, cover 162 may comprise a breathable fabric.
  • Cover 162 may comprise many known breathable fabrics, for example breathable fabrics as described above. In some embodiments, the breathable cover may comprise a breathable water resistant cover. In some embodiments, the breathable fabric may comprise polyester, nylon, polyamide, and/or elastane (Spandex™) to allow the breathable fabric to stretch with body movement. In some embodiments, the breathable tape may contain and elute a pharmaceutical agent, such as an antibiotic, anti-inflammatory or antifungal agent, when the adherent device is placed on the patient.
  • The breathable cover 162 and adherent patch 110 comprise breathable tape can be configured to couple continuously for at least one week the at least one electrode to the skin so as to measure breathing of the patient. The breathable tape may comprise the stretchable breathable material with the adhesive and the breathable cover may comprises a stretchable water resistant material connected to the breathable tape, as described above, such that both the adherent patch and cover can stretch with the skin of the patient. Arrows 182 show stretching of adherent patch 110, and the stretching of adherent patch can be at least two dimensional along the surface of the skin of the patient. As noted above, connectors 122A, 122B, 122C and 122D between PCB 130 and electrodes 112A, 112B, 112C and 112D may comprise insulated wires that provide strain relief between the PCB and the electrodes, such that the electrodes can move with the adherent patch as the adherent patch comprising breathable tape stretches. Arrows 184 show stretching of cover 162, and the stretching of the cover can be at least two dimensional along the surface of the skin of the patient. Cover 162 can be attached to adherent patch 110 with adhesive 116B such that cover 162 stretches and/or retracts when adherent patch 110 stretches and/or retracts with the skin of the patient. For example, cover 162 and adherent patch 110 can stretch in two dimensions along length 170 and width 174 with the skin of the patient, and stretching along length 170 can increase spacing between electrodes. Stretching of the cover and adherent patch 110, for example in two dimensions, can extend the time the patch is adhered to the skin as the patch can move with the skin such that the patch remains adhered to the skin. Electronics housing 160 can be smooth and allow breathable cover 162 to slide over electronics housing 160, such that motion and/or stretching of cover 162 is slidably coupled with housing 160. The printed circuit board can be slidably coupled with adherent patch 110 that comprises breathable tape 110T, such that the breathable tape can stretch with the skin of the patient when the breathable tape is adhered to the skin of the patient, for example along two dimensions comprising length 170 and width 174. Electronics components 130 can be affixed to printed circuit board 120, for example with solder, and the electronics housing can be affixed over the PCB and electronics components, for example with dip coating, such that electronics components 130, printed circuit board 120 and electronics housing 160 are coupled together. Electronics components 130, printed circuit board 120, and electronics housing 160 are disposed between the stretchable breathable material of adherent patch 110 and the stretchable water resistant material of cover 160 so as to allow the adherent patch 110 and cover 160 to stretch together while electronics components 130, printed circuit board 120, and electronics housing 160 do not stretch substantially, if at all. This decoupling of electronics housing 160, printed circuit board 120 and electronic components 130 can allow the adherent patch 110 comprising breathable tape to move with the skin of the patient, such that the adherent patch can remain adhered to the skin for an extended time of at least one week, for example two or more weeks.
  • An air gap 169 may extend from adherent patch 110 to the electronics module and/or PCB, so as to provide patient comfort. Air gap 169 allows adherent patch 110 and breathable tape 110T to remain supple and move, for example bend, with the skin of the patient with minimal flexing and/or bending of printed circuit board 120 and electronic components 130, as indicated by arrows 186. Printed circuit board 120 and electronics components 130 that are separated from the breathable tape 110T with air gap 169 can allow the skin to release moisture as water vapor through the breathable tape, gel cover, and breathable cover. This release of moisture from the skin through the air gap can minimize, and even avoid, excess moisture, for example when the patient sweats and/or showers.
  • The breathable tape of adherent patch 110 may comprise a first mesh with a first porosity and gel cover 180 may comprise a breathable tape with a second porosity, in which the second porosity is less than the first porosity to minimize, and even inhibit, flow of the gel through the breathable tape. The gel cover may comprise a polyurethane film with the second porosity.
  • In many embodiments, the adherent device comprises a patch component and at least one electronics module. The patch component may comprise adherent patch 110 comprising the breathable tape with adhesive coating 116A, at least one electrode, for example electrode 114A and gel 114. The at least one electronics module can be separable from the patch component. In many embodiments, the at least one electronics module comprises the flex printed circuit board 120, electronic components 130, electronics housing 160 and cover 162, such that the flex printed circuit board, electronic components, electronics housing and cover are reusable and/or removable for recharging and data transfer, for example as described above. In many embodiments, adhesive 116B is coated on upper side 110A of adherent patch 110B, such that the electronics module can be adhered to and/or separated from the adhesive component. In specific embodiments, the electronic module can be adhered to the patch component with a releasable connection, for example with Velcro™, a known hook and loop connection, and/or snap directly to the electrodes. Two electronics modules can be provided, such that one electronics module can be worn by the patient while the other is charged, as described above. Monitoring with multiple adherent patches for an extended period is described in U.S. patent application No. 60/972,537, the full disclosure of which has been previously incorporated herein by reference. Many patch components can be provided for monitoring over the extended period. For example, about 12 patches can be used to monitor the patient for at least 90 days with at least one electronics module, for example with two reusable electronics modules.
  • At least one electrode 112A can extend through at least one aperture 180A in the breathable tape 110 and gel cover 180.
  • In some embodiments, the adhesive patch may comprise a medicated patch that releases a medicament, such as antibiotic, beta-blocker, ACE inhibitor, diuretic, or steroid to reduce skin irritation. The adhesive patch may comprise a thin, flexible, breathable patch with a polymer grid for stiffening. This grid may be anisotropic, may use electronic components to act as a stiffener, may use electronics-enhanced adhesive elution, and may use an alternating elution of adhesive and steroid.
  • FIG. 1K shows at least one electrode 190 configured to electrically couple to a skin of the patient through a breathable tape 192. In many embodiments, at least one electrode 190 and breathable tape 192 comprise electrodes and materials similar to those described above. Electrode 190 and breathable tape 192 can be incorporated into adherent devices as described above, so as to provide electrical coupling between the skin an electrode through the breathable tape, for example with the gel.
  • FIGS. 2A to 2C show a schematic illustration of a system 200 to monitor a patient for an extended period. FIG. 2A shows a schematic illustration of system 200 comprising a reusable electronics module 210 and a plurality of disposable patch components comprising a first disposable patch component 220A, a second disposable patch component 220B, a third disposable patch component 220C and a fourth disposable patch component 220D. Although four patch components a shown the plurality may comprise as few as two patch component and as many as three or more patch components, for example 25 patch components.
  • FIG. 2B shows a schematic illustration of a side cross-sectional view of reusable electronics module 210. Reusable electronics module 210 may comprises many of the structures described above that may comprise the electronics module. In many embodiments, reusable electronics module 210 comprises a PCB, for example a flex PCB 212, electronics components 216, batteries 216, and a cover 217, for example as described above. In some embodiments, reusable electronics module 210 may comprise an electronics housing over the electronics components and/or PCB as described above. The electronics components may comprise circuitry and/or sensors for measuring ECG signals, hydration impedance signals, respiration impedance signals and accelerometer signals, for example as described above. In many embodiments, reusable electronics module 210 comprises a connector 219 adapted to connect to each of the disposable patch components, sequentially, for example one disposable patch component at a time. Connector 219 can be formed in many ways, and may comprise known connectors as described above, for example a snap. In some embodiments, the connectors on the electronics module and adhesive component can be disposed at several locations on the reusable electronics module and disposable patch component, for example near each electrode, such that each electrode can couple directly to a corresponding location on the flex PCB of the reusable electronics component.
  • Alternatively or in combination with batteries 216, each of the plurality of disposable patch components may comprise a disposable battery. For example first disposable patch component 220A may comprise a disposable battery 214A; second disposable patch component 220B may comprise a disposable battery 214B; third disposable patch component 220C may comprise a disposable battery 214C; and a fourth disposable patch component 220D may comprise a disposable battery 214D. Each of the disposable batteries, 214A, 214B, 214C and 214D may be affixed to each of disposable patches 220A, 220B, 220C and 220D, respectively, such that the batteries are adhered to the disposable patch component before, during and after the respective patch component is adhered to the patient. Each of the disposable batteries, 214A, 214B, 214C and 214D may be coupled to connectors 215A, 215B, 215C and 215D, respectively. Each of connectors 215A, 215B, 215C and 215D can be configured to couple to a connector of the reusable module 220, so as to power the reusable module with the disposable battery coupled thereto. Each of the disposable batteries, 214A, 214B, 214C and 214D may be coupled to connectors 215A, 215B, 215C and 215D, respectively, such that the batteries are not coupled to the electrodes of the respective patch component, so as to minimize, and even avoid, degradation of the electrodes and/or gel during storage when each disposable battery is adhered to each respective disposable patch component.
  • FIG. 2C shows a schematic illustration first disposable patch component 220A of the plurality of disposable patch components that is similar to the other disposable patch components, for example second disposable patch component 220B, third disposable patch component 220C and fourth disposable patch component 220C. The disposable patch component comprises a breathable tape 227A, an adhesive 226A on an underside of breathable tape 227A to adhere to the skin of the patient, and at least four electrodes 222A. The at least four electrodes 224A are configured to couple to the skin of a patient, for example with a gel 226A, in some embodiments the electrodes may extend through the breathable tape to couple directly to the skin of the patient with aid form the gel. In some embodiments, the at least four electrodes may be indirectly coupled to the skin through a gel and/or the breathable tape, for example as described above. A connector 229A on the upper side of the disposable adhesive component can be configured for attachment to connector 219 on reusable electronics module 210 so as to electrically couple the electrodes with the electronics module. The upper side of the disposable patch component may comprise an adhesive 224A to connect the disposable patch component to the reusable electronics module. The reusable electronics module can be adhered to the patch component with many additional known ways to adhere components, for example with Velcro™ comprising hooks and loops, snaps, a snap fit, a lock and key mechanisms, magnets, detents and the like.
  • FIG. 2D shows a method 250 of using system 200, as in FIGS. 2A to 2C. A step 252 adheres electronics module 210 to first disposable adherent patch component 220A of the plurality of adherent patch components and adheres the first disposable patch component to the skin of the patient, for example with the first adherent patch component adhered to the reusable electronics module. A step 254 removes the first disposable adherent patch from the patient and separates first disposable adherent patch component 220A from reusable electronics module 210. A step 256 adheres electronics module 210 to second disposable adherent patch component 220B and adheres the second disposable patch component to the skin of the patient, for example with the second adherent patch component adhered to the reusable electronics module. A step 258 removes the second disposable adherent patch from the patient and separates second disposable adherent patch component 220B from reusable electronics module 210. A step 260 adheres electronics module 210 to third disposable adherent patch component 220C and adheres the third disposable patch component to the skin of the patient, for example with the third adherent patch component adhered to the reusable electronics module. A step 262 removes the third disposable adherent patch from the patient and separates third disposable adherent patch component 220C from reusable electronics module 210. A step 264 adheres electronics module 210 to fourth disposable adherent patch component 220D and adheres the fourth disposable patch component to the skin of the patient, for example with the third adherent patch component adhered to the reusable electronics module. A step 268 removes the fourth disposable adherent patch from the patient and separates fourth disposable adherent patch component 220D from reusable electronics module 210.
  • In many embodiments, physiologic signals, for example ECG, hydration impedance, respiration impedance and accelerometer impedance are measured when the adherent patch component is adhered to the patient, for example when any of the first, second, third or fourth disposable adherent patches is adhered to the patient.
  • FIGS. 3A to 3D show a method 300 of monitoring a patient for an extended period with adherent patches alternatively adhered to a right side 302 and a left side 304 of the patient. Work in relation to embodiments of the present invention suggests that repeated positioning of a patch at the same location can irritate the skin and may cause patient discomfort. This can be avoided by alternating the patch placement between left and right sides of the patient, often a front left and a front right side of the patient where the patient can reach easily to replace the patch. In some embodiments, the patch location can be alternated on the same side of the patient, for example higher and/or lower on the same side of the patient without substantial overlap to allow the skin to recover and/or heal. In many embodiments, the patch can be symmetrically positioned on an opposite side such that signals may be similar to a previous position of the patch symmetrically disposed on an opposite side of the patient. In many embodiments, the duration between removal of one patch and placement of the other patch can be short, such that any differences between the signals may be assumed to be related to placement of the patch, and these differences can be removed with signal processing.
  • In many embodiments each patch comprises at least four electrodes configured to measure an ECG signal and impedance, for example hydration and/or respiration impedance. In many embodiments, the patient comprises a midline 306, with first side, for example right side 302, and second side, for example left side 304, symmetrically disposed about the midline. A step 310 adheres a first adherent patch 312 to at a first location 314 on a first side 302 of the patient for a first period of time, for example about 1 week. While the adherent patch 312 is position at first location 314 on the first side of the patient, the electrodes of the patch are coupled to the skin of the patient to measure the ECG signal and impedance signals.
  • A step 320 removes patch 312 and adheres a second adherent patch 322 at a second location 324 on a second side 206 of the patient for a second period of time, for example about 1 week. In many embodiments, second location 324 can be symmetrically disposed opposite first location 314 across midline 304, for example so as to minimize changes in the sequential impedance signals measured from the second side and first side. While adherent patch 322 is position at second location 324 on the second side of the patient, the electrodes of the patch are coupled to the skin of the patient to measure the ECG signal and impedance signals. In many embodiments, while adherent patch 322 is positioned at second location 324, skin at first location 314 can heal and recover from adherent coverage of the first patch. In many embodiments, second location 324 is symmetrically disposed opposite first location 314 across midline 304, for example so as to minimize changes in the impedance signals measured between the first side and second side. In many embodiments, the duration between removal of one patch and placement of the other patch can be short, such that any differences between the signals may be assumed to be related to placement of the patch, and these differences can be removed with signal processing.
  • A step 330 removes second patch 322 and adheres a third adherent patch 332 at a third location 334 on the first side, for example right side 302, of the patient for a third period of time, for example about 1 week. In many embodiments, third location 334 can be symmetrically disposed opposite second location 324 across midline 304, for example so as to minimize changes in the sequential impedance signals measured from the third side and second side. In many embodiments, third location 334 substantially overlaps with first location 314, so as to minimize differences in measurements between the first adherent patch and third adherent patch that may be due to patch location. While adherent patch 332 is positioned at third location 334 on the first side of the patient, the electrodes of the patch are coupled to the skin of the patient to measure the ECG signal and impedance signals. In many embodiments, while adherent patch 332 is positioned at third location 334, skin at second location 324 can heal and recover from adherent coverage of the second patch. In many embodiments, the duration between removal of one patch and placement of the other patch can be short, such that any differences between the signals may be assumed to be related to placement of the patch, and these differences can be removed with signal processing.
  • A step 340 removes third patch 332 and adheres a fourth adherent patch 342 at a fourth location 344 on the second side, for example left side 306, of the patient for a fourth period of time, for example about 1 week. In many embodiments, fourth location 344 can be symmetrically disposed opposite third location 334 across midline 304, for example so as to minimize changes in the sequential impedance signal measured from the fourth side and third side. In many embodiments, fourth location 344 substantially overlaps with second location 324, so as to minimize differences in measurements between the second adherent patch and fourth adherent patch that may be due to patch location. While adherent patch 342 is positioned at fourth location 344 on the second side of the patient, the electrodes of the patch are coupled to the skin of the patient to measure the ECG signal and impedance signals. In many embodiments, while adherent patch 342 is positioned at fourth location 324, skin at third location 334 can heal and recover from adherent coverage of the third patch. In many embodiments, the duration between removal of one patch and placement of the other patch can be short, such that any differences between the signals may be assumed to be related to placement of the patch, and these differences can be removed with signal processing.
  • It should be appreciated that the specific steps illustrated in FIGS. 3A to 3D provide a particular method of monitoring a patient for an extended period, according to an embodiment of the present invention. Other sequences of steps may also be performed according to alternative embodiments. For example, alternative embodiments of the present invention may perform the steps outlined above in a different order. Moreover, the individual steps illustrated in FIGS. 3A to 3D may include multiple sub-steps that may be performed in various sequences as appropriate to the individual step. Furthermore, additional steps may be added or removed depending on the particular applications. One of ordinary skill in the art would recognize many variations, modifications, and alternatives.
  • FIG. 4A shows a monitoring system 400 comprising an adherent device 410 to measure an impedance signal and an electrocardiogram signal. Device 410 may comprise wireless communication circuitry, accelerometer sensors and/or circuitry and many sensors and electronics components and structures as described above. Adherent device 410 comprises at least four electrodes. In many embodiments, the at least four electrodes comprises four electrodes, for example a first electrode 412A, a second electrode 412B, a third electrode 412C and a fourth electrode 412D. Work in relation to embodiments of the present invention suggests that embodiments in which the at least four electrodes comprises four electrodes can decrease a footprint, or size, of the device on the patient and may provide improved patient comfort. In many embodiments, first electrode 412A and fourth electrode 412D comprise outer electrodes, and second electrode 412B and third electrode 412C comprise inner electrodes, for example in embodiments where the electrodes are arranged in an elongate pattern.
  • Adherent device 410 comprises impedance circuitry 420 that can be used to measure hydration and respiration of the patient, and ECG circuitry 430 that is used to measure an electrocardiogram signal of the patient. Impedance circuitry 420 comprises force circuitry connected to the outer electrodes to drive a current between the electrodes. Impedance circuitry 420 comprises sense circuitry to measure a voltage between the inner electrodes resulting from the current passed between the outer force electrodes, such that the impedance of the tissue can be determined. Impedance circuitry 420 may comprise known 4-pole, or quadrature, low power circuitry. ECG circuitry 430 can be connected to the outer electrodes, or force electrodes, to measure an ECG signal. Work in relation to embodiments of the present invention suggests that this use of the outer electrodes can increase the ECG signal as compared to the inner electrodes, in some embodiments, that may be due to the increased distance between the outer electrodes. ECG circuitry 430 may comprise known ECG circuitry and components, for example low power instrumentation and/or operational amplifiers.
  • In many embodiments, electronic switch 432A and electronic switch 432D are connected in series between impedance circuitry 420 and electrode 412A and 412D, respectively. In many embodiments, electronic switch 432A and electronic switch 432D open such that the outer electrodes can be isolated from the impedance circuitry when the ECG circuitry measures ECG signals. When electronic switch 432A and electronic switch 432D are closed, impedance circuitry 420 can force electrical current through the outer electrodes to measure impedance. In many embodiments, electronic switch 432A and electronic switch 432D can be located in the same packaging, and may comprise CMOS, precision, analog switches with low power consumption, low leakage currents, and fast switching speeds.
  • A processor 440 can be connected to electronic switch 423A, electronic switch 432D, impedance circuitry 420 and ECG circuitry 430 to control measurement of the ECG and impedance signals. Processor 430 comprises a tangible medium, for example read only memory (ROM), electrically erasable programmable read only memory (EEPROM) and/or random access memory (RAM). In many embodiments, processor 440 controls the measurements such that the measurements from impedance circuitry 420 and ECG circuitry 430 are time division multiplexed in response to control signals from processor 440.
  • FIG. 4B shows a method 450 of measuring the impedance signal and the electrocardiogram signal with processor 440. A step 452 closes the switches. A step 454 drives the force electrodes. A step 456 measures the impedance signal with the inner electrodes. A step 458 determines the impedance, hydration and/or respiration from the impedance signal. A step 460 opens the switches. A step 462 measures the ECG signal with the outer electrodes. A step 464 stores the data from the impedance signals and ECG signals. A step 466 processes the data. A step 468 transmits the data, for example wirelessly to the remove center. A step 470 repeats the above steps.
  • It should be appreciated that the specific steps illustrated in FIG. 4B provide a particular method of measuring signals, according to an embodiment of the present invention. Other sequences of steps may also be performed according to alternative embodiments. For example, alternative embodiments of the present invention may perform the steps outlined above in a different order. Moreover, the individual steps illustrated in FIG. 4B may include multiple sub-steps that may be performed in various sequences as appropriate to the individual step. Furthermore, additional steps may be added or removed depending on the particular applications. One of ordinary skill in the art would recognize many variations, modifications, and alternatives.
  • FIG. 5A shows a method 500 for monitoring a patient and responding to a signal event. A step 501 activates a processor system. A step 503 calculates a risk of sudden cardiac death. A step 506 reports to a remote center and/or physician. A step 509 combines at least two of the electrocardiogram signal, respiration signal, and/or activity signals. A step 512 detects an adverse cardiac event. An adverse cardiac event may comprise an atrial fibrillation in response to the electrocardiogram signal and/or an acute myocardial infarction in response to an ST segment elevation of the electrocardiogram signal. A step 515 triggers an alarm. A step 518 continuously monitors and stores in tangible media at least two of the electrocardiogram signal, the respiration signal, or the activity signal. In some embodiments, a step may also comprise monitoring a high risk patent post myocardial infarction with the at least two of the electrocardiogram signal, the respiration signal or the activity signal, and/or a bradycardia of the patient at risk for sudden death. The electrocardiogram signal may comprise at least one of a Brugada Syndrome with an ST elevation and a short QT interval or long-QT interval. A step 521 loop records the aforementioned data. A step 524 determines a tiered response. In many embodiments, the tiered response may comprise tiers, or levels, appropriate to the detected status of the patient. A step 527 comprises a first tier response which alerts an emergency responder. A step 530 comprises a second tier response which alerts a physician. A step 533 comprises a third tier response which alerts a patient, family, or caregiver. A step 537 comprises a fourth tier response which alerts a remote center. A tiered response may also comprise of wirelessly transmitting the at least two of the electro cardiogram signal, the respiration signal, or the activity signal with a single wireless hop from a wireless communication circuitry to an intermediate device.
  • The signals can be combined in many ways. In some embodiments, the signals can be used simultaneously to determine the impending cardiac decompensation.
  • In some embodiments, the signals can be combined by using the at least two of the electrocardiogram signal, the respiration signal or the activity signal to look up a value in a previously existing array.
  • TABLE 1
    Lookup Table for ECG and Respiration Signals.
    Heart Rate
    Respiration A-B bpm C-D bpm E-F bpm
    U-V per min N N Y
    W-X per min N Y Y
    Y-Z per min Y Y Y
  • Table 1 shows combination of the electrocardiogram signal with the respiration signal to look up a value in a pre-existing array. For example, at a heart rate in the range from A to B bpm and a respiration rate in the range from U to V per minute triggers a response of N. In some embodiments, the values in the table may comprise a tier or level of the response, for example four tiers. In specific embodiments, the values of the look up table can be determined in response to empirical data measured for a patient population of at least about 100 patients, for example measurements on about 1000 to 10,000 patients. The look up table shown in Table 1 illustrates the use of a look up table according to one embodiment, and one will recognize that many variables can be combined with a look up table.
  • In some embodiments, the table may comprise a three or more dimensional look up table, and the look up table may comprises a tier, or level, of the response, for example an alarm.
  • In some embodiments, the signals may be combined with at least one of adding, subtracting, multiplying, scaling or dividing the at least two of the electrocardiogram signal, the respiration signal or the activity signal. In specific embodiments, the measurement signals can be combined with positive and or negative coefficients determined in response to empirical data measured for a patient population of at least about 100 patients, for example data on about 1000 to 10,000 patients.
  • In some embodiments, a weighted combination may combine at least two measurement signals to generate an output value according to a formula of the general form

  • OUTPUT=aX+bY
  • where a and b comprise positive or negative coefficients determined from empirical data and X, and Z comprise measured signals for the patient, for example at least two of the electrocardiogram signal, the respiration signal or the activity signal. While two coefficients and two variables are shown, the data may be combined with multiplication and/or division. One or more of the variables may be the inverse of a measured variable. In some embodiments, the ECG signal comprises a heart rate signal that can be divided by the activity signal. Work in relation to embodiments of the present invention suggest that an increase in heart rate with a decrease in activity can indicate an impending decompensation. The signals can be combined to generate an output value with an equation of the general form

  • OUTPUT=aX Y+bZ
  • where X comprise a heart rate signal, Y comprises an activity signal and Z comprises a respiration signal, with each of the coefficients determined in response to empirical data as described above.
  • In some embodiments, the data may be combined with a tiered combination. While many tiered combinations can be used a tiered combination with three measurement signals can be expressed as

  • OUTPUT=(ΔX)+(ΔY)+(ΔZ)
  • where (ΔX), (ΔY), (ΔZ) may comprise change in heart rate signal from baseline, change in respiration signal from baseline and change in activity signal from baseline, and each may have a value of zero or one, based on the values of the signals. For example if the heart rate increase by 10%, (ΔX) can be assigned a value of 1. If respiration increases by 5%, (ΔY) can be assigned a value of 1. If activity decreases below 10% of a baseline value (ΔZ) can be assigned a value of 1. When the output signal is three, a flag may be set to trigger an alarm.
  • In some embodiments, the data may be combined with a logic gated combination. While many logic gated combinations can be used, a logic gated combination with three measurement signals can be expressed as

  • OUTPUT=(ΔX) AND (ΔY) AND (ΔZ)
  • where (ΔX), (ΔY), (ΔZ) may comprise change in heart rate signal from baseline, change in respiration signal from baseline and change in activity signal from baseline, and each may have a value of zero or one, based on the values of the signals. For example if the heart rate increase by 10%, (ΔX) can be assigned a value of 1. If respiration increases by 5%, (ΔY) can be assigned a value of 1. If activity decreases below 10% of a baseline value (ΔZ) can be assigned a value of 1. When each of (ΔX), (ΔY), (ΔZ) is one, the output signal is one, and a flag may be set to trigger an alarm. If any one of (ΔX), (ΔY) or (ΔZ) is zero, the output signal is zero and a flag may be set so as not to trigger an alarm. While a specific example with AND gates has been shown the data can be combined in may ways with known gates for example NAND, NOR, OR, NOT, XOR, XNOR gates. In some embodiments, the gated logic may be embodied in a truth table.
  • The processor system, as described above, performs the methods 500, including many of the steps described above. It should be appreciated that the specific steps illustrated in FIG. 5A provide a particular method of monitoring a patient and responding to a signal event, according to an embodiment of the present invention. Other sequences of steps may also be performed according to alternative embodiments. For example, alternative embodiments of the present invention may perform the steps outlined above in a different order. Moreover, the individual steps illustrated in FIG. 5A may include multiple sub-steps that may be performed in various sequences as appropriate to the individual step. Furthermore, additional steps may be added or removed depending on the particular applications. One of ordinary skill in the art would recognize many variations, modifications, and alternatives.
  • Experimental Clinical Study
  • The protocol below has been used to measure signals from actual patients with an adherent device. These data show that an adherent patch as described above can be continuously adhered for at least one week. These data also show that 90 day continuous in home monitoring can be achieved with a set of 13 patches in which one of the patches is replaced each week. The clinical testing device used an adherent device with modifications, as described more fully below and referred to as the MS system (multi-sensor). Although the clinical device did not include wireless circuitry and processor circuitry supported with the patch adhered to the skin of the patient, these data do show that such a device, as described above, can be made by one of ordinary skill in the art based on the teachings described herein. Additional empirical studies can be conducted on a suitable number of patients.
  • MS Clinical System Description
  • The MS clinical system includes many of the structure components described above. There is a flexible connection between the electrodes and the flex PCB, for example wires or polyurethane with silver ink. The cover can stretch with the breathable tape on both the clinical device and the above described wireless device. There is generally a gap between the flex PCB and breathable tape in both clinical and above described wireless devices. The tested device used weights to at least partially simulate the weight of wireless and processor circuitry. The adherent device of the MS clinical system comprises four electrodes to measure bioimpedance and ECG signals and a 3-axis accelerometer, as described above. Bioimpedance signals were used to determine patient respiration and patient hydration, and accelerometer signals were used to determine patient activity and posture. The MS clinical adherent patch device comprising the sensors and at least some sensor circuitry were connected to a processor to record data. The processor was connected to the tested adherent device with wires and supported away from the tested adherent patch device, for example around the patient's waist. Data were collected at regular intervals and uploaded to a remote site, as described above.
  • Clinical testing of the MS clinical system shows the effectiveness of the structures for continuous adherence of at least one week and data collection, and that patches can be successively removed and replaced by the patient for in-home monitoring. This effectiveness has been shown without requiring fully functional electronics circuitry such as a battery, wireless circuitry and process circuitry on the adherent device. For example, the MS system includes an insert with about 20 g of additional weight. Although an insert with a 20 gram weight was used for the MS clinical device, greater amounts of weight and circuitry can be used, for example about 30-50 g. The patch device may be modified to accommodate additional weight, for example by increasing the size of the adherent surface. The shape of the MS clinical patch is generally elongate, similar to the elongate shape shown above.
  • Study Design and Rationale
  • The MS System is used in a clinical study of heart failure patients to gather data that can be used to develop an algorithm for diagnosing and predicting impending heart failure decompensation events. Events typically manifest as heart failure-related hospitalization, emergency room or urgent care visits leading to a change in oral or IV diuretic treatment.
  • The purpose of the clinical study is to correlate physiological signals recorded by the system to clinical events of acute heart failure decompensation (AHFD). Signals from the patch can be weighted and combined to determine an index that associates physiologic parameters to impending events of decompensation. Patients who have been classified as New York Heart Association class III and IV within the last 12 months and have had a recent AHFD event can be enrolled into the study and are monitored with the MS system for approximately 90 days.
  • AHFD events are defined as any of the following:
  • 1) Any heart failure related ER, Urgent Care, in-office visit or hospitalization requiring administration of IV diuretics, administration of IV inotropes, or ultrafiltration for fluid removal.
  • 2) A change in diuretic, defined as a change in diuretic directed by the health care provider occurring inside a hospital, emergency room, or urgent care setting (i.e. no patient self-directed changes to medications not approved by a health care provider would be included), that satisfies one or more of the following: a) a change in the type of diuretic the patient is taking, b) a dose increase of an existing diuretic, or c) the addition of another diuretic.
  • 3) A heart failure decompensation event for which death is the outcome.
  • Patients enrolled in the study were asked to replace the patch weekly. The study can enroll at least about 550 patients. The patient was provided with a kit comprising 13 patches for replacement. The patches were placed on alternating left and right sides of the patient's thorax, as described above, to minimize progressive irritation.
  • The data collected in the study can be used to develop an algorithm to at least one of detect, diagnose or predict an impending cardiac decompensation. The algorithm can be implemented on a processor system as described above. Known methods can be used to analyze the data, for example splitting the patients into two groups, one to develop parameters for the algorithm and a second group to test the algorithm developed with the first group. In many embodiments, the signal of the algorithm may comprise a simple binary output for impending cardiac decompensation of the patient. The logic output, yes or no, can be determined in response to patient data combined as described above. The logic output may comprise a signal, such as a binary Y or N signal.
  • The developed algorithm can be evaluated with composite sensitivity and false positive patient signal status rates. The sensitivity may be defined as the percent of true positive events out of all condition present events, and the false positive patient status signal status rate can be defined as the number of false positive patient status signals per patient-years of follow up. For example, the sensitivity can be at least 50%, for example at least 60%, at least 70%, or even at least 80%. The false positive patient signal status rate may be limited to no more than about 1.1 false positive patient status signals per patient year, for example no more than about 1.0 false positive patient status signals per patient year, no more than about 0.9 false positive patient status signals per patient year, and even no more than about 0.8 false positive patient status signals per patient year.
  • Clinical Results
  • Clinical data are available for the first 180 patients enrolled in the study.
  • FIGS. 6A and 6B show clinical data measured with an adherent patch device, in accordance with the above protocol. FIG. 6A shows data from a patient with the MS patch adhered to a first patient, and the data was acquired over the 90 day period with the series of 13 patches. The signals measured included Heart Rate (beats per minute), Heart Rate Variability (ms), Respiratory Rate (breaths per minute), Activity (m-G's) and Body Fluid (Ohms). FIG. 6B shows data from a second patient similar to FIG. 6A.
  • Of the 180 patients who have completed the study with the MS adherent patch, as described above, all patches in all patients adhered continuously without patch failure. In all patients, the first patch adhered continuously for the first week. With the exception of a handful of patient deaths and early withdrawals that were unrelated to device failure, all patients reached the end of 90-day follow-up period having used 13 weekly patches without incident. None of the 180 patients showed skin irritation or damage that required withdrawal from the study.
  • The above data show that the wireless adherent patch device can be constructed for in home wireless patient monitoring for an extended period of at least 90 day, in which each patch of a set is continuously adhered to a patient for at least one week and each patch is configured to support the measurement circuitry, the processor, the wireless communication circuitry and the battery with the skin of the patient.
  • While the exemplary embodiments have been described in some detail, by way of example and for clarity of understanding, those of skill in the art will recognize that a variety of modifications, adaptations, and changes may be employed. Hence, the scope of the present invention should be limited solely by the appended claims.

Claims (90)

  1. 1. An adherent device to monitor a patient, the device comprising:
    an adhesive patch to adhere to a skin of the patient;
    at least four electrodes connected to the patch and capable of electrically coupling to the patient;
    impedance circuitry coupled to the at least four electrodes to measure a hydration signal of the patient;
    electrocardiogram circuitry coupled to at least two of the at least four electrodes to measure an electrocardiogram signal of the patient; and
    an accelerometer mechanically coupled to the adhesive patch to generate an accelerometer signal in response to at least one of an activity or a position of the patient.
  2. 2. The adherent device of claim 1 wherein the adhesive patch is mechanically coupled to the at least four electrodes, the impedance circuitry, the electrocardiogram circuitry and the accelerometer, such that the patch is capable of supporting the at least four electrodes, the impedance circuitry, the electrocardiogram circuitry and the accelerometer when the adherent patch is adhered to the skin of the patient.
  3. 3. The adherent device of claim 1 further comprising a wireless communication circuitry coupled to the impedance circuitry, the electrocardiogram circuitry and the accelerometer to transmit to a remote center with a communication protocol at least one of the hydration signal, the electrocardiogram signal or the accelerometer signal.
  4. 4. The adherent device of claim 3 wherein wireless communication circuitry is configured to transmit the hydration signal, the electrocardiogram signal and the accelerometer signal to the remote center with a single wireless hop from the wireless communication circuitry to an intermediate device.
  5. 5. The adherent device of claim 4 wherein the communication protocol comprises at least one of Bluetooth, Zigbee, WiFi, WiMax, IR, a cellular protocol, amplitude modulation or frequency modulation.
  6. 6. The adherent device of claim 4 wherein the intermediate device comprises a data collection system to collect and/or store data from the wireless transmitter and wherein the data collection system is configured to communicate periodically with the remote center with wireless connection and/or wired communication.
  7. 7. The adherent device of claim 4 wherein the communications protocol comprises a two way protocol such that the remote center is capable of issuing commands to control data collection.
  8. 8. The adherent device of claim 1 wherein the accelerometer comprises at least one of a piezoelectric accelerometer, capacitive accelerometer or electromechanical accelerometer and wherein the accelerometer comprises a 3-axis accelerometer to measure at least one of an inclination, a position, an orientation or acceleration of the patient in three dimensions.
  9. 9. The adherent device of claim 1 wherein the impedance circuitry is adapted to measure extra cellular fluid of the patient with at least one frequency within a range from about 0.5 kHz to about 200 kHz. and wherein the impedance circuitry is configured to determine a respiration of the patient.
  10. 10. The adherent device of claim 1 wherein the device comprises a microphone to detect an audio signal from within the patient, the audio signal comprising a heart sound with an S3 heart sound and/or a respiratory sound with rales and/or crackles.
  11. 11. The adherent device of claim 1 wherein the device comprises a temperature sensor to measure a temperature of the patient.
  12. 12. The adherent device of claim 1 wherein the device comprises a heat flux sensor to measure a skin heat flow of the patient.
  13. 13. The adherent device of claim 1 comprising a processor comprising a tangible medium, the processor configured to control a collection and transmission of data from the impedance circuitry, the electrocardiogram circuitry and the accelerometer.
  14. 14. The adherent device of claim 1 comprising a real time clock and a frequency generator.
  15. 15. A method of monitoring a patient, the method comprising:
    adhering an adhesive patch to a skin of the patient to couple at least four electrodes to the skin of the patient;
    measuring a hydration signal of the patient with impedance circuitry coupled to the at least four electrodes;
    measuring an electrocardiogram signal of the patient with electrocardiogram circuitry coupled to at least two of the at least four electrodes; and
    measuring a signal from an accelerometer in response to at least one of an activity or a position of the patient.
  16. 16. The method of claim 15 wherein the adhesive patch supports the at least four electrodes, the impedance circuitry, the electrocardiogram circuitry and the accelerometer when the adherent patch is adhered to the skin of the patient.
  17. 17. An adherent device to monitor a patient, the device comprising:
    an adhesive patch to adhere to a skin of the patient;
    at least four electrodes affixed to the patch and capable of electrically coupling to the patient, a maximum dimension across the at least 4 electrodes comprising no more that about eight inches, such that the at least four electrodes are capable of adhering to either a left side or a right side of the patient;
    impedance circuitry coupled to the at least four electrodes to measure hydration of the patient; and
    electrocardiogram circuitry coupled to at least two of the at least four electrodes to measure an electrocardiogram of the patient.
  18. 18. The adherent device of claim 17 wherein the maximum distance across the at least four electrodes comprises no more than about six inches.
  19. 19. The adherent device of claim 17 wherein the device comprises a maximum dimension across no more than about 8 inches and wherein the patch is capable of measuring the electrocardiogram and the impedance from a left side or a right side of the patient.
  20. 20. An adherent device to monitor a patient for an extended period, the device comprising:
    a breathable tape comprising a porous material with an adhesive coating to adhere the breathable tape to a skin of the patient;
    at least one electrode affixed to the breathable tape and capable of electrically coupling to a skin of the patient;
    at least one gel disposed over a contact surface of the at least one electrode to electrically connect the electrode to the skin;
    a circuit board connected to the breathable tape to support the printed circuit board with the breathable tape when the tape is adhered to the patient;
    electronic components electrically connected to the printed circuit board and coupled to the at least one electrode to measure physiologic signals of the patient; and
    a breathable water resistant cover disposed over the circuit board and electronic components and connected to at least one of the electronics components, the printed circuit board or the breathable tape.
  21. 21. The adherent device of claim 20 further comprising an electronics housing adhered to at least one of the electronics components or the printed circuit board, such that the electronics housing is disposed between the cover and electronics components.
  22. 22. The adherent device of claim 20 further comprising a gel cover positioned over the breathable tape to inhibit a flow of the gel through the breathable tape and wherein the printed circuit board is located over the gel cover such that the gel cover is disposed between the breathable tape and the printed circuit board.
  23. 23. The adherent device of claim 20 wherein the breathable tape comprises a tricot-knit polyester fabric backing and the gel cover comprises a polyurethane, non-woven backing.
  24. 24. The adherent device of claim 20 wherein the breathable tape comprises a first porosity and wherein the gel cover comprises a breathable tape with a second porosity, the second porosity less than the first porosity to inhibit flow of the gel through the breathable tape having the first porosity.
  25. 25. The adherent device of claim 20 wherein breathable tape, the adhesive coating, the at least one electrode and gel are separable from the printed circuit board, electronic components and cover, such that the printed circuit board, electronic components, housing and cover are reusable.
  26. 26. The adherent device of claim 20 wherein the at least one electrode extends through at least one aperture in the breathable tape.
  27. 27. The adherent device of claim 20 wherein the at least one electrode is configured to electrically couple to the printed circuit board through the breathable tape.
  28. 28. A method of monitoring a patient for an extended period, the method comprising:
    attaching an electronics module to a first adherent patch component of a plurality of adherent patch components;
    adhering the first adherent patch component to a skin of the patient;
    removing the electronics module from the first adherent patch component; and
    attaching the electronics module to a second patch component of the plurality of patch components after the first adherent patch component has been removed.
  29. 29. The method of claim 28 further comprising:
    removing the electronics module from the second adherent patch component; and
    attaching the electronics module to a third patch component of the plurality of patch components after the second adherent patch component has been removed.
  30. 30. The method of claim 29 further comprising measuring impedance signals when the third adherent patch component is adhered to the patient.
  31. 31. A system to monitor a patient for an extended period, the system comprising:
    a plurality of adherent patch components; and
    an electronics module adapted to couple to each of the plurality of patch components for sequential measurements from each of the patch components.
  32. 32. The system of claim 31 wherein each of the plurality of adherent patch components comprises a breathable tape with an adhesive coating to adhere the breathable tape to a skin of the patient, and at least one electrode affixed to the breathable tape.
  33. 33. The system of claim 31 wherein the electronics module comprises a printed circuit board configured to connect electrically to the at least one electrode to measure physiologic signals of the patient, electronic components electrically connected to the printed circuit board, and a housing adhered to at least one of the electronics module or the printed circuit board.
  34. 34. A method of monitoring a patient for an extended period of time, the method comprising:
    placing a first adherent patch on a first side of the patient, the first adherent patch comprising first electrodes to measure at least one of an electrocardiogram or an impedance;
    measuring the at least one of the electrocardiogram or the impedance from the first side of the patient for a first period of time;
    removing the first patch from the first side of the patient;
    placing a second adherent patch on a second side of the patient, the second patch comprising second electrodes to measure the at least one of the electrocardiogram or the impedance; and
    measuring the at least one of the electrocardiogram or the impedance from the second side of the patient for a second period of time after the first patch has been removed.
  35. 35. The method of claim 34 wherein the first side comprises at least one of a left side or a right side of the patient and the second side is opposite the first side.
  36. 36. The method of claim 34 further comprising:
    removing the second patch from the second side of the patient;
    placing a third adherent patch on the first side of the patient, the third patch comprising third electrodes to measure the at least one of the electrocardiogram or the impedance; and
    measuring the at least one of the electrocardiogram or the impedance from the first side of the patient for a third period of time after the second patch has been removed.
  37. 37. The method of claim 36 further comprising:
    removing the third patch from the first side of the patient;
    placing a fourth adherent patch on the second side of the patient, the fourth patch comprising fourth electrodes to measure the at least one of the electrocardiogram or the impedance; and
    measuring the at least one of the electrocardiogram or the impedance from the second side of the patient for a fourth period of time after the third patch has been removed.
  38. 38. The method of claim 37 wherein each of the first period of time, the second period of time, the third period of time and the fourth period of time comprises at least about 1 week.
  39. 39. A method of monitoring a patient for an extended period of time, the method comprising:
    placing a first adherent patch on a skin location on a first side of the patient, the first adherent patch comprising first electrodes to measure at least one of an electrocardiogram or an impedance;
    measuring the at least one of the electrocardiogram or the impedance from the first adherent patch on the first skin location for a first period of time;
    removing the first patch from the first skin location;
    placing a second adherent patch on a second skin location on a second side of the patient, the second patch comprising second electrodes to measure the at least one of the electrocardiogram or the impedance; and
    measuring the at least one of the electrocardiogram or the impedance from the second skin location for a second period of time after the first patch has been removed.
  40. 40. The method of claim 39 wherein the first skin location heals during the second period of time.
  41. 41. An adherent device to monitor a patient, the device comprising:
    an adhesive patch to adhere to a skin of the patient;
    at least four electrodes mechanically coupled to the patch and capable of electrically coupling to the patient, the at least four electrodes comprising at least two force electrodes and at least two sense electrodes;
    impedance circuitry electrically coupled to the at least two force electrodes to force an electrical current and coupled to the at least two sense electrodes to measure a hydration signal of the patient; and
    electrocardiogram circuitry coupled to the at least two force electrodes to measure an electrocardiogram signal of the patient.
  42. 42. The adherent device of claim 41 further comprising electrical switches connected to the at least two force electrodes to isolate the at least two force electrodes from the impedance circuitry when the electrocardiogram circuitry measures the electrocardiogram.
  43. 43. The adherent device of claim 41 further comprising a processor configured to control the impedance circuitry and the electrocardiogram circuitry so as to time division multiplex collection the hydration signal and the electrocardiogram signal.
  44. 44. The adherent device of claim 43 wherein the processor is configured to decouple the at least two force electrodes from the impedance circuitry when the electrocardiogram circuitry measures the electrocardiogram signal.
  45. 45. The adherent device of claim 41 wherein the at least four electrodes comprise no more than four electrodes.
  46. 46. The adherent device of claim 41 wherein the at least two force electrodes comprise outer electrodes and the at least two sense electrodes comprise inner electrodes.
  47. 47. The adherent device of claim 41 wherein the at least two force electrodes comprise inner electrodes and the at least two sense electrodes comprise outer electrodes.
  48. 48. A method of monitoring a patient, the method comprising:
    adhering an adhesive patch to a skin of the patient so as to couple at least four electrodes to the skin of the patient, the at least four electrodes comprising at least two force electrodes and at least two sense electrodes;
    measuring a hydration signal of the patient with impedance circuitry electrically coupled to the at least two force electrodes and to the at least two sense electrodes, such that the force electrodes force an electrical current between the at least two force electrodes; and
    measuring an electrocardiogram signal of the patient with electrocardiogram circuitry coupled to the at least two force electrodes.
  49. 49. The method of claim 48 wherein electrical switches connected to the at least two force electrodes are opened to isolate the at least two force electrodes from the impedance circuitry when the electrocardiogram circuitry measures the electrocardiogram.
  50. 50. The method of claim 48 wherein the hydration signal and the electrocardiogram signal are time division multiplexed.
  51. 51. An adherent device to monitor a patient, the device comprising:
    an adhesive patch to adhere to a skin of the patient;
    at least two electrodes connected to the patch and capable of electrically coupling to the patient;
    circuitry coupled to the at least two electrodes and configured to measure at least two of an electrocardiogram signal of the patient, a respiration signal of the patient or an activity signal of the patient; and
    a processor system comprising a tangible medium configured to trigger an alarm in response to the at least two of the electrocardiogram signal, the respiration signal or the activity signal.
  52. 52. The adherent device of claim 51 wherein the processor system comprises a first processor comprising a tangible medium attached to the adherent patch and a second processor comprising a tangible medium at a remote center.
  53. 53. The adherent device of claim 51 wherein the processor system comprises of a configuration for combining the at least two of the electrocardiogram signal, the respiration signal or the activity signal.
  54. 54. The adherent device of claim 53 wherein combining comprises the processor system using the at least two of the electrocardiogram signal, the hydration signal, the respiration signal or the activity signal to look up a value in a previously existing array.
  55. 55. The adherent device of claim 53 wherein combining comprises at least one of adding, subtracting, multiplying, scaling, or dividing the at least two of the electrocardiogram signal, the respiration signal, or the activity signal.
  56. 56. The adherent device of claim 53 wherein the at least two of the electrocardiogram signal, the accelerometer signal, or the respiration signal are combined with at least one of a weighted combination, a tiered combination or a logic gated combination, a time weighted combination or a rate of change.
  57. 57. The adherent device of claim 51 wherein the processor system is configured to continuously monitor, store and transmit to a remote center the at least two of the electrocardiogram signal, the respiration signal or the activity signal when the alarm is triggered.
  58. 58. The adherent device of claim 51 wherein the processor system is configured to trigger the alarm and alert the patient and/or the physician in response to an adverse cardiac event.
  59. 59. The adherent device of claim 51 wherein the processor system is configured to calculate and report a patient risk of sudden cardiac death to at least one of a remote center or a physician.
  60. 60. The adherent device of claim 51 wherein the processor system is configured to detect at least one of a T-wave alternans, a pulsus alternans, an autonomic imbalance, a heart rate variability in response to the at least two of the electrocardiogram signal, the respiration signal or the activity signal.
  61. 61. The adherent device of claim 51 wherein the processor system is configured to loop record the at least two of the electrocardiogram signal, the respiration signal or the activity signal for diagnosis of an unexplained syncope and/or arrhythmia when the alarm is triggered.
  62. 62. The adherent device of claim 51 wherein the processor system is configured to detect an event comprising at least one of an atrial fibrillation in response to the electrocardiogram signal or an acute myocardial infarction in response to an ST segment elevation of the electrocardiogram signal.
  63. 63. The adherent device of claim 51 wherein the processor system is configured to monitor a high risk patent post myocardial infarction with the at least two of the electrocardiogram signal, the respiration signal or the activity signal.
  64. 64. The adherent device of claim 51 wherein the processor system is configured to continuously monitor a bradycardia of the patient at risk for sudden death, the electrocardiogram signal comprising at least one of a Brugada Syndrome with an ST elevation and a short QT interval or long-QT interval.
  65. 65. The adherent device of claim 51 wherein the processor system is configured to monitor the electrocardiogram signal and alert at least one of a patient, a remote center, a physician, emergency responder, or family/caregiver in response to an adverse event.
  66. 66. The adherent device of claim 51 wherein the processor system is configured to determine a tiered response to the at least two of the electrocardiogram signal, the respiration signal or the activity signal.
  67. 67. The adherent device of claim 66 wherein the tiered response comprises a first tier to contact an emergency responder in response to an immediate life threatening event, a second tier to contact a physician in response to an event that requires medical care, a third tier to contact a family member and/or care giver, and a fourth tier to contact the center.
  68. 68. The adherent device of claim 66 wherein immediate life threatening event comprises at least one of a sustained ventricular tachycardia, a sustained ventricular fibrillation, an asystole, an arrhythmia with no respiration or an arrhythmia with no patient movement.
  69. 69. The adherent device of claim 66 wherein the event that requires medical care comprises an atrial fibrillation that is not immediately life threatening.
  70. 70. The adherent device of claim 67 wherein wireless communication circuitry is configured to transmit the at least two of the electrocardiogram signal, the respiration signal or the activity signal with a single wireless hop from the wireless communication circuitry to an intermediate device.
  71. 71. A method of monitoring a patient, the method comprising:
    adhering an adhesive patch to a skin of the patient so as to couple at least two electrodes to the skin of the patient;
    measuring at least two of an electrocardiogram signal of the patient, a respiration signal of the patient or an activity signal of the patient with circuitry coupled to the at least two electrodes; and
    triggering an alarm in response to the at least two of the electrocardiogram signal, the respiration signal or the activity signal with a processor system comprising a tangible medium.
  72. 72. The method of claim 71 wherein the processor system comprises a first processor comprising a tangible medium attached to the adherent patch and a second processor comprising a tangible medium at a remote center.
  73. 73. The method of claim 71 comprising combining at least two of the electrocardiogram signal, the respiration signal, or the activity signal.
  74. 74. The method of claim 73 wherein combining comprises the processor system using the at least two of the electrocardiogram signal, the hydration signal, the respiration signal or the activity signal to look up a value in a previously existing array.
  75. 75. The method of claim 73 wherein combining comprises at least one of adding, subtracting, multiplying, scaling, or dividing the at least two of the electrocardiogram signal, the respiration signal, or the activity signal.
  76. 76. The method of claim 73 wherein the at least two of the electrocardiogram signal, the accelerometer signal, or the respiration signal are combined with at least one of a weighted combination, a tiered combination or a logic gated combination, a time weighted combination or a rate of change.
  77. 77. The method of claim 71 wherein the at least two of the electrocardiogram signal, the respiration signal, or the activity signal are continuously monitored, stored, and/or transmitted to a remote center.
  78. 78. The method of claim 71 wherein the alarm is triggered and the patient and/or the physician is alerted in response to an adverse cardiac event.
  79. 79. The method of claim 71 wherein a patient risk of sudden cardiac death is calculated and/or reported to at least one of a remote center or a physician.
  80. 80. The method of claim 71 wherein at least one of a T-wave alternans, a pulsus alternans, an autonomic imbalance, a heart rate variability in response to the at least two of the electrocardiogram signal, the respiration signal or the activity signal is detected.
  81. 81. The method of claim 71 wherein the at least two of the electrocardiogram signal, the respiration signal or the activity signal is loop recorded when the alarm is triggered.
  82. 82. The method of claim 71 wherein an event comprising at least one of an atrial fibrillation in response to the electrocardiogram signal or an acute myocardial infarction in response to an ST segment elevation of the electrocardiogram signal is detected.
  83. 83. The method of claim 71 wherein a high risk patent post myocardial infarction is monitored with the at least two of the electrocardiogram signal, the respiration signal or the activity signal.
  84. 84. The method of claim 71 wherein a bradycardia of the patient at risk for sudden death, the electrocardiogram signal comprising at least one of a Brugada Syndrome with an ST elevation and a short QT interval or long-QT interval are continuously monitored.
  85. 85. The method of claim 71 wherein the electrocardiogram signal is monitored and/or at least one of a patient, a remote center, a physician, emergency responder, or family/caregiver is alerted in response to an adverse event.
  86. 86. The method of claim 71 wherein a tiered response to the at least two of the electrocardiogram signal, the respiration signal or the activity signal is determined.
  87. 87. The method of claim 86 wherein the tiered response comprises a first tier to contact an emergency responder in response to an immediate life threatening event, a second tier to contact a physician in response to an event that requires medical care, a third tier to contact a family member and/or care giver, and a fourth tier to contact the center.
  88. 88. The method of claim 86 wherein immediate life threatening event comprises at least one of a sustained ventricular tachycardia, a sustained ventricular fibrillation, an asystole, an arrhythmia with no respiration or an arrhythmia with no patient movement.
  89. 89. The method of claim 86 wherein the event that requires medical care comprises an atrial fibrillation that is not immediately life threatening.
  90. 90. The method of claim 87 wherein wireless communication circuitry transmits the at least two of the electrocardiogram signal, the respiration signal or the activity signal with a single wireless hop from the wireless communication circuitry to an intermediate device.
US12209288 2007-09-14 2008-09-12 Adherent Device with Multiple Physiological Sensors Abandoned US20090076345A1 (en)

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US12209288 US20090076345A1 (en) 2007-09-14 2008-09-12 Adherent Device with Multiple Physiological Sensors

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US13598238 US8795174B2 (en) 2007-09-14 2012-08-29 Adherent device with multiple physiological sensors
US14322676 US20140330136A1 (en) 2007-09-14 2014-07-02 Adherent device with multiple physiological sensors

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US13347238 Active US8285356B2 (en) 2007-09-14 2012-01-10 Adherent device with multiple physiological sensors
US13598238 Active US8795174B2 (en) 2007-09-14 2012-08-29 Adherent device with multiple physiological sensors
US13647284 Active US8818481B2 (en) 2007-09-14 2012-10-08 Adherent device with multiple physiological sensors
US14322676 Abandoned US20140330136A1 (en) 2007-09-14 2014-07-02 Adherent device with multiple physiological sensors
US14322435 Active 2030-07-27 US9770182B2 (en) 2007-09-14 2014-07-02 Adherent device with multiple physiological sensors
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US13647284 Active US8818481B2 (en) 2007-09-14 2012-10-08 Adherent device with multiple physiological sensors
US14322676 Abandoned US20140330136A1 (en) 2007-09-14 2014-07-02 Adherent device with multiple physiological sensors
US14322435 Active 2030-07-27 US9770182B2 (en) 2007-09-14 2014-07-02 Adherent device with multiple physiological sensors
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Cited By (119)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20080270051A1 (en) * 2005-08-02 2008-10-30 Impedimed Limited Impedance Parameter Values
US20080306562A1 (en) * 2007-06-07 2008-12-11 Donnelly Edward J Medical device configured to test for user responsiveness
US20080306560A1 (en) * 2007-06-06 2008-12-11 Macho John D Wearable defibrillator with audio input/output
US20080306325A1 (en) * 2006-10-02 2008-12-11 Emkinetics Method and apparatus for magnetic induction therapy
US20080312709A1 (en) * 2007-06-13 2008-12-18 Volpe Shane S Wearable medical treatment device with motion/position detection
US20090287102A1 (en) * 2008-02-15 2009-11-19 Impedimed Limited Blood flow assessment of venous insufficiency
US20100081960A1 (en) * 2008-09-30 2010-04-01 Nellcor Puritan Bennett Llc Bioimpedance System and Sensor and Technique for Using the Same
US20100100003A1 (en) * 2007-01-15 2010-04-22 Impedimed Limited Monitoring system
US20100099958A1 (en) * 2008-10-16 2010-04-22 Fresenius Medical Care Holdings Inc. Method of identifying when a patient undergoing hemodialysis is at increased risk of death
US20100109739A1 (en) * 2007-03-30 2010-05-06 Impedimed Limited Active guarding for reduction of resistive and capacitive signal loading with adjustable control of compensation level
US20100160712A1 (en) * 2006-10-02 2010-06-24 Daniel Rogers Burnett Method and apparatus for magnetic induction therapy
US20100179421A1 (en) * 2007-05-24 2010-07-15 Joe Tupin System and method for non-invasive instantaneous and continuous measurement of cardiac chamber volume.
WO2010105203A2 (en) * 2009-03-12 2010-09-16 Corventis, Inc. Method and apparatus for elder care monitoring
US20100298899A1 (en) * 2007-06-13 2010-11-25 Donnelly Edward J Wearable medical treatment device
US20110021863A1 (en) * 2009-07-24 2011-01-27 Daniel Rogers Burnett Cooling systems and methods for conductive coils
US20110025348A1 (en) * 2007-11-05 2011-02-03 Impedimed Limited Impedance determination
US20110054343A1 (en) * 2005-07-01 2011-03-03 Impedimed Limited Monitoring system
US20110060215A1 (en) * 2009-03-30 2011-03-10 Tupin Jr Joe Paul Apparatus and method for continuous noninvasive measurement of respiratory function and events
US20110087129A1 (en) * 2005-07-01 2011-04-14 Impedimed Limited Monitoring system
WO2011050283A2 (en) 2009-10-22 2011-04-28 Corventis, Inc. Remote detection and monitoring of functional chronotropic incompetence
US20110137136A1 (en) * 2008-10-16 2011-06-09 Fresenius Medical Care Holdings, Inc. Method of identifying when a patient undergoing hemodialysis is at increased risk of death
WO2011081891A1 (en) 2009-12-14 2011-07-07 Corventis, Inc. Body adherent patch with electronics for physiologic monitoring
US20110178565A1 (en) * 2010-01-15 2011-07-21 Dan Li Automatic mechanical alternans detection
US20110178375A1 (en) * 2010-01-19 2011-07-21 Avery Dennison Corporation Remote physiological monitoring
WO2011126951A1 (en) 2010-04-05 2011-10-13 Corventis, Inc. Method and apparatus for personalized physiologic parameters
US8103337B2 (en) 2004-11-26 2012-01-24 Impedimed Limited Weighted gradient method and system for diagnosing disease
US8116841B2 (en) 2007-09-14 2012-02-14 Corventis, Inc. Adherent device with multiple physiological sensors
US20120108917A1 (en) * 2008-12-15 2012-05-03 Corventis, Inc. Patient monitoring systems and methods
US20120123223A1 (en) * 2010-11-11 2012-05-17 Freeman Gary A Acute care treatment systems dashboard
US20120184878A1 (en) * 2011-01-13 2012-07-19 Bijan Najafi Intelligent device to monitor and remind patients with footwear, walking aids, braces, or orthotics
US20120191151A1 (en) * 2011-01-21 2012-07-26 Nader Kameli Implantable cardiac devices and methods with body orientation unit
US8233974B2 (en) 1999-06-22 2012-07-31 Impedimed Limited Method and device for measuring tissue oedema
WO2012106086A1 (en) 2011-01-31 2012-08-09 Medtronic, Inc. External cardiac monitor
FR2971137A1 (en) * 2011-02-09 2012-08-10 Univ Nancy 1 Henri Poincare motion sensor combines a diagnostic electrode for applications in medical imaging.
US8249686B2 (en) 2007-09-14 2012-08-21 Corventis, Inc. Adherent device for sleep disordered breathing
US20120215076A1 (en) * 2009-08-18 2012-08-23 Ming Young Biomedical Corp. Product, method and system for monitoring physiological function and posture
US20120226170A1 (en) * 2009-11-13 2012-09-06 Omron Healthcare Co., Ltd. Electronic sphygmomanometer
WO2012125135A1 (en) * 2011-03-11 2012-09-20 Spacelabs Healthcare, Llc Methods and systems to determine multi-parameter managed alarm hierarchy during patient monitoring
US8374688B2 (en) 2007-09-14 2013-02-12 Corventis, Inc. System and methods for wireless body fluid monitoring
US8406842B2 (en) 2010-12-09 2013-03-26 Zoll Medical Corporation Electrode with redundant impedance reduction
US8412317B2 (en) 2008-04-18 2013-04-02 Corventis, Inc. Method and apparatus to measure bioelectric impedance of patient tissue
US8460189B2 (en) 2007-09-14 2013-06-11 Corventis, Inc. Adherent cardiac monitor with advanced sensing capabilities
US8478418B2 (en) 2011-04-15 2013-07-02 Infobionic, Inc. Remote health monitoring system
US8588884B2 (en) 2010-05-28 2013-11-19 Emkinetics, Inc. Microneedle electrode
US8600486B2 (en) 2011-03-25 2013-12-03 Zoll Medical Corporation Method of detecting signal clipping in a wearable ambulatory medical device
US20140031663A1 (en) * 2011-02-03 2014-01-30 Isansys Lifecare Limited Health Monitoring
US8644925B2 (en) 2011-09-01 2014-02-04 Zoll Medical Corporation Wearable monitoring and treatment device
US8684925B2 (en) 2007-09-14 2014-04-01 Corventis, Inc. Injectable device for physiological monitoring
US8706215B2 (en) 2010-05-18 2014-04-22 Zoll Medical Corporation Wearable ambulatory medical device with multiple sensing electrodes
US8718752B2 (en) 2008-03-12 2014-05-06 Corventis, Inc. Heart failure decompensation prediction based on cardiac rhythm
US8761870B2 (en) 2006-05-30 2014-06-24 Impedimed Limited Impedance measurements
US8814792B2 (en) 2010-07-27 2014-08-26 Carefusion 303, Inc. System and method for storing and forwarding data from a vital-signs monitor
WO2014157896A1 (en) * 2013-03-24 2014-10-02 서울대학교산학협력단 Film-type device for measuring biomedical signal, and blood pressure measurement device, cardiopulmonary endurance estimation device, and individual certification device using same
US8880196B2 (en) 2013-03-04 2014-11-04 Zoll Medical Corporation Flexible therapy electrode
US8897868B2 (en) 2007-09-14 2014-11-25 Medtronic, Inc. Medical device automatic start-up upon contact to patient tissue
US8897860B2 (en) 2011-03-25 2014-11-25 Zoll Medical Corporation Selection of optimal channel for rate determination
KR101489503B1 (en) 2013-03-24 2015-02-04 서울대학교산학협력단 Film-type bio-signal measurement device
US20150057515A1 (en) * 2012-04-04 2015-02-26 University Of Cincinnati Sweat simulation, collecting and sensing systems
US20150073285A1 (en) * 2011-05-16 2015-03-12 Alivecor, Inc. Universal ecg electrode module for smartphone
US8983597B2 (en) 2012-05-31 2015-03-17 Zoll Medical Corporation Medical monitoring and treatment device with external pacing
US8979665B1 (en) 2010-03-22 2015-03-17 Bijan Najafi Providing motion feedback based on user center of mass
US9002477B2 (en) 2006-01-17 2015-04-07 Emkinetics, Inc. Methods and devices for performing electrical stimulation to treat various conditions
US9005141B1 (en) 2007-10-12 2015-04-14 Biosensics, L.L.C. Ambulatory system for measuring and monitoring physical activity and risk of falling and for automatic fall detection
US9007216B2 (en) 2010-12-10 2015-04-14 Zoll Medical Corporation Wearable therapeutic device
US9008801B2 (en) 2010-05-18 2015-04-14 Zoll Medical Corporation Wearable therapeutic device
US9005102B2 (en) 2006-10-02 2015-04-14 Emkinetics, Inc. Method and apparatus for electrical stimulation therapy
US20150106020A1 (en) * 2013-10-10 2015-04-16 Wireless Medical Monitoring Inc. Method and Apparatus for Wireless Health Monitoring and Emergent Condition Prediction
US9017256B2 (en) 2010-09-22 2015-04-28 Milieu Institute, Llc System and method for physiological monitoring
US9017255B2 (en) 2010-07-27 2015-04-28 Carefusion 303, Inc. System and method for saving battery power in a patient monitoring system
KR101524248B1 (en) * 2014-02-27 2015-05-29 서울대학교산학협력단 System and method for cardiopulmonary fitness estimatiion using film-type bio-signal measurement device
US9055925B2 (en) 2010-07-27 2015-06-16 Carefusion 303, Inc. System and method for reducing false alarms associated with vital-signs monitoring
US9078582B2 (en) 2009-04-22 2015-07-14 Lifewave Biomedical, Inc. Fetal monitoring device and methods
US9135398B2 (en) 2011-03-25 2015-09-15 Zoll Medical Corporation System and method for adapting alarms in a wearable medical device
US9149235B2 (en) 2004-06-18 2015-10-06 Impedimed Limited Oedema detection
US9152765B2 (en) 2010-03-21 2015-10-06 Spacelabs Healthcare Llc Multi-display bedside monitoring system
US9173670B2 (en) 2013-04-08 2015-11-03 Irhythm Technologies, Inc. Skin abrader
FR3020959A1 (en) * 2014-05-19 2015-11-20 Commissariat Energie Atomique Cutaneous device including pulse generator for electrostimulation.
WO2015127466A3 (en) * 2014-02-24 2015-11-26 Element Science, Inc External defibrillator
US9241649B2 (en) 2010-05-12 2016-01-26 Irhythm Technologies, Inc. Device features and design elements for long-term adhesion
US9298889B2 (en) 2007-03-09 2016-03-29 Spacelabs Healthcare Llc Health data collection tool
US9311789B1 (en) 2013-04-09 2016-04-12 BioSensics LLC Systems and methods for sensorimotor rehabilitation
US9339641B2 (en) 2006-01-17 2016-05-17 Emkinetics, Inc. Method and apparatus for transdermal stimulation over the palmar and plantar surfaces
WO2016081227A1 (en) 2014-11-17 2016-05-26 Medtronic Monitoring, Inc. Qt interval determination methods and related devices
US9357929B2 (en) 2010-07-27 2016-06-07 Carefusion 303, Inc. System and method for monitoring body temperature of a person
US9374698B2 (en) * 2014-08-22 2016-06-21 Verizon Patent And Licensing Inc. Personalized emergency identification and communication
US9384652B2 (en) 2010-11-19 2016-07-05 Spacelabs Healthcare, Llc System and method for transfer of primary alarm notification on patient monitoring systems
US9411936B2 (en) 2007-09-14 2016-08-09 Medtronic Monitoring, Inc. Dynamic pairing of patients to data collection gateways
US9420952B2 (en) 2010-07-27 2016-08-23 Carefusion 303, Inc. Temperature probe suitable for axillary reading
US9427564B2 (en) 2010-12-16 2016-08-30 Zoll Medical Corporation Water resistant wearable medical device
US9427165B2 (en) 2012-03-02 2016-08-30 Medtronic Monitoring, Inc. Heuristic management of physiological data
US9504406B2 (en) 2006-11-30 2016-11-29 Impedimed Limited Measurement apparatus
WO2016205187A1 (en) * 2015-06-15 2016-12-22 Medtronic Monitoring, Inc. System and method for monitoring and classifying atrial fibrillations
US9579516B2 (en) 2013-06-28 2017-02-28 Zoll Medical Corporation Systems and methods of delivering therapy using an ambulatory medical device
US9585620B2 (en) * 2010-07-27 2017-03-07 Carefusion 303, Inc. Vital-signs patch having a flexible attachment to electrodes
US9585593B2 (en) 2009-11-18 2017-03-07 Chung Shing Fan Signal distribution for patient-electrode measurements
US9597004B2 (en) 2014-10-31 2017-03-21 Irhythm Technologies, Inc. Wearable monitor
US9597523B2 (en) 2014-02-12 2017-03-21 Zoll Medical Corporation System and method for adapting alarms in a wearable medical device
US9604020B2 (en) 2009-10-16 2017-03-28 Spacelabs Healthcare Llc Integrated, extendable anesthesia system
US9615792B2 (en) 2010-07-27 2017-04-11 Carefusion 303, Inc. System and method for conserving battery power in a patient monitoring system
US9615766B2 (en) 2008-11-28 2017-04-11 Impedimed Limited Impedance measurement process
US9615767B2 (en) 2009-10-26 2017-04-11 Impedimed Limited Fluid level indicator determination
US9629566B2 (en) 2011-03-11 2017-04-25 Spacelabs Healthcare Llc Methods and systems to determine multi-parameter managed alarm hierarchy during patient monitoring
US9655518B2 (en) 2009-03-27 2017-05-23 Braemar Manufacturing, Llc Ambulatory and centralized processing of a physiological signal
US9684767B2 (en) 2011-03-25 2017-06-20 Zoll Medical Corporation System and method for adapting alarms in a wearable medical device
US9724012B2 (en) 2005-10-11 2017-08-08 Impedimed Limited Hydration status monitoring
USD794806S1 (en) 2016-04-29 2017-08-15 Infobionic, Inc. Health monitoring device
USD794807S1 (en) 2016-04-29 2017-08-15 Infobionic, Inc. Health monitoring device with a display
USD794805S1 (en) 2016-04-29 2017-08-15 Infobionic, Inc. Health monitoring device with a button
US9782578B2 (en) 2011-05-02 2017-10-10 Zoll Medical Corporation Patient-worn energy delivery apparatus and techniques for sizing same
US9782132B2 (en) 2012-10-07 2017-10-10 Rhythm Diagnostic Systems, Inc. Health monitoring systems and methods
US9797764B2 (en) 2009-10-16 2017-10-24 Spacelabs Healthcare, Llc Light enhanced flow tube
US9814894B2 (en) 2012-05-31 2017-11-14 Zoll Medical Corporation Systems and methods for detecting health disorders
US9848779B2 (en) 2014-02-24 2017-12-26 Medtronic Monitoring, Inc. Separable monitoring device and method
US9872087B2 (en) 2010-10-19 2018-01-16 Welch Allyn, Inc. Platform for patient monitoring
US9878171B2 (en) 2012-03-02 2018-01-30 Zoll Medical Corporation Systems and methods for configuring a wearable medical monitoring and/or treatment device
US9925387B2 (en) 2010-11-08 2018-03-27 Zoll Medical Corporation Remote medical device alarm
US9968274B2 (en) 2016-04-29 2018-05-15 Infobionic, Inc. Systems and methods for processing ECG data
US9999393B2 (en) 2013-01-29 2018-06-19 Zoll Medical Corporation Delivery of electrode gel using CPR puck
US10136831B2 (en) 2014-10-17 2018-11-27 University Of Cincinnati Sweat sensing with chronological assurance

Families Citing this family (163)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8730031B2 (en) 2005-04-28 2014-05-20 Proteus Digital Health, Inc. Communication system using an implantable device
US9198608B2 (en) 2005-04-28 2015-12-01 Proteus Digital Health, Inc. Communication system incorporated in a container
US9756874B2 (en) 2011-07-11 2017-09-12 Proteus Digital Health, Inc. Masticable ingestible product and communication system therefor
EP1920418A4 (en) 2005-09-01 2010-12-29 Proteus Biomedical Inc Implantable zero-wire communications system
US8956287B2 (en) 2006-05-02 2015-02-17 Proteus Digital Health, Inc. Patient customized therapeutic regimens
US9962098B2 (en) 2006-06-02 2018-05-08 Global Cardiac Monitors, Inc. Heart monitor electrode system
US8858325B2 (en) * 2006-09-29 2014-10-14 The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration Team electronic gameplay combining different means of control
JP5916277B2 (en) 2006-10-25 2016-05-11 プロテウス デジタル ヘルス, インコーポレイテッド Ingestible control activation identifier
US8214007B2 (en) 2006-11-01 2012-07-03 Welch Allyn, Inc. Body worn physiological sensor device having a disposable electrode module
WO2008063626A3 (en) 2006-11-20 2008-07-03 Proteus Biomedical Inc Active signal processing personal health signal receivers
EP2107883A4 (en) 2007-02-01 2013-07-03 Proteus Digital Health Inc Ingestible event marker systems
CN103066226B (en) 2007-02-14 2016-09-14 普罗透斯数字保健公司 The body having a high surface area electrode power supply
US8932221B2 (en) 2007-03-09 2015-01-13 Proteus Digital Health, Inc. In-body device having a multi-directional transmitter
US8540632B2 (en) 2007-05-24 2013-09-24 Proteus Digital Health, Inc. Low profile antenna for in body device
US8602997B2 (en) 2007-06-12 2013-12-10 Sotera Wireless, Inc. Body-worn system for measuring continuous non-invasive blood pressure (cNIBP)
WO2008154643A1 (en) 2007-06-12 2008-12-18 Triage Wireless, Inc. Vital sign monitor for measuring blood pressure using optical, electrical, and pressure waveforms
WO2009042812A1 (en) 2007-09-25 2009-04-02 Proteus Biomedical, Inc. In-body device with virtual dipole signal amplification
WO2009061920A1 (en) 2007-11-06 2009-05-14 Hydrodot, Inc. Device and method for performing electroencephalography
JP2011513865A (en) 2008-03-05 2011-04-28 プロテウス バイオメディカル インコーポレイテッド Ingestible event markers and systems of the multi-mode communication, as well as how to use it
EP2313002B1 (en) 2008-07-08 2018-08-29 Proteus Digital Health, Inc. Ingestible event marker data framework
US20100042012A1 (en) * 2008-08-15 2010-02-18 Karim Alhussiny Diagnostic device for remote sensing and transmitting biophysiological signals
US20150201858A1 (en) * 2008-08-15 2015-07-23 Global Cardiac Monitors, Inc. Diagnostic device for remote sensing and transmitting biophysiological signals
US8389862B2 (en) 2008-10-07 2013-03-05 Mc10, Inc. Extremely stretchable electronics
EP2358270A4 (en) 2008-12-11 2014-08-13 Proteus Digital Health Inc Evaluation of gastrointestinal function using portable electroviscerography systems and methods of using the same
US9659423B2 (en) 2008-12-15 2017-05-23 Proteus Digital Health, Inc. Personal authentication apparatus system and method
US9439566B2 (en) 2008-12-15 2016-09-13 Proteus Digital Health, Inc. Re-wearable wireless device
US8771204B2 (en) * 2008-12-30 2014-07-08 Masimo Corporation Acoustic sensor assembly
CA2750158A1 (en) 2009-01-06 2010-07-15 Proteus Biomedical, Inc. Ingestion-related biofeedback and personalized medical therapy method and system
US20100298661A1 (en) 2009-05-20 2010-11-25 Triage Wireless, Inc. Method for generating alarms/alerts based on a patient's posture and vital signs
US8475370B2 (en) 2009-05-20 2013-07-02 Sotera Wireless, Inc. Method for measuring patient motion, activity level, and posture along with PTT-based blood pressure
US10085657B2 (en) 2009-06-17 2018-10-02 Sotera Wireless, Inc. Body-worn pulse oximeter
US8740807B2 (en) 2009-09-14 2014-06-03 Sotera Wireless, Inc. Body-worn monitor for measuring respiration rate
US8527038B2 (en) 2009-09-15 2013-09-03 Sotera Wireless, Inc. Body-worn vital sign monitor
US8321004B2 (en) 2009-09-15 2012-11-27 Sotera Wireless, Inc. Body-worn vital sign monitor
US8364250B2 (en) 2009-09-15 2013-01-29 Sotera Wireless, Inc. Body-worn vital sign monitor
US20110066010A1 (en) * 2009-09-15 2011-03-17 Jim Moon Body-worn vital sign monitor
WO2011047216A3 (en) 2009-10-15 2011-08-04 Masimo Corporation Physiological acoustic monitoring system
CN102946798A (en) 2010-02-01 2013-02-27 普罗秋斯数字健康公司 Data gathering system
US20110224499A1 (en) 2010-03-10 2011-09-15 Sotera Wireless, Inc. Body-worn vital sign monitor
US8979765B2 (en) 2010-04-19 2015-03-17 Sotera Wireless, Inc. Body-worn monitor for measuring respiratory rate
US9339209B2 (en) 2010-04-19 2016-05-17 Sotera Wireless, Inc. Body-worn monitor for measuring respiratory rate
US8798709B1 (en) * 2010-04-19 2014-08-05 Neotech Products, Inc. Dermal sensing package and use
US9173593B2 (en) 2010-04-19 2015-11-03 Sotera Wireless, Inc. Body-worn monitor for measuring respiratory rate
US8747330B2 (en) 2010-04-19 2014-06-10 Sotera Wireless, Inc. Body-worn monitor for measuring respiratory rate
US8888700B2 (en) 2010-04-19 2014-11-18 Sotera Wireless, Inc. Body-worn monitor for measuring respiratory rate
US9173594B2 (en) 2010-04-19 2015-11-03 Sotera Wireless, Inc. Body-worn monitor for measuring respiratory rate
US20120065479A1 (en) * 2010-04-26 2012-03-15 Lahiji Rosa R Ultrasound patch
KR101048662B1 (en) * 2010-05-03 2011-07-14 한국과학기술원 A body attaching type sensor and monitoring apparatus thereof
EP3078324A1 (en) * 2010-05-08 2016-10-12 The Regents of The University of California Method and apparatus for early detection of ulcers by scanning of subepidermal moisture
WO2011146708A3 (en) 2010-05-21 2013-10-24 Medicomp, Inc. Retractable multi-use cardiac monitor
US9585584B2 (en) 2010-05-21 2017-03-07 Medicomp, Inc. Physiological signal monitor with retractable wires
US9326712B1 (en) 2010-06-02 2016-05-03 Masimo Corporation Opticoustic sensor
US9351654B2 (en) 2010-06-08 2016-05-31 Alivecor, Inc. Two electrode apparatus and methods for twelve lead ECG
US8509882B2 (en) 2010-06-08 2013-08-13 Alivecor, Inc. Heart monitoring system usable with a smartphone or computer
US20120029300A1 (en) * 2010-07-27 2012-02-02 Carefusion 303, Inc. System and method for reducing false alarms and false negatives based on motion and position sensing
US9554725B2 (en) 2010-08-03 2017-01-31 Medtronic Monitoring, Inc. Medical device and methods of monitoring a patient with renal dysfunction
US8473047B2 (en) 2010-08-03 2013-06-25 Corventis, Inc. Multifrequency bioimpedence device and related methods
US10004428B2 (en) 2010-10-29 2018-06-26 Orpyx Medical Technologies, Inc. Peripheral sensory and supersensory replacement system
US9717412B2 (en) 2010-11-05 2017-08-01 Gary And Mary West Health Institute Wireless fetal monitoring system
EP2465415B1 (en) * 2010-12-20 2013-07-03 General Electric Company Single-use biomedical sensors
KR101747858B1 (en) * 2011-01-03 2017-06-16 삼성전자주식회사 Electrode for living body and device for measuring living body signal
US20120197144A1 (en) * 2011-01-27 2012-08-02 Koninklijke Philips Electronics N.V. Exchangeable electrode and ecg cable snap connector
CN103582449B (en) 2011-02-18 2017-06-09 索泰拉无线公司 Modular wrist-worn processor for patient monitoring of
US8482418B1 (en) * 2011-02-18 2013-07-09 Pursuit Enterprises Method and apparatus for monitoring and treatment of sleep-related conditions
EP2683291A4 (en) 2011-03-11 2014-09-03 Proteus Digital Health Inc Wearable personal body associated device with various physical configurations
KR101754095B1 (en) * 2011-04-29 2017-07-05 인텔렉추얼디스커버리 주식회사 RFID tag for laundry
US20130053668A1 (en) * 2011-08-26 2013-02-28 Compose Element Limited Kit and method for detecting blood sugar
US9220436B2 (en) * 2011-09-26 2015-12-29 Covidien Lp Technique for remanufacturing a BIS sensor
US9235683B2 (en) 2011-11-09 2016-01-12 Proteus Digital Health, Inc. Apparatus, system, and method for managing adherence to a regimen
US9700222B2 (en) 2011-12-02 2017-07-11 Lumiradx Uk Ltd Health-monitor patch
US9734304B2 (en) 2011-12-02 2017-08-15 Lumiradx Uk Ltd Versatile sensors with data fusion functionality
CA2858244A1 (en) 2011-12-14 2013-06-20 Intersection Medical, Inc. Devices, systems and methods for determining the relative spatial change in subsurface resistivities across frequencies in tissue
CN104703651A (en) 2012-05-01 2015-06-10 高等教育联邦系统-匹兹堡大学 Tip-loaded microneedle arrays for transdermal insertion
US9277864B2 (en) * 2012-05-24 2016-03-08 Vital Connect, Inc. Modular wearable sensor device
US20130331720A1 (en) * 2012-06-11 2013-12-12 Triomi Medical Innovations, Llc Electrocardiograph system
US9042596B2 (en) 2012-06-14 2015-05-26 Medibotics Llc Willpower watch (TM)—a wearable food consumption monitor
US9630093B2 (en) 2012-06-22 2017-04-25 The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration Method and system for physiologically modulating videogames and simulations which use gesture and body image sensing control input devices
DE102012106893B4 (en) * 2012-07-30 2016-10-27 Karlsruher Institut für Technologie Electrode and measuring means for detecting vital parameters biomedical
US9955937B2 (en) 2012-09-20 2018-05-01 Masimo Corporation Acoustic patient sensor coupler
US9171794B2 (en) 2012-10-09 2015-10-27 Mc10, Inc. Embedding thin chips in polymer
FR2997600B1 (en) * 2012-10-29 2015-12-25 Controle Instrumentation Et Diagnostic Electroniques Sa Cidelec Detector its sealed with two sensors for measuring the sound and the static pressure
KR101759806B1 (en) 2012-11-01 2017-07-19 블루 스파크 테크놀러지스, 인크. Body temperature logging patch
US9869594B2 (en) * 2012-11-05 2018-01-16 Steamist, Inc. Controller for steam bath having multiple temperature sensors
US9254095B2 (en) 2012-11-08 2016-02-09 Alivecor Electrocardiogram signal detection
US20140187896A1 (en) * 2012-12-31 2014-07-03 Perminova Inc. Body-worn sensor for characterizing patients with heart failure
US9974444B2 (en) * 2012-12-31 2018-05-22 Tosense, Inc. Body-worn sensor for characterizing patients with heart failure
US20140187897A1 (en) * 2012-12-31 2014-07-03 Perminova Inc. Body-worn sensor for characterizing patients with heart failure
WO2014107700A1 (en) 2013-01-07 2014-07-10 Alivecor, Inc. Methods and systems for electrode placement
US20140275932A1 (en) * 2013-03-12 2014-09-18 Vital Connect, Inc. Disposable biometric patch device
US20140275817A1 (en) * 2013-03-13 2014-09-18 Guardit Technologies, Llc Portable, Pediatric Medical Diagnostic Device
US20140285326A1 (en) * 2013-03-15 2014-09-25 Aliphcom Combination speaker and light source responsive to state(s) of an organism based on sensor data
US9254092B2 (en) 2013-03-15 2016-02-09 Alivecor, Inc. Systems and methods for processing and analyzing medical data
DE102013205403A1 (en) * 2013-03-27 2014-10-16 Robert Bosch Gmbh Method and apparatus for detection of hydration of a human or animal body
US20140323818A1 (en) * 2013-04-25 2014-10-30 Melanie Axelgaard Wireless Physiological Monitoring Device
JP6420321B2 (en) 2013-05-21 2018-11-07 オーピクス・メディカル・テクノロジーズ・インコーポレイテッド Pressure data acquisition assembly
US9254099B2 (en) 2013-05-23 2016-02-09 Medibotics Llc Smart watch and food-imaging member for monitoring food consumption
US9536449B2 (en) 2013-05-23 2017-01-03 Medibotics Llc Smart watch and food utensil for monitoring food consumption
US9529385B2 (en) 2013-05-23 2016-12-27 Medibotics Llc Smart watch and human-to-computer interface for monitoring food consumption
CA2916618A1 (en) * 2013-06-24 2014-12-31 Event Cardio Group, Inc. Wireless cardiac event recorder
EP3016586A4 (en) * 2013-07-01 2017-10-04 Mayo Foundation for Medical Education and Research Advanced health monitoring system
US9247911B2 (en) 2013-07-10 2016-02-02 Alivecor, Inc. Devices and methods for real-time denoising of electrocardiograms
KR20160071371A (en) * 2013-09-19 2016-06-21 로레알 Systems and methods for measuring and categorizing colors and spectra of surfaces
WO2015044722A1 (en) 2013-09-24 2015-04-02 Proteus Digital Health, Inc. Method and apparatus for use with received electromagnetic signal at a frequency not known exactly in advance
US9655538B2 (en) 2013-09-25 2017-05-23 Bardy Diagnostics, Inc. Self-authenticating electrocardiography monitoring circuit
WO2016201135A1 (en) * 2015-06-10 2016-12-15 Bardy Diagnostics, Inc. Extended wear electrocardiography patch
US9717432B2 (en) 2013-09-25 2017-08-01 Bardy Diagnostics, Inc. Extended wear electrocardiography patch using interlaced wire electrodes
US9408551B2 (en) 2013-11-14 2016-08-09 Bardy Diagnostics, Inc. System and method for facilitating diagnosis of cardiac rhythm disorders with the aid of a digital computer
US9655537B2 (en) 2013-09-25 2017-05-23 Bardy Diagnostics, Inc. Wearable electrocardiography and physiology monitoring ensemble
US9433367B2 (en) 2013-09-25 2016-09-06 Bardy Diagnostics, Inc. Remote interfacing of extended wear electrocardiography and physiological sensor monitor
US9433380B1 (en) 2013-09-25 2016-09-06 Bardy Diagnostics, Inc. Extended wear electrocardiography patch
US9700227B2 (en) 2013-09-25 2017-07-11 Bardy Diagnostics, Inc. Ambulatory electrocardiography monitoring patch optimized for capturing low amplitude cardiac action potential propagation
US9730593B2 (en) 2013-09-25 2017-08-15 Bardy Diagnostics, Inc. Extended wear ambulatory electrocardiography and physiological sensor monitor
US9364155B2 (en) 2013-09-25 2016-06-14 Bardy Diagnostics, Inc. Self-contained personal air flow sensing monitor
US9615763B2 (en) 2013-09-25 2017-04-11 Bardy Diagnostics, Inc. Ambulatory electrocardiography monitor recorder optimized for capturing low amplitude cardiac action potential propagation
US9737224B2 (en) * 2013-09-25 2017-08-22 Bardy Diagnostics, Inc. Event alerting through actigraphy embedded within electrocardiographic data
US9717433B2 (en) 2013-09-25 2017-08-01 Bardy Diagnostics, Inc. Ambulatory electrocardiography monitoring patch optimized for capturing low amplitude cardiac action potential propagation
US9408545B2 (en) 2013-09-25 2016-08-09 Bardy Diagnostics, Inc. Method for efficiently encoding and compressing ECG data optimized for use in an ambulatory ECG monitor
US9775536B2 (en) 2013-09-25 2017-10-03 Bardy Diagnostics, Inc. Method for constructing a stress-pliant physiological electrode assembly
US9345414B1 (en) 2013-09-25 2016-05-24 Bardy Diagnostics, Inc. Method for providing dynamic gain over electrocardiographic data with the aid of a digital computer
US9619660B1 (en) 2013-09-25 2017-04-11 Bardy Diagnostics, Inc. Computer-implemented system for secure physiological data collection and processing
US10084880B2 (en) 2013-11-04 2018-09-25 Proteus Digital Health, Inc. Social media networking based on physiologic information
USD717955S1 (en) 2013-11-07 2014-11-18 Bardy Diagnostics, Inc. Electrocardiography monitor
USD744659S1 (en) 2013-11-07 2015-12-01 Bardy Diagnostics, Inc. Extended wear electrode patch
USD831833S1 (en) 2013-11-07 2018-10-23 Bardy Diagnostics, Inc. Extended wear electrode patch
USD801528S1 (en) 2013-11-07 2017-10-31 Bardy Diagnostics, Inc. Electrocardiography monitor
CN105828710A (en) 2013-11-26 2016-08-03 心脏起搏器股份公司 Detection of chronic obstructive pulmonary disease exacerbations from breathing patterns
EP3079571A4 (en) 2013-12-12 2017-08-02 Alivecor, Inc. Methods and systems for arrhythmia tracking and scoring
US9442100B2 (en) 2013-12-18 2016-09-13 Medibotics Llc Caloric intake measuring system using spectroscopic and 3D imaging analysis
WO2015123157A1 (en) * 2014-02-14 2015-08-20 Zansors Wearable sensor
US9582035B2 (en) 2014-02-25 2017-02-28 Medibotics Llc Wearable computing devices and methods for the wrist and/or forearm
US20150257664A1 (en) * 2014-03-17 2015-09-17 Avatar Engineering Corporation Heart monitoring sensor
WO2015187377A1 (en) * 2014-06-02 2015-12-10 Avery Dennison Corporation Sensor patches
WO2016030869A1 (en) * 2014-08-29 2016-03-03 Ecole Polytechnique Federale De Lausanne (Epfl) Wearable, multi-parametric wireless system-in-patch for hydration level monitoring
GB2530355A (en) * 2014-09-16 2016-03-23 Joseph Duncanan Farley Electric impedance tomographic device
USD781270S1 (en) 2014-10-15 2017-03-14 Mc10, Inc. Electronic device having antenna
JP2016126897A (en) * 2014-12-26 2016-07-11 株式会社東芝 Fitting apparatus and electronic device
US9693689B2 (en) 2014-12-31 2017-07-04 Blue Spark Technologies, Inc. Body temperature logging patch
US20160206224A1 (en) * 2015-01-20 2016-07-21 Medicomp, Inc. Ecg electrode snap connector and associated methods
US10098544B2 (en) 2015-03-11 2018-10-16 Medicomp, Inc. Wireless ECG sensor system and method
KR101614153B1 (en) * 2015-04-14 2016-05-11 (주)하늘마음바이오 Gel Type Electrode Unit for High Frequency Treatment Apparatus
WO2017073861A1 (en) * 2015-10-30 2017-05-04 (주)하늘마음바이오 Gel-type electrode unit for high frequency treatment device
WO2016181241A1 (en) * 2015-05-08 2016-11-17 Koninklijke Philips N.V. A wet/dry convertible electrode and method of use
US9839363B2 (en) 2015-05-13 2017-12-12 Alivecor, Inc. Discordance monitoring
WO2016187536A1 (en) * 2015-05-20 2016-11-24 Mc10 Inc. Ultra-thin wearable sensing device
EP3307535A1 (en) * 2015-06-15 2018-04-18 Mc10, Inc. Moisture wicking adhesives for skin-mounted devices
US9706269B2 (en) * 2015-07-24 2017-07-11 Hong Kong Applied Science and Technology Research Institute Company, Limited Self-powered and battery-assisted CMOS wireless bio-sensing IC platform
US10105100B2 (en) 2015-07-28 2018-10-23 Verily Life Sciences Llc Display on a bandage-type monitoring device
USD766447S1 (en) 2015-09-10 2016-09-13 Bardy Diagnostics, Inc. Extended wear electrode patch
USD793566S1 (en) 2015-09-10 2017-08-01 Bardy Diagnostics, Inc. Extended wear electrode patch
US9504423B1 (en) 2015-10-05 2016-11-29 Bardy Diagnostics, Inc. Method for addressing medical conditions through a wearable health monitor with the aid of a digital computer
US20170095177A1 (en) * 2015-10-05 2017-04-06 Infobionic, Inc. Electrode patch for health monitoring
KR101786531B1 (en) * 2015-11-05 2017-10-18 재단법인 구미전자정보기술원 A method for manufacturing a patch type wearable temperature sensor
FR3050024A1 (en) * 2016-04-08 2017-10-13 Henri Cedric Steeves Vouters Adapter inclinometer (d7e-3)
US20170336227A1 (en) * 2016-05-20 2017-11-23 Health Care Originals, Inc. Wearable apparatus
EP3251585A1 (en) * 2016-05-30 2017-12-06 Roche Diabetes Care GmbH Body-mountable device
US9954309B2 (en) 2016-07-20 2018-04-24 Intel Corporation Magnetic detachable electrical connections between circuits
US9735893B1 (en) * 2016-07-21 2017-08-15 Intel Corporation Patch system for in-situ therapeutic treatment
US20180070850A1 (en) * 2016-09-15 2018-03-15 Karen S. Stafford Apparatus and method for detecting body composition and correlating it with cognitive efficiency
US10039186B2 (en) 2016-09-16 2018-07-31 Intel Corporation Stretchable and flexible electrical substrate interconnections
US9893438B1 (en) 2016-09-30 2018-02-13 Intel Corporation Electrical connectors for high density attach to stretchable boards
US10111618B2 (en) * 2017-03-13 2018-10-30 VivaLnk, Inc. Dual purpose wearable patch for measurement and treatment
DE102017204491A1 (en) * 2017-03-17 2018-09-20 Henkel Ag & Co. Kgaa Method and apparatus for determining a skin moisture content
GB201706354D0 (en) * 2017-04-21 2017-06-07 Surepulse Medical Ltd Electrocardiogram sensor

Citations (91)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3170459A (en) * 1962-03-20 1965-02-23 Clifford G Phipps Bio-medical instrumentation electrode
US3370459A (en) * 1964-04-16 1968-02-27 Cescati Arturo Device for detecting pressure existing in pneumatic tires
US4008712A (en) * 1975-11-14 1977-02-22 J. M. Richards Laboratories Method for monitoring body characteristics
US4141366A (en) * 1977-11-18 1979-02-27 Medtronic, Inc. Lead connector for tape electrode
US4185621A (en) * 1977-10-28 1980-01-29 Triad, Inc. Body parameter display incorporating a battery charger
US4308872A (en) * 1977-04-07 1982-01-05 Respitrace Corporation Method and apparatus for monitoring respiration
US4498479A (en) * 1981-06-24 1985-02-12 Kone Oy Electrocardiograph (ECG) electrode testing system
US4721110A (en) * 1984-08-06 1988-01-26 Lampadius Michael S Respiration-controlled cardiac pacemaker
US4895163A (en) * 1988-05-24 1990-01-23 Bio Analogics, Inc. System for body impedance data acquisition
US4981139A (en) * 1983-08-11 1991-01-01 Pfohl Robert L Vital signs monitoring and communication system
US4988335A (en) * 1988-08-16 1991-01-29 Ideal Instruments, Inc. Pellet implanter apparatus
US5080099A (en) * 1988-08-26 1992-01-14 Cardiotronics, Inc. Multi-pad, multi-function electrode
US5083563A (en) * 1990-02-16 1992-01-28 Telectronics Pacing Systems, Inc. Implantable automatic and haemodynamically responsive cardioverting/defibrillating pacemaker
US5086781A (en) * 1989-11-14 1992-02-11 Bookspan Mark A Bioelectric apparatus for monitoring body fluid compartments
US5282840A (en) * 1992-03-26 1994-02-01 Medtronic, Inc. Multiple frequency impedance measurement system
US5482036A (en) * 1991-03-07 1996-01-09 Masimo Corporation Signal processing apparatus and method
US5718234A (en) * 1996-09-30 1998-02-17 Northrop Grumman Corporation Physiological data communication system
US5855614A (en) * 1993-02-22 1999-01-05 Heartport, Inc. Method and apparatus for thoracoscopic intracardiac procedures
US5860860A (en) * 1996-01-31 1999-01-19 Federal Patent Corporation Integral video game and cardio-waveform display
US5862803A (en) * 1993-09-04 1999-01-26 Besson; Marcus Wireless medical diagnosis and monitoring equipment
US5862802A (en) * 1981-04-03 1999-01-26 Forrest M. Bird Ventilator having an oscillatory inspiratory phase and method
US5865733A (en) * 1997-02-28 1999-02-02 Spacelabs Medical, Inc. Wireless optical patient monitoring apparatus
US6027523A (en) * 1997-10-06 2000-02-22 Arthrex, Inc. Suture anchor with attached disk
US6181963B1 (en) * 1998-11-02 2001-01-30 Alza Corporation Transdermal electrotransport delivery device including a cathodic reservoir containing a compatible antimicrobial agent
US6185452B1 (en) * 1997-02-26 2001-02-06 Joseph H. Schulman Battery-powered patient implantable device
US6190313B1 (en) * 1998-04-20 2001-02-20 Allen J. Hinkle Interactive health care system and method
US6190324B1 (en) * 1999-04-28 2001-02-20 Medtronic, Inc. Implantable medical device for tracking patient cardiac status
US6336903B1 (en) * 1999-11-16 2002-01-08 Cardiac Intelligence Corp. Automated collection and analysis patient care system and method for diagnosing and monitoring congestive heart failure and outcomes thereof
US6339722B1 (en) * 1995-09-26 2002-01-15 A. J. Van Liebergen Holding B.V. Apparatus for the in-vivo non-invasive measurement of a biological parameter concerning a bodily fluid of a person or animal
US20020019588A1 (en) * 2000-06-23 2002-02-14 Marro Dominic P. Frontal electrode array for patient EEG signal acquisition
US20030009092A1 (en) * 1998-10-15 2003-01-09 Sensidyne, Inc. Reusable pulse oximeter probe and disposable bandage apparatus
US6512949B1 (en) * 1999-07-12 2003-01-28 Medtronic, Inc. Implantable medical device for measuring time varying physiologic conditions especially edema and for responding thereto
US20030023184A1 (en) * 2001-07-23 2003-01-30 Jonathan Pitts-Crick Method and system for diagnosing and administering therapy of pulmonary congestion
US20030028221A1 (en) * 2001-07-31 2003-02-06 Qingsheng Zhu Cardiac rhythm management system for edema
US20030028321A1 (en) * 2001-06-29 2003-02-06 The Regents Of The University Of California Method and apparatus for ultra precise GPS-based mapping of seeds or vegetation during planting
US6520967B1 (en) * 1999-10-20 2003-02-18 Cauthen Research Group, Inc. Spinal implant insertion instrument for spinal interbody prostheses
US20040006279A1 (en) * 2002-07-03 2004-01-08 Shimon Arad (Abboud) Apparatus for monitoring CHF patients using bio-impedance technique
US20040010303A1 (en) * 2001-09-26 2004-01-15 Cvrx, Inc. Electrode structures and methods for their use in cardiovascular reflex control
US6687540B2 (en) * 1999-03-12 2004-02-03 Cardiac Pacemakers, Inc. Discrimination of supraventricular tachycardia and ventricular tachycardia events
US6697658B2 (en) * 2001-07-02 2004-02-24 Masimo Corporation Low power pulse oximeter
US20050015095A1 (en) * 2003-07-15 2005-01-20 Cervitech, Inc. Insertion instrument for cervical prostheses
US20050015094A1 (en) * 2003-07-15 2005-01-20 Cervitech, Inc. Arrangement of a cervical prosthesis and insertion instrument
US20050020935A1 (en) * 2001-11-20 2005-01-27 Thomas Helzel Electrode for biomedical measurements
US20050027918A1 (en) * 2002-12-23 2005-02-03 Microtune (Texas), L.P. Automatically establishing a wireless connection between adapters
US20050027175A1 (en) * 2003-07-31 2005-02-03 Zhongping Yang Implantable biosensor
US20050027204A1 (en) * 2003-06-26 2005-02-03 Kligfield Paul D. ECG diagnostic system and method
US20050027207A1 (en) * 2000-12-29 2005-02-03 Westbrook Philip R. Sleep apnea risk evaluation
US6858006B2 (en) * 2000-09-08 2005-02-22 Wireless Medical, Inc. Cardiopulmonary monitoring
US20050043675A1 (en) * 2003-08-21 2005-02-24 Pastore Joseph M. Method and apparatus for modulating cellular metabolism during post-ischemia or heart failure
US20050113703A1 (en) * 2003-09-12 2005-05-26 Jonathan Farringdon Method and apparatus for measuring heart related parameters
US20050192488A1 (en) * 2004-02-12 2005-09-01 Biopeak Corporation Non-invasive method and apparatus for determining a physiological parameter
US20060004300A1 (en) * 2002-11-22 2006-01-05 James Kennedy Multifrequency bioimpedance determination
US6985078B2 (en) * 2000-03-14 2006-01-10 Kabushiki Kaisha Toshiba Wearable life support apparatus and method
US20060009697A1 (en) * 2004-04-07 2006-01-12 Triage Wireless, Inc. Wireless, internet-based system for measuring vital signs from a plurality of patients in a hospital or medical clinic
US20060009701A1 (en) * 2004-06-29 2006-01-12 Polar Electro Oy Method of monitoring human relaxation level, and user-operated heart rate monitor
US20060010090A1 (en) * 2004-07-12 2006-01-12 Marina Brockway Expert system for patient medical information analysis
US6987965B2 (en) * 2000-04-18 2006-01-17 Motorola, Inc. Programmable wireless electrode system for medical monitoring
US6988989B2 (en) * 2000-05-19 2006-01-24 Welch Allyn Protocol, Inc. Patient monitoring system
US20060020218A1 (en) * 2004-02-26 2006-01-26 Warwick Freeman Method and apparatus for continuous electrode impedance monitoring
US6993378B2 (en) * 2001-06-25 2006-01-31 Science Applications International Corporation Identification by analysis of physiometric variation
US20060025661A1 (en) * 2004-08-02 2006-02-02 Sweeney Robert J Device for monitoring fluid status
US20060031102A1 (en) * 2000-06-16 2006-02-09 Bodymedia, Inc. System for detecting, monitoring, and reporting an individual's physiological or contextual status
US20060030781A1 (en) * 2004-08-05 2006-02-09 Adnan Shennib Emergency heart sensor patch
US20060030782A1 (en) * 2004-08-05 2006-02-09 Adnan Shennib Heart disease detection patch
US6997879B1 (en) * 2002-07-09 2006-02-14 Pacesetter, Inc. Methods and devices for reduction of motion-induced noise in optical vascular plethysmography
US20060041280A1 (en) * 2004-08-19 2006-02-23 Cardiac Pacemakers, Inc. Thoracic impedance detection with blood resistivity compensation
US7156808B2 (en) * 1999-12-17 2007-01-02 Q-Tec Systems Llc Method and apparatus for health and disease management combining patient data monitoring with wireless internet connectivity
US7160252B2 (en) * 2003-01-10 2007-01-09 Medtronic, Inc. Method and apparatus for detecting respiratory disturbances
US7160253B2 (en) * 2002-11-08 2007-01-09 Polar Electro Oy Method and device for measuring stress
US20070010750A1 (en) * 2003-10-03 2007-01-11 Akinori Ueno Biometric sensor and biometric method
US20070010721A1 (en) * 2005-06-28 2007-01-11 Chen Thomas C H Apparatus and system of Internet-enabled wireless medical sensor scale
US20070015973A1 (en) * 2005-06-03 2007-01-18 Reuven Nanikashvili Communication terminal, medical telemetry system and method for monitoring physiological data
US20070015976A1 (en) * 2005-06-01 2007-01-18 Medtronic, Inc. Correlating a non-polysomnographic physiological parameter set with sleep states
US20070016089A1 (en) * 2005-07-15 2007-01-18 Fischell David R Implantable device for vital signs monitoring
US7167743B2 (en) * 2004-03-16 2007-01-23 Medtronic, Inc. Collecting activity information to evaluate therapy
US7166063B2 (en) * 2001-10-01 2007-01-23 The Nemours Foundation Brace compliance monitor
US20070021678A1 (en) * 2005-07-19 2007-01-25 Cardiac Pacemakers, Inc. Methods and apparatus for monitoring physiological responses to steady state activity
US20070027497A1 (en) * 2005-07-27 2007-02-01 Cyberonics, Inc. Nerve stimulation for treatment of syncope
US20070027388A1 (en) * 2005-08-01 2007-02-01 Chang-An Chou Patch-type physiological monitoring apparatus, system and network
US20070038078A1 (en) * 2005-07-08 2007-02-15 Daniel Osadchy Relative impedance measurement
US20070038038A1 (en) * 1999-10-18 2007-02-15 Bodymedia, Inc. Wearable human physiological and environmental data sensors and reporting system therefor
US20070043303A1 (en) * 2005-08-17 2007-02-22 Osypka Markus J Method and apparatus for digital demodulation and further processing of signals obtained in the measurement of electrical bioimpedance or bioadmittance in an object
US20070043301A1 (en) * 2002-05-14 2007-02-22 Idex Asa Volume specific characterization of human skin by electrical immitance
US7184821B2 (en) * 2003-12-03 2007-02-27 Regents Of The University Of Minnesota Monitoring thoracic fluid changes
US20080004499A1 (en) * 2006-06-28 2008-01-03 Davis Carl C System and method for the processing of alarm and communication information in centralized patient monitoring
US7318808B2 (en) * 2001-12-14 2008-01-15 Isis Innovation Limited Combining measurements from breathing rate sensors
US7319386B2 (en) * 2004-08-02 2008-01-15 Hill-Rom Services, Inc. Configurable system for alerting caregivers
US20080024294A1 (en) * 2003-06-23 2008-01-31 Cardiac Pacemakers, Inc. Systems, devices, and methods for selectively preventing data transfer from a medical device
US20080024293A1 (en) * 2006-07-28 2008-01-31 Lee Stylos Adaptations to optivol alert algorithm
US20090018410A1 (en) * 2006-03-02 2009-01-15 Koninklijke Philips Electronics N.V. Body parameter sensing
US20090018456A1 (en) * 2007-07-11 2009-01-15 Chin-Yeh Hung Display storage apparatus capable of detecting a pulse

Family Cites Families (557)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US834261A (en) 1906-04-04 1906-10-30 Clarence S Chambers Vaccine-injector.
US2087124A (en) 1936-10-08 1937-07-13 Clarence O Smith Wire cable cutter
US2184511A (en) 1937-10-28 1939-12-26 Samuel M Bagno Method and apparatus for measuring impedance
US3232291A (en) 1962-11-23 1966-02-01 San Francisco Res Corp Surgical adhesive tape and bandage
USRE30101E (en) 1964-08-19 1979-09-25 Regents Of The University Of Minnesota Impedance plethysmograph
US3517999A (en) 1966-01-07 1970-06-30 Itt Optical strain gauge
US3584618A (en) 1969-03-17 1971-06-15 Beckman Instruments Inc A system and method for monitoring a progressive sequence of physiological conditions
US3620216A (en) 1969-06-25 1971-11-16 Abbott Lab Implant trocar
US3677260A (en) 1970-09-04 1972-07-18 Statham Instrument Inc Arrhythmia detector
US3805769A (en) 1971-08-27 1974-04-23 R Sessions Disposable electrode
US3845757A (en) 1972-07-12 1974-11-05 Minnesota Mining & Mfg Biomedical monitoring electrode
US3882853A (en) 1973-02-15 1975-05-13 Cardiodynamics Biomedical electrode
US3874368A (en) 1973-04-19 1975-04-01 Manfred Asrican Impedance plethysmograph having blocking system
US4121573A (en) 1973-10-04 1978-10-24 Goebel Fixture Co. Wireless cardiac monitoring system and electrode-transmitter therefor
US3942517A (en) 1973-12-03 1976-03-09 Dracard Limited Electrodes
US3972329A (en) 1974-11-25 1976-08-03 Kaufman John George Body electrode for electro-medical use
US4024312A (en) 1976-06-23 1977-05-17 Johnson & Johnson Pressure-sensitive adhesive tape having extensible and elastic backing composed of a block copolymer
US4077406A (en) 1976-06-24 1978-03-07 American Cyanamid Company Pellet implanter for animal treatment
US4216462A (en) 1978-03-06 1980-08-05 General Electric Company Patient monitoring and data processing system
JPS5746964Y2 (en) * 1978-03-29 1982-10-15
US4838273A (en) 1979-04-30 1989-06-13 Baxter International Inc. Medical electrode
US4674511A (en) 1979-04-30 1987-06-23 American Hospital Supply Corporation Medical electrode
US4300575A (en) * 1979-06-25 1981-11-17 Staodynamics, Inc. Air-permeable disposable electrode
US4522211A (en) 1979-12-06 1985-06-11 C. R. Bard, Inc. Medical electrode construction
US4358678A (en) 1980-11-19 1982-11-09 Hersey Products, Inc. Fiber optic transducer and method
US4409983A (en) 1981-08-20 1983-10-18 Albert David E Pulse measuring device
US4699146A (en) 1982-02-25 1987-10-13 Valleylab, Inc. Hydrophilic, elastomeric, pressure-sensitive adhesive
US4451254A (en) 1982-03-15 1984-05-29 Eli Lilly And Company Implant system
US4450527A (en) 1982-06-29 1984-05-22 Bomed Medical Mfg. Ltd. Noninvasive continuous cardiac output monitor
US4478223A (en) 1982-12-06 1984-10-23 Allor Douglas R Three dimensional electrocardiograph
US4692685A (en) 1984-03-14 1987-09-08 Blaze Kevin L Electrical measuring apparatus, and methods for determining the condition or identity of biological material
JPH0148014B2 (en) 1984-06-11 1989-10-17 Toshio Asai
DE3513400C2 (en) 1985-04-15 1993-09-09 Philips Patentverwaltung Gmbh, 20097 Hamburg, De
US4781200A (en) 1985-10-04 1988-11-01 Baker Donald A Ambulatory non-invasive automatic fetal monitoring system
US4669480A (en) 1985-10-16 1987-06-02 Murray Electronics Associates Limited Partnership Temperature indicating electrotherapy electrode/coil and method of use
US4661103A (en) 1986-03-03 1987-04-28 Engineering Development Associates, Ltd. Multiple implant injector
US4733107A (en) 1986-07-10 1988-03-22 Western Digital Corporation Low current high precision CMOS schmitt trigger circuit
US4730611A (en) 1986-09-02 1988-03-15 Absorbent Cotton Company Medical dressing device
FR2604890A1 (en) 1986-10-14 1988-04-15 Thomson Csf An optical detection simultaneous movements of the heart and respiration and its use synchronizing image acquisition devices is nuclear magnetic resonance
US4838279A (en) 1987-05-12 1989-06-13 Fore Don C Respiration monitor
US4850370A (en) 1987-07-22 1989-07-25 Dower Gordon E Method and apparatus for sensing and analyzing electrical activity of the human heart
US4911175A (en) 1987-09-17 1990-03-27 Diana Twyman Method for measuring total body cell mass and total extracellular mass by bioelectrical resistance and reactance
JPH0445778B2 (en) 1987-11-12 1992-07-27 Kao Corp
US4880004A (en) 1988-06-07 1989-11-14 Intermedics, Inc. Implantable cardiac stimulator with automatic gain control and bandpass filtering in feedback loop
US4955381A (en) 1988-08-26 1990-09-11 Cardiotronics, Inc. Multi-pad, multi-function electrode
US5012810A (en) 1988-09-22 1991-05-07 Minnesota Mining And Manufacturing Company Biomedical electrode construction
US5133355A (en) 1988-09-22 1992-07-28 Minnesota Mining And Manufacturing Company Biomedical electrode construction
US5168874A (en) 1989-02-15 1992-12-08 Jacob Segalowitz Wireless electrode structure for use in patient monitoring system
US5511553A (en) 1989-02-15 1996-04-30 Segalowitz; Jacob Device-system and method for monitoring multiple physiological parameters (MMPP) continuously and simultaneously
JPH0315502U (en) 1989-06-28 1991-02-15
US5769793A (en) 1989-09-08 1998-06-23 Steven M. Pincus System to determine a relative amount of patternness
US5050612A (en) 1989-09-12 1991-09-24 Matsumura Kenneth N Device for computer-assisted monitoring of the body
US5027824A (en) 1989-12-01 1991-07-02 Edmond Dougherty Method and apparatus for detecting, analyzing and recording cardiac rhythm disturbances
US5140985A (en) 1989-12-11 1992-08-25 Schroeder Jon M Noninvasive blood glucose measuring device
US5001632A (en) 1989-12-22 1991-03-19 Hall Tipping Justin Video game difficulty level adjuster dependent upon player's aerobic activity level during exercise
US5125412A (en) 1990-07-23 1992-06-30 Thornton William E Musculoskeletal activity monitor
US5113869A (en) 1990-08-21 1992-05-19 Telectronics Pacing Systems, Inc. Implantable ambulatory electrocardiogram monitor
US5063937A (en) 1990-09-12 1991-11-12 Wright State University Multiple frequency bio-impedance measurement system
US5271411A (en) 1990-09-21 1993-12-21 Colin Electronics Co., Ltd. Method and apparatus for ECG signal analysis and cardiac arrhythmia detection
US5642734A (en) 1990-10-04 1997-07-01 Microcor, Inc. Method and apparatus for noninvasively determining hematocrit
US5150708A (en) 1990-12-03 1992-09-29 Spacelabs, Inc. Tabbed defibrillator electrode pad
US5437285A (en) 1991-02-20 1995-08-01 Georgetown University Method and apparatus for prediction of sudden cardiac death by simultaneous assessment of autonomic function and cardiac electrical stability
US5632272A (en) 1991-03-07 1997-05-27 Masimo Corporation Signal processing apparatus
US5226417A (en) 1991-03-11 1993-07-13 Nellcor, Inc. Apparatus for the detection of motion transients
CA2111106C (en) 1991-06-12 2002-12-24 Ravi Shankar Detecting atherosclerosis in humans
NL9101489A (en) 1991-09-03 1993-04-01 Texas Instruments Holland Injector for hypodermically implanting an object into a living being.
US5309917A (en) 1991-09-12 1994-05-10 Drexel University System and method of impedance cardiography and heartbeat determination
US5335664A (en) 1991-09-17 1994-08-09 Casio Computer Co., Ltd. Monitor system and biological signal transmitter therefor
US5257627A (en) 1991-11-14 1993-11-02 Telmed, Inc. Portable non-invasive testing apparatus
US5353793A (en) 1991-11-25 1994-10-11 Oishi-Kogyo Company Sensor apparatus
US5291013A (en) 1991-12-06 1994-03-01 Alamed Corporation Fiber optical monitor for detecting normal breathing and heartbeat motion based on changes in speckle patterns
DE69215204D1 (en) 1992-01-29 1996-12-19 Hewlett Packard Gmbh A method and system for monitoring vital functions
US5301677A (en) 1992-02-06 1994-04-12 Cardiac Pacemakers, Inc. Arrhythmia detector using delta modulated turning point morphology of the ECG wave
ES2155068T3 (en) 1992-04-03 2001-05-01 Micromedical Ind Ltd Physiological supervision system.
US5241300B1 (en) 1992-04-24 1995-10-31 Johannes Buschmann Sids detection apparatus and methods
US5984102A (en) 1992-09-24 1999-11-16 Survivalink Corporation Medical electrode packaging technology
US5411530A (en) 1992-11-13 1995-05-02 Akhtar; Masood Sensing algorithm for anti-tachycardia devices using dual chamber sensing
US5362069A (en) 1992-12-03 1994-11-08 Heartbeat Corporation Combination exercise device/video game
US5375604A (en) 1992-12-11 1994-12-27 Siemens Medical Electronics, Inc. Transportable modular patient monitor
US5450845A (en) 1993-01-11 1995-09-19 Axelgaard; Jens Medical electrode system
US5558638A (en) 1993-04-30 1996-09-24 Healthdyne, Inc. Patient monitor and support system
US5406945A (en) * 1993-05-24 1995-04-18 Ndm Acquisition Corp. Biomedical electrode having a secured one-piece conductive terminal
US5607454A (en) * 1993-08-06 1997-03-04 Heartstream, Inc. Electrotherapy method and apparatus
US5464012A (en) 1993-09-13 1995-11-07 Hewlett-Packard Company Patient alarm detection using target mode
US5454377A (en) 1993-10-08 1995-10-03 The Ohio State University Method for measuring the myocardial electrical impedance spectrum
US5724025A (en) 1993-10-21 1998-03-03 Tavori; Itzchak Portable vital signs monitor
US5523742A (en) 1993-11-18 1996-06-04 The United States Of America As Represented By The Secretary Of The Army Motion sensor
US5544661A (en) 1994-01-13 1996-08-13 Charles L. Davis Real time ambulatory patient monitor
US5964703A (en) 1994-01-14 1999-10-12 E-Z-Em, Inc. Extravasation detection electrode patch
US5713367A (en) * 1994-01-26 1998-02-03 Cambridge Heart, Inc. Measuring and assessing cardiac electrical stability
US5447529A (en) 1994-01-28 1995-09-05 Philadelphia Heart Institute Method of using endocardial impedance for determining electrode-tissue contact, appropriate sites for arrhythmia ablation and tissue heating during ablation
US6067467A (en) 1994-02-07 2000-05-23 New York University EEG operative and post-operative patient monitoring method
US5458124A (en) 1994-02-08 1995-10-17 Stanko; Bruce E. Electrocardiographic signal monitoring system
US5598848A (en) 1994-03-31 1997-02-04 Ep Technologies, Inc. Systems and methods for positioning multiple electrode structures in electrical contact with the myocardium
US5575284A (en) 1994-04-01 1996-11-19 University Of South Florida Portable pulse oximeter
US5566671A (en) 1994-05-23 1996-10-22 Lyons; Chad Medical acoustic sensor receptacle
WO1995033372A1 (en) 1994-06-07 1995-12-14 Agrizap, Inc. A portable pest electrocution device with resistive switch sensor
US5518001A (en) 1994-06-17 1996-05-21 Pacesetter, Inc. Cardiac device with patient-triggered storage of physiological sensor data
US5560368A (en) 1994-11-15 1996-10-01 Berger; Ronald D. Methodology for automated QT variability measurement
US5772508A (en) 1995-09-28 1998-06-30 Amtex Co., Ltd. Game or play facilities controlled by physiological information
US5778882A (en) 1995-02-24 1998-07-14 Brigham And Women's Hospital Health monitoring system
US5564434A (en) 1995-02-27 1996-10-15 Medtronic, Inc. Implantable capacitive absolute pressure and temperature sensor
US5503157A (en) 1995-03-17 1996-04-02 Sramek; Bohumir System for detection of electrical bioimpedance signals
US5788682A (en) * 1995-04-28 1998-08-04 Maget; Henri J.R. Apparatus and method for controlling oxygen concentration in the vicinity of a wound
US6327487B1 (en) 1995-05-04 2001-12-04 Robert A. Stratbucker Bioelectric interface
US5807272A (en) 1995-10-31 1998-09-15 Worcester Polytechnic Institute Impedance spectroscopy system for ischemia monitoring and detection
US5678562A (en) 1995-11-09 1997-10-21 Burdick, Inc. Ambulatory physiological monitor with removable disk cartridge and wireless modem
US5944659A (en) 1995-11-13 1999-08-31 Vitalcom Inc. Architecture for TDMA medical telemetry system
US5748103A (en) 1995-11-13 1998-05-05 Vitalcom, Inc. Two-way TDMA telemetry system with power conservation features
US5803915A (en) 1995-12-07 1998-09-08 Ohmeda Inc. System for detection of probe dislodgement
US6035233A (en) 1995-12-11 2000-03-07 Intermedics Inc. Implantable medical device responsive to heart rate variability analysis
US5710376A (en) 1995-12-22 1998-01-20 International Business Machines Corporation Charged mass thin film condenser accelerometer
US6463328B1 (en) 1996-02-02 2002-10-08 Michael Sasha John Adaptive brain stimulation method and system
FI960636A (en) 1996-02-12 1997-08-13 Nokia Mobile Phones Ltd A method for monitoring the patient's state of health
US5833603A (en) 1996-03-13 1998-11-10 Lipomatrix, Inc. Implantable biosensing transponder
EP0944414B1 (en) 1996-07-11 2005-11-09 Medtronic, Inc. Minimally invasive implantable device for monitoring physiologic events
US6496715B1 (en) 1996-07-11 2002-12-17 Medtronic, Inc. System and method for non-invasive determination of optimal orientation of an implantable sensing device
US5687717A (en) 1996-08-06 1997-11-18 Tremont Medical, Inc. Patient monitoring system with chassis mounted or remotely operable modules and portable computer
US6141575A (en) 1996-08-16 2000-10-31 Price; Michael A. Electrode assemblies
US6112224A (en) 1996-09-20 2000-08-29 Georgia Tech Research Corporation Patient monitoring station using a single interrupt resource to support multiple measurement devices
DE19638585A1 (en) 1996-09-20 1998-03-26 Biotronik Mess & Therapieg Device for Rejektionsdiagnostik after organ transplantation
US5814079A (en) 1996-10-04 1998-09-29 Medtronic, Inc. Cardiac arrhythmia management by application of adnodal stimulation for hyperpolarization of myocardial cells
US6198394B1 (en) 1996-12-05 2001-03-06 Stephen C. Jacobsen System for remote monitoring of personnel
US5876353A (en) 1997-01-31 1999-03-02 Medtronic, Inc. Impedance monitor for discerning edema through evaluation of respiratory rate
US5957861A (en) 1997-01-31 1999-09-28 Medtronic, Inc. Impedance monitor for discerning edema through evaluation of respiratory rate
US6102856A (en) 1997-02-12 2000-08-15 Groff; Clarence P Wearable vital sign monitoring system
US6164284A (en) 1997-02-26 2000-12-26 Schulman; Joseph H. System of implantable devices for monitoring and/or affecting body parameters
US6208894B1 (en) 1997-02-26 2001-03-27 Alfred E. Mann Foundation For Scientific Research And Advanced Bionics System of implantable devices for monitoring and/or affecting body parameters
US6148233A (en) 1997-03-07 2000-11-14 Cardiac Science, Inc. Defibrillation system having segmented electrodes
US5959529A (en) 1997-03-07 1999-09-28 Kail, Iv; Karl A. Reprogrammable remote sensor monitoring system
JP4555919B2 (en) 1997-03-17 2010-10-06 ノンインベイシブ モニタリング システムズ インコーポレイテッド Feedback system of physiological sign
US7941534B2 (en) 1997-04-14 2011-05-10 Carlos De La Huerga System and method to authenticate users to computer systems
US5788643A (en) 1997-04-22 1998-08-04 Zymed Medical Instrumentation, Inc. Process for monitoring patients with chronic congestive heart failure
US6050267A (en) 1997-04-28 2000-04-18 American Cardiac Ablation Co. Inc. Catheter positioning system
FR2766376B1 (en) 1997-07-25 1999-10-22 Lhd Lab Hygiene Dietetique Device for therapeutic treatment of wounds
CA2300843A1 (en) 1997-08-19 1999-02-25 Philipp Lang Measurement of capillary related interstitial fluid using ultrasound methods and devices
US6259939B1 (en) 1997-08-20 2001-07-10 R. Z. Comparative Diagnostics Ltd. Electrocardiography electrodes holder including electrocardiograph electronics
US6090056A (en) 1997-08-27 2000-07-18 Emergency Medical Systems, Inc. Resuscitation and alert system
US6007532A (en) 1997-08-29 1999-12-28 3M Innovative Properties Company Method and apparatus for detecting loss of contact of biomedical electrodes with patient skin
US5836990A (en) 1997-09-19 1998-11-17 Medtronic, Inc. Method and apparatus for determining electrode/tissue contact
US6080106A (en) 1997-10-28 2000-06-27 Alere Incorporated Patient interface system with a scale
US6050951A (en) 1997-11-10 2000-04-18 Critikon Company, L.L.C. NIBP trigger in response to detected heart rate variability
US20020180605A1 (en) * 1997-11-11 2002-12-05 Ozguz Volkan H. Wearable biomonitor with flexible thinned integrated circuit
US20050096513A1 (en) 1997-11-11 2005-05-05 Irvine Sensors Corporation Wearable biomonitor with flexible thinned integrated circuit
US6129744A (en) 1997-12-04 2000-10-10 Vitatron Medical, B.V. Cardiac treatment system and method for sensing and responding to heart failure
US6047259A (en) 1997-12-30 2000-04-04 Medical Management International, Inc. Interactive method and system for managing physical exams, diagnosis and treatment protocols in a health care practice
US6125297A (en) 1998-02-06 2000-09-26 The United States Of America As Represented By The United States National Aeronautics And Space Administration Body fluids monitor
US6038464A (en) 1998-02-09 2000-03-14 Axelgaard Manufacturing Co., Ltd. Medical electrode
US5904708A (en) 1998-03-19 1999-05-18 Medtronic, Inc. System and method for deriving relative physiologic signals
US6579231B1 (en) 1998-03-27 2003-06-17 Mci Communications Corporation Personal medical monitoring unit and system
US5941831A (en) 1998-04-03 1999-08-24 Pacesetter, Inc. Method for diagnosing cardiac arrhythmias using interval irregularity
US5967995A (en) 1998-04-28 1999-10-19 University Of Pittsburgh Of The Commonwealth System Of Higher Education System for prediction of life-threatening cardiac arrhythmias
US6045513A (en) 1998-05-13 2000-04-04 Medtronic, Inc. Implantable medical device for tracking patient functional status
JP3507437B2 (en) * 1998-05-13 2004-03-15 シグナス, インコーポレイテッド Collection assembly for the transdermal sampling system
US6095991A (en) 1998-07-23 2000-08-01 Individual Monitoring Systems, Inc. Ambulatory body position monitor
EP1102560A4 (en) 1998-08-07 2003-03-12 Infinite Biomedical Technologi Implantable myocardial ischemia detection, indication and action technology
US6052615A (en) 1998-08-17 2000-04-18 Zymed Medical Instrumentation, Inc. Method and apparatus for sensing and analyzing electrical activity of the human heart using a four electrode arrangement
US6267730B1 (en) 1998-08-25 2001-07-31 Kenneth M. Pacunas Apnea detecting system
US6104949A (en) 1998-09-09 2000-08-15 Vitatron Medical, B.V. Medical device
US6343140B1 (en) 1998-09-11 2002-01-29 Quid Technologies Llc Method and apparatus for shooting using biometric recognition
WO2000017615A3 (en) 1998-09-23 2000-07-13 Keith Bridger Physiological sensing device
US6409674B1 (en) 1998-09-24 2002-06-25 Data Sciences International, Inc. Implantable sensor with wireless communication
US6402689B1 (en) 1998-09-30 2002-06-11 Sicel Technologies, Inc. Methods, systems, and associated implantable devices for dynamic monitoring of physiological and biological properties of tumors
US6306088B1 (en) 1998-10-03 2001-10-23 Individual Monitoring Systems, Inc. Ambulatory distributed recorders system for diagnosing medical disorders
US6358208B1 (en) 1998-11-21 2002-03-19 Philipp Lang Assessment of cardiovascular performance using ultrasound methods and devices that interrogate interstitial fluid
US6398727B1 (en) 1998-12-23 2002-06-04 Baxter International Inc. Method and apparatus for providing patient care
US6049730A (en) 1998-12-28 2000-04-11 Flaga Hf Method and apparatus for improving the accuracy of interpretation of ECG-signals
US6206831B1 (en) 1999-01-06 2001-03-27 Scimed Life Systems, Inc. Ultrasound-guided ablation catheter and methods of use
US6117077A (en) * 1999-01-22 2000-09-12 Del Mar Medical Systems, Llc Long-term, ambulatory physiological recorder
US6473640B1 (en) 1999-01-25 2002-10-29 Jay Erlebacher Implantable device and method for long-term detection and monitoring of congestive heart failure
DE19983911B4 (en) 1999-01-27 2018-09-06 Compumedics Sleep Pty. Ltd. Wachsamkeitsüberwachungssystem
US6305943B1 (en) 1999-01-29 2001-10-23 Biomed Usa, Inc. Respiratory sinus arrhythmia training system
US6212427B1 (en) 1999-02-02 2001-04-03 J&J Engineering Heart rate variability feedback monitor system
US6266554B1 (en) 1999-02-12 2001-07-24 Cardiac Pacemakers, Inc. System and method for classifying cardiac complexes
US6454707B1 (en) 1999-03-08 2002-09-24 Samuel W. Casscells, III Method and apparatus for predicting mortality in congestive heart failure patients
US6821249B2 (en) 1999-03-08 2004-11-23 Board Of Regents, The University Of Texas Temperature monitoring of congestive heart failure patients as an indicator of worsening condition
US6751498B1 (en) 1999-03-15 2004-06-15 The Johns Hopkins University Apparatus and method for non-invasive, passive fetal heart monitoring
GB2348707B (en) 1999-04-07 2003-07-09 Healthcare Technology Ltd Heart activity detection apparatus
US6450953B1 (en) 1999-04-15 2002-09-17 Nexan Limited Portable signal transfer unit
US6385473B1 (en) 1999-04-15 2002-05-07 Nexan Limited Physiological sensor device
US6416471B1 (en) 1999-04-15 2002-07-09 Nexan Limited Portable remote patient telemonitoring system
US6454708B1 (en) 1999-04-15 2002-09-24 Nexan Limited Portable remote patient telemonitoring system using a memory card or smart card
US6494829B1 (en) 1999-04-15 2002-12-17 Nexan Limited Physiological sensor array
US7577475B2 (en) 1999-04-16 2009-08-18 Cardiocom System, method, and apparatus for combining information from an implanted device with information from a patient monitoring apparatus
US6290646B1 (en) 1999-04-16 2001-09-18 Cardiocom Apparatus and method for monitoring and communicating wellness parameters of ambulatory patients
US6312378B1 (en) 1999-06-03 2001-11-06 Cardiac Intelligence Corporation System and method for automated collection and analysis of patient information retrieved from an implantable medical device for remote patient care
US7454359B2 (en) 1999-06-23 2008-11-18 Visicu, Inc. System and method for displaying a health status of hospitalized patients
US6287252B1 (en) 1999-06-30 2001-09-11 Monitrak Patient monitor
US7149773B2 (en) 1999-07-07 2006-12-12 Medtronic, Inc. System and method of automated invoicing for communications between an implantable medical device and a remote computer system or health care provider
US6450820B1 (en) 1999-07-09 2002-09-17 The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration Method and apparatus for encouraging physiological self-regulation through modulation of an operator's control input to a video game or training simulator
US6347245B1 (en) 1999-07-14 2002-02-12 Medtronic, Inc. Medical device ECG marker for use in compressed data system
CA2314517A1 (en) 1999-07-26 2001-01-26 Gust H. Bardy System and method for determining a reference baseline of individual patient status for use in an automated collection and analysis patient care system
US6221011B1 (en) 1999-07-26 2001-04-24 Cardiac Intelligence Corporation System and method for determining a reference baseline of individual patient status for use in an automated collection and analysis patient care system
JP2001052930A (en) 1999-08-06 2001-02-23 Tdk Corp Laminated inductor and manufacture thereof
US6442422B1 (en) 1999-08-11 2002-08-27 Ge Medical Systems Information Technologies, Inc. Compliance monitoring apparatus and method
US6721594B2 (en) 1999-08-24 2004-04-13 Cardiac Pacemakers, Inc. Arrythmia display
US6790178B1 (en) 1999-09-24 2004-09-14 Healthetech, Inc. Physiological monitor and associated computation, display and communication unit
US6272377B1 (en) 1999-10-01 2001-08-07 Cardiac Pacemakers, Inc. Cardiac rhythm management system with arrhythmia prediction and prevention
US6350237B1 (en) 1999-11-05 2002-02-26 General Electric Company Method and apparatus for monitoring fetal status data
US6527729B1 (en) 1999-11-10 2003-03-04 Pacesetter, Inc. Method for monitoring patient using acoustic sensor
US6942622B1 (en) 1999-11-10 2005-09-13 Pacesetter, Inc. Method for monitoring autonomic tone
US6480733B1 (en) 1999-11-10 2002-11-12 Pacesetter, Inc. Method for monitoring heart failure
US6600949B1 (en) 1999-11-10 2003-07-29 Pacesetter, Inc. Method for monitoring heart failure via respiratory patterns
US6368284B1 (en) 1999-11-16 2002-04-09 Cardiac Intelligence Corporation Automated collection and analysis patient care system and method for diagnosing and monitoring myocardial ischemia and outcomes thereof
US6277078B1 (en) 1999-11-19 2001-08-21 Remon Medical Technologies, Ltd. System and method for monitoring a parameter associated with the performance of a heart
US7127370B2 (en) 2000-01-07 2006-10-24 Nocwatch International Inc. Attitude indicator and activity monitoring device
US6970742B2 (en) 2000-01-11 2005-11-29 Savacor, Inc. Method for detecting, diagnosing, and treating cardiovascular disease
US6714813B2 (en) 2000-01-21 2004-03-30 Tanita Corporation Method for measuring the degree of edema and apparatus using the same
US6551251B2 (en) 2000-02-14 2003-04-22 The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration Passive fetal heart monitoring system
US6893396B2 (en) 2000-03-01 2005-05-17 I-Medik, Inc. Wireless internet bio-telemetry monitoring system and interface
US6699200B2 (en) 2000-03-01 2004-03-02 Medtronic, Inc. Implantable medical device with multi-vector sensing electrodes
GB0005247D0 (en) 2000-03-03 2000-04-26 Btg Int Ltd Electrical impedance method for differentiating tissue types
US6584343B1 (en) 2000-03-15 2003-06-24 Resolution Medical, Inc. Multi-electrode panel system for sensing electrical activity of the heart
US6871211B2 (en) 2000-03-28 2005-03-22 Ge Medical Systems Information Technologies, Inc. Intranet-based medical data distribution system
JP2003530184A (en) 2000-04-17 2003-10-14 ビボメトリックス,インコーポレイテッド Monitoring device, system and storage medium for monitoring a physiological signs ambulatory
WO2001086605A3 (en) 2000-05-05 2002-03-28 Hill Rom Services Inc Hospital monitoring and control system and method
FR2808609B1 (en) 2000-05-05 2006-02-10 Univ Rennes And device for detecting abnormal situations METHOD
US6478800B1 (en) 2000-05-08 2002-11-12 Depuy Acromed, Inc. Medical installation tool
US6572557B2 (en) 2000-05-09 2003-06-03 Pacesetter, Inc. System and method for monitoring progression of cardiac disease state using physiologic sensors
US20040049132A1 (en) 2000-06-15 2004-03-11 The Procter & Gamble Company Device for body activity detection and processing
US7261690B2 (en) 2000-06-16 2007-08-28 Bodymedia, Inc. Apparatus for monitoring health, wellness and fitness
US6605038B1 (en) 2000-06-16 2003-08-12 Bodymedia, Inc. System for monitoring health, wellness and fitness
US20060122474A1 (en) 2000-06-16 2006-06-08 Bodymedia, Inc. Apparatus for monitoring health, wellness and fitness
US6480734B1 (en) 2000-06-30 2002-11-12 Cardiac Science Inc. Cardiac arrhythmia detector using ECG waveform-factor and its irregularity
US6569160B1 (en) 2000-07-07 2003-05-27 Biosense, Inc. System and method for detecting electrode-tissue contact
US6602201B1 (en) 2000-07-10 2003-08-05 Cardiodynamics International Corporation Apparatus and method for determining cardiac output in a living subject
US6636754B1 (en) 2000-07-10 2003-10-21 Cardiodynamics International Corporation Apparatus and method for determining cardiac output in a living subject
US7149576B1 (en) 2000-07-10 2006-12-12 Cardiodynamics International Corporation Apparatus and method for defibrillation of a living subject
US6659947B1 (en) 2000-07-13 2003-12-09 Ge Medical Systems Information Technologies, Inc. Wireless LAN architecture for integrated time-critical and non-time-critical services within medical facilities
US20020032581A1 (en) 2000-07-17 2002-03-14 Reitberg Donald P. Single-patient drug trials used with accumulated database: risk of habituation
US7933642B2 (en) * 2001-07-17 2011-04-26 Rud Istvan Wireless ECG system
JP3977983B2 (en) 2000-07-31 2007-09-19 株式会社タニタ Dehydrated state determining apparatus according to the bioelectrical impedance measurement
US20020099277A1 (en) 2000-09-12 2002-07-25 Nexan Limited Disposable vital signs monitoring sensor band with removable alignment sheet
DE10046075A1 (en) 2000-09-15 2002-04-04 Friendly Sensors Ag Apparatus and method for generating measurement data
US6572636B1 (en) 2000-09-19 2003-06-03 Robert Sean Hagen Pulse sensing patch and associated methods
US6752151B2 (en) 2000-09-25 2004-06-22 Respironics, Inc. Method and apparatus for providing variable positive airway pressure
US6490478B1 (en) 2000-09-25 2002-12-03 Cardiac Science Inc. System and method for complexity analysis-based cardiac tachyarrhythmia detection
US6665559B2 (en) 2000-10-06 2003-12-16 Ge Medical Systems Information Technologies, Inc. Method and apparatus for perioperative assessment of cardiovascular risk
CA2425224A1 (en) 2000-10-10 2002-04-18 Alan Remy Magill Health monitoring
US20020045836A1 (en) 2000-10-16 2002-04-18 Dima Alkawwas Operation of wireless biopotential monitoring system
FI119716B (en) 2000-10-18 2009-02-27 Polar Electro Oy The electrode and the heart rate measurement arrangement
US6738671B2 (en) 2000-10-26 2004-05-18 Medtronic, Inc. Externally worn transceiver for use with an implantable medical device
US6978177B1 (en) 2000-11-14 2005-12-20 Cardiac Pacemakers, Inc. Method and apparatus for using atrial discrimination algorithms to determine optimal pacing therapy and therapy timing
US6658300B2 (en) 2000-12-18 2003-12-02 Biosense, Inc. Telemetric reader/charger device for medical sensor
WO2002052480A1 (en) 2000-12-22 2002-07-04 Trac Medical Solutions, Inc. Dynamic electronic chain-of-trust document with audit trail
DE10103330B4 (en) * 2001-01-25 2009-04-30 Siemens Ag A medical system for monitoring a measured value relating to the blood coagulation of a patient
US6821256B2 (en) * 2001-02-01 2004-11-23 Mayo Foundation For Medical Education And Research Non-alternating beat-to-beat fluctuations in T wave morphology
JP3927495B2 (en) 2001-02-08 2007-06-06 ミニ−ミッター カンパニー,インコーポレイテッドMini−Mitter Company, Incorporated Skin patch material with a built-in temperature sensor
US6749566B2 (en) 2001-02-14 2004-06-15 Draeger Medical Systems, Inc. Patient monitoring area network
US6595929B2 (en) 2001-03-30 2003-07-22 Bodymedia, Inc. System for monitoring health, wellness and fitness having a method and apparatus for improved measurement of heat flow
WO2002080762A1 (en) 2001-04-06 2002-10-17 Medic4All Inc. A physiological monitoring system for a computational device of a human subject
US20050283197A1 (en) 2001-04-10 2005-12-22 Daum Douglas R Systems and methods for hypotension
EP1249691A1 (en) 2001-04-11 2002-10-16 Omron Corporation Electronic clinical thermometer
US6453186B1 (en) 2001-04-13 2002-09-17 Ge Medical Systems Information Technologies, Inc. Electrocardiogram electrode patch
US6665385B2 (en) 2001-04-23 2003-12-16 Cardionet, Inc. Medical monitoring system having multipath communications capability
US6641542B2 (en) 2001-04-30 2003-11-04 Medtronic, Inc. Method and apparatus to detect and treat sleep respiratory events
US7702394B2 (en) 2001-05-01 2010-04-20 Intrapace, Inc. Responsive gastric stimulator
US6894204B2 (en) 2001-05-02 2005-05-17 3M Innovative Properties Company Tapered stretch removable adhesive articles and methods
US20060161073A1 (en) 2001-05-03 2006-07-20 Singer Michael G In vitro and in vivo assessment of organs and tissue and use, transplant, freshness and tissue conditions
US7003346B2 (en) 2001-05-03 2006-02-21 Singer Michaeal G Method for illness and disease determination and management
US20070104840A1 (en) 2001-05-03 2007-05-10 Singer Michael G Method and system for the determination of palatability
US6587715B2 (en) 2001-05-03 2003-07-01 The Nutrition Solutions Corporation Assessment of organs for transplant, xenotransplant, and predicting time of death
US7242306B2 (en) 2001-05-08 2007-07-10 Hill-Rom Services, Inc. Article locating and tracking apparatus and method
US6622042B1 (en) 2001-05-09 2003-09-16 Pacesetter, Inc. Implantable cardiac stimulation device and method utilizing electrogram spectral analysis for therapy administration
US6952695B1 (en) 2001-05-15 2005-10-04 Global Safety Surveillance, Inc. Spontaneous adverse events reporting
JP2005502937A (en) 2001-05-15 2005-01-27 サイコジェニックス・インコーポレーテッドPsychogenics Inc. System and method for monitoring the behavior and Information Engineering
US6701271B2 (en) 2001-05-17 2004-03-02 International Business Machines Corporation Method and apparatus for using physical characteristic data collected from two or more subjects
US20050065445A1 (en) 2001-05-22 2005-03-24 Arzbaecher Robert C. Cardiac arrest monitor and alarm system
US6816744B2 (en) 2001-05-29 2004-11-09 Reproductive Health Technologies, Inc. Device and system for remote for in-clinic trans-abdominal/vaginal/cervical acquisition, and detection, analysis, and communication of maternal uterine and maternal and fetal cardiac and fetal brain activity from electrical signals
US6653014B2 (en) * 2001-05-30 2003-11-25 Birch Point Medical, Inc. Power sources for iontophoretic drug delivery systems
US6795722B2 (en) 2001-06-18 2004-09-21 Neotech Products, Inc. Electrode sensor package and application to the skin of a newborn or infant
US7044911B2 (en) 2001-06-29 2006-05-16 Philometron, Inc. Gateway platform for biological monitoring and delivery of therapeutic compounds
WO2003009221A3 (en) 2001-07-20 2003-12-04 Hill Rom Services Inc Badge for a locating and tracking system
DE60143115D1 (en) 2001-09-28 2010-11-04 Csem Ct Suisse Electronique Method and apparatus for pulse measurement
DE10148440A1 (en) 2001-10-01 2003-04-17 Inflow Dynamics Inc Implantable medical device for monitoring congestive heart failure comprises electrodes for measuring lung and heart tissue impedance, with an increase in impedance above a threshold value triggering an alarm
US20090182204A1 (en) 2001-10-04 2009-07-16 Semler Herbert J Body composition, circulation, and vital signs monitor and method
US20030069510A1 (en) 2001-10-04 2003-04-10 Semler Herbert J. Disposable vital signs monitor
US20030087244A1 (en) 2001-10-09 2003-05-08 Vitivity, Inc Diagnosis and treatment of vascular disease
US6748254B2 (en) 2001-10-12 2004-06-08 Nellcor Puritan Bennett Incorporated Stacked adhesive optical sensor
US20030093298A1 (en) 2001-10-12 2003-05-15 Javier Hernandez System and method for providing secure remote access to patient files by authenticating personnel with biometric data
US6748269B2 (en) 2001-10-17 2004-06-08 Cardiac Pacemakers, Inc. Algorithm for discrimination of 1:1 tachycardias
US6810282B2 (en) 2001-10-25 2004-10-26 GE Medical Systems Information Technolgies, Inc. Method and apparatus for dynamically selecting an electrocardiogram compression process based on computerized analysis of cardiac rhythm and contour
FR2831450B1 (en) 2001-10-30 2004-07-30 Ela Medical Sa Implantable medical device active for the treatment of cardiac rhythm disorders, including improved means of detection of atrial arrhythmias
US20030083559A1 (en) * 2001-10-31 2003-05-01 Thompson David L. Non-contact monitor
US7054679B2 (en) 2001-10-31 2006-05-30 Robert Hirsh Non-invasive method and device to monitor cardiac parameters
US6577139B2 (en) 2001-11-06 2003-06-10 Keystone Thermometrics Impedance converter circuit
US6894456B2 (en) 2001-11-07 2005-05-17 Quallion Llc Implantable medical power module
US6980851B2 (en) 2001-11-15 2005-12-27 Cardiac Pacemakers, Inc. Method and apparatus for determining changes in heart failure status
US6643541B2 (en) * 2001-12-07 2003-11-04 Motorola, Inc Wireless electromyography sensor and system
US20030149349A1 (en) 2001-12-18 2003-08-07 Jensen Thomas P. Integral patch type electronic physiological sensor
US20030143544A1 (en) 2002-01-09 2003-07-31 Vitivity, Inc. Diagnosis and treatment of vascular disease
US6980852B2 (en) 2002-01-25 2005-12-27 Subqiview Inc. Film barrier dressing for intravascular tissue monitoring system
US6912414B2 (en) 2002-01-29 2005-06-28 Southwest Research Institute Electrode systems and methods for reducing motion artifact
US6645153B2 (en) 2002-02-07 2003-11-11 Pacesetter, Inc. System and method for evaluating risk of mortality due to congestive heart failure using physiologic sensors
US6936006B2 (en) 2002-03-22 2005-08-30 Novo Nordisk, A/S Atraumatic insertion of a subcutaneous device
CA2379268A1 (en) 2002-03-26 2003-09-26 Izmail Batkin Skin impedance matched biopotential electrode
US20030187370A1 (en) 2002-03-27 2003-10-02 Kodama Roy K. Uterine contraction sensing system and method
WO2003082403A3 (en) 2002-03-27 2004-01-08 Cvrx Inc Devices and methods for cardiovascular reflex control via coupled electrodes
US7654901B2 (en) 2002-04-10 2010-02-02 Breving Joel S Video game system using bio-feedback devices
US7136703B1 (en) 2002-04-16 2006-11-14 Pacesetter, Inc. Programmer and surface ECG system with wireless communication
EP1501414A1 (en) 2002-05-07 2005-02-02 Izmail Batkin Remote monitoring of cardiac electrical activity using a cell phone device
US20030221687A1 (en) 2002-05-09 2003-12-04 William Kaigler Medication and compliance management system and method
US6922586B2 (en) 2002-05-20 2005-07-26 Richard J. Davies Method and system for detecting electrophysiological changes in pre-cancerous and cancerous tissue
US6906530B2 (en) 2002-05-30 2005-06-14 D.J. Geisel Technology, Inc. Apparatus and method to detect moisture
US7047067B2 (en) 2002-05-31 2006-05-16 Uab Research Foundation Apparatus, methods, and computer program products for evaluating a risk of cardiac arrhythmias from restitution properties
EP1521615A4 (en) 2002-06-11 2010-11-03 Jeffrey A Matos System for cardiac resuscitation
US7257438B2 (en) 2002-07-23 2007-08-14 Datascope Investment Corp. Patient-worn medical monitoring device
US7027862B2 (en) 2002-07-25 2006-04-11 Medtronic, Inc. Apparatus and method for transmitting an electrical signal in an implantable medical device
US20040019292A1 (en) 2002-07-29 2004-01-29 Drinan Darrel Dean Method and apparatus for bioelectric impedance based identification of subjects
GB2391625A (en) 2002-08-09 2004-02-11 Diagnostic Ultrasound Europ B Instantaneous ultrasonic echo measurement of bladder urine volume with a limited number of ultrasound beams
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
CA2560323C (en) * 2004-03-22 2014-01-07 Bodymedia, Inc. Non-invasive temperature monitoring device
US7020508B2 (en) 2002-08-22 2006-03-28 Bodymedia, Inc. Apparatus for detecting human physiological and contextual information
US7294105B1 (en) 2002-09-03 2007-11-13 Cheetah Omni, Llc System and method for a wireless medical communication system
US7118531B2 (en) 2002-09-24 2006-10-10 The Johns Hopkins University Ingestible medical payload carrying capsule with wireless communication
US20040073094A1 (en) 2002-10-15 2004-04-15 Baker Donald A. Fetal monitoring systems with ambulatory patient units and telemetric links for improved uses
GB2394294A (en) 2002-10-18 2004-04-21 Cambridge Neurotechnology Ltd Cardiac sensor with accelerometer
GB0224425D0 (en) 2002-10-21 2002-11-27 Univ Leicester Method for prediction of cardiac disease
US6878121B2 (en) 2002-11-01 2005-04-12 David T. Krausman Sleep scoring apparatus and method
US7130679B2 (en) 2002-11-20 2006-10-31 Medtronic, Inc. Organ rejection monitoring
US20040106951A1 (en) 2002-11-22 2004-06-03 Edman Carl Frederick Use of electric fields to minimize rejection of implanted devices and materials
US20040100376A1 (en) 2002-11-26 2004-05-27 Kimberly-Clark Worldwide, Inc. Healthcare monitoring system
EP1571982A1 (en) 2002-11-27 2005-09-14 Z-Tech (Canada) Inc. Apparatus for determining adequacy of electrode-to-skin contact and electrode quality for bioelectrical measurements
US7072718B2 (en) 2002-12-03 2006-07-04 Cardiac Pacemakers, Inc. Antenna systems for implantable medical device telemetry
US8814793B2 (en) 2002-12-03 2014-08-26 Neorad As Respiration monitor
US7986994B2 (en) 2002-12-04 2011-07-26 Medtronic, Inc. Method and apparatus for detecting change in intrathoracic electrical impedance
WO2004054430A3 (en) 2002-12-16 2004-10-07 Tal Davidson Device, system and method for selective activation of in vivo sensors
US7452334B2 (en) 2002-12-16 2008-11-18 The Regents Of The University Of Michigan Antenna stent device for wireless, intraluminal monitoring
US8043213B2 (en) * 2002-12-18 2011-10-25 Cardiac Pacemakers, Inc. Advanced patient management for triaging health-related data using color codes
US7468032B2 (en) 2002-12-18 2008-12-23 Cardiac Pacemakers, Inc. Advanced patient management for identifying, displaying and assisting with correlating health-related data
US20040143170A1 (en) 2002-12-20 2004-07-22 Durousseau Donald R. Intelligent deception verification system
US7395117B2 (en) 2002-12-23 2008-07-01 Cardiac Pacemakers, Inc. Implantable medical device having long-term wireless capabilities
GB0230361D0 (en) 2002-12-27 2003-02-05 Koninkl Philips Electronics Nv Electrode arrangement
US20040133079A1 (en) 2003-01-02 2004-07-08 Mazar Scott Thomas System and method for predicting patient health within a patient management system
DE10300735A1 (en) 2003-01-11 2004-07-22 Corscience Gmbh & Co.Kg A method for detecting a fibrillation condition and apparatus for defibrillation
US7423526B2 (en) 2003-01-29 2008-09-09 Despotis George J Integrated patient diagnostic and identification system
US7445605B2 (en) 2003-01-31 2008-11-04 The Board Of Trustees Of The Leland Stanford Junior University Detection of apex motion for monitoring cardiac dysfunction
US6956572B2 (en) 2003-02-10 2005-10-18 Siemens Medical Solutions Health Services Corporation Patient medical parameter user interface system
EP1594551A2 (en) 2003-02-19 2005-11-16 Sicel Technologies, Inc. In vivo fluorescence sensors, systems, and related methods operating in conjunction with fluorescent analytes
JP2006520657A (en) 2003-03-21 2006-09-14 ウェルチ・アリン・インコーポレーテッド Personal status physiological monitoring systems and structures, and monitoring method
US20040199056A1 (en) 2003-04-03 2004-10-07 International Business Machines Corporation Body monitoring using local area wireless interfaces
US7134999B2 (en) 2003-04-04 2006-11-14 Dexcom, Inc. Optimized sensor geometry for an implantable glucose sensor
US20040215240A1 (en) 2003-04-11 2004-10-28 Lovett Eric G. Reconfigurable subcutaneous cardiac device
US7130684B2 (en) 2003-04-30 2006-10-31 Medtronic, Inc. Method and apparatus for improving ventricular status using the force interval relationship
US20040225203A1 (en) 2003-05-06 2004-11-11 Jemison Mae C. Real-time and simultaneous monitoring of multiple parameters from multiple living beings
US20040225199A1 (en) 2003-05-08 2004-11-11 Evanyk Shane Walter Advanced physiological monitoring systems and methods
US7149574B2 (en) 2003-06-09 2006-12-12 Palo Alto Investors Treatment of conditions through electrical modulation of the autonomic nervous system
US20050158539A1 (en) 2003-06-25 2005-07-21 Andover Coated Products, Inc. Pressure-sensitive adhesive tapes
US7171258B2 (en) 2003-06-25 2007-01-30 Cardiac Pacemakers, Inc. Method and apparatus for trending a physiological cardiac parameter
US7142907B2 (en) 2003-07-01 2006-11-28 Ge Medical Systems Information Technologies, Inc. Method and apparatus for algorithm fusion of high-resolution electrocardiograms
US7145027B2 (en) 2003-07-08 2006-12-05 W.C. Heraeus Gmbh & Co. Kg Method for producing chlorotris(triphenylphosphine) rhodium (i)
US20060195020A1 (en) 2003-08-01 2006-08-31 Martin James S Methods, systems, and apparatus for measuring a pulse rate
US20050131288A1 (en) 2003-08-15 2005-06-16 Turner Christopher T. Flexible, patient-worn, integrated, self-contained sensor systems for the acquisition and monitoring of physiologic data
EP2382920A1 (en) 2003-08-20 2011-11-02 Philometron, Inc. Hydration monitoring
US20070299325A1 (en) 2004-08-20 2007-12-27 Brian Farrell Physiological status monitoring system
US7194306B1 (en) 2003-09-05 2007-03-20 Pacesetter, Inc. Cardiac optimization through low-frequency analysis of hemodynamic variables
EP1512371B1 (en) 2003-09-05 2007-01-03 Tanita Corporation Bioelectrical impedance measuring apparatus
WO2005025405A3 (en) 2003-09-10 2005-06-30 Maternus Partners Ltd Periumbilical infant ecg sensor and monitoring system
US20050059867A1 (en) 2003-09-13 2005-03-17 Cheng Chung Yuan Method for monitoring temperature of patient
US7088242B2 (en) 2003-09-16 2006-08-08 International Business Machines Corporation Collective personal articles tracking
US20050187482A1 (en) 2003-09-16 2005-08-25 O'brien David Implantable wireless sensor
US7616988B2 (en) 2003-09-18 2009-11-10 Cardiac Pacemakers, Inc. System and method for detecting an involuntary muscle movement disorder
US7129836B2 (en) 2003-09-23 2006-10-31 Ge Medical Systems Information Technologies, Inc. Wireless subject monitoring system
US7225024B2 (en) 2003-09-30 2007-05-29 Cardiac Pacemakers, Inc. Sensors having protective eluting coating and method therefor
US8428717B2 (en) 2003-10-14 2013-04-23 Medtronic, Inc. Method and apparatus for monitoring tissue fluid content for use in an implantable cardiac device
US8467876B2 (en) 2003-10-15 2013-06-18 Rmx, Llc Breathing disorder detection and therapy delivery device and method
WO2005046446A3 (en) 2003-11-10 2006-08-31 Darrel Dean Drinan Structures and devices for parenteral drug delivery and diagnostic sampling
CA2545881C (en) 2003-11-18 2014-04-08 Vivometrics, Inc. Method and system for processing data from ambulatory physiological monitoring
EP1691683B1 (en) 2003-11-26 2014-12-31 CardioNet, Inc. System and method for processing and presenting arrhythmia information to facilitate heart arrhythmia identification and treatment
US20050124901A1 (en) 2003-12-05 2005-06-09 Misczynski Dale J. Method and apparatus for electrophysiological and hemodynamic real-time assessment of cardiovascular fitness of a user
JP4845739B2 (en) 2003-12-12 2011-12-28 フィロメトロン,インコーポレイティド Multiplex section-type non-oral drug delivery device
US20050137626A1 (en) 2003-12-19 2005-06-23 Pastore Joseph M. Drug delivery system and method employing external drug delivery device in conjunction with computer network
US20050137464A1 (en) 2003-12-23 2005-06-23 Bomba Frank C. Wireless sensor and sensor initialization device and method
US20050148895A1 (en) 2004-01-06 2005-07-07 Misczynski Dale J. Method and apparatus for ECG derived sleep monitoring of a user
EP1708613B1 (en) 2004-01-15 2011-12-14 Koninklijke Philips Electronics N.V. Adaptive physiological monitoring system and methods of using the same
EP1720446B1 (en) 2004-02-27 2010-07-14 Philips Electronics N.V. Wearable wireless device for monitoring, analyzing and communicating physiological status
US7277741B2 (en) 2004-03-09 2007-10-02 Nellcor Puritan Bennett Incorporated Pulse oximetry motion artifact rejection using near infrared absorption by water
JP2005253840A (en) 2004-03-15 2005-09-22 Tanita Corp Skin condition estimating device
US7805196B2 (en) 2004-03-16 2010-09-28 Medtronic, Inc. Collecting activity information to evaluate therapy
EP1737341A4 (en) 2004-03-24 2009-07-29 Noninvasive Medical Technologi Thoracic impedance monitor and electrode array and method of use
CN1933871A (en) 2004-03-25 2007-03-21 皇家飞利浦电子股份有限公司 Defibrillation electrode having drug delivery capability
US20050215844A1 (en) 2004-03-25 2005-09-29 Ten Eyck Lawrence G Patient carestation
US7505814B2 (en) 2004-03-26 2009-03-17 Pacesetter, Inc. System and method for evaluating heart failure based on ventricular end-diastolic volume using an implantable medical device
US20050228244A1 (en) 2004-04-07 2005-10-13 Triage Wireless, Inc. Small-scale, vital-signs monitoring device, system and method
US7238159B2 (en) 2004-04-07 2007-07-03 Triage Wireless, Inc. Device, system and method for monitoring vital signs
US20080058614A1 (en) 2005-09-20 2008-03-06 Triage Wireless, Inc. Wireless, internet-based system for measuring vital signs from a plurality of patients in a hospital or medical clinic
US20050261598A1 (en) 2004-04-07 2005-11-24 Triage Wireless, Inc. Patch sensor system for measuring vital signs
US20050228238A1 (en) 2004-04-09 2005-10-13 Arnold Monitzer Patient parameter automatic acquisition system
WO2005104930A1 (en) 2004-04-30 2005-11-10 Biowatch Pty Ltd Animal health monitoring system
US7470232B2 (en) 2004-05-04 2008-12-30 General Electric Company Method and apparatus for non-invasive ultrasonic fetal heart rate monitoring
US7899526B2 (en) 2004-05-10 2011-03-01 Regents Of The University Of Minnesota Portable device for monitoring electrocardiographic signals and indices of blood flow
US7324845B2 (en) 2004-05-17 2008-01-29 Beth Israel Deaconess Medical Center Assessment of sleep quality and sleep disordered breathing based on cardiopulmonary coupling
US20050261743A1 (en) 2004-05-19 2005-11-24 Kroll Mark W System and method for automated fluid monitoring
KR100592934B1 (en) 2004-05-21 2006-06-23 한국전자통신연구원 Wearable physiological signal detection module and measurement apparatus with the same
US7333850B2 (en) 2004-05-28 2008-02-19 University Of Florida Research Foundation, Inc. Maternal-fetal monitoring system
US20050277841A1 (en) 2004-06-10 2005-12-15 Adnan Shennib Disposable fetal monitor patch
US7548785B2 (en) 2004-06-10 2009-06-16 Pacesetter, Inc. Collecting and analyzing sensed information as a trend of heart failure progression or regression
KR100624425B1 (en) 2004-06-17 2006-09-19 삼성전자주식회사 Integrated multiple electrodes for bio signal measurement, method and apparatus for bio signal measurement using the same, and method of seaching leads using the same
WO2006009767A1 (en) * 2004-06-18 2006-01-26 Neuronetrix, Inc Wireless electrode for biopotential measurement
US7206630B1 (en) 2004-06-29 2007-04-17 Cleveland Medical Devices, Inc Electrode patch and wireless physiological measurement system and method
WO2006008745A3 (en) 2004-07-23 2007-10-18 Intercure Ltd Apparatus and method for breathing pattern determination using a non-contact microphone
US20060047215A1 (en) 2004-09-01 2006-03-02 Welch Allyn, Inc. Combined sensor assembly
US20060058593A1 (en) 2004-09-02 2006-03-16 Drinan Darrel D Monitoring platform for detection of hypovolemia, hemorrhage and blood loss
US20060066449A1 (en) 2004-09-08 2006-03-30 Industrial Widget Works Company RFMON: devices and methods for wireless monitoring of patient vital signs through medical sensor readings from passive RFID tags
US20060135858A1 (en) 2004-09-13 2006-06-22 International Business Machines Corporation Displaying information related to a physical parameter of an individual
US8271093B2 (en) 2004-09-17 2012-09-18 Cardiac Pacemakers, Inc. Systems and methods for deriving relative physiologic measurements using a backend computing system
US20070106132A1 (en) * 2004-09-28 2007-05-10 Elhag Sammy I Monitoring device, method and system
US7840275B2 (en) 2004-10-01 2010-11-23 Medtronic, Inc. In-home remote monitor with smart repeater, memory and emergency event management
US7341560B2 (en) 2004-10-05 2008-03-11 Rader, Fishman & Grauer Pllc Apparatuses and methods for non-invasively monitoring blood parameters
US7609145B2 (en) 2004-10-06 2009-10-27 Martis Ip Holdings, Llc Test authorization system
US20080058656A1 (en) 2004-10-08 2008-03-06 Costello Benedict J Electric tomography
US7865236B2 (en) 2004-10-20 2011-01-04 Nervonix, Inc. Active electrode, bio-impedance based, tissue discrimination system and methods of use
US7996075B2 (en) 2004-10-20 2011-08-09 Cardionet, Inc. Monitoring physiological activity using partial state space reconstruction
US7212849B2 (en) 2004-10-28 2007-05-01 Cardiac Pacemakers, Inc. Methods and apparatuses for arrhythmia detection and classification using wireless ECG
US7917199B2 (en) 2004-11-02 2011-03-29 Medtronic, Inc. Patient event marking in combination with physiological signals
US8768446B2 (en) 2004-11-02 2014-07-01 Medtronic, Inc. Clustering with combined physiological signals
WO2006050602A1 (en) 2004-11-09 2006-05-18 Cybiocare Inc. Method and apparatus for the reduction of spurious effects on physiological measurements
US7751868B2 (en) 2004-11-12 2010-07-06 Philips Electronics Ltd Integrated skin-mounted multifunction device for use in image-guided surgery
JP2006343306A (en) 2004-11-15 2006-12-21 Denso Corp Gas concentration detector
US20060116592A1 (en) 2004-12-01 2006-06-01 Medtronic, Inc. Method and apparatus for detection and monitoring of T-wave alternans
US8041418B2 (en) 2004-12-17 2011-10-18 Medtronic, Inc. System and method for regulating cardiac triggered therapy to the brain
US8108046B2 (en) 2004-12-17 2012-01-31 Medtronic, Inc. System and method for using cardiac events to trigger therapy for treating nervous system disorders
US8734341B2 (en) 2004-12-20 2014-05-27 Ipventure, Inc. Method and apparatus to sense hydration level of a person
FI20045503A (en) 2004-12-28 2006-06-29 Polar Electro Oy The sensor system, accessories and a heart rate monitor
US7701227B2 (en) 2005-01-05 2010-04-20 Rensselaer Polytechnic Institute High precision voltage source for electrical impedance tomography
US8577455B2 (en) 2005-01-18 2013-11-05 Medtronic, Inc. Method and apparatus for arrhythmia detection in a medical device
JP2006198334A (en) 2005-01-24 2006-08-03 Tanita Corp Bioelectrical impedance measuring device and body composition measuring apparatus
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
JP4731936B2 (en) 2005-02-09 2011-07-27 本田技研工業株式会社 Rotary variable resistor
EP1871219A4 (en) 2005-02-22 2011-06-01 Health Smart Ltd Methods and systems for physiological and psycho-physiological monitoring and uses thereof
US20060212097A1 (en) 2005-02-24 2006-09-21 Vijay Varadan Method and device for treatment of medical conditions and monitoring physical movements
US7722622B2 (en) 2005-02-25 2010-05-25 Synthes Usa, Llc Implant insertion apparatus and method of use
US7616110B2 (en) 2005-03-11 2009-11-10 Aframe Digital, Inc. Mobile wireless customizable health and condition monitor
EP1865779A4 (en) 2005-03-21 2008-06-04 Vicus Therapeutics Spe 1 Llc Compositions and methods for ameliorating cachexia
US20060224079A1 (en) 2005-03-31 2006-10-05 Washchuk Bohdan O Edema monitoring system and method utilizing an implantable medical device
US20060224072A1 (en) 2005-03-31 2006-10-05 Cardiovu, Inc. Disposable extended wear heart monitor patch
WO2006109072A3 (en) * 2005-04-14 2007-02-01 Hidalgo Ltd Apparatus and system for monitoring
US8480577B2 (en) 2005-04-15 2013-07-09 Ivy Biomedical Systems, Inc. Wireless patient monitoring system
CN101163439A (en) 2005-04-20 2008-04-16 皇家飞利浦电子股份有限公司 Patient monitoring systems
US20060241641A1 (en) 2005-04-22 2006-10-26 Sdgi Holdings, Inc. Methods and instrumentation for distraction and insertion of implants in a spinal disc space
US7991467B2 (en) 2005-04-26 2011-08-02 Medtronic, Inc. Remotely enabled pacemaker and implantable subcutaneous cardioverter/defibrillator system
US7657317B2 (en) 2005-04-26 2010-02-02 Boston Scientific Neuromodulation Corporation Evaluating stimulation therapies and patient satisfaction
US7822627B2 (en) 2005-05-02 2010-10-26 St Martin Edward Method and system for generating an echocardiogram report
US20060252999A1 (en) 2005-05-03 2006-11-09 Devaul Richard W Method and system for wearable vital signs and physiology, activity, and environmental monitoring
US7917196B2 (en) 2005-05-09 2011-03-29 Cardiac Pacemakers, Inc. Arrhythmia discrimination using electrocardiograms sensed from multiple implanted electrodes
US7907997B2 (en) 2005-05-11 2011-03-15 Cardiac Pacemakers, Inc. Enhancements to the detection of pulmonary edema when using transthoracic impedance
US9089275B2 (en) 2005-05-11 2015-07-28 Cardiac Pacemakers, Inc. Sensitivity and specificity of pulmonary edema detection when using transthoracic impedance
US8688189B2 (en) 2005-05-17 2014-04-01 Adnan Shennib Programmable ECG sensor patch
WO2006124623A3 (en) 2005-05-18 2007-09-20 Wyk Rachelle Van System, method, and kit for positioning a monitor transducer on a patient
US7340296B2 (en) 2005-05-18 2008-03-04 Cardiac Pacemakers, Inc. Detection of pleural effusion using transthoracic impedance
US8900154B2 (en) 2005-05-24 2014-12-02 Cardiac Pacemakers, Inc. Prediction of thoracic fluid accumulation
KR100634544B1 (en) 2005-06-04 2006-10-09 삼성전자주식회사 Apparatus and method for measuring moisture content in skin using portable terminal
US7387607B2 (en) 2005-06-06 2008-06-17 Intel Corporation Wireless medical sensor system
FR2886532B1 (en) 2005-06-07 2008-03-28 Commissariat Energie Atomique Method and fall detection system of a person
US20060293571A1 (en) 2005-06-23 2006-12-28 Skanda Systems Distributed architecture for remote patient monitoring and caring
US7295879B2 (en) 2005-06-24 2007-11-13 Kenergy, Inc. Double helical antenna assembly for a wireless intravascular medical device
US7813778B2 (en) 2005-07-29 2010-10-12 Spectros Corporation Implantable tissue ischemia sensor
US20070033072A1 (en) * 2005-08-04 2007-02-08 Bildirici Nesim N System and method for comprehensive remote patient monitoring and management
US8494618B2 (en) * 2005-08-22 2013-07-23 Cardiac Pacemakers, Inc. Intracardiac impedance and its applications
US7775983B2 (en) 2005-09-16 2010-08-17 Cardiac Pacemakers, Inc. Rapid shallow breathing detection for use in congestive heart failure status determination
US7731663B2 (en) * 2005-09-16 2010-06-08 Cardiac Pacemakers, Inc. System and method for generating a trend parameter based on respiration rate distribution
US8992436B2 (en) 2005-09-16 2015-03-31 Cardiac Pacemakers, Inc. Respiration monitoring using respiration rate variability
US20070073361A1 (en) 2005-09-23 2007-03-29 Bioq, Inc. Medical device for restoration of autonomic and immune functions impaired by neuropathy
WO2007038607A3 (en) 2005-09-27 2007-07-05 Telzuit Technologies Llc Apparatus and method for monitoring patients
US20070083092A1 (en) 2005-10-07 2007-04-12 Rippo Anthony J External exercise monitor
US20070082189A1 (en) * 2005-10-11 2007-04-12 Gillette William J Waterproof, breathable composite material
JP5208749B2 (en) 2005-10-11 2013-06-12 インペダイムド・リミテッドImpedimed Limited Hydration status monitoring
JP2007105316A (en) 2005-10-14 2007-04-26 Konica Minolta Sensing Inc Bioinformation measuring instrument
US7420472B2 (en) 2005-10-16 2008-09-02 Bao Tran Patient monitoring apparatus
US8118750B2 (en) 2005-10-21 2012-02-21 Medtronic, Inc. Flow sensors for penile tumescence
US20070123903A1 (en) 2005-10-31 2007-05-31 Depuy Spine, Inc. Medical Device installation tool and methods of use
US20070123904A1 (en) 2005-10-31 2007-05-31 Depuy Spine, Inc. Distraction instrument and method for distracting an intervertebral site
US7942824B1 (en) 2005-11-04 2011-05-17 Cleveland Medical Devices Inc. Integrated sleep diagnostic and therapeutic system and method
US7682313B2 (en) 2005-11-23 2010-03-23 Vital Sensors Holding Company, Inc. Implantable pressure monitor
US7766840B2 (en) 2005-12-01 2010-08-03 Cardiac Pacemakers, Inc. Method and system for heart failure status evaluation based on a disordered breathing index
US8016776B2 (en) 2005-12-02 2011-09-13 Medtronic, Inc. Wearable ambulatory data recorder
US7957809B2 (en) 2005-12-02 2011-06-07 Medtronic, Inc. Closed-loop therapy adjustment
WO2007065015A3 (en) 2005-12-03 2008-02-14 Masimo Corp Physiological alarm notification system
CA2631940C (en) 2005-12-06 2016-06-21 St. Jude Medical, Atrial Fibrillation Division, Inc. Assessment of electrode coupling for tissue ablation
WO2007066270A3 (en) * 2005-12-08 2007-09-20 Brett Cross Medical sensor having electrodes and a motion sensor
US20070180047A1 (en) 2005-12-12 2007-08-02 Yanting Dong System and method for providing authentication of remotely collected external sensor measures
EP1965697A2 (en) 2005-12-19 2008-09-10 Philips Electronics N.V. Apparatus for monitoring a person's heart rate and/or heart rate variation; wristwatch comprising the same
US20070142715A1 (en) 2005-12-20 2007-06-21 Triage Wireless, Inc. Chest strap for measuring vital signs
US7761158B2 (en) 2005-12-20 2010-07-20 Cardiac Pacemakers, Inc. Detection of heart failure decompensation based on cumulative changes in sensor signals
US8050774B2 (en) 2005-12-22 2011-11-01 Boston Scientific Scimed, Inc. Electrode apparatus, systems and methods
US20070162089A1 (en) 2006-01-09 2007-07-12 Transoma Medical, Inc. Cross-band communications in an implantable device
RU2008134459A (en) 2006-01-23 2010-02-27 Конинклейке Филипс Электроникс Н.В. (Nl) Improved biomedical electrode for improved patient wearing the tongue or buttons which (A N) is isolated (a) from the holding pads
US20070172424A1 (en) 2006-01-26 2007-07-26 Mark Costin Roser Enabling drug adherence through closed loop monitoring & communication
WO2007092543A3 (en) 2006-02-06 2008-05-08 Univ Leland Stanford Junior Non-invasive cardiac monitor and methods of using continuously recorded cardiac data
US20070255184A1 (en) 2006-02-10 2007-11-01 Adnan Shennib Disposable labor detection patch
EP2032025A4 (en) 2006-02-28 2011-10-26 St Jude Medical Medical device and method for monitoring hematocrit and svo2
US20070208232A1 (en) 2006-03-03 2007-09-06 Physiowave Inc. Physiologic monitoring initialization systems and methods
US8200320B2 (en) 2006-03-03 2012-06-12 PhysioWave, Inc. Integrated physiologic monitoring systems and methods
US7668588B2 (en) * 2006-03-03 2010-02-23 PhysioWave, Inc. Dual-mode physiologic monitoring systems and methods
WO2007106455A3 (en) 2006-03-10 2008-02-21 Optical Sensors Inc Cardiography system and method using automated recognition of hemodynamic parameters and waveform attributes
DE102006015291B4 (en) 2006-04-01 2015-10-29 Drägerwerk AG & Co. KGaA A method for adjusting a patient monitor
US20080021336A1 (en) 2006-04-24 2008-01-24 Dobak John D Iii Devices and methods for accelerometer-based characterization of cardiac synchrony and dyssynchrony
US7359837B2 (en) 2006-04-27 2008-04-15 Medtronic, Inc. Peak data retention of signal data in an implantable medical device
US7818050B2 (en) 2006-05-02 2010-10-19 Lono Medical Systems, Llc Passive phonography heart monitor
US7616980B2 (en) 2006-05-08 2009-11-10 Tyco Healthcare Group Lp Radial electrode array
US7539532B2 (en) * 2006-05-12 2009-05-26 Bao Tran Cuffless blood pressure monitoring appliance
US7539533B2 (en) 2006-05-16 2009-05-26 Bao Tran Mesh network monitoring appliance
US20070282173A1 (en) 2006-05-31 2007-12-06 Bily Wang Vital sign sending method and a sending apparatus thereof
US7346380B2 (en) 2006-06-16 2008-03-18 Axelgaard Manufacturing Co., Ltd. Medical electrode
US7733224B2 (en) * 2006-06-30 2010-06-08 Bao Tran Mesh network personal emergency response appliance
US20080013747A1 (en) * 2006-06-30 2008-01-17 Bao Tran Digital stethoscope and monitoring instrument
US9820658B2 (en) 2006-06-30 2017-11-21 Bao Q. Tran Systems and methods for providing interoperability among healthcare devices
WO2008017042A1 (en) 2006-08-03 2008-02-07 Microchips, Inc. Cardiac biosensor devices and methods
US9773060B2 (en) 2006-09-05 2017-09-26 Cardiac Pacemaker, Inc. System and method for providing automatic setup of a remote patient care environment
US20080091090A1 (en) 2006-10-12 2008-04-17 Kenneth Shane Guillory Self-contained surface physiological monitor with adhesive attachment
US20080091089A1 (en) 2006-10-12 2008-04-17 Kenneth Shane Guillory Single use, self-contained surface physiological monitor
CN101601040A (en) 2006-10-24 2009-12-09 麦德爱普斯股份有限公司 Systems and methods for adapter-based communication with a medical device
US8214007B2 (en) * 2006-11-01 2012-07-03 Welch Allyn, Inc. Body worn physiological sensor device having a disposable electrode module
US8449469B2 (en) 2006-11-10 2013-05-28 Sotera Wireless, Inc. Two-part patch sensor for monitoring vital signs
US20080120784A1 (en) 2006-11-28 2008-05-29 General Electric Company Smart bed system and apparatus
US8315687B2 (en) * 2006-12-07 2012-11-20 Koninklijke Philips Electronics N.V. Handheld, repositionable ECG detector
US8157730B2 (en) 2006-12-19 2012-04-17 Valencell, Inc. Physiological and environmental monitoring systems and methods
US20080171929A1 (en) 2007-01-11 2008-07-17 Katims Jefferson J Method for standardizing spacing between electrodes, and medical tape electrodes
US20080294020A1 (en) 2007-01-25 2008-11-27 Demetrios Sapounas System and method for physlological data readings, transmission and presentation
US9044136B2 (en) 2007-02-16 2015-06-02 Cim Technology Inc. Wearable mini-size intelligent healthcare system
US20080221399A1 (en) 2007-03-05 2008-09-11 Triage Wireless, Inc. Monitor for measuring vital signs and rendering video images
US20080220865A1 (en) 2007-03-06 2008-09-11 Wei Hsu Interactive playstation controller
WO2008133897A1 (en) * 2007-04-30 2008-11-06 Dacso Clifford C Non-invasive monitoring of physiological measurements in a distributed health care environment
US20080287752A1 (en) 2007-05-10 2008-11-20 Mayo Foundation For Medical Education And Research Ear canal physiological parameter monitoring system
US7884727B2 (en) 2007-05-24 2011-02-08 Bao Tran Wireless occupancy and day-light sensing
WO2008148067A3 (en) 2007-05-24 2009-01-15 Micro Inc H An integrated wireless sensor for physiological monitoring
US9754078B2 (en) 2007-06-21 2017-09-05 Immersion Corporation Haptic health feedback monitoring
US9380966B2 (en) 2007-06-22 2016-07-05 Vioptix, Inc. Tissue retractor oximeter
US20090017910A1 (en) 2007-06-22 2009-01-15 Broadcom Corporation Position and motion tracking of an object
US20090005016A1 (en) 2007-06-29 2009-01-01 Betty Eng Apparatus and method to maintain a continuous connection of a cellular device and a sensor network
US8926509B2 (en) 2007-08-24 2015-01-06 Hmicro, Inc. Wireless physiological sensor patches and systems
US20090062670A1 (en) 2007-08-30 2009-03-05 Gary James Sterling Heart monitoring body patch and system
WO2009036260A1 (en) 2007-09-14 2009-03-19 Corventis, Inc. Data collection in a multi-sensor patient monitor
WO2009036319A1 (en) 2007-09-14 2009-03-19 Corventis, Inc. Adherent emergency patient monitor
US8116841B2 (en) 2007-09-14 2012-02-14 Corventis, Inc. Adherent device with multiple physiological sensors
WO2009036256A1 (en) 2007-09-14 2009-03-19 Corventis, Inc. Injectable physiological monitoring system
EP2194864B1 (en) 2007-09-14 2018-08-29 Medtronic Monitoring, Inc. System and methods for wireless body fluid monitoring
US20090076341A1 (en) 2007-09-14 2009-03-19 Corventis, Inc. Adherent Athletic Monitor
US9411936B2 (en) 2007-09-14 2016-08-09 Medtronic Monitoring, Inc. Dynamic pairing of patients to data collection gateways
EP2194858B1 (en) 2007-09-14 2017-11-22 Corventis, Inc. Medical device automatic start-up upon contact to patient tissue
US8591430B2 (en) 2007-09-14 2013-11-26 Corventis, Inc. Adherent device for respiratory monitoring
EP2195076A4 (en) 2007-09-14 2014-12-31 Corventis Inc Adherent device for cardiac rhythm management
US20090076342A1 (en) 2007-09-14 2009-03-19 Corventis, Inc. Adherent Multi-Sensor Device with Empathic Monitoring
EP2194856A4 (en) 2007-09-14 2014-07-16 Corventis Inc Adherent cardiac monitor with advanced sensing capabilities
US8260439B2 (en) * 2007-11-16 2012-09-04 Ethicon, Inc. Nerve stimulation patches and methods for stimulating selected nerves
WO2009114548A1 (en) 2008-03-12 2009-09-17 Corventis, Inc. Heart failure decompensation prediction based on cardiac rhythm
EP2254461A4 (en) 2008-03-19 2012-12-26 Ericsson Telefon Ab L M Nfc communications for implanted medical data acquisition devices
US20090292194A1 (en) 2008-05-23 2009-11-26 Corventis, Inc. Chiropractic Care Management Systems and Methods
US20100191310A1 (en) 2008-07-29 2010-07-29 Corventis, Inc. Communication-Anchor Loop For Injectable Device
US9067338B2 (en) 2008-08-04 2015-06-30 Semlux Technologies, Inc. Method to convert waste silicon to high purity silicon
WO2010025144A1 (en) 2008-08-29 2010-03-04 Corventis, Inc. Method and apparatus for acute cardiac monitoring
WO2011050283A3 (en) 2009-10-22 2011-07-14 Corventis, Inc. Remote detection and monitoring of functional chronotropic incompetence
US9451897B2 (en) 2009-12-14 2016-09-27 Medtronic Monitoring, Inc. Body adherent patch with electronics for physiologic monitoring
US8965498B2 (en) 2010-04-05 2015-02-24 Corventis, Inc. Method and apparatus for personalized physiologic parameters
JP5559425B2 (en) * 2010-05-12 2014-07-23 イリズム・テクノロジーズ・インコーポレイテッドIrhythm Technologies,Inc. Device mechanism and components for prolonged tack
US9420952B2 (en) * 2010-07-27 2016-08-23 Carefusion 303, Inc. Temperature probe suitable for axillary reading

Patent Citations (101)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3170459A (en) * 1962-03-20 1965-02-23 Clifford G Phipps Bio-medical instrumentation electrode
US3370459A (en) * 1964-04-16 1968-02-27 Cescati Arturo Device for detecting pressure existing in pneumatic tires
US4008712A (en) * 1975-11-14 1977-02-22 J. M. Richards Laboratories Method for monitoring body characteristics
US4308872A (en) * 1977-04-07 1982-01-05 Respitrace Corporation Method and apparatus for monitoring respiration
US4185621A (en) * 1977-10-28 1980-01-29 Triad, Inc. Body parameter display incorporating a battery charger
US4141366A (en) * 1977-11-18 1979-02-27 Medtronic, Inc. Lead connector for tape electrode
US5862802A (en) * 1981-04-03 1999-01-26 Forrest M. Bird Ventilator having an oscillatory inspiratory phase and method
US4498479A (en) * 1981-06-24 1985-02-12 Kone Oy Electrocardiograph (ECG) electrode testing system
US4981139A (en) * 1983-08-11 1991-01-01 Pfohl Robert L Vital signs monitoring and communication system
US4721110A (en) * 1984-08-06 1988-01-26 Lampadius Michael S Respiration-controlled cardiac pacemaker
US4895163A (en) * 1988-05-24 1990-01-23 Bio Analogics, Inc. System for body impedance data acquisition
US4988335A (en) * 1988-08-16 1991-01-29 Ideal Instruments, Inc. Pellet implanter apparatus
US5080099A (en) * 1988-08-26 1992-01-14 Cardiotronics, Inc. Multi-pad, multi-function electrode
US5086781A (en) * 1989-11-14 1992-02-11 Bookspan Mark A Bioelectric apparatus for monitoring body fluid compartments
US5083563A (en) * 1990-02-16 1992-01-28 Telectronics Pacing Systems, Inc. Implantable automatic and haemodynamically responsive cardioverting/defibrillating pacemaker
US5482036A (en) * 1991-03-07 1996-01-09 Masimo Corporation Signal processing apparatus and method
US5282840A (en) * 1992-03-26 1994-02-01 Medtronic, Inc. Multiple frequency impedance measurement system
US5855614A (en) * 1993-02-22 1999-01-05 Heartport, Inc. Method and apparatus for thoracoscopic intracardiac procedures
US20040015058A1 (en) * 1993-09-04 2004-01-22 Motorola, Inc. Wireless medical diagnosis and monitoring equipment
US5862803A (en) * 1993-09-04 1999-01-26 Besson; Marcus Wireless medical diagnosis and monitoring equipment
US6339722B1 (en) * 1995-09-26 2002-01-15 A. J. Van Liebergen Holding B.V. Apparatus for the in-vivo non-invasive measurement of a biological parameter concerning a bodily fluid of a person or animal
US5860860A (en) * 1996-01-31 1999-01-19 Federal Patent Corporation Integral video game and cardio-waveform display
US5718234A (en) * 1996-09-30 1998-02-17 Northrop Grumman Corporation Physiological data communication system
US6185452B1 (en) * 1997-02-26 2001-02-06 Joseph H. Schulman Battery-powered patient implantable device
US5865733A (en) * 1997-02-28 1999-02-02 Spacelabs Medical, Inc. Wireless optical patient monitoring apparatus
US6027523A (en) * 1997-10-06 2000-02-22 Arthrex, Inc. Suture anchor with attached disk
US6190313B1 (en) * 1998-04-20 2001-02-20 Allen J. Hinkle Interactive health care system and method
US20030009092A1 (en) * 1998-10-15 2003-01-09 Sensidyne, Inc. Reusable pulse oximeter probe and disposable bandage apparatus
US6181963B1 (en) * 1998-11-02 2001-01-30 Alza Corporation Transdermal electrotransport delivery device including a cathodic reservoir containing a compatible antimicrobial agent
US6687540B2 (en) * 1999-03-12 2004-02-03 Cardiac Pacemakers, Inc. Discrimination of supraventricular tachycardia and ventricular tachycardia events
US6190324B1 (en) * 1999-04-28 2001-02-20 Medtronic, Inc. Implantable medical device for tracking patient cardiac status
US6512949B1 (en) * 1999-07-12 2003-01-28 Medtronic, Inc. Implantable medical device for measuring time varying physiologic conditions especially edema and for responding thereto
US20070038038A1 (en) * 1999-10-18 2007-02-15 Bodymedia, Inc. Wearable human physiological and environmental data sensors and reporting system therefor
US6520967B1 (en) * 1999-10-20 2003-02-18 Cauthen Research Group, Inc. Spinal implant insertion instrument for spinal interbody prostheses
US6336903B1 (en) * 1999-11-16 2002-01-08 Cardiac Intelligence Corp. Automated collection and analysis patient care system and method for diagnosing and monitoring congestive heart failure and outcomes thereof
US7156808B2 (en) * 1999-12-17 2007-01-02 Q-Tec Systems Llc Method and apparatus for health and disease management combining patient data monitoring with wireless internet connectivity
US6985078B2 (en) * 2000-03-14 2006-01-10 Kabushiki Kaisha Toshiba Wearable life support apparatus and method
US6987965B2 (en) * 2000-04-18 2006-01-17 Motorola, Inc. Programmable wireless electrode system for medical monitoring
US6988989B2 (en) * 2000-05-19 2006-01-24 Welch Allyn Protocol, Inc. Patient monitoring system
US20060031102A1 (en) * 2000-06-16 2006-02-09 Bodymedia, Inc. System for detecting, monitoring, and reporting an individual's physiological or contextual status
US20020019588A1 (en) * 2000-06-23 2002-02-14 Marro Dominic P. Frontal electrode array for patient EEG signal acquisition
US6858006B2 (en) * 2000-09-08 2005-02-22 Wireless Medical, Inc. Cardiopulmonary monitoring
US20070021792A1 (en) * 2000-09-27 2007-01-25 Cvrx, Inc. Baroreflex Modulation Based On Monitored Cardiovascular Parameter
US20070038255A1 (en) * 2000-09-27 2007-02-15 Cvrx, Inc. Baroreflex stimulator with integrated pressure sensor
US20070021797A1 (en) * 2000-09-27 2007-01-25 Cvrx, Inc. Baroreflex stimulation synchronized to circadian rhythm
US20070021799A1 (en) * 2000-09-27 2007-01-25 Cvrx, Inc. Automatic baroreflex modulation based on cardiac activity
US20070021794A1 (en) * 2000-09-27 2007-01-25 Cvrx, Inc. Baroreflex Therapy for Disordered Breathing
US20070021798A1 (en) * 2000-09-27 2007-01-25 Cvrx, Inc. Baroreflex stimulation to treat acute myocardial infarction
US20070038262A1 (en) * 2000-09-27 2007-02-15 Cvrx, Inc. Baroreflex stimulation system to reduce hypertension
US20070021796A1 (en) * 2000-09-27 2007-01-25 Cvrx, Inc. Baroreflex modulation to gradually decrease blood pressure
US20050027207A1 (en) * 2000-12-29 2005-02-03 Westbrook Philip R. Sleep apnea risk evaluation
US6993378B2 (en) * 2001-06-25 2006-01-31 Science Applications International Corporation Identification by analysis of physiometric variation
US20030028321A1 (en) * 2001-06-29 2003-02-06 The Regents Of The University Of California Method and apparatus for ultra precise GPS-based mapping of seeds or vegetation during planting
US6697658B2 (en) * 2001-07-02 2004-02-24 Masimo Corporation Low power pulse oximeter
US20030023184A1 (en) * 2001-07-23 2003-01-30 Jonathan Pitts-Crick Method and system for diagnosing and administering therapy of pulmonary congestion
US20030028221A1 (en) * 2001-07-31 2003-02-06 Qingsheng Zhu Cardiac rhythm management system for edema
US20040010303A1 (en) * 2001-09-26 2004-01-15 Cvrx, Inc. Electrode structures and methods for their use in cardiovascular reflex control
US7166063B2 (en) * 2001-10-01 2007-01-23 The Nemours Foundation Brace compliance monitor
US20050020935A1 (en) * 2001-11-20 2005-01-27 Thomas Helzel Electrode for biomedical measurements
US7318808B2 (en) * 2001-12-14 2008-01-15 Isis Innovation Limited Combining measurements from breathing rate sensors
US20070043301A1 (en) * 2002-05-14 2007-02-22 Idex Asa Volume specific characterization of human skin by electrical immitance
US20040006279A1 (en) * 2002-07-03 2004-01-08 Shimon Arad (Abboud) Apparatus for monitoring CHF patients using bio-impedance technique
US6997879B1 (en) * 2002-07-09 2006-02-14 Pacesetter, Inc. Methods and devices for reduction of motion-induced noise in optical vascular plethysmography
US7160253B2 (en) * 2002-11-08 2007-01-09 Polar Electro Oy Method and device for measuring stress
US20060004300A1 (en) * 2002-11-22 2006-01-05 James Kennedy Multifrequency bioimpedance determination
US20050027918A1 (en) * 2002-12-23 2005-02-03 Microtune (Texas), L.P. Automatically establishing a wireless connection between adapters
US7160252B2 (en) * 2003-01-10 2007-01-09 Medtronic, Inc. Method and apparatus for detecting respiratory disturbances
US20080024294A1 (en) * 2003-06-23 2008-01-31 Cardiac Pacemakers, Inc. Systems, devices, and methods for selectively preventing data transfer from a medical device
US20050027204A1 (en) * 2003-06-26 2005-02-03 Kligfield Paul D. ECG diagnostic system and method
US20050015094A1 (en) * 2003-07-15 2005-01-20 Cervitech, Inc. Arrangement of a cervical prosthesis and insertion instrument
US20050015095A1 (en) * 2003-07-15 2005-01-20 Cervitech, Inc. Insertion instrument for cervical prostheses
US20060004377A1 (en) * 2003-07-15 2006-01-05 Cervitech, Inc. Insertion instrument for cervical prostheses
US20050027175A1 (en) * 2003-07-31 2005-02-03 Zhongping Yang Implantable biosensor
US20050043675A1 (en) * 2003-08-21 2005-02-24 Pastore Joseph M. Method and apparatus for modulating cellular metabolism during post-ischemia or heart failure
US20050113703A1 (en) * 2003-09-12 2005-05-26 Jonathan Farringdon Method and apparatus for measuring heart related parameters
US20070010750A1 (en) * 2003-10-03 2007-01-11 Akinori Ueno Biometric sensor and biometric method
US7184821B2 (en) * 2003-12-03 2007-02-27 Regents Of The University Of Minnesota Monitoring thoracic fluid changes
US20050192488A1 (en) * 2004-02-12 2005-09-01 Biopeak Corporation Non-invasive method and apparatus for determining a physiological parameter
US20060020218A1 (en) * 2004-02-26 2006-01-26 Warwick Freeman Method and apparatus for continuous electrode impedance monitoring
US7167743B2 (en) * 2004-03-16 2007-01-23 Medtronic, Inc. Collecting activity information to evaluate therapy
US20060009697A1 (en) * 2004-04-07 2006-01-12 Triage Wireless, Inc. Wireless, internet-based system for measuring vital signs from a plurality of patients in a hospital or medical clinic
US20060009701A1 (en) * 2004-06-29 2006-01-12 Polar Electro Oy Method of monitoring human relaxation level, and user-operated heart rate monitor
US20060010090A1 (en) * 2004-07-12 2006-01-12 Marina Brockway Expert system for patient medical information analysis
US7319386B2 (en) * 2004-08-02 2008-01-15 Hill-Rom Services, Inc. Configurable system for alerting caregivers
US20060025661A1 (en) * 2004-08-02 2006-02-02 Sweeney Robert J Device for monitoring fluid status
US20060030781A1 (en) * 2004-08-05 2006-02-09 Adnan Shennib Emergency heart sensor patch
US20060030782A1 (en) * 2004-08-05 2006-02-09 Adnan Shennib Heart disease detection patch
US20060041280A1 (en) * 2004-08-19 2006-02-23 Cardiac Pacemakers, Inc. Thoracic impedance detection with blood resistivity compensation
US20070015976A1 (en) * 2005-06-01 2007-01-18 Medtronic, Inc. Correlating a non-polysomnographic physiological parameter set with sleep states
US20070015973A1 (en) * 2005-06-03 2007-01-18 Reuven Nanikashvili Communication terminal, medical telemetry system and method for monitoring physiological data
US20070010721A1 (en) * 2005-06-28 2007-01-11 Chen Thomas C H Apparatus and system of Internet-enabled wireless medical sensor scale
US20070038078A1 (en) * 2005-07-08 2007-02-15 Daniel Osadchy Relative impedance measurement
US20070016089A1 (en) * 2005-07-15 2007-01-18 Fischell David R Implantable device for vital signs monitoring
US20070021678A1 (en) * 2005-07-19 2007-01-25 Cardiac Pacemakers, Inc. Methods and apparatus for monitoring physiological responses to steady state activity
US20070027497A1 (en) * 2005-07-27 2007-02-01 Cyberonics, Inc. Nerve stimulation for treatment of syncope
US20070027388A1 (en) * 2005-08-01 2007-02-01 Chang-An Chou Patch-type physiological monitoring apparatus, system and network
US20070043303A1 (en) * 2005-08-17 2007-02-22 Osypka Markus J Method and apparatus for digital demodulation and further processing of signals obtained in the measurement of electrical bioimpedance or bioadmittance in an object
US20090018410A1 (en) * 2006-03-02 2009-01-15 Koninklijke Philips Electronics N.V. Body parameter sensing
US20080004499A1 (en) * 2006-06-28 2008-01-03 Davis Carl C System and method for the processing of alarm and communication information in centralized patient monitoring
US20080024293A1 (en) * 2006-07-28 2008-01-31 Lee Stylos Adaptations to optivol alert algorithm
US20090018456A1 (en) * 2007-07-11 2009-01-15 Chin-Yeh Hung Display storage apparatus capable of detecting a pulse

Cited By (217)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8233974B2 (en) 1999-06-22 2012-07-31 Impedimed Limited Method and device for measuring tissue oedema
US9149235B2 (en) 2004-06-18 2015-10-06 Impedimed Limited Oedema detection
US8103337B2 (en) 2004-11-26 2012-01-24 Impedimed Limited Weighted gradient method and system for diagnosing disease
US20110087129A1 (en) * 2005-07-01 2011-04-14 Impedimed Limited Monitoring system
US20110054343A1 (en) * 2005-07-01 2011-03-03 Impedimed Limited Monitoring system
US8548580B2 (en) 2005-07-01 2013-10-01 Impedimed Limited Monitoring system
US20080270051A1 (en) * 2005-08-02 2008-10-30 Impedimed Limited Impedance Parameter Values
US8099250B2 (en) 2005-08-02 2012-01-17 Impedimed Limited Impedance parameter values
US9724012B2 (en) 2005-10-11 2017-08-08 Impedimed Limited Hydration status monitoring
US9757584B2 (en) 2006-01-17 2017-09-12 Emkinetics, Inc. Methods and devices for performing electrical stimulation to treat various conditions
US9387338B2 (en) 2006-01-17 2016-07-12 Emkinetics, Inc. Methods and devices for performing electrical stimulation to treat various conditions
US9630004B2 (en) 2006-01-17 2017-04-25 Emkinetics, Inc. Method and apparatus for transdermal stimulation over the palmar and plantar surfaces
US9002477B2 (en) 2006-01-17 2015-04-07 Emkinetics, Inc. Methods and devices for performing electrical stimulation to treat various conditions
US9339641B2 (en) 2006-01-17 2016-05-17 Emkinetics, Inc. Method and apparatus for transdermal stimulation over the palmar and plantar surfaces
US8761870B2 (en) 2006-05-30 2014-06-24 Impedimed Limited Impedance measurements
US20080306325A1 (en) * 2006-10-02 2008-12-11 Emkinetics Method and apparatus for magnetic induction therapy
US20100204538A1 (en) * 2006-10-02 2010-08-12 Daniel Rogers Burnett Method and apparatus for magnetic induction therapy
US20090234179A1 (en) * 2006-10-02 2009-09-17 Burnett Daniel R Method and apparatus for magnetic induction therapy
US20090227831A1 (en) * 2006-10-02 2009-09-10 Burnett Daniel R Method and apparatus for magnetic induction therapy
US20100168501A1 (en) * 2006-10-02 2010-07-01 Daniel Rogers Burnett Method and apparatus for magnetic induction therapy
US8430805B2 (en) 2006-10-02 2013-04-30 Emkinetics, Inc. Method and apparatus for magnetic induction therapy
US20100160712A1 (en) * 2006-10-02 2010-06-24 Daniel Rogers Burnett Method and apparatus for magnetic induction therapy
US9005102B2 (en) 2006-10-02 2015-04-14 Emkinetics, Inc. Method and apparatus for electrical stimulation therapy
US20090227829A1 (en) * 2006-10-02 2009-09-10 Burnett Daniel R Method and apparatus for magnetic induction therapy
US8435166B2 (en) 2006-10-02 2013-05-07 Emkinetics, Inc. Method and apparatus for magnetic induction therapy
US9504406B2 (en) 2006-11-30 2016-11-29 Impedimed Limited Measurement apparatus
US8594781B2 (en) 2007-01-15 2013-11-26 Impedimed Limited Monitoring system
US20100100003A1 (en) * 2007-01-15 2010-04-22 Impedimed Limited Monitoring system
US9298889B2 (en) 2007-03-09 2016-03-29 Spacelabs Healthcare Llc Health data collection tool
US20100109739A1 (en) * 2007-03-30 2010-05-06 Impedimed Limited Active guarding for reduction of resistive and capacitive signal loading with adjustable control of compensation level
US8487686B2 (en) 2007-03-30 2013-07-16 Impedimed Limited Active guarding for reduction of resistive and capacitive signal loading with adjustable control of compensation level
US20100179421A1 (en) * 2007-05-24 2010-07-15 Joe Tupin System and method for non-invasive instantaneous and continuous measurement of cardiac chamber volume.
US8463361B2 (en) 2007-05-24 2013-06-11 Lifewave, Inc. System and method for non-invasive instantaneous and continuous measurement of cardiac chamber volume
US10004893B2 (en) 2007-06-06 2018-06-26 Zoll Medical Corporation Wearable defibrillator with audio input/output
US8965500B2 (en) 2007-06-06 2015-02-24 Zoll Medical Corporation Wearable defibrillator with audio input/output
US10029110B2 (en) 2007-06-06 2018-07-24 Zoll Medical Corporation Wearable defibrillator with audio input/output
US9492676B2 (en) 2007-06-06 2016-11-15 Zoll Medical Corporation Wearable defibrillator with audio input/output
US20080306560A1 (en) * 2007-06-06 2008-12-11 Macho John D Wearable defibrillator with audio input/output
US8774917B2 (en) 2007-06-06 2014-07-08 Zoll Medical Corporation Wearable defibrillator with audio input/output
US8369944B2 (en) 2007-06-06 2013-02-05 Zoll Medical Corporation Wearable defibrillator with audio input/output
US20080306562A1 (en) * 2007-06-07 2008-12-11 Donnelly Edward J Medical device configured to test for user responsiveness
US9370666B2 (en) 2007-06-07 2016-06-21 Zoll Medical Corporation Medical device configured to test for user responsiveness
US8271082B2 (en) 2007-06-07 2012-09-18 Zoll Medical Corporation Medical device configured to test for user responsiveness
US7974689B2 (en) 2007-06-13 2011-07-05 Zoll Medical Corporation Wearable medical treatment device with motion/position detection
US9737262B2 (en) 2007-06-13 2017-08-22 Zoll Medical Corporation Wearable medical monitoring device
US9283399B2 (en) 2007-06-13 2016-03-15 Zoll Medical Corporation Wearable medical treatment device
US20100312297A1 (en) * 2007-06-13 2010-12-09 Zoll Medical Corporation Wearable medical treatment device with motion/position detection
US20080312709A1 (en) * 2007-06-13 2008-12-18 Volpe Shane S Wearable medical treatment device with motion/position detection
US8676313B2 (en) 2007-06-13 2014-03-18 Zoll Medical Corporation Wearable medical treatment device with motion/position detection
US20100298899A1 (en) * 2007-06-13 2010-11-25 Donnelly Edward J Wearable medical treatment device
US8649861B2 (en) 2007-06-13 2014-02-11 Zoll Medical Corporation Wearable medical treatment device
US8140154B2 (en) 2007-06-13 2012-03-20 Zoll Medical Corporation Wearable medical treatment device
US9398859B2 (en) 2007-06-13 2016-07-26 Zoll Medical Corporation Wearable medical treatment device with motion/position detection
US9320443B2 (en) 2007-09-14 2016-04-26 Medtronic Monitoring, Inc. Multi-sensor patient monitor to detect impending cardiac decompensation
US8374688B2 (en) 2007-09-14 2013-02-12 Corventis, Inc. System and methods for wireless body fluid monitoring
US8285356B2 (en) 2007-09-14 2012-10-09 Corventis, Inc. Adherent device with multiple physiological sensors
US8790257B2 (en) 2007-09-14 2014-07-29 Corventis, Inc. Multi-sensor patient monitor to detect impending cardiac decompensation
US8897868B2 (en) 2007-09-14 2014-11-25 Medtronic, Inc. Medical device automatic start-up upon contact to patient tissue
US8249686B2 (en) 2007-09-14 2012-08-21 Corventis, Inc. Adherent device for sleep disordered breathing
US8460189B2 (en) 2007-09-14 2013-06-11 Corventis, Inc. Adherent cardiac monitor with advanced sensing capabilities
US9186089B2 (en) 2007-09-14 2015-11-17 Medtronic Monitoring, Inc. Injectable physiological monitoring system
US9411936B2 (en) 2007-09-14 2016-08-09 Medtronic Monitoring, Inc. Dynamic pairing of patients to data collection gateways
US9770182B2 (en) 2007-09-14 2017-09-26 Medtronic Monitoring, Inc. Adherent device with multiple physiological sensors
US8116841B2 (en) 2007-09-14 2012-02-14 Corventis, Inc. Adherent device with multiple physiological sensors
US10028699B2 (en) 2007-09-14 2018-07-24 Medtronic Monitoring, Inc. Adherent device for sleep disordered breathing
US8591430B2 (en) 2007-09-14 2013-11-26 Corventis, Inc. Adherent device for respiratory monitoring
US8684925B2 (en) 2007-09-14 2014-04-01 Corventis, Inc. Injectable device for physiological monitoring
US9579020B2 (en) 2007-09-14 2017-02-28 Medtronic Monitoring, Inc. Adherent cardiac monitor with advanced sensing capabilities
US9538960B2 (en) 2007-09-14 2017-01-10 Medtronic Monitoring, Inc. Injectable physiological monitoring system
US9901290B2 (en) 2007-10-12 2018-02-27 BioSensics LLC Fall detection and fall risk detection systems and methods
US9005141B1 (en) 2007-10-12 2015-04-14 Biosensics, L.L.C. Ambulatory system for measuring and monitoring physical activity and risk of falling and for automatic fall detection
US20110025348A1 (en) * 2007-11-05 2011-02-03 Impedimed Limited Impedance determination
US8836345B2 (en) 2007-11-05 2014-09-16 Impedimed Limited Impedance determination
US9392947B2 (en) 2008-02-15 2016-07-19 Impedimed Limited Blood flow assessment of venous insufficiency
US20090287102A1 (en) * 2008-02-15 2009-11-19 Impedimed Limited Blood flow assessment of venous insufficiency
US8718752B2 (en) 2008-03-12 2014-05-06 Corventis, Inc. Heart failure decompensation prediction based on cardiac rhythm
US9668667B2 (en) 2008-04-18 2017-06-06 Medtronic Monitoring, Inc. Method and apparatus to measure bioelectric impedance of patient tissue
US8412317B2 (en) 2008-04-18 2013-04-02 Corventis, Inc. Method and apparatus to measure bioelectric impedance of patient tissue
US8406865B2 (en) * 2008-09-30 2013-03-26 Covidien Lp Bioimpedance system and sensor and technique for using the same
US20100081960A1 (en) * 2008-09-30 2010-04-01 Nellcor Puritan Bennett Llc Bioimpedance System and Sensor and Technique for Using the Same
US20100099958A1 (en) * 2008-10-16 2010-04-22 Fresenius Medical Care Holdings Inc. Method of identifying when a patient undergoing hemodialysis is at increased risk of death
US9883799B2 (en) 2008-10-16 2018-02-06 Fresenius Medical Care Holdings, Inc. Method of identifying when a patient undergoing hemodialysis is at increased risk of death
US20110137136A1 (en) * 2008-10-16 2011-06-09 Fresenius Medical Care Holdings, Inc. Method of identifying when a patient undergoing hemodialysis is at increased risk of death
US9615766B2 (en) 2008-11-28 2017-04-11