WO2015153426A1 - Détection de la saturation dans un amplificateur à commande neutre pour électrocardiogramme - Google Patents

Détection de la saturation dans un amplificateur à commande neutre pour électrocardiogramme Download PDF

Info

Publication number
WO2015153426A1
WO2015153426A1 PCT/US2015/023285 US2015023285W WO2015153426A1 WO 2015153426 A1 WO2015153426 A1 WO 2015153426A1 US 2015023285 W US2015023285 W US 2015023285W WO 2015153426 A1 WO2015153426 A1 WO 2015153426A1
Authority
WO
WIPO (PCT)
Prior art keywords
ecg
lead
characterization
comparison
wilson point
Prior art date
Application number
PCT/US2015/023285
Other languages
English (en)
Inventor
Daniel K. FREEMAN
Ronald Gatzke
Original Assignee
Draeger Medical Systems, Inc.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Draeger Medical Systems, Inc. filed Critical Draeger Medical Systems, Inc.
Publication of WO2015153426A1 publication Critical patent/WO2015153426A1/fr

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7203—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/25—Bioelectric electrodes therefor
    • A61B5/276—Protection against electrode failure
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/30—Input circuits therefor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7221—Determining signal validity, reliability or quality
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/30—Input circuits therefor
    • A61B5/304—Switching circuits

Definitions

  • An electrocardiogram can be used to measure a heart's electrical conduction system.
  • An ECG monitor can include more than two leads with electrodes, for example, left arm (LA), right arm (RA), and left leg (LL) electrodes.
  • Electrodes are placed on a patient to record voltages on various points of the body.
  • ECG monitor can detect electrical impulses generated by the polarization and depolarization of cardiac tissue using electrodes connected to a patient's skin and can translate the electrical impulses into a waveform.
  • This waveform can be used, for example by a clinician, to measure a rate and regularity of heartbeats, as well as size and position of heart chambers, presence of damage to the heart, and effects of drugs or devices used to regulate the heart, such as a pacemaker.
  • the ECG electrodes should be properly placed on a patient's skin to create a sufficient electrical connection.
  • ECG monitoring is an important tool in modem healthcare facilities, such as hospitals, but its utility can be balanced with the burden of frequent false alarms. For example, it has been estimated that greater than 80% of all alarms from patient ECG monitors are false positive.
  • ECG monitors include a right-leg drive (RLD) or neutral drive system, which can operate to reduce alternating current (AC) noise that couples to a body.
  • RLD right-leg drive
  • AC alternating current
  • Similar systems were introduced into commercial ECG monitors in the 1960's, and were designed to address pronounced ECG noise sources, such as that of mains power (i.e., 50Hz in Europe, 60Hz in the United States). These types of noise couples into the body through stray capacitance to the main power, producing a large AC voltage on the body that can be common to all ECG electrodes, thus serving as a source of common- mode noise in the ECG monitor.
  • a Wilson point can be monitored in an ECG monitor having a plurality of recording ECG leads each electrically connected to a body of a patient.
  • the ECG monitor can have a feedback ECG lead electrically connected to the body of the patient and to an amplifier to compensate for noise on the plurality of recording ECG leads by injecting current into the body of the patient.
  • Each of the plurality of recording ECG leads can have an associated lead-off circuit.
  • the Wilson point can be compared to a threshold. A characterization of the comparison can be provided when the Wilson point is beyond the threshold.
  • the Wilson point can be an average of voltages measured on each of the plurality of recording ECG leads.
  • the feedback amplifier can inject current into the body of the patient to drive the Wilson point towards a reference voltage.
  • Providing the characterization of the comparison can include one or more of generating an alarm, displaying the characterization of the comparison, storing data comprising the characterization of the comparison, loading data comprising the characterization of the comparison, and transmitting data comprising the characterization of the comparison.
  • Each of the associated lead-off circuits can include a pull-down resistor connected to a negative voltage.
  • Each of the associated lead-off circuits can include a pull-up resistor connected to a positive voltage.
  • the providing the characterization of the comparison can occur when the Wilson point is beyond the threshold for a predefined length of time.
  • the threshold can be predetermined to correspond to the feedback amplifier being saturated.
  • the Wilson point can be continuously monitored.
  • the feedback amplifier can be switched to a different ECG lead.
  • the different ECG lead can be selected from one of the plurality of recording ECG leads.
  • Each of the associated lead-off circuits can provide a positive direct current source.
  • Each of the associated lead-off circuits can provide a negative direct current source.
  • Each of the associated lead-off circuits can provide an alternating current source.
  • At least one of the monitoring, comparing, or providing, can be implemented by at least one data processor.
  • Computer program products are also described that comprise non- transitory computer readable media storing instructions, which when executed by at least one data processors of one or more computing systems, causes at least one data processor to perform operations herein.
  • computer systems are also described that may include one or more data processors and a memory coupled to the one or more data processors.
  • the memory may temporarily or permanently store instructions that cause at least one processor to perform one or more of the operations described herein.
  • methods can be implemented by one or more data processors either within a single computing system or distributed among two or more computing systems.
  • monitoring and detection of saturation of a neutral drive amplifier can be performed without having to record an output of the neutral drive amplifier or voltage on an electrode.
  • ECG measurement noise can be reduced, the number of false- positive monitor alarms can be reduced, and ECG monitor performance can be improved.
  • FIG 1 is a process flow diagram illustrating a method of monitoring a
  • FIG. 2 is an example implementation of an ECG monitoring system configured to monitor the Wilson point
  • FIG. 3 is a circuit model of the example ECG monitoring system
  • FIG. 4 is an example implementation of a circuit for monitoring the Wilson point
  • FIG. 5 is a circuit model of an example ECG monitoring system in which the lead-off circuits include positive direct current sources;
  • FIG. 6 is a circuit model of an example ECG monitoring system in which the lead-off circuits include alternating current sources;
  • FIG.7 is another example implementation of a circuit for monitoring the Wilson point.
  • FIG 1 is a process flow diagram 100 illustrating a method of monitoring a Wilson point in an ECG monitor to, for example, detect when a neutral drive amplifier is saturated. Saturation of a neutral drive amplifier can lead to increased noise in ECG measurements and poor ECG monitor performance. Additionally, once saturation of the neutral drive amplifier is detected, steps can be taken to correct the condition or notify a clinician or other healthcare provider of the condition.
  • Wilson point in an ECG monitor can, at 1 10, be monitored.
  • Wilson point can be an average of voltages or signals measured on a number of recording
  • the Wilson point can be an average body voltage. Electrical signals detected by the recording ECG leads can be used to create the ECG waveforms. When the ECG monitor is operating under normal conditions with each lead properly connected to a patient, the Wilson point can be at or near zero volts, although there may be transient voltage values. The monitoring can be performed, for example, using analog and/or digital systems.
  • FIG. 2 is an example implementation of an ECG monitor 200 configured to monitor the Wilson point and FIG. 3 is a circuit model of the example ECG monitor 200.
  • the example ECG monitor 200 includes three recording leads (205LL, 205- LA, and 205RA) each having a respective recording electrode (210LL, 21 OLA, and 210RA) electrically connected to a body 215 of a patient.
  • the example ECG monitor 200 can further include one or more precordial leads 205p having a precordial electrode 21 Op and a neutral drive lead 205RL having a neutral drive electrode 210RL.
  • the neutral drive lead 205RL can be a feedback lead, and the neutral drive electrode 210RL can be a feedback electrode.
  • the voltage on each lead (205LL, 205LA, 205RA, and 205p) is denoted by
  • VLL,VLA, VRA, and Vp feeds a buffer 255, the output of which can be further processed.
  • the body 215 voltage VB can be modeled to a first order as ground.
  • Commonly used "12-lead ECG" configurations use 10 total electrodes, with 6 precordial leads.
  • Each of the respective electrodes (210LL, 21 OLA, 210RA, 21 Op, and 210RL) can be electrically connected to the body 215 through respective skin-electrode interfaces (220LL, 220LA, 220RA, 220p, and 220RL).
  • each skin- electrode interface (220LL, 220LA, 220RA, 220p, and 220RL) can be modeled as a parallel RC circuit having some resistance R and some capacitance C.
  • each skin-electrode interface (220LL, 220LA, 220RA, 220p, and 220RL) can vary over time and based on the quality of the physical connection between the body 215 and the corresponding electrode (210LL, 21 OLA, 210RA, 21 Op, and 210RL). For example, a poor electrical connection resulting from a semi-detached electrode can lead to a large resistance R.
  • example nominal skin-electrode impedance can derive from the American Association of the Advancement of Medical Instrumentation (AAMI): 50k ⁇ for skin resistance R and 47nF for skin capacitance C. But impedance can vary over time through a number of factors, such as electrode gel drying out, skin moisture level, or loss of secure contact between electrode and skin.
  • An averager 235 can be included to provide an average of the voltage on the recording leads (205LL, 205LA, and 205RA).
  • the output of the averager 235 can be the Wilson point 240.
  • the averager 235 can include equal-valued resistors, each buffered by a high input impedance buffer stage.
  • the ECG monitor 200 can include a neutral drive amplifier 230 (e.g., a feedback amplifier) electrically connected to the neutral drive lead 205RL.
  • the neutral drive amplifier 230 operates to inject current into the body 215 via the neutral drive lead 205RL and the neutral drive electrode 210 ⁇ , ⁇ compensate for noise on one or more recording ECG leads (205LL, 205LA, and 205RA).
  • the neutral drive amplifier 230 can take the Wilson point 240, which can be the average voltage appearing on all recording electrodes (210LL, 21 OLA, and 210RA), invert and amplify this voltage, and apply the inverted amplified voltage to the neutral drive electrode 210RL to effectively cancel out and compensate for any AC noise source on the body 215.
  • the neutral drive amplifier 230 can operate to drive the Wilson point 240 to zero volts.
  • the Wilson point 240 can be a reference voltage or value, can be a voltage or value other than zero, and/or can be predefined or predetermined.
  • an example implementation of a neutral drive amplifier 230 can include an operational amplifier with the Wilson point 240 (also denoted as Vw) connected to the negative input, with a ground reference (or 0V) connected to the positive input.
  • the output VRL is thus the inverted and amplified Wilson point 240.
  • the body 215 and ECG monitor 200 forms a feedback loop in which the Wilson point 240 is driven to the volts reference level potential (e.g., zero volts).
  • the neutral drive amplifier 230 can have an open loop gain of 10 5 , and a gain bandwidth product of 700kHz.
  • the neutral drive amplifier 230 output can generate significant alternating current (AC) voltage on its output particularly when the neutral drive electrode 210RL impedance (modeled as RRL in FIG. 3) becomes high. But the neutral drive amplifier 230 is susceptible to saturation (or "clipping") on its output. Saturation occurs when the neutral drive amplifier 230 attempts to output a voltage greater in magnitude than its power supplies. For example, if the neutral drive amplifier 230 is powered with +3V (e.g., +VSUPPLY), then any attempt to exceed +3V on its output will cause saturation of the neutral drive amplifier 230. When the neutral drive amplifier 230 saturates, it will cease to function properly, the common-mode noise rejection of the ECG monitor 200 will drop, and noise can appear on the ECG output.
  • +3V e.g., +VSUPPLY
  • the ECG monitor 200 can include a lead-off circuit (225LL, 225LA, 225RA, 225RL, and 225p) for each recording lead (205LL, 205LA, and 205RA); the one or more precordial leads 205p; and the neutral drive amplifier lead 205RL.
  • Each lead-off circuit (225LL, 225LA, 225RA, 225p, and 225RL) can be used to detect if and when the corresponding electrode (210LL, 21 OLA, 210RA, 21 Op, or 210RL) has a poor electrical connection with the body 215.
  • An example implementation of a lead-off circuit (225LL, 225LA, 225RA, 225p, and 225RL) can include a current source ISENSE (as illustrated in FIG. 3) or a pull-down resistor to a negative DC voltage, which acts to change the DC voltage on the electrodes (210LL, 21 OLA, 210RA, 21 Op, or 210RL) when the skin-electrode interface (220LL, 220LA, 220RA, 220p, and 220RL) resistance R becomes high.
  • the DC voltage becomes negative when an electrode contact is poor. For example, if a the right-arm lead-off circuit 225RA
  • neutral drive amplifier lead 205RL does not include an associated lead-off circuit 225RL.
  • the lead-off circuit (225LL, 225LA, 225RA, 225p, and 225RL) can include a positive current source ISENSE (as illustrated in FIG. 5) or a pull-up resistor to a positive DC voltage.
  • the lead-off circuit (225LL, 225LA, 225RA, 225p, and 225RL) can include an AC source ISENSE (as illustrated in FIG. 6).
  • the lead-off circuits (225LL, 225LA, 225RA, and 225p) can be a cause of neutral drive amplifier 230 saturation, such as when electrode (210LL, 21 OLA, and 210RA 21 Op, and 210RL) contact becomes poor. If, for example, the electrode resistance on the right arm (RRA) increases due to poor electrode-skin contact, this will cause the voltage on the right-arm (VRA) to have negative DC voltage.
  • the lead-off circuits By causing a negative DC voltage on one or more of the recording leads (205RA, 205LA, and 205LL) and precordial leads 205p, the lead-off circuits (225LL, 225LA, 225RA, and 225p) causes the Wilson point 240, which is the average of the recording lead voltages, to become non-zero.
  • the neutral drive amplifier 230 attempting to bring the Wilson point 240 back to zero voltage, can output a relatively high DC voltage. This is because all of the DC current that is drawn into each of the leads (205LL, 205LA, 205RA, and 205p) is supplied from the neutral drive amplifier 230.
  • the neutral drive amplifier 230 is sourcing at least 3uA.
  • a DC voltage can develop on the neutral drive amplifier 230 output (e.g., VRL), which can cause or contribute to saturation of the neutral drive amplifier 230.
  • a similar saturation effect can occur when the resistance RRL on the neutral drive electrode 210RL becomes high.
  • the neutral drive amplifier 230 is supplying current for the lead-off circuits (225LL, 225LA, 225RA, 225p, and 225RL)
  • the lead-off circuits 225LL, 225LA, 225RA, 225p, and/or 225RL
  • the lead-off circuits can also be chosen to source current rather than sink current without changing the performance of the system.
  • the lead-off circuits (225LL, 225LA, 225RA, 225p, and/or 225RL) source current then the neutral drive amplifier 230 would sink this current, and therefore any increase to the resistance RRL will cause the Wilson point 240 to become positive, which in turn causes VRL to become negative and can contribute to the neutral amplifier saturating on its negative power rail.
  • the Wilson voltage can be monitored to detect when it goes beyond (e.g., greater than) a threshold.
  • the leads-off circuits (225LL, 225LA, 225RA, 225p, and 225RL) can be chosen to provide an AC source rather than a DC source (e.g., as illustrated in FIG. 6).
  • each of the lead-off circuits can provide a positive direct current source, a negative direct current source, or an alternating current source.
  • Another cause or contributor to saturation of the neutral drive amplifier 230 can include low voltage power supplies.
  • V SU ppiy +1.5V
  • the neutral drive amplifier 230 output can saturate even under normal conditions.
  • V SU ppiy +1.5V
  • the neutral drive amplifier 230 output can saturate even under normal conditions.
  • V SU ppiy +1.5V
  • Monitoring of the Wilson point can be performed by a controller 245.
  • the controller 245 can monitor the Wilson point by measuring the voltages (V RA , V LA , and V LL ) on each of the recording leads (205 RA , 205 LA , and 205 LL ) and computing the average.
  • the controller 245 can measure the Wilson point 240 directly on the output of the averager 235. The Wilson point can be continuously monitored.
  • the controller 245 can also perform operations related to processing the ECG monitor measurements (e.g., the ECG signal); computing heart rate and other patient physiological parameters; displaying, transmitting, and storing related information; and generating alarms for clinicians related to the ECG signal.
  • ECG monitor measurements e.g., the ECG signal
  • computing heart rate and other patient physiological parameters e.g., the ECG signal
  • displaying, transmitting, and storing related information e.g., the ECG signal
  • the Wilson point 240 can be compared to a threshold.
  • the threshold can be predetermined or predefined and can be a voltage value.
  • the threshold can correspond to a value that occurs when the neutral drive amplifier 230 is saturating, is close to saturating, or is intermittently saturating.
  • the comparison can further include a time component. For example, comparing the Wilson point 240 to a threshold and length of time the Wilson point 240 has been beyond (e.g., less than or greater than) the threshold.
  • the comparison can be performed by the controller 245, for example, in software.
  • a characterization of the comparison can be provided at 130 when the Wilson point is beyond (e.g., less than or greater than) the threshold.
  • the characterization of the comparison can include, for example, generating an alarm or notification for a clinician or other health care provider.
  • the alarm or notification can indicate that the neutral drive amplifier 230 is saturated, that the ECG monitor 200 is not operating under normal conditions or is experiencing increased noise, that one or more electrodes has a poor electrical connection, and the like.
  • Providing the characterization of the comparison can include displaying the characterization (for example, on a display of the ECG monitor 200), storing the characterization of the comparison (for example, in memory of the ECG monitor 200), and transmitting the characterization of the comparison (for example, to a hospital network or remote monitoring system).
  • the neutral drive amplifier 230 can be switched or reconfigured to connect to a different ECG lead.
  • the ECG monitor 200 can include a switch or multiplexer (MUX) 250 between the neutral drive amplifier 230 and the ECG leads (205LL, 205LA, 205RA, 205p, and 205RL).
  • MUX multiplexer
  • the left-leg recording ECG lead 205LL may no longer be used for recording the ECG measurement (e.g., signal), but rather for injecting current into the body to cancel out noise.
  • the controller 245 can control the MUX 250 to, for example, switch the ECG lead being driving by the neutral drive amplifier 230 from a first lead to a second lead based on whether the neutral drive amplifier 230 is saturating.
  • the lead to which the neutral drive amplifier 230 is switched can be determined based, for example, on a priority list of leads, which can be static or dynamic based on a quality of electrical contact for each lead (e.g., the magnitude of impedance).
  • steps of the method 100 of FIG. 1 can be performed using analog hardware.
  • FIG. 4 is an example
  • FIG. 7 is another example implementation of a circuit for monitoring the Wilson point 240, comparing the Wilson point 240 to a threshold, and providing a characterization of the threshold.
  • the implementation of FIG. 7 includes a comparator circuit 705, which can control the MUX 250 based on whether the Wilson point 240 is beyond (e.g., less than or greater than) the predetermined value (denoted as V REF ).
  • the controller 245 can monitor the neutral drive electrode 210 RL voltage V RL directly, rather than the Wilson point 240.
  • Various implementations of the subject matter described herein may be realized in digital electronic circuitry, integrated circuitry, specially designed ASICs (application specific integrated circuits), computer hardware, firmware, software, and/or combinations thereof. These various implementations may include implementation in one or more computer programs that are executable and/or interpretable on a programmable system including at least one programmable processor, which may be special or general purpose, coupled to receive data and instructions from, and to transmit data and instructions to, a storage system, at least one input device, and at least one output device.
  • ASICs application specific integrated circuits
  • the subject matter described herein may be implemented on a computer having a display device (e.g., a CRT (cathode ray tube) or LCD (liquid crystal display) monitor) for displaying information to the user and a keyboard and a pointing device (e.g., a mouse or a trackball) by which the user may provide input to the computer.
  • a display device e.g., a CRT (cathode ray tube) or LCD (liquid crystal display) monitor
  • a keyboard and a pointing device e.g., a mouse or a trackball
  • Other kinds of devices may be used to provide for interaction with a user as well; for example, feedback provided to the user may be any form of sensory feedback (e.g., visual feedback, auditory feedback, or tactile feedback); and input from the user may be received in any form, including acoustic, speech, or tactile input.
  • the subject matter described herein may be implemented in a computing system that includes a back-end component (e.g., as a data server), or that includes a middleware component (e.g., an application server), or that includes a front- end component (e.g., a client computer having a graphical user interface or a Web browser through which a user may interact with an implementation of the subject matter described herein), or any combination of such back-end, middleware, or front-end components.
  • the components of the system may be interconnected by any form or medium of digital data communication (e.g., a communication network). Examples of communication networks include a local area network ("LAN”), a wide area network (“WAN”), and the Internet.
  • LAN local area network
  • WAN wide area network
  • the Internet the global information network
  • the computing system may include clients and servers.
  • a client and server are generally remote from each other and typically interact through a
  • client and server arises by virtue of computer programs running on the respective computers and having a client-server relationship to each other.

Landscapes

  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • Veterinary Medicine (AREA)
  • Public Health (AREA)
  • Physics & Mathematics (AREA)
  • General Health & Medical Sciences (AREA)
  • Biophysics (AREA)
  • Pathology (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Medical Informatics (AREA)
  • Molecular Biology (AREA)
  • Signal Processing (AREA)
  • Artificial Intelligence (AREA)
  • Physiology (AREA)
  • Computer Vision & Pattern Recognition (AREA)
  • Psychiatry (AREA)
  • Measurement And Recording Of Electrical Phenomena And Electrical Characteristics Of The Living Body (AREA)

Abstract

Un point de Wilson peut être monitoré dans un moniteur ECG ayant une pluralité de dérivations ECG d'enregistrement, dont chacune est électriquement raccordée au corps d'un patient. Le moniteur ECG peut être une dérivation ECG à rétroaction électriquement reliée au corps du patient et à un amplificateur pour compenser le bruit agissant sur la pluralité de dérivations ECG d'enregistrement, par injection d'un courant dans le corps du patient. Chacune de la pluralité de dérivations ECG d'enregistrement peut avoir un circuit associé de désactivation de dérivation. Le point de Wilson peut être comparé à un seuil. Une caractérisation de la comparaison peut être réalisée quand le point de Wilson est au-delà du seuil. Un appareillage, des systèmes, des techniques et des articles sont aussi décrits.
PCT/US2015/023285 2014-04-02 2015-03-30 Détection de la saturation dans un amplificateur à commande neutre pour électrocardiogramme WO2015153426A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US201461974022P 2014-04-02 2014-04-02
US61/974,022 2014-04-02

Publications (1)

Publication Number Publication Date
WO2015153426A1 true WO2015153426A1 (fr) 2015-10-08

Family

ID=52829436

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/US2015/023285 WO2015153426A1 (fr) 2014-04-02 2015-03-30 Détection de la saturation dans un amplificateur à commande neutre pour électrocardiogramme

Country Status (1)

Country Link
WO (1) WO2015153426A1 (fr)

Cited By (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP3335623A1 (fr) * 2016-12-16 2018-06-20 Draeger Medical Systems, Inc. Compensation de boucle de rétroaction d'entraînement neutre pour signal d'unité électrochirurgicale détectée
US10314504B2 (en) 2016-11-15 2019-06-11 Microsoft Technology Licensing, Llc Electrocardiogram (EKG) indication saturation correction
US10368805B2 (en) 2016-12-29 2019-08-06 Drägerwerk AG & Co. KGaA Electrode impedance measurement
EP3586736A1 (fr) * 2018-06-26 2020-01-01 General Electric Company Système d'acquisition de données d'électrophysiologie et procédé faisant appel à des circuits à commande d'égalisation différenciée
EP4091548A4 (fr) * 2020-02-29 2023-05-10 Huawei Technologies Co., Ltd. Procédé et dispositif de mesure de signal
EP4190241A1 (fr) 2021-12-06 2023-06-07 Draeger Medical Systems, Inc. Détermination complète d'impédance de contact d'ecg

Citations (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4658831A (en) * 1984-06-18 1987-04-21 Pacific Communications, Inc. Telemetry system and method for transmission of ECG signals with heart pacer signals and loose lead detection
EP0571075A2 (fr) * 1992-04-30 1993-11-24 Hewlett-Packard Company Convertisseur analogique-numérique à réglage automatique de gamme de décalage
WO1998030145A1 (fr) * 1997-01-10 1998-07-16 Micromedical Industries Limited Cable d'interface d'electrocardiogramme universel
WO2001006923A1 (fr) * 1999-07-08 2001-02-01 Instrumentarium Oy Systeme de surveillance d'electrocardiographie
US20030083584A1 (en) * 2000-08-15 2003-05-01 Cardiac Pacemakers, Inc. Electrocardiograph leads-off indicator
US20040138540A1 (en) * 2003-01-10 2004-07-15 Nellcor Puritan Bennett Inc. Signal quality metrics design for qualifying data for a physiological monitor
WO2006050325A2 (fr) * 2004-10-29 2006-05-11 Worcester Polytechnic Institute Systeme d'acquisition de donnees de signal electrophysiologique a canaux multiples sur un circuit integre
US20070038257A1 (en) * 2005-08-11 2007-02-15 Gray James M Impedance measurement apparatus for assessment of biomedical electrode interface quality
EP2442443A1 (fr) * 2010-10-15 2012-04-18 Imec Systèmes d'acquisition de signaux de biopotentiel multicanaux

Patent Citations (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4658831A (en) * 1984-06-18 1987-04-21 Pacific Communications, Inc. Telemetry system and method for transmission of ECG signals with heart pacer signals and loose lead detection
EP0571075A2 (fr) * 1992-04-30 1993-11-24 Hewlett-Packard Company Convertisseur analogique-numérique à réglage automatique de gamme de décalage
WO1998030145A1 (fr) * 1997-01-10 1998-07-16 Micromedical Industries Limited Cable d'interface d'electrocardiogramme universel
WO2001006923A1 (fr) * 1999-07-08 2001-02-01 Instrumentarium Oy Systeme de surveillance d'electrocardiographie
US20030083584A1 (en) * 2000-08-15 2003-05-01 Cardiac Pacemakers, Inc. Electrocardiograph leads-off indicator
US20040138540A1 (en) * 2003-01-10 2004-07-15 Nellcor Puritan Bennett Inc. Signal quality metrics design for qualifying data for a physiological monitor
WO2006050325A2 (fr) * 2004-10-29 2006-05-11 Worcester Polytechnic Institute Systeme d'acquisition de donnees de signal electrophysiologique a canaux multiples sur un circuit integre
US20070038257A1 (en) * 2005-08-11 2007-02-15 Gray James M Impedance measurement apparatus for assessment of biomedical electrode interface quality
EP2442443A1 (fr) * 2010-10-15 2012-04-18 Imec Systèmes d'acquisition de signaux de biopotentiel multicanaux

Cited By (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US10314504B2 (en) 2016-11-15 2019-06-11 Microsoft Technology Licensing, Llc Electrocardiogram (EKG) indication saturation correction
EP3335623A1 (fr) * 2016-12-16 2018-06-20 Draeger Medical Systems, Inc. Compensation de boucle de rétroaction d'entraînement neutre pour signal d'unité électrochirurgicale détectée
US20180168708A1 (en) * 2016-12-16 2018-06-21 Draeger Medical Systems, Inc. Neutral drive feedback loop compensation for detected electrosurgical unit signal
US10568678B2 (en) 2016-12-16 2020-02-25 Drägerwerk AG & Co. KGaA Neutral drive feedback loop compensation for detected electrosurgical unit signal
US10368805B2 (en) 2016-12-29 2019-08-06 Drägerwerk AG & Co. KGaA Electrode impedance measurement
EP3586736A1 (fr) * 2018-06-26 2020-01-01 General Electric Company Système d'acquisition de données d'électrophysiologie et procédé faisant appel à des circuits à commande d'égalisation différenciée
EP4306052A3 (fr) * 2018-06-26 2024-03-13 General Electric Company Système d'acquisition de données électrophysiologiques avec circuits d'attaque à égalisation différenciée
EP4091548A4 (fr) * 2020-02-29 2023-05-10 Huawei Technologies Co., Ltd. Procédé et dispositif de mesure de signal
EP4190241A1 (fr) 2021-12-06 2023-06-07 Draeger Medical Systems, Inc. Détermination complète d'impédance de contact d'ecg

Similar Documents

Publication Publication Date Title
WO2015153426A1 (fr) Détection de la saturation dans un amplificateur à commande neutre pour électrocardiogramme
EP2443995A2 (fr) Appareil ECG avec détection de l'état des contacts à la demande
US8366628B2 (en) Signal sensing in an implanted apparatus with an internal reference
US9897629B2 (en) Bioelectric signal detecting circuits, lead wire detecting circuits and medical devices
US20150241505A1 (en) System And Method For Measuring Contact Impedance Of An Electrode
JP6659536B2 (ja) 電位測定装置及び電位検出方法
Patel et al. Equipment-related electrocardiographic artifacts: causes, characteristics, consequences, and correction
US10368805B2 (en) Electrode impedance measurement
US8827993B2 (en) Gated sampling of electrocardiogram signals during ablation waveform zero-crossing
Bocchiardo et al. Intracardiac impedance monitors stroke volume in resynchronization therapy patients
US9474459B2 (en) ECG electrode and leadwire connection integrity detection
Lynn et al. Arm and wrist surface potential mapping for wearable ECG rhythm recording devices: a pilot clinical study
Freeman et al. Saturation of the right-leg drive amplifier in low-voltage ECG monitors
Gawali et al. Implementation of ECG sensor for real time signal processing applications
CN110267592B (zh) 具有电容除颤保护的ecg传感器
EP3335623B1 (fr) Compensation de boucle de rétroaction d'entraînement neutre pour signal d'unité électrochirurgicale détectée
JP6828178B2 (ja) 電気生理学的測定の間に電極インピーダンスを測定する装置及び方法
Maji et al. Electrical characterization of conductive textile based ECG recording electrodes
Sandra et al. Simulation study of a contactless, capacitive ECG system
Haberman et al. Capacitive driven–right–leg circuit design
EP3091898B1 (fr) Électrode active à faible impédance
Maji Design of a high performance low-power ECG amplifier for textile based un-gelled electrodes
Bifulco et al. A simple, wide bandwidth, biopotential amplifier to record pacemaker pulse waveform
US20210356513A1 (en) Testing electrode quality
TWI504384B (zh) 生理訊號偵測系統

Legal Events

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

Ref document number: 15716325

Country of ref document: EP

Kind code of ref document: A1

NENP Non-entry into the national phase
122 Ep: pct application non-entry in european phase

Ref document number: 15716325

Country of ref document: EP

Kind code of ref document: A1