WO2008084464A1 - Système destiné à fournir des informations cardiovasculaires - Google Patents

Système destiné à fournir des informations cardiovasculaires Download PDF

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Publication number
WO2008084464A1
WO2008084464A1 PCT/IE2008/000003 IE2008000003W WO2008084464A1 WO 2008084464 A1 WO2008084464 A1 WO 2008084464A1 IE 2008000003 W IE2008000003 W IE 2008000003W WO 2008084464 A1 WO2008084464 A1 WO 2008084464A1
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WIPO (PCT)
Prior art keywords
blood flow
location
transducers
flow characteristic
data
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PCT/IE2008/000003
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English (en)
Inventor
David Brown
David Nordin
Andrew John O'riordan
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Emergent Medical Innovations Patents Limited
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Publication of WO2008084464A1 publication Critical patent/WO2008084464A1/fr

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/026—Measuring blood flow
    • A61B5/0285—Measuring or recording phase velocity of blood waves
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B7/00—Instruments for auscultation
    • A61B7/02—Stethoscopes
    • A61B7/04—Electric stethoscopes

Definitions

  • This invention relates to analysis of blood flow.
  • WO2007/057825 and US6786917 With use of the Doppler technique, common variations in vessel anatomy and location and differences in individual body size and habitus become very troublesome as the quality of output is dependent upon the patient remaining perfectly still during a study. This is because the transmitted signal must remain at a constant angle to blood flow in order for the received signal to be detected appropriately. Similarly, the proximity of arteries and veins to one another with blood flowing in opposite directions makes the isolation of the desired blood flow to be analysed very difficult even for a specialist. Similarly, Doppler devices are typically required to operate within a narrow angle to the blood flow in order to attain a quality signal, therefore leading to the output quality being heavily dependent upon the user's skills and experience.
  • the invention is directed towards achieving improved patient blood flow monitoring by non-specialist trained individuals working in relatively uncontrolled environments such as occurs during the management of cardiac arrest.
  • the objective of the invention is to improve the quality of cardiopulmonary resuscitation chest compressions.
  • a method of monitoring in real-time blood flow pulsation caused by blood flowing through a blood vessel and directly resulting from heart activity and/or from artificial chest compressions comprising the steps of:-
  • a passive acoustic transducer receiving acoustic energy from a first location near the vessel
  • a passive acoustic transducer receiving acoustic energy from a second location near the same vessel
  • determining the at least one blood flow characteristic at the second location determining the change in the at least one blood flow characteristic between the first location and the second location to provide data concerning the blood flow.
  • the method comprises the further steps of:-
  • the method comprises the step of, responsive to the comparison of the change in the at least one blood flow characteristic, determining whether the blood flow is driven by a physiological heart-beat or by manual and/or mechanical chest compressions.
  • the method comprises the step of comparing blood flow characteristic data against previous characteristic data from the same monitoring episode.
  • the method comprises the step of comparing blood flow characteristic data against a pre-defined set of data taken from a control population of individuals.
  • the method comprises the step of, responsive to the comparison of the change in the at least one blood flow characteristic, generating an output indicating variations in blood flow pulsation velocity and acceleration.
  • the method comprises the step of indicating to a user a desired action of manual compression of the patient's chest.
  • the method comprises the step of generating a control signal to a mechanical chest compressor.
  • a change in the pulse rhythm of the at least one blood flow characteristic is compared against the pulse rhythm of a pre-defined set of data taken from a control population of individuals.
  • the at least one blood flow characteristic comprises the location of the distal limit of the blood flow wave-front.
  • the at least one blood flow characteristic comprises the location of a peak amplitude and peak frequency of the blood flow wave-front.
  • the at least one blood flow characteristic comprises the velocity of the blood flow pulsation.
  • the at least one blood flow characteristic comprises the acceleration of the blood flow pulsation.
  • a change in the at least one blood flow characteristic per unit time is determined.
  • the step of determining a characteristic comprises analysing low- frequency acoustic components to determine information about pulses of blood flow in the vessel at the locations. In one embodiment, the step of determining a characteristic comprises analysing high frequency acoustic components to determine information about blood flow in the vessel at the locations.
  • the acoustic transducers are located less than 10 cm apart along the blood vessel, and preferably less than 5cm apart.
  • the transducers are supported on a single support, providing a fixed separation between the transducers.
  • At least two transducers are used at each location.
  • the method comprises the step of detecting background acoustic energy at a location removed from the blood vessel and using signals from said transducer for background compensation.
  • the invention provides a blood flow monitoring system comprising: a plurality of acoustic transducers, and a processor linked with the transducers, the processor being adapted to, when a transducer receives acoustic energy from a first location near a blood vessel and a transducer receives acoustic energy from a second location near the same vessel:
  • the system comprises a sensor head with plurality of acoustic transducers, including at least two transducers for sensing at each vessel location. In one embodiment, the system comprises a linear array of acoustic transducers.
  • the system comprises a matrix array of acoustic transducers.
  • the acoustic transducers are embedded in a flexible electrical and sound insulating material of the sensor head.
  • At least two of the transducers are located less than 1 Ocm apart, and preferably less than 5 cm.
  • the sensor head comprises a communication interface for transmission of data within the system.
  • the communication interface is a wireless interface.
  • the sensor head includes a signal conditioning circuit and the data processor.
  • the sensor head comprises an output device for indicating blood flow indications.
  • system further comprises a chest compressor and means in the processor for generating control signals for the chest compressor according to the blood flow data.
  • the processor is adapted to perform the processor operations of any method defined above
  • Fig. 1 is a schematic illustration of a system for the non-invasive, real-time monitoring of blood flow pulsations in a blood vessel according to the invention
  • Fig. 2 is a flow diagram for operation of the system
  • Fig. 3 is a perspective view of a sensor head of the system
  • Figs. 4, 5, and 6 are views showing placement of the sensor head in different positions, namely side of neck, back of neck, and arm;
  • Figs. 7 and 8 are plots illustrating operation of the system.
  • the invention provides feedback to a first responder administering CPR using an improved method of detecting and analysing blood flow pulses.
  • the invention takes advantage of the fact that patients experiencing shock or cardiac arrest have very low blood pressure and corresponding low vascular elasticity, which means that the blood flow pulse velocity is much lower than that of a healthy patient.
  • a lower velocity means that pulse transit times are longer and hence can be measured accurately by a pair of sensors close together( ⁇ 10cm).
  • blood flow can be monitored without need to very accurately position the sensor head. This is particularly so if there are at least two sensors per monitoring location along the vessel. This is particularly advantageous in emergency situations. If the distance between two sensors Sl and S2 in the array is ⁇ d and the time taken for the blood pulse wave to travel between the two sensors is ⁇ t then - - -
  • Pulse acceleration (PA) ⁇ PV/ ⁇ t
  • PV and PA indicate the degree to which CPR chest compressions are being carried out relative to a base-line measurement as taken from the initiation of CPR for any given patient.
  • PV and PA may be manipulated to give audio/visual output and recommendations to the practitioner, to supply control data to a mechanical chest compressor, to supply data to incorporate into AED algorithms, to record, and/or be transmitted to a remote location or network.
  • PV and PA may be compared between similar populations of cardiac arrest patients who have undergone CPR chest compressions in order to further gain insight into compression technique and effectiveness and when monitoring adherence to current ACLS protocol.
  • PV and PA could potentially be used to gain valuable insight and guide therapies in not just cardiac arrest patients but many critically ill patients, chronically ill patients, and even healthy individuals such as athletes.
  • PV and PA may be directly proportional to the rate of CPR chest compressions and the force of compressions respectively.
  • An advantage of an array of sensors is to avoid the necessity of having to locate the exact line of the carotid artery, which is difficult if there is no pulse.
  • the first responder only needs to place the head in the region of the carotid artery, there being at least two transducers for each location along the artery.
  • Using passive acoustic sensors in the array provide information on which activity, a physiological heart beat or chest compressions, is the source of the detected acoustic waveforms. This is because the acoustic waveforms for a particular activity will have temporal and spectral characteristics which are different from that of another.
  • a physiological heart beat will generate blood flow pulses which have a spectral density different from pulses caused by manual chest compressions. The same holds true in consideration of mechanical chest compressions in both cases.
  • the quality of the CPR compressions can be determined by analysing the blood flow pulse wave velocity and acceleration. A faster velocity implies higher blood pressure and more blood flowing through the artery.
  • the system may be used on a patient in shock (i.e. cardiogenic shock:-severe heart failure; septic: infection; neurogenic: brain injury; hypovolemic: excessive blood loss; hypothermic: low body temperature.
  • shock is used here to mean a state where the cardiac output or blood flow does not meet the minimum needs of the organs.
  • unique characteristic waveforms may be detectable that would indicate very low cardiac output and impending cardiac arrest. Cardiac arrest may be considered the most extreme form of cardiogenic shock.
  • these patients receive continuous IV medication in order to maintain a blood pressure that is adequate for support of life.
  • the system may act as a quality control device, on a per-patient basis, that permits the practitioner to monitor their own progress by setting a base-line of performance from the first series of chest compressions (e.g. the first 30 compressions). Then, the system will track the progression of CPR chest compressions during the patient's treatment and indicate whether the practitioner is maintaining adequate chest compressions as compared to their own base-line performance or where their technique is deteriorating from the base-line.
  • the analysis may be based on both the unique CPR chest compression acoustic blood flow pulsation waveform and the blood flow pulsation velocity and acceleration as measured by the time it takes for the waveform to pass along the linear array of sensor rows given the known distance between sensor rows. The system can determine if the practitioner's technique is deteriorating by detecting a decreasing average blood flow pulsation velocity and acceleration between sensor rows.
  • the system 1 comprises two main components, a sensor head 2 and a monitor 100.
  • the sensor head 2 attaches to the patient and communicates with the monitor over a wireless link 27/30.
  • the sensor head 2 comprises an array of ten acoustic transducers 21 and 22 (shown most clearly in Fig. 3). Within the head 2, the transducers 21 are linked with a signal processing unit 25, in turn linked with a control unit 26, in turn connected to the wireless communications interface 27. There is a battery power supply 28.
  • the sensor head 2 comprises an adhesive, sound-insulating, flexible sleeve or pad. The sensor head 2 is approximately 5mm thick.
  • the sensor head is a disposable component due to hygienic precautionary measures. Also, the system 1 will use either rechargeable or disposable batteries as well as carry DC power capabilities for long term monitoring.
  • the acoustic transducers (or “sensors”) 21 and 22 comprise electret microphones because the lower cut-off of their frequency range can be ⁇ 10Hz. This means they can detect pulse-waves.
  • the sensors 21 are arranged in an array with two rows with four sensors per row. This arrangement provides four pairs of side-by-side sensors, thereby covering four locations along an artery, and without need for very accurate placement of the head 2.
  • the sensors are contained in a partially flexible electrical and sound proof housing 20 (see Fig 3).
  • the spacing between the sensors is fixed and may be in the range 0.5cm to 10cm, and is preferably in the range of 0.5cm to 5cm, and in this case are approximately lcm.
  • the sensor head 2 also contains two sensors 22, on the right hand side as viewed in Fig. 3, which are used only to detect background noise and vibrations and not signals emanating from blood flow pulsations in an artery. This enables filtering of external noise from the array of sensors.
  • Other embodiments may have a different number and arrangement of sensors.
  • the head is designed to fit to the body over an artery, for instance a carotid artery in the neck as shown in Fig. 4. It may also function, similarly, when placed over other large arteries such as a vertebral artery in the back of the neck (Fig. 5), a brachial artery in the upper arm (Fig. 6), the abdominal aorta, or the femoral artery in the upper leg.
  • the sensor head may be held in place using an adhesive with or without an accompanying strap.
  • Each sensor 21 and 22 has a broad frequency response (approximately 2Hz to 5 kHz).
  • the mechanical design provides insulation against external sounds.
  • the signal conditioning unit 25 amplifies and filters the electrical signals from each of the sensors 21 and converts them to digital values.
  • the control unit 25 controls the operation of the entire system. In addition, it may carry out further filtering of the sensor data in software.
  • the communications interface 27 wirelessly transmits the sensor data and blood flow pulsation analysis results, stored in the control unit 26, to the monitor 100.
  • the head 2 has a low power consumption and hence can be powered by a battery 28. It could also be powered by an external power supply. The head 2 need not have any external cables. This makes the sensor head 2 less likely to be pulled off the body during resuscitation or other forms of treatment.
  • the patient can easily be moved without the need for unplugging cables.
  • Another advantage of no external cables is reduced vibrations which would otherwise be caused by the movement of the wires.
  • the monitor 100 comprises the communications interface 30, a microcontroller 31, a memory 32, a speaker 33, a keypad 34, and an LCD 35.
  • the monitor provides visual and audio information to the practitioner or in the case of treating cardiac arrest the 'first responder'.
  • a first responder includes anyone who is trained in Advanced Cardiac Life Support and attends the treatment of a patient in cardiac arrest).
  • the monitor 100 need not be in the same physical location as the patient, for example, when the sensor head is attached to the patient by a first responder the data from the sensor head could be transmitted to a hospital and viewed by a physician in the hospital. The physician is then able to provide instruction if necessary to a first responder.
  • the monitor provides an audio output such that the user can hear the blood flow pulsations as well as communicate audible instructions on how to perform and potentially improve chest compressions.
  • the monitor has memory to store the information, microprocessor for processing the information and a communications module for receiving information from the sensor head 2 and transmitting the information to another computer, to a network, to a remote location, or to another medical device such as a mechanical chest compressor or AED.
  • the monitor keyboard and/or touch screen allow data entry. It has an alarm which is activated in the case of system malfunction or for a particular condition of the patient.
  • an LED display may be incorporated onto the sensor head in order to allow more effective visualization output to the practitioner.
  • the monitor provides the following information to the user:-
  • the system 1 measures blood flow pulsation characteristics, such as the location of the distal limit of the blood flow pulsation acoustic wave-front, the location of an acoustic waveform peak, the distance between two acoustic waveform distal limits or peaks, the velocity of the blood flow pulsation, and the acceleration or deceleration of the blood flow pulsation. It achieves this by passively monitoring unique, characteristic acoustic waves resulting from blood flow pulsations as they move past a series of sensors placed at successive locations along the blood flow path.
  • the system is also configured to determine the change in the blood flow pulsation characteristics per unit time between a first location and a second location, between the second location and a third location, between the third location and a fourth location.
  • there are four sensor pairs however there may be more or less pairs, for example to determine changes between the fourth location and a fifth location, and between the fifth location and a sixth location etc.
  • the data flows and control flows are shown in Fig. 2.
  • the transducers 21 detect acoustic changes that result as blood flow pulsations travel through the carotid artery away from the heart during the downward compression of the chest during CPR.
  • the system samples acoustic signals for each sensor in the sensor head and computes the blood flow velocity.
  • three acoustic sensors Sl, S2 and S3 in the sensor head are located at locations A, B and C respectively along the path of an artery.
  • the sampled time varying acoustic waveforms at A, B and C are also shown.
  • the pulse arrives at A first and then ⁇ t(sl-2) seconds later arrives at B. It takes a further ⁇ t(s2-3) seconds to go from B to C.
  • a cross-correlation of waveform A with B will generate a mathematical waveform and the highest peak of that waveform will occur at ⁇ t(sl-2) seconds from the 0 position.
  • the system calculates the pulse velocities PV 11 -PV n-1 at points Sl..Sn-I. Applying statistical analysis to PV 1 ⁇ PV n-1 yields the mean pulse velocity PV.
  • the waveforms sampled at A, B and C can be further processed by performing a spectral analysis which provides information on the shape of the waveform.
  • the spectral analysis of pulsations caused by a natural heart-beat will be different from that caused by manual compressions.
  • the spectral analysis allows one waveform to be computationally compared with another.
  • the results of such comparisons will provide the practitioner with information on the cardiac state of the patient, hi addition, the spectral analysis of the real-time data can be compared with a set of predefined spectral analyses, corresponding to blood flow generated by various artificial means.
  • the results of these comparisons can assist a practitioner in optimising their technique of administering CPR to a patient.
  • the spectral analysis involves a Fourier Transform to find the waveform frequency components.
  • the frequency components provide information on the conditions of the heart and artery: the lower frequency components generally representing the artery and the higher frequency components the heart.
  • the characteristics determines at the locations may be velocity and/or acceleration, and/or frequency components.
  • the resultant spatial (three plots together) and temporal (within any one plot) waveforms may have single peak or multiple peaks.
  • a unique signature waveform specific to a blood flow pulsation for instance that resulting from a chest compression, will be detectable.
  • the monitor 100 will show the absolute values of the blood flow pulsation acoustic amplitude and frequency waveforms and the average blood flow pulsation velocity and acceleration over a predefined time interval in for instance a carotid artery. It may also show an index (i.e. ratio) of these average values compared to normal physiologic average values of blood flow pulsation velocity and acceleration...
  • an index i.e. ratio
  • the output will advise the practitioner on how to improve CPR chest compressions.
  • the system acts as a feedback controller directing the mechanical compressor to modify its function as necessary (i.e. compression rate, depth, force) in order to optimize blood flow.
  • the monitor has the ability to record, store, and transmit data to a remote location in addition to offering audio and visual output.
  • Another configuration entails using a handheld computer as a processor and display unit instead of a host computer or monitor, hi this configuration the sensor head can communicate via a wireless or a serial interface for example with the hand held device.
  • Proprietary software that will be compatible with the operating system of the hand held device will carryout the evaluation of the raw data. This data will again be presented in a format on the screen of the hand held device that will represent the blood flow pulsation velocity and acceleration in a visual display as well as offer auditory output.
  • the hand held device will also offer recording, storage, and remote transmission functionality.
  • the acoustic transducers 21 detect real-time variations in the unique spatial and temporal characteristics of acoustic signals of blood flow pulsations as they pass through an artery, for instance a carotid artery.
  • the system 1 measures, simultaneously, blood flow pulsation characteristics at various locations along an artery. These characteristics are dependant on what activity causes the blood flow pulsations, be it from a physiologic beating heart, manual chest compressions, or a mechanical chest compression device.
  • the primary purpose of the system is to confirm the presence or absence of physiologic blood flow pulsations, then if absent verify that either mechanical or manual chest compressions are generating adequate carotid blood flow pulsations.
  • the system determines which activity, a physiologic heart beat or chest compressions, is the source of the detected acoustic waveforms by performing spatial and temporal analyses of the real-time acoustic data from each of the sensor rows.
  • a particular activity will have an associated spatial and temporal waveform and frequency (spectral) components distinct from that of another. For example, the frequency distribution of a physiologic heart beat will be distinctly different from that resulting - -
  • Spatial analysis of the acoustic signals can be carried out because there are a number of sensors in an array equidistant from one another, placed along an artery. External noise and vibrations can be filtered out from the analysis by using the sensors 22, with similar characteristics as those in the array, but being insulated from signals emanating from the region of the monitored artery.
  • the system represents all data from the active monitoring episode in terms of absolute and average values such as absolute and average blood flow pulsation velocity and acceleration. Also, it represents all data from the active monitoring episode in terms of a performance index that is a ratio of the average blood flow pulsation velocity and acceleration of the active monitoring episode versus predefined values taken from a control population of individuals.
  • the system also represents all data from the active monitoring episode in terms of absolute and average values such as absolute and average blood flow velocity and acceleration. It compares the change in the at least one blood flow characteristic against the pre-defined set of data taken from a control population of individuals. It represents all data from the active monitoring episode in terms of a performance index that is a ratio of the average blood flow velocity and acceleration of the active monitoring episode versus predefined values taken from a control population of individuals.
  • Step 6 data recorded, stored, and/or transmitted to remote location
  • the LCD display shows carotid blood flow pulsation waveforms and average blood flow pulsation velocity and acceleration values as well as a performance index of secondary (i.e. chest compression) vs. normal primary carotid blood flow pulsations.
  • c. Push the 'audio' button to hear the blood flow pulsations and the blood flow pulsation velocity and acceleration values and recommendations on how to improve chest compression technique.
  • Data will be automatically recorded and saved. Before turning off power or when the link to the 'sensor head' is interrupted the user will be prompted to enter the patient's identification information.
  • the monitor When not in use the monitor should remain plugged into the power charger to ensure the batteries are fully charged. If necessary, a DC power source from an ambulance or vehicle may be used for long term monitoring.
  • the system according to the invention is not limited to use for analysing blood flow during chest compressions.
  • the system may be employed to analyse blood flow during other procedures or during an examination such as an exercise stress test in the evaluation of ischemic heart disease. Changes in PV and PA during the stress test may be indicative of the heart's ability to compensate during exercise.
  • the system may be used to montior the long term progress on individuals suffering congestive heart failure by monitoring changes in PV and PA over a period of months or years.
  • the embodiments of the invention described with reference to the accompanying drawings comprise a computer system and processes performed by the computer system. However the invention also extends to computer programs, particularly computer programs stored on or in a carrier adapted to bring the invention into practice.
  • the program may be in the form of source code, object code, or a code intermediate source and object code, such as in partially compiled form or in any other form suitable for use in the implementation of the method according to the invention.
  • the carrier may comprise a storage medium such as ROM, such as a CD-ROM, or magnetic recording medium, such as a floppy disk or hard disk or solid-state flash memory device.
  • the carrier may be an electrical or optical signal which may be transmitted via an electrical or an optical cable or by radio or other means.
  • the system may be configured to measure the blood flow pulsation characteristics at any number, of successive locations along the blood flow path.
  • a monitor may exist as a customised display/audio device or a PC (including desktop, laptop, palm device pocket PC).

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Physics & Mathematics (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Molecular Biology (AREA)
  • Acoustics & Sound (AREA)
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  • Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)

Abstract

La présente invention concerne un système (1) qui analyse des pulsations de flux sanguin chez un patient. Ledit système se compose de deux éléments principaux, une tête de capteur (2) et un moniteur (100). La tête de capteur (2) se fixe sur le patient et communique avec le moniteur par une liaison sans fil (27/30). La tête de capteur (2) comprend une barrette de dix transducteurs acoustiques (21, 22) et à l'intérieur de la tête (2), les transducteurs (21) sont reliés à une unité de traitement des signaux (25), elle-même reliée à une unité de commande (26), elle-même reliée à l'interface de communication sans fil (27). Il y a une alimentation électrique par batterie (28). La tête de capteur (2) comprend un manchon ou un coussinet (20) adhésif, insonorisant et flexible. Puisqu'il y a une barrette de transducteurs, il y en a au moins deux par emplacement sur l'artère, et la tête peut être placée en un emplacement approximatif. Parce qu'une énergie acoustique est détectée, et qu'il y a une analyse temporelle, spatiale et spectrale, des informations très complètes peuvent être déduites. Les informations sont particulièrement utiles pour une analyse d'une RCP et pour fournir un retour d'information immédiat.
PCT/IE2008/000003 2007-01-09 2008-01-09 Système destiné à fournir des informations cardiovasculaires WO2008084464A1 (fr)

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GB2465817A (en) * 2008-11-10 2010-06-09 Rashid Mazhar CPR feedback system
ITPI20090099A1 (it) * 2009-07-31 2011-02-01 Cnr Consiglio Naz Delle Ric Erche Apparecchiatura per la misura della velocità di propagazione di un'onda pressoria nel sistema arterioso
WO2012037614A1 (fr) * 2010-09-24 2012-03-29 Sonomedical Pty Ltd Système et appareil de surveillance électronique destinés à la collecte, à la présentation et à l'analyse de données
WO2013169346A1 (fr) 2012-05-07 2013-11-14 Zoll Medical Corporation Métrique de performances de sauvetage
CN104799837A (zh) * 2015-05-22 2015-07-29 上海斐讯数据通信技术有限公司 血压血流控制方法、系统、按摩设备及智能移动终端
US11179293B2 (en) 2017-07-28 2021-11-23 Stryker Corporation Patient support system with chest compression system and harness assembly with sensor system

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WO2002015836A2 (fr) * 2000-08-23 2002-02-28 Cpr Devices Ltd. Dispositif de surveillance de reanimation cardio-respiratoire
US20020173725A1 (en) * 2001-05-18 2002-11-21 Rock Joseph E. Integrated cardiac resuscitation system with ability to detect perfusion

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GB2465817A (en) * 2008-11-10 2010-06-09 Rashid Mazhar CPR feedback system
ITPI20090099A1 (it) * 2009-07-31 2011-02-01 Cnr Consiglio Naz Delle Ric Erche Apparecchiatura per la misura della velocità di propagazione di un'onda pressoria nel sistema arterioso
WO2011039580A3 (fr) * 2009-07-31 2011-05-26 Cnr-Dipartimento Di Medicina Appareil de mesure de vitesse de propagation d'onde de pression artérielle
WO2012037614A1 (fr) * 2010-09-24 2012-03-29 Sonomedical Pty Ltd Système et appareil de surveillance électronique destinés à la collecte, à la présentation et à l'analyse de données
WO2013169346A1 (fr) 2012-05-07 2013-11-14 Zoll Medical Corporation Métrique de performances de sauvetage
EP2847702A4 (fr) * 2012-05-07 2016-02-10 Zoll Medical Corp Métrique de performances de sauvetage
CN104799837A (zh) * 2015-05-22 2015-07-29 上海斐讯数据通信技术有限公司 血压血流控制方法、系统、按摩设备及智能移动终端
CN104799837B (zh) * 2015-05-22 2018-07-31 上海斐讯数据通信技术有限公司 血压血流控制方法、系统、按摩设备及智能移动终端
US11179293B2 (en) 2017-07-28 2021-11-23 Stryker Corporation Patient support system with chest compression system and harness assembly with sensor system
US11723835B2 (en) 2017-07-28 2023-08-15 Stryker Corporation Patient support system with chest compression system and harness assembly with sensor system

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