Patent Description:
When people suffer from some types of heart arrhythmias, the result may be that blood flow to various parts of the body is reduced. Some arrhythmias may even result in a Sudden Cardiac Arrest (SCA). SCA can lead to death very quickly, e.g. within <NUM> minutes, unless treated in the interim.

Some people have an increased risk of SCA. People at a higher risk include patients who have had a heart attack, or a prior SCA episode. A frequent recommendation is for these people to receive an Implantable Cardioverter Defibrillator (ICD). The ICD is surgically implanted in the chest, and continuously monitors the patient's electrocardiogram (ECG). If certain types of heart arrhythmias are detected, then the ICD delivers an electric shock through the heart.

After being identified as having an increased risk of an SCA, and before receiving an ICD, these people are sometimes given a Wearable Cardioverter Defibrillator (WCD) system. (Early versions of such systems were called wearable cardiac defibrillator systems. ) A WCD system typically includes a harness, vest, or other garment that the patient is to wear. The WCD system further includes electronic components, such as a defibrillator and electrodes, coupled to the harness, vest, or other garment. When the patient wears the WCD system, the external electrodes may then make good electrical contact with the patient's skin, and therefore can help sense the patient's ECG. If a shockable heart arrhythmia is detected, then the defibrillator delivers the appropriate electric shock through the patient's body, and thus through the heart.

Often the patient's ECG includes electrical noise, which can be created at the interface of the electrodes with the patient's skin. Such noise can make it difficult to diagnose the patient's condition accurately from the ECG, and detect whether or not the patient is having a shockable arrhythmia.

All subject matter discussed in this Background section of this document is not necessarily prior art, and may not be presumed to be prior art simply because it is presented in this Background section. Plus, any reference to any prior art in this description is not, and should not be taken as, an acknowledgement or any form of suggestion that such prior art forms parts of the common general knowledge in any art in any country. Along these lines, any recognition of problems in the prior art discussed in this Background section or associated with such subject matter should not be treated as prior art, unless expressly stated to be prior art. Rather, the discussion of any subject matter in this Background section should be treated as part of the approach taken towards the particular problem by the inventors. This approach in and of itself may also be inventive.

Document <CIT> describes a wearable cardioverter defibrillator system with a processor, which can make a shock/no shock determination based on ECG signals and cause a discharge circuit to discharge the stored energy, if the determination is to shock. Prior to making the shock/no shock decision, the processor mas discard at least one of the ECG signals.

Document <CIT> discloses an implantable medical device which is configured to detect saturation events from a cardiac electrical signal. Before delivering a therapy, a noise analysis may be is performed.

The present description gives instances of wearable cardioverter defibrillator (WCD) systems, storage media that may store programs, and methods, the use of which may help overcome problems and limitations of the prior art.

In embodiments a WCD system is worn and/or carried by an ambulatory patient. The WCD system analyzes an ECG signal of the patient, to determine whether or not the patient should be given an electric shock to restart their heart. If so, then the WCD system first gives a preliminary alarm to the patient, asking them to prove they are alive if they are. The WCD system further determines whether the ECG signal contains too much High Amplitude (H-A) noise, which can distort the analysis of the ECG signal. If too much H-A noise is detected for a long time, the WCD system may eventually alert the patient about their activity, so that the ECG noise may be abated. The WCD system may even pause the analysis of the ECG signal, so that there will be no preliminary alarms that could be false until the ECG noise is abated.

Another advantage can be that, with fewer false preliminary alarms, the patient can be more compliant in actually wearing and/or carrying the WCD system.

These and other features and advantages of the claimed invention will become more readily apparent in view of the embodiments described and illustrated in this specification, namely in this written specification and the associated drawings.

The present invention provides a wearable cardioverter defibrillator (WCD) system, comprising:.

The present invention further provides a non-transitory computer-readable storage medium storing one or more programs which, when executed by at least one processor of a wearable cardioverter defibrillator (WCD) system, the WCD system further including a support structure configured to be worn by an ambulatory patient, an energy storage module configured to store an electrical charge, a discharge circuit coupled to the energy storage module, and electrodes configured to sense an Electrocardiogram (ECG) signal of the patient, these one or more programs result in operations comprising:.

As has been mentioned, the present description is about wearable cardioverter defibrillator (WCD) systems, media that store instructions, and methods. Embodiments are now described in more detail.

A wearable cardioverter defibrillator (WCD) system made according to embodiments has a number of components. These components can be provided separately as modules that can be interconnected, or can be combined with other components, etc..

<FIG> depicts a patient <NUM>. Patient <NUM> may also be referred to as a person and/or wearer, since the patient is wearing components of the WCD system. Patient <NUM> is ambulatory, which means patient <NUM> can walk around, and is not necessarily bed-ridden.

<FIG> also depicts components of a WCD system made according to embodiments. One such component is a support structure <NUM> that is wearable by patient <NUM>. It will be understood that support structure <NUM> is shown only generically in <FIG>, and in fact partly conceptually. <FIG> is provided merely to illustrate concepts about support structure <NUM>, and is not to be construed as limiting how support structure <NUM> is implemented, or how it is worn.

Support structure <NUM> can be implemented in many different ways. For example, it can be implemented in a single component or a combination of multiple components. In embodiments, support structure <NUM> could include a vest, a half-vest, a garment, etc. In such embodiments such items can be worn similarly to parallel articles of clothing. In embodiments, support structure <NUM> could include a harness, one or more belts or straps, etc. In such embodiments, such items can be worn by the patient around the torso, hips, over the shoulder, etc. In embodiments, support structure <NUM> can include a container or housing, which can even be waterproof. In such embodiments, the support structure can be worn by being attached to the patient by adhesive material, for example as shown in <CIT>. Support structure <NUM> can even be implemented as described for the support structure of US Pat. Of course, in such embodiments, the person skilled in the art will recognize that additional components of the WCD system can be in the housing of a support structure instead of being attached externally to the support structure, for example as described in the <CIT> document. There can be other examples.

A WCD system according to embodiments is configured to defibrillate a patient who is wearing it, by delivering an electrical charge to the patient's body in the form of an electric shock delivered in one or more pulses. <FIG> shows a sample external defibrillator <NUM>, and sample defibrillation electrodes <NUM>, <NUM>, which are coupled to external defibrillator <NUM> via electrode leads <NUM>. Defibrillator <NUM> and defibrillation electrodes <NUM>, <NUM> can be coupled to support structure <NUM>. As such, many of the components of defibrillator <NUM> could be therefore coupled to support structure <NUM>. When defibrillation electrodes <NUM>, <NUM> make good electrical contact with the body of patient <NUM>, defibrillator <NUM> can administer, via electrodes <NUM>, <NUM>, a brief, strong electric pulse <NUM> through the body. Pulse <NUM> is also known as shock, defibrillation shock, therapy and therapy shock. Pulse <NUM> is intended to go through and restart heart <NUM>, in an effort to save the life of patient <NUM>. Pulse <NUM> can further include one or more pacing pulses, and so on.

A prior art defibrillator typically decides whether to defibrillate or not based on an ECG signal of the patient. However, external defibrillator <NUM> may initiate defibrillation (or hold-off defibrillation) based on a variety of inputs, with ECG merely being one of them.

Accordingly, it will be appreciated that signals such as physiological signals containing physiological data can be obtained from patient <NUM>. While the patient may be considered also a "user" of the WCD system, this is not a requirement. That is, for example, a user of the wearable cardioverter defibrillator (WCD) may include a clinician such as a doctor, nurse, emergency medical technician (EMT) or other similarly situated individual (or group of individuals). The particular context of these and other related terms within this description should be interpreted accordingly.

The WCD system may optionally include an outside monitoring device <NUM>. Device <NUM> is called an "outside" device because it could be provided as a standalone device, for example not within the housing of defibrillator <NUM>. Device <NUM> can be configured to sense or monitor at least one local parameter. A local parameter can be a parameter of patient <NUM>, or a parameter of the WCD system, or a parameter of the environment, as will be described later in this document. Device <NUM> may include one or more transducers or sensors that are configured to render one or more physiological inputs or signals from one or more patient parameters that they sense.

Optionally, device <NUM> is physically coupled to support structure <NUM>. In addition, device <NUM> can be communicatively coupled with other components, which are coupled to support structure <NUM>. Such communication can be implemented by a communication module, as will be deemed applicable by a person skilled in the art in view of this description.

<FIG> is a diagram showing components of an external defibrillator <NUM>, made according to embodiments. These components can be, for example, included in external defibrillator <NUM> of <FIG>. The components shown in <FIG> can be provided in a housing <NUM>, which may also be referred to as casing <NUM>.

External defibrillator <NUM> is intended for a patient who would be wearing it, such as patient <NUM> of <FIG>. Defibrillator <NUM> may further include a user interface <NUM> for a user <NUM>. User <NUM> can be patient <NUM>, also known as wearer <NUM>. Or, user <NUM> can be a local rescuer at the scene, such as a bystander who might offer assistance, or a trained person. Or, user <NUM> might be a remotely located trained caregiver in communication with the WCD system.

User interface <NUM> can be made in a number of ways. User interface <NUM> may include output devices, which can be visual, audible or tactile, for communicating to a user by outputting images, sounds or vibrations. Images, sounds, vibrations, and anything that can be perceived by user <NUM> can also be called human-perceptible indications. There are many examples of output devices. For example, an output device can be a light, or a screen to display what is sensed, detected and/or measured, and provide visual feedback to rescuer <NUM> for their resuscitation attempts, and so on. Another output device can be a speaker, which can be configured to issue voice prompts, beeps, loud alarm sounds and/or words to warn bystanders, etc..

User interface <NUM> may further include input devices for receiving inputs from users. Such input devices may additionally include various controls, such as pushbuttons, keyboards, touchscreens, one or more microphones, and so on. An input device can be a cancel switch, which is sometimes called an "I am alive" switch or "live man" switch. In some embodiments, actuating the cancel switch can prevent the impending delivery of a shock.

Defibrillator <NUM> may include an internal monitoring device <NUM>. Device <NUM> is called an "internal" device because it is incorporated within housing <NUM>. Monitoring device <NUM> can sense or monitor patient parameters such as patient physiological parameters, system parameters and/or environmental parameters, all of which can be called patient data. In other words, internal monitoring device <NUM> can be complementary or an alternative to outside monitoring device <NUM> of <FIG>. Allocating which of the parameters are to be monitored by which of monitoring devices <NUM>, <NUM> can be done according to design considerations. Device <NUM> may include one or more transducers or sensors that are configured to render one or more physiological inputs from one or more patient parameters that it senses.

Patient parameters may include patient physiological parameters. Patient physiological parameters may include, for example and without limitation, those physiological parameters that can be of any help in detecting by the wearable defibrillation system whether the patient is in need of a shock, plus optionally their medical history and/or event history. Examples of such parameters include the patient's ECG, blood oxygen level, blood flow, blood pressure, blood perfusion, pulsatile change in light transmission or reflection properties of perfused tissue, heart sounds, heart wall motion, breathing sounds and pulse. Accordingly, monitoring devices <NUM>, <NUM> may include one or more sensors configured to acquire patient physiological signals. Examples of such sensors or transducers include electrodes to detect ECG data, a perfusion sensor, a pulse oximeter, a device for detecting blood flow (e.g. a Doppler device), a sensor for detecting blood pressure (e.g. a cuff), an optical sensor, illumination detectors and sensors perhaps working together with light sources for detecting color change in tissue, a motion sensor, a device that can detect heart wall movement, a sound sensor, a device with a microphone, an SpO2 sensor, and so on. In view of this disclosure, it will be appreciated that such sensors can help detect the patient's pulse, and can therefore also be called pulse detection sensors, pulse sensors, and pulse rate sensors. Pulse detection is also taught at least in Physio-Control's <CIT>. In addition, a person skilled in the art may implement other ways of performing pulse detection. In such cases, the transducer includes an appropriate sensor, and the physiological input is a measurement by the sensor of that patient parameter. For example, the appropriate sensor for a heart sound may include a microphone, etc..

In some embodiments, the local parameter is a trend that can be detected in a monitored physiological parameter of patient <NUM>. A trend can be detected by comparing values of parameters at different times. Parameters whose detected trends can particularly help a cardiac rehabilitation program include: a) cardiac function (e.g. ejection fraction, stroke volume, cardiac output, etc.); b) heart rate variability at rest or during exercise; c) heart rate profile during exercise and measurement of activity vigor, such as from the profile of an accelerometer signal and informed from adaptive rate pacemaker technology; d) heart rate trending; e) perfusion, such as from SpO2 or CO2; f) respiratory function, respiratory rate, etc.; g) motion, level of activity; and so on. Once a trend is detected, it can be stored and/or reported via a communication link, along perhaps with a warning. From the report, a physician monitoring the progress of patient <NUM> will know about a condition that is either not improving or deteriorating.

Patient state parameters include recorded aspects of patient <NUM>, such as motion, posture, whether they have spoken recently plus maybe also what they said, and so on, plus optionally the history of these parameters. Or, one of these monitoring devices could include a location sensor such as a Global Positioning System (GPS) location sensor. Such a sensor can detect the location, plus a speed can be detected as a rate of change of location over time. Many motion detectors output a motion signal that is indicative of the motion of the detector, and thus of the patient's body. Patient state parameters can be very helpful in narrowing down the determination of whether SCA is indeed taking place.

A WCD system made according to embodiments may include a motion detector. In embodiments, a motion detector can be implemented within monitoring device <NUM> or monitoring device <NUM>. Such a motion detector can be made in many ways as is known in the art, for example by using an accelerometer. In this example, a motion detector <NUM> is implemented within monitoring device <NUM>.

A motion detector of a WCD system according to embodiments can be configured to detect a motion event. In response, the motion detector may render or generate, from the detected motion event or motion, a motion detection input that can be received by a subsequent device or functionality. A motion event can be defined as is convenient, for example a change in motion from a baseline motion or rest, etc. In such cases, a sensed patient parameter is motion.

System parameters of a WCD system can include system identification, battery status, system date and time, reports of self-testing, records of data entered, records of episodes and intervention, and so on.

Environmental parameters can include ambient temperature and pressure. Moreover, a humidity sensor may provide information as to whether it is likely raining. Presumed patient location could also be considered an environmental parameter. The patient location could be presumed, if monitoring device <NUM> or <NUM> includes a GPS location sensor as per the above, and if it is presumed that the patient is wearing the WCD system.

Defibrillator <NUM> typically includes a defibrillation port <NUM>, such as a socket in housing <NUM>. Defibrillation port <NUM> includes electrical nodes <NUM>, <NUM>. Leads of defibrillation electrodes <NUM>, <NUM>, such as leads <NUM> of <FIG>, can be plugged into defibrillation port <NUM>, so as to make electrical contact with nodes <NUM>, <NUM>, respectively. It is also possible that defibrillation electrodes <NUM>, <NUM> are connected continuously to defibrillation port <NUM>, instead. Either way, defibrillation port <NUM> can be used for guiding, via electrodes, to the wearer the electrical charge that has been stored in an energy storage module <NUM> that is described more fully later in this document. The electric charge will be the shock for defibrillation, pacing, and so on.

Defibrillator <NUM> may optionally also have a sensor port <NUM> in housing <NUM>, which is also sometimes known as an ECG port. Sensor port <NUM> can be adapted for plugging in sensing electrodes <NUM>, which are also known as ECG electrodes and ECG leads. It is also possible that sensing electrodes <NUM> can be connected continuously to sensor port <NUM>, instead. Sensing electrodes <NUM> are types of transducers that can help sense an ECG signal, e.g. a <NUM>-lead signal, or a signal from a different number of leads, especially if they make good electrical contact with the body of the patient and in particular with the skin of the patient. Sensing electrodes <NUM> can be attached to the inside of support structure <NUM> for making good electrical contact with the patient, similarly with defibrillation electrodes <NUM>, <NUM>.

Optionally a WCD system according to embodiments also includes a fluid that it can deploy automatically between the electrodes and the patient's skin. The fluid can be conductive, such as by including an electrolyte, for establishing a better electrical contact between the electrode and the skin. Electrically speaking, when the fluid is deployed, the electrical impedance between the electrode and the skin is reduced. Mechanically speaking, the fluid may be in the form of a low-viscosity gel, so that it does not flow away from the electrode, after it has been deployed. The fluid can be used for both defibrillation electrodes <NUM>, <NUM>, and for sensing electrodes <NUM>.

The fluid may be initially stored in a fluid reservoir, not shown in <FIG>, which can be coupled to the support structure. In addition, a WCD system according to embodiments further includes a fluid deploying mechanism <NUM>. Fluid deploying mechanism <NUM> can be configured to cause at least some of the fluid to be released from the reservoir, and be deployed near one or both of the patient locations, to which the electrodes are configured to be attached to the patient. In some embodiments, fluid deploying mechanism <NUM> is activated prior to the electrical discharge responsive to receiving activation signal AS from a processor <NUM>, which is described more fully later in this document.

The intent for a WCD system is to shock when needed, and not shock when not needed. An ECG signal may provide sufficient data for making a shock/no shock determination. The problem is that, at any given point in time, some of these ECG signals may include noise, while others not. The noise may be due to patient movement, how well the electrodes contact the skin, and so on. The inventor has identified that some types of ECG noise for a WCD system can be classified as High-Frequency (H-F) noise, while other types of such ECG noise can be classified as High-Amplitude (H-A) noise. The noise problem for a WCD may be further exacerbated by the desire to use dry, non-adhesive monitoring electrodes. Dry, non-adhesive electrodes are thought to be more comfortable for the patient to wear in the long term, but may produce more noise than a conventional ECG monitoring electrode that includes adhesive to hold the electrode in place and an electrolyte gel to reduce the impedance of the electrode-skin interface.

Defibrillator <NUM> also includes a measurement circuit <NUM>, as one or more of its sensors or transducers. Measurement circuit <NUM> senses one or more electrical physiological signals of the patient from sensor port <NUM>, if provided. Even if defibrillator <NUM> lacks sensor port <NUM>, measurement circuit <NUM> may optionally obtain physiological signals through nodes <NUM>, <NUM> instead, when defibrillation electrodes <NUM>, <NUM> are attached to the patient. In these cases, the physiological input reflects an ECG measurement. The patient parameter can be an ECG, which can be sensed as a voltage difference between electrodes <NUM>, <NUM>. In addition the patient parameter can be an impedance, which can be sensed between electrodes <NUM>, <NUM> and/or the connections of sensor port <NUM>. Sensing the impedance can be useful for detecting, among other things, whether these electrodes <NUM>, <NUM> and/or sensing electrodes <NUM> are not making good electrical contact with the patient's body. These patient physiological signals can be sensed, when available. Measurement circuit <NUM> can then render or generate information about them as physiological inputs, data, other signals, etc. More strictly speaking, the information rendered by measurement circuit <NUM> is output from it, but this information can be called an input because it is received by a subsequent device or functionality as an input.

Defibrillator <NUM> also includes a processor <NUM>. Processor <NUM> may be implemented in a number of ways. Such ways include, by way of example and not of limitation, digital and/or analog processors such as microprocessors and Digital Signal Processors (DSPs); controllers such as microcontrollers; software running in a machine; programmable circuits such as Field Programmable Gate Arrays (FPGAs), Field-Programmable Analog Arrays (FPAAs), Programmable Logic Devices (PLDs), Application Specific Integrated Circuits (ASICs), any combination of one or more of these, and so on.

Processor <NUM> may include, or have access to, a non-transitory storage medium, such as memory <NUM> that is described more fully later in this document. Such a memory can have a non-volatile component for storage of machine-readable and machine-executable instructions. A set of such instructions can also be called a program. The instructions, which may also referred to as "software," generally provide functionality by performing methods as may be disclosed herein or understood by one skilled in the art in view of the disclosed embodiments. In some embodiments, and as a matter of convention used herein, instances of the software may be referred to as a "module" and by other similar terms. Generally, a module includes a set of the instructions so as to offer or fulfill a particular functionality. Embodiments of modules and the functionality delivered are not limited by the embodiments described in this document. Processor <NUM> may, among other functions, set a flag, unset a flag, and so on.

Processor <NUM> can be considered to have a number of modules. One such module can be a detection module <NUM>. Detection module <NUM> can include a Ventricular Fibrillation (VF) detector. The patient's sensed ECG from measurement circuit <NUM>, which can be available as physiological inputs, data, or other signals, may be used by the VF detector to determine whether the patient is experiencing VF. Detecting VF is useful, because VF typically results in SCA. Detection module <NUM> can also include a Ventricular Tachycardia (VT) detector, and so on.

Another such module in processor <NUM> can be an advice module <NUM>, which generates advice for what to do. The advice can be based on outputs of detection module <NUM>. There can be many types of advice according to embodiments. In some embodiments, the advice is a shock/no shock determination that processor <NUM> can make, for example via advice module <NUM>. The shock/no shock determination can be made by executing a stored Shock Advisory Algorithm. A Shock Advisory Algorithm can make a shock/no shock determination from one or more ECG signals that are captured according to embodiments, and determining whether a shock criterion is met. The determination can be made from a rhythm analysis of the captured ECG signal or otherwise.

In some embodiments, when the determination is to shock, an electrical charge is delivered to the patient. Delivering the electrical charge is also known as discharging. Shocking can be for defibrillation, pacing, and so on.

Processor <NUM> can include additional modules, such as other module <NUM>, for other functions. In addition, if internal monitoring device <NUM> is indeed provided, it may be operated in part by processor <NUM>, etc..

Defibrillator <NUM> optionally further includes a memory <NUM>, which can work together with processor <NUM>. Memory <NUM> may be implemented in a number of ways. Such ways include, by way of example and not of limitation, volatile memories, Nonvolatile Memories (NVM), Read-Only Memories (ROM), Random Access Memories (RAM), magnetic disk storage media, optical storage media, smart cards, flash memory devices, any combination of these, and so on. Memory <NUM> is thus a non-transitory storage medium. Memory <NUM>, if provided, can include programs for processor <NUM>, which processor <NUM> may be able to read and execute. More particularly, the programs can include sets of instructions in the form of code, which processor <NUM> may be able to execute upon reading. Executing is performed by physical manipulations of physical quantities, and may result in functions, operations, processes, actions and/or methods to be performed, and/or the processor to cause other devices or components or blocks to perform such functions, operations, processes, actions and/or methods. The programs can be operational for the inherent needs of processor <NUM>, and can also include protocols and ways that decisions can be made by advice module <NUM>. In addition, memory <NUM> can store prompts for user <NUM>, if this user is a local rescuer. Moreover, memory <NUM> can store data. This data can include patient data, system data and environmental data, for example as learned by internal monitoring device <NUM> and outside monitoring device <NUM>. The data can be stored in memory <NUM> before it is transmitted out of defibrillator <NUM>, or stored there after it is received by defibrillator <NUM>.

Defibrillator <NUM> may also include a power source <NUM>. To enable portability of defibrillator <NUM>, power source <NUM> typically includes a battery. Such a battery is typically implemented as a battery pack, which can be rechargeable or not. Sometimes a combination is used of rechargeable and non-rechargeable battery packs. Other embodiments of power source <NUM> can include an AC power override, for where AC power will be available, an energy-storing capacitor, and so on. In some embodiments, power source <NUM> is controlled by processor <NUM>. Appropriate components may be included to provide for charging or replacing power source <NUM>.

Defibrillator <NUM> may additionally include an energy storage module <NUM>. Energy storage module <NUM> can be coupled to the support structure of the WCD system, for example either directly or via the electrodes and their leads. Module <NUM> is where some electrical energy can be stored temporarily in the form of an electrical charge, when preparing it for discharge to administer a shock. In embodiments, module <NUM> can be charged from power source <NUM> to the desired amount of energy, as controlled by processor <NUM>. In typical implementations, module <NUM> includes a capacitor <NUM>, which can be a single capacitor or a system of capacitors, and so on. In some embodiments, energy storage module <NUM> includes a device that exhibits high power density, such as an ultracapacitor. As described above, capacitor <NUM> can store the energy in the form of an electrical charge, for delivering to the patient.

Defibrillator <NUM> moreover includes a discharge circuit <NUM>. When the decision is to shock, processor <NUM> can be configured to control discharge circuit <NUM> to discharge through the patient the electrical charge stored in energy storage module <NUM>. When so controlled, circuit <NUM> can permit the energy stored in module <NUM> to be discharged to nodes <NUM>, <NUM>, and from there also to defibrillation electrodes <NUM>, <NUM>, so as to cause a shock to be delivered to the patient. Circuit <NUM> can include one or more switches <NUM>. Switches <NUM> can be made in a number of ways, such as by an H-bridge, and so on. Circuit <NUM> can also be controlled via user interface <NUM>.

Defibrillator <NUM> can optionally include a communication module <NUM>, for establishing one or more wired or wireless communication links with other devices of other entities, such as a remote assistance center, Emergency Medical Services (EMS), and so on. The data can include patient data, event information, therapy attempted, CPR performance, system data, environmental data, and so on. For example, communication module <NUM> may transmit wirelessly, e.g. on a daily basis, heart rate, respiratory rate, and other vital signs data to a server accessible over the internet, for instance as described in <CIT>. This data can be analyzed directly by the patient's physician and can also be analyzed automatically by algorithms designed to detect a developing illness and then notify medical personnel via text, email, phone, etc. Module <NUM> may also include such interconnected sub-components as may be deemed necessary by a person skilled in the art, for example an antenna, portions of a processor, supporting electronics, outlet for a telephone or a network cable, etc. This way, data, commands, etc. can be communicated.

Defibrillator <NUM> can optionally include other components.

Operations according to embodiments is now described in more detail. <FIG> is a conceptual diagram for illustrating how electrodes of a WCD system may sense or capture ECG signals of the patient, and how these sensed ECG signals may be used according to embodiments to yield a heart rate of the patient and other information. Two electrodes <NUM>, <NUM> are attached to the torso of a patient, who is not shown. It will be appreciated that electrical noise may be introduced into the ECG signal at this point. Each of electrodes <NUM>, <NUM> has a wire lead <NUM>. Together, electrodes <NUM>, <NUM> sense an ECG signal of the patient along a single vector. Additional ECG signals may be sensed along additional vectors.

<FIG> also shows a measurement circuit <NUM> and a processor <NUM>, which can be made as described for measurement circuit <NUM> and processor <NUM>. A filter <NUM> is optionally implemented in measurement circuit <NUM> and/or in processor <NUM>. Filter <NUM> may be implemented as an analog filter, a digital filter, and so on. Filter <NUM> may help overcome some types of ECG noise by suppressing it, making this noise easier to detect, and so on.

Processor <NUM> may perform a full ECG rhythm analysis <NUM>. As a result of such an analysis <NUM>, a shock/no shock decision may be arrived at, and so on. Sometimes as a precursor to analysis <NUM>, processor <NUM> may compute a heart rate <NUM> according to embodiments. A computation of heart rate <NUM> maybe repeated, if the result of a previous computation does not meet a confidence criterion. The computation of heart rate <NUM> may be thus repeated in the same way, or in a different way, for example with additional safeguards, such as for addressing noise in the ECG signal. Plus, for a full ECG rhythm analysis <NUM> additional more parameters may be computed, such as a QRS width and so on.

Computed heart rate <NUM> and the results of analysis <NUM> may be further used in additional ways. For example, they may be stored in memory <NUM>, downloaded later from memory <NUM>, transmitted wirelessly via communication module <NUM>, displayed by a screen of user interface <NUM>, and so on.

The devices and/or systems mentioned in this document perform functions, processes and/or methods. These functions, processes and/or methods may be implemented by one or more devices that include logic circuitry. Such a device can be alternately called a computer, and so on. It may be a standalone device or computer, such as a general purpose computer, or part of a device that has one or more additional functions. The logic circuitry may include a processor and non-transitory computer-readable storage media, such as memories, of the type described elsewhere in this document. Often, for the sake of convenience only, it is preferred to implement and describe a program as various interconnected distinct software modules or features. These, along with data are individually and also collectively known as software. In some instances, software is combined with hardware, in a mix called firmware.

Moreover, methods and algorithms are described below. These methods and algorithms are not necessarily inherently associated with any particular logic device or other apparatus. Rather, they are advantageously implemented by programs for use by a computing machine, such as a general-purpose computer, a special purpose computer, a microprocessor, a processor such as described elsewhere in this document, and so on.

This detailed description includes flowcharts, display images, algorithms, and symbolic representations of program operations within at least one computer readable medium. An economy is achieved in that a single set of flowcharts is used to describe both programs, and also methods. So, while flowcharts described methods in terms of boxes, they also concurrently describe programs.

<FIG> shows a flowchart <NUM> for describing methods according to embodiments. The operations of flowchart <NUM> can be broadly divided in a first group <NUM> and in a second group <NUM>. First group <NUM> is distinguished from second group <NUM> according to the current state of a flag <NUM>, which is also called a noise-detected flag <NUM>. According to a comment oval <NUM>, for operations in first group <NUM> flag <NUM> is unset, and is shown as lowered. According to a comment oval <NUM>, for operations in second group <NUM> flag <NUM> is set, and is shown as raised.

A current value of flag <NUM>, namely its current state of being set or unset, can be a value of a parameter maintained in software, or expressed by a state machine of processor <NUM> and/or related components, and so on. It will be appreciated that the current value of flag <NUM> can alternate between being set and being unset, as the execution of operations of flowchart <NUM> alternates between group <NUM> and <NUM>.

Individual operations of flowchart <NUM> are now described.

A WCD system may start its operations from an operation <NUM>. According to operation <NUM>, noise-detected flag <NUM> can be unset, resulting in the orientation of comment oval <NUM>. Flag <NUM> may be unset for a number of reasons, for example responsive to the sensed ECG signal meeting a High-Amplitude (H-A) quiet criterion, as will be seen later from operation <NUM>. Or, flag <NUM> may be unset after a tolerance time passes since flag <NUM> was set, e.g. as per operation <NUM>. Suitable such tolerance times can be <NUM> minutes (min), <NUM>, <NUM>, min, <NUM>, <NUM>, etc., as will be seen later from the description of operations <NUM> and <NUM>. Or, flag <NUM> may be unset responsive to outputting an alert for patient <NUM>, as will be seen later from operation <NUM>.

According to another operation <NUM>, a next ECG portion may be received where processing is taking place, such as in processor <NUM>. Sample ECG portions <NUM> are shown in <FIG>.

<FIG> shows sample time evolutions of a number of quantities according to embodiments, against a time axis <NUM>. Sample ECG portions <NUM> are shown with reference to an ECG portions axis <NUM>. Of those, two sample ECG portions <NUM>, <NUM> are identified for subsequent explanations. In particular, starting from the ECG signal that can be sensed by the electrodes continuously, ECG portions of the sensed ECG signal can be defined. Such ECG portions can be defined in a number of ways. For example, each ECG portion can be a part of the sensed ECG signal that processor <NUM> processes at one time. An ECG portion may be long enough to perform a full ECG rhythm analysis <NUM>. As such, An ECG portion may include several QRS complexes. Or an ECG portion may be shorter. In fact, in some embodiments, an ECG portion can be simply a peak identified in the ECG signal, which may be an R peak of a QRS complex. ECG portions can be stored in memory <NUM> for later analysis, repeated analysis, different analysis, and so on.

Each of ECG portions <NUM> is intended to be drawn generically in <FIG>, while in fact they could have waveforms different from what is shown in <FIG>. More particular examples will be shown later in this document. It will be recognized that, in the instances where an ECG signal actually has the exact appearance seen in <FIG>, that ECG signal might indicate VT, or even VF, but that need not be the case for <FIG>. In addition, ECG portions <NUM> are drawn contracted in <FIG>, while some more expanded versions appear in <FIG>.

Returning to <FIG>, according to another operation <NUM>, it can be determined whether or not the sensed ECG signal meets a High-Amplitude (H-A) noise criterion. This may be performed in a number of ways. In some embodiments, the H-A noise criterion is met responsive to a group of the most recent ECG portions <NUM> meeting a noise condition. Such a group can have any suitable number of ECG portions <NUM>, for example from one to <NUM> ECG portions <NUM> per group. A good number is for a group to have <NUM> ECG portions <NUM>. Sample such groupings <NUM> of ECG portions <NUM> are shown in <FIG>.

Returning again to <FIG> if, at operation <NUM> the answer is NO, then according to another operation <NUM>, it may be determined whether or not a shock criterion is met. The determination may be made from the sensed ECG signal, for example as was described for operation <NUM>. Plus, as described later in more detail, in some embodiments the H-A noise criterion of operation <NUM> may be met by analyzing ECG segments for whether or not they meet a noise condition. In such embodiments, if the H-A noise criterion is not met, it can be determined whether or not the shock criterion is met for operation <NUM> only from the ECG portions that do not meet the noise condition.

If at operation <NUM> the answer is NO, the execution may return to an earlier operation, such as operation <NUM>. For as long as the H-A noise criterion of operation <NUM> is not being met and the patient is well, execution could continue to loop through operations <NUM>, <NUM>, <NUM> indefinitely.

If at operation <NUM> the answer is YES then, according to a shock operation <NUM>, a shock <NUM> may be administered to patient <NUM>. For shock operation <NUM>, processor <NUM> may control, responsive to the shock criterion being met and noise-detected flag <NUM> being unset, discharge circuit <NUM> to discharge through patient <NUM> an electrical charge that is stored in energy storage module <NUM>, while support structure <NUM> is worn by patient <NUM> so as to deliver a shock <NUM> to patient <NUM>. Of course, before shock operation <NUM> is performed, another process may be undertaken where the patient is alerted by a preliminary alarm, challenged to demonstrate they are alive, and so on.

If at operation <NUM> the answer is YES, then according to another operation <NUM>, noise-detected flag <NUM> may be set. In embodiments, therefore, noise-detected flag becomes set responsive to the sensed ECG signal meeting the H-A noise criterion at operation <NUM>.

The reader will observe that, starting with operation <NUM>, execution has now transitioned from first group of operations <NUM> to second group of operations <NUM>. According to a comment oval <NUM>, flag <NUM> is shown as set. While flag <NUM> is set, a number of aspects may be different.

First, in some embodiments the discharge circuit is controlled to not thus discharge when noise-detected flag <NUM> is set as per comment oval <NUM>. This can be true even if it were thus determined that the shock criterion is met by another operation that is not shown in <FIG>. In the example of <FIG>, a shock operation similar to shock operation <NUM> is not among the second group of operations <NUM>. And, as described above, this shock operation <NUM> first gives preliminary alarms to the patient, and so on. So, in these embodiments where the discharge circuit is controlled to not thus discharge when noise-detected flag <NUM> is set, patient <NUM> does not receive such preliminary alarms.

Second, in some embodiments it is not even determined whether or not the shock criterion is met when the noise-detected flag is set. In the example of <FIG>, an operation similar to operation <NUM> is not among the second group of operations <NUM>. As such, the patient's ECG might not be monitored while flag <NUM> is set. (At the same time, however, the patient may continue to be monitored by a monitoring device, a motion sensor whose signal might suggest that the patient is engaged in a certain activity, and so on. ) But then again, the ECG that is not monitored may include too much high-amplitude noise, detected at operation <NUM>, to give reliable answers. Indeed, high-amplitude noise tends to obscure the ECG signal. Rhythm analysis <NUM> during high-amplitude noise may generate results that are unpredictable, because they depend more on the noise than on the ECG signal.

While it is desirable to alert patient <NUM> that they should stop the activity that gives rise to the noise in the ECG signal, it is not a good idea to alert patient <NUM> too quickly, so as not to bother patient <NUM> unnecessarily. In any event, given enough time, high-amplitude noise often becomes abated without the intervention of alerting the patient.

Of course, if large amplitude noise persists for an extended period of time, the patient must be alerted to correct the situation. Sometimes the noise might be the result of activity on the part of the patient, and sometimes it might be due to a problem with the garment, such as a poor fit or electrodes that are too dry. So, tolerance time for purposes of this document is the time that a WCD system according to embodiments would tolerate neither analyzing the patient, nor alerting them. After that time passes, the WCD system may alert the patient and/or unset flag <NUM>. Some tolerance times were indicated earlier in this document, and these can even be adjusted by what is suggested by other sensors such as a motion sensor.

For implementing a tolerance time, according to another, optional operation <NUM>, a tolerance time countdown may be started. This may be by a clock or timer that counts up or down, and so on.

According to another operation <NUM>, the next ECG portion may be received, similarly to what was described for operation <NUM>. According to another, optional operation <NUM>, it can be determined whether or not the countdown of operation <NUM> is complete.

If at operation <NUM> the answer is NO, then according to another, optional operation <NUM> it can be determined whether or not the H-A quiet criterion is met, for deciding that the noise in the ECG signal has been abated. This can be accomplished in a number of ways.

First, the H-A quiet criterion may be met responsive to the H-A noise criterion no longer being met. For example, another group of the most recent ECG portions may be considered, which are received later. For instance, at least one ECG portion of the other group may occur after at least one ECG portion of the group that was used to determine that the H-A noise criterion was being met in the first place. And the H-A quiet criterion may be thus met responsive to this other group of the most recent ECG portions not meeting the H-A noise condition.

Second, the H-A quiet criterion may be met responsive to different conditions than the H-A noise criterion. For instance, the H-A quiet criterion may be met responsive to the other, later group of the most recent ECG portions meeting a quiet condition, which is not the same as or an inverse of the noise condition.

Moreover, everything else described for determining whether or not the H-A noise criterion is met can be used analogously for determining whether or not the H-A quiet criterion is met. This includes what is described below for noisiness criteria, spuriousness criteria, and so on.

If at operation <NUM> the answer is NO, then execution may return to another operation from group <NUM>, such as operation <NUM>. If at operation <NUM> the answer is YES, however, then execution may return to operation <NUM>, unsetting noise-detecting flag <NUM>, and so on.

If at operation <NUM> the answer is NO, then according to another, optional operation <NUM>, an alert can be output for the patient. As such, user interface <NUM> can be configured to output an alert, responsive to noise-detected flag <NUM> being set. The alert can be about correcting a noise situation. The alert can be output further responsive to the noise-detected flag having been set for the tolerance time. And, different tolerance times may be used for alerting and for exiting group <NUM>. For example, group <NUM> may be exited more times than one before alerting per operation <NUM>, and so on. After operation <NUM>, execution may return to operation <NUM>, unsetting noise-detecting flag <NUM>, and so on.

As mentioned above, algorithms of WCD system embodiments can make decisions about whether noise is detected or not, for example by deciding whether or not certain conditions and/or criteria are met. Two such criteria have already been mentioned, namely the High-Amplitude (H-A) noise criterion of operation <NUM> and the H-A quiet criterion of operation <NUM>. There are more such criteria and conditions, as algorithms according to embodiments begin with examining portions of the sensed ECG signal, and continue with the more detailed examination of identifying peaks in these ECG portions, and trying to determine whether these peaks are R peaks of QRS complexes or spikes due to high amplitude noise, which is also known as large amplitude noise.

As already mentioned above, in some embodiments the H-A noise criterion of operation <NUM> is met responsive to a group of the most recent ECG portions meeting a noise condition. And the H-A quiet criterion of operation <NUM> is met responsive to another group of the most recent ECG portions no longer meeting the noise condition, or meeting a different quiet condition, and so on.

ECG portions of the group become marked responsive to meeting a noisiness criterion, examples of which are given later in this document. Then a fraction can be computed. The fraction can be of a number of the marked ECG portions of the group over a total number of the ECG portions of the group. For meeting the H-A noise criterion of operation <NUM>, the fraction can be a so-called noise fraction, and the noise condition can be met responsive to the noise fraction exceeding a threshold noise fraction. On the other hand, for meeting the H-A quiet criterion of operation <NUM>, the fraction can be the noise fraction, or a so-called quiet fraction. In the latter case, the quiet condition can be met responsive to the quiet fraction being less than a threshold quiet fraction. Examples are now described.

Returning to <FIG>, ECG portions <NUM> include two consecutive sample ECG portions <NUM>, <NUM>. Groupings <NUM> are suggested for groups of five ECG portions at a time, which is a good number for a group size. In some embodiments groupings can be fixed, for example as suggested by groupings <NUM>. At any one time, five ECG portions are considered as a single group, then the next five as another group, and so on, without overlap among the groups. For instance, the earliest group is made from the left-most five ECG portions, including ECG portion <NUM> but not including ECG portion <NUM>. In other embodiments groupings can be variable, for instance counting only the most recent five ECG portions at any one time with overlap among the groups. The remainder of <FIG>, however, proceeds with groupings <NUM> because they are visually more easy to follow due to the lack of overlap. As such, in the example of <FIG>, each ECG portion belongs in a single group.

In <FIG>, below groupings <NUM>, ECG portions <NUM> repeat ECG portions <NUM> next to a vertical axis <NUM>. In addition, some of ECG portions <NUM> are shown marked with a shadow <NUM>. For example ECG portion <NUM> is marked with a shadow <NUM>, but ECG portion <NUM> is not. As mentioned above, such marking can be for those of ECG portions <NUM> that meet a noisiness criterion. An easy way to think about the marked ECG portions is that they are "noisy".

The above-mentioned fraction can now be described in more detail. A diagram <NUM> shows the time evolution of a sample fraction using two vertical abscissa axes: a noise fraction axis <NUM>, and then another a quiet fraction axis <NUM> that follows axis <NUM>. Such fractions can be conveniently defined to have a value between <NUM> and <NUM>.

In diagram <NUM>, each of groupings <NUM> gives rise to a different value for the noise fraction. Generally it will be observed that there are more ECG portions <NUM> near the middle of time axis <NUM>, which are marked with a shadow <NUM> due to being noisy. When considered in groupings <NUM>, these noisy ECG portions <NUM> result in the noise fraction having the higher values of <NUM>, <NUM> during the subsequent grouping <NUM>. Moreover, the noise fraction has the value of zero in the beginning and the end of time axis <NUM>.

So, as mentioned above, the noise condition is met responsive to the noise fraction exceeding a threshold noise fraction. It is desired to set the noise flag when, in a group of five ECG portions, two or more are marked. So, the threshold noise fraction can be set at a value between <NUM> and <NUM>, for example at <NUM>. The value of <NUM> for the threshold noise fraction is shown by a dotted line <NUM>, and a time intercept TNF on axis <NUM>.

It will be observed that the plot of noise fraction <NUM> intersects dotted line <NUM> at time T1. In fact, that is how time T1 is defined. As such, the H-A noise criterion of operation <NUM> is answered YES for the first time at time T1.

After time T1, the next criterion that matters is the H-A quiet criterion of operation <NUM>. This is indicated in <FIG> by axis <NUM> for the quiet fraction. In the example of <FIG>, the quiet fraction is computed in the same way as the noise fraction.

As further mentioned above, the quiet condition can be met responsive to the quiet fraction being less than a threshold quiet fraction. In some embodiments, the threshold quiet fraction can be set at less than the threshold noise fraction, to make sure that the noise has been abated. For example, the threshold quiet fraction can be set at <NUM>. As such, the quiet condition can be met when, in a group of <NUM> consecutive ECG portions <NUM>, no ECG portion is marked. That value for the threshold quiet fraction of <NUM> is shown by a dotted line <NUM>, and a time intercept TQF on axis <NUM>.

It will be observed that the plot of noise fraction <NUM> intersects dotted line <NUM> at time T2. In fact, that is how time T2 is defined. As such, the H-A quiet criterion of operation <NUM> is answered YES for the first time at time T2. Of course, if the groupings were variable, time T2 would have occurred one ECG portion earlier. It will be further appreciated that, at time T1, a countdown may have been started for the tolerance time, according to operation <NUM>. In the example of <FIG>, time T2 was reached before such a countdown was complete at operation <NUM>.

Accordingly, diagram <NUM> has provided the answers of times T1 and T2. Returning to <FIG>, at time T1 execution transitions from operations group <NUM> to operations group <NUM>. And, at time T2 execution transitions from operations group <NUM> back to operations group <NUM>. As such, per comment oval <NUM>, flag <NUM> is set or raised between times T1 and T2. And, per comment oval <NUM>, flag <NUM> is unset or lowered for all other times of time axis <NUM>.

also shows the state of flag <NUM> at various times. It will be observed that flag <NUM> is shown raised between times T1 and T2, and lowered for all other times of time axis <NUM>.

Moreover, as mentioned above, in some embodiments operation <NUM> does not take place while flag <NUM> is set or raised. This is also depicted graphically in the example of <FIG>. As such, between times T1 and T2 there can be no false preliminary alarms to the patient due to a false decision to shock.

Examples are now described for how it can be decided which of ECG portions <NUM> to mark, which means deciding whether or not an ECG portion meets a noisiness criterion. <FIG> shows ECG portions <NUM>, which repeat ECG portions <NUM>, <NUM> of <FIG>. In <FIG>, ECG portions <NUM>, <NUM> are shown more fully, but still somewhat idealized (for example the baseline level is not changing, etc.).

Potential R peaks <NUM> of QRS complexes are identified in a certain ECG portion, such as ECG portions <NUM>, <NUM>. As can be seen in <FIG>, these potential R peaks <NUM> are peaks with much higher amplitude than their neighbor peaks. Of those, two sample peaks are <NUM>, <NUM>.

Moreover, some of the identified potential R peaks <NUM> in ECG portions <NUM>, <NUM> can be deemed invalid, if they meet a spuriousness criterion that is described later in this document. In the example of <FIG>, the identified potential R peaks <NUM> that are deemed invalid are further shown each with a shadow <NUM>. Potential R peak <NUM> is acceptable, does not meet the spuriousness criterion, and is not marked with a shadow. However, potential R peak <NUM> meet the spuriousness criterion, and therefore is deemed invalid and is marked with a shadow <NUM>.

Then a validity ratio can be defined for ECG portions <NUM>, <NUM>. In each case the validity ratio can be a number of the potential R peaks in the ECG portion that are deemed invalid over a total number of the identified potential R peaks the ECG portion. As such, a validity ratio will have values between <NUM> and <NUM>.

In such embodiments, the certain ECG portion may meet the noisiness criterion responsive to the validity ratio exceeding a threshold validity ratio. A good threshold validity ratio can be about <NUM>/<NUM>. So, for practical purposes, the threshold validity ratio can be set at <NUM>.

For example, per comment oval <NUM>, for ECG portion <NUM> the validity ratio is <NUM>/<NUM> = <NUM>, which is less than <NUM>. As such, ECG portion <NUM> is acceptable, and it is not deemed invalid. Therefore, ECG portion <NUM> is repeated as ECG portion <NUM> without being marked by a shadow, similarly with <FIG>.

For another example, per comment oval <NUM>, for ECG portion <NUM> the validity ratio is <NUM>/<NUM> = <NUM>, which is more than <NUM>. As such, ECG portion <NUM> is not acceptable, and is deemed invalid. Therefore, ECG portion <NUM> is repeated as ECG portion <NUM> where it is also marked by shadow <NUM>, similarly with <FIG>.

The determination of whether or not identified potential R peaks <NUM> in ECG portions <NUM>, <NUM> meet a spuriousness criterion can be done in a number of ways. Examples are now described.

<FIG> has a time diagram <NUM> for illustrating a first spuriousness criterion. Diagram <NUM> has an R peak amplitude axis <NUM> and a time axis <NUM>. Diagram <NUM> shows sample identified potential R peaks <NUM>, <NUM>, which could be as peaks <NUM>, <NUM>.

An identified potential R peak <NUM>, <NUM> meets the spuriousness criterion responsive to having an amplitude larger than a threshold amplitude <NUM>. A suitable value for the threshold amplitude is <NUM> mV. Accordingly, identified potential R peaks with an amplitude less than threshold amplitude <NUM> do not meet the spuriousness criterion.

<FIG> also has another time diagram <NUM>, for showing results similar to R peaks <NUM>. Diagram <NUM> also has an R peak amplitude axis <NUM> and a time axis <NUM> that is repeated from diagram <NUM>.

As can be seen, identified potential R peak <NUM> has an amplitude less than threshold amplitude <NUM>, and therefore the spuriousness criterion is not met. Accordingly, identified potential R peak <NUM> is repeated in diagram <NUM> without being marked by a shadow, similarly with <FIG>. However, identified potential R peak <NUM> has an amplitude larger than threshold amplitude <NUM>, and therefore the spuriousness criterion is met. Accordingly, identified potential R peak <NUM> is repeated in diagram <NUM>, where it is further marked by shadow <NUM>, similarly with <FIG>.

In some embodiments, the sensed ECG signal is filtered, and therefore the ECG portions filtered may be filtered as well. Filtering may take place, for example, by filter <NUM>. Filter <NUM> may be a bandpass filter that passes frequencies between <NUM> and <NUM>. In such embodiments, all of what was written above may apply to the filtered ECG signal. In particular, an identified potential R peak in the certain filtered ECG portion may meet the spuriousness criterion responsive to having an amplitude larger than a threshold amplitude.

<FIG> has a time diagram <NUM> for illustrating a second spuriousness criterion. Diagram <NUM> has an ECG amplitude axis <NUM> and a time axis <NUM>. Diagram <NUM> shows sample identified potential R peaks <NUM>, <NUM>, which could be as peaks <NUM>, <NUM>.

In some embodiments, ECG segments <NUM>, <NUM> become defined so as to have time durations <NUM>, <NUM> that include the respective identified potential R peaks <NUM>, <NUM>. In some embodiments, an identified potential R peak (<NUM>, <NUM>) meets the spuriousness criterion responsive to a starting amplitude at the beginning of the ECG segment differing from an ending amplitude at the end of the ECG segment by more than a threshold baseline shift <NUM>.

<FIG> also has another time diagram <NUM>, for showing results similar to R peaks <NUM>. Diagram <NUM> also has an ECG amplitude axis <NUM> and a time axis <NUM> that is repeated from diagram <NUM>.

As can be seen, for identified potential R peak <NUM>, the spuriousness criterion would be met if a starting amplitude at a beginning point <NUM> of ECG segment <NUM> differs from an ending amplitude at an end point <NUM> of ECG segment <NUM> by more than threshold baseline shift <NUM>. Beginning point <NUM> and end point <NUM> are further shown projected onto vertical axis <NUM>, from where it becomes apparent that their difference is smaller than threshold baseline shift <NUM>. As such, the spuriousness criterion is not met for identified potential R peak <NUM>. Accordingly, identified potential R peak <NUM> is repeated in diagram <NUM> without being marked by a shadow, similarly with <FIG>.

As can be seen further, for identified potential R peak <NUM>, the spuriousness criterion would be met if a starting amplitude at a beginning point <NUM> of ECG segment <NUM> differs from an ending amplitude at an end point <NUM> of ECG segment <NUM> by more than threshold baseline shift <NUM>. Beginning point <NUM> and end point <NUM> are further shown projected onto vertical axis <NUM>, from where it becomes apparent that their difference is larger than threshold baseline shift <NUM>. As such, the spuriousness criterion is met for identified potential R peak <NUM>. Accordingly, identified potential R peak <NUM> is repeated in diagram <NUM>, where it is further marked by shadow <NUM>, similarly with <FIG>.

In some embodiments, a ratio of threshold baseline shift <NUM> over time durations <NUM>, <NUM> of ECG segments <NUM>, <NUM> is at least 5mV/<NUM>. Practically speaking, time duration <NUM> can be chosen to start <NUM> milliseconds (ms) prior to identified potential R peak <NUM>, and end <NUM> after it. As such, time duration <NUM> would be <NUM> and threshold baseline shift <NUM> can be <NUM> mV.

As mentioned above, the ECG portions are defined as the identified potential R peaks in the sensed ECG signal. The identified potential R peaks become marked responsive to meeting a spuriousness criterion. The spuriousness criterion can be as mentioned above, and described with reference to <FIG>. Then a noise fraction can be computed, of a number of the identified potential R peaks of the group over a total number of the identified potential R peaks of the group. Then the noise condition can be met responsive to the noise fraction exceeding a threshold noise fraction, as per the above, and similarly also with the quiet fraction.

<FIG> shows sample time evolutions of a number of quantities according to embodiments, against a time axis <NUM>. Sample ECG portions <NUM> are shown with reference to an ECG portions axis <NUM>. It will be observed that ECG portions <NUM> are depicted as single peaks. Two sample such peaks <NUM>, <NUM> are identified, which could be identified from the ECG signal as shown in <FIG> for peaks <NUM>, <NUM>. In addition, groupings <NUM> are shown, and what is written above about groupings <NUM> also applies. As such, a single group in this instance can be a collection of peaks detected in the sensed ECG signal, which can be R peaks of respective QRS complexes.

Below groupings <NUM>, ECG portions <NUM> repeat ECG portions <NUM> next to a vertical axis <NUM>. In addition, some of ECG portions <NUM> are shown marked with a shadow <NUM>. For example ECG portion <NUM> is marked with a shadow <NUM>, but ECG portion <NUM> is not. Such marking can be for those of ECG portions <NUM> that meet a spuriousness criterion.

Moreover, a diagram <NUM> shows the time evolution of a sample fraction using two vertical abscissa axes: a noise fraction axis <NUM>, and then another a quiet fraction axis <NUM> that follows axis <NUM>. A value of <NUM> for the threshold noise fraction is shown by a dotted line <NUM>, and a time intercept TNF on axis <NUM>. A plot of noise fraction <NUM> intersects dotted line <NUM> at time T3. A value for the threshold quiet fraction of <NUM> is shown by a dotted line <NUM>, and a time intercept TQF on axis <NUM>. The plot of noise fraction <NUM> intersects dotted line <NUM> at time T4. The remainder of <FIG> is similar to what was described above with reference to <FIG>.

In the methods described above, each operation can be performed as an affirmative act or operation of doing, or causing to happen, what is written that can take place. Such doing or causing to happen can be by the whole system or device, or just one or more components of it. It will be recognized that the methods and the operations may be implemented in a number of ways, including using systems, devices and implementations described above. In addition, the order of operations is not constrained to what is shown, and different orders may be possible according to different embodiments. Examples of such alternate orderings may include overlapping, interleaved, interrupted, reordered, incremental, preparatory, supplemental, simultaneous, reverse, or other variant orderings, unless context dictates otherwise. Moreover, in certain embodiments, new operations may be added, or individual operations may be modified or deleted. The added operations can be, for example, from what is mentioned while primarily describing a different system, apparatus, device or method.

A person skilled in the art will be able to practice the present invention in view of this description, which is to be taken as a whole. Details have been included to provide a thorough understanding. In other instances, well-known aspects have not been described, in order to not obscure unnecessarily this description.

Some technologies or techniques described in this document may be known. Even then, however, it does not necessarily follow that it is known to apply such technologies or techniques as described in this document, or for the purposes described in this document.

This description includes one or more examples, but this fact does not limit how the invention may be practiced. Indeed, examples, instances, versions or embodiments of the invention may be practiced according to what is described, or yet differently, and also in conjunction with other present or future technologies. Other such embodiments include combinations and sub-combinations of features described herein, including for example, embodiments that are equivalent to the following: providing or applying a feature in a different order than in a described embodiment; extracting an individual feature from one embodiment and inserting such feature into another embodiment; removing one or more features from an embodiment; or both removing a feature from an embodiment and adding a feature extracted from another embodiment, while providing the features incorporated in such combinations and sub-combinations.

In general, the present disclosure reflects preferred embodiments of the invention. The attentive reader will note, however, that some aspects of the disclosed embodiments extend beyond the scope of the claims. To the respect that the disclosed embodiments indeed extend beyond the scope of the claims, the disclosed embodiments are to be considered supplementary background information and do not constitute definitions of the claimed invention.

In this document, the phrases "constructed to" and/or "configured to" denote one or more actual states of construction and/or configuration that is fundamentally tied to physical characteristics of the element or feature preceding these phrases and, as such, reach well beyond merely describing an intended use. Any such elements or features can be implemented in a number of ways, as will be apparent to a person skilled in the art after reviewing the present disclosure, beyond any examples shown in this document.

In this description a single reference numeral may be used consistently to denote a single item, aspect, component, or process. Moreover, a further effort may have been made in the drafting of this description to use similar though not identical reference numerals to denote other versions or embodiments of an item, aspect, component or process that are identical or at least similar or related. Where made, such a further effort was not required, but was nevertheless made gratuitously so as to accelerate comprehension by the reader. Even where made in this document, such a further effort might not have been made completely consistently for all of the versions or embodiments that are made possible by this description. Accordingly, the description controls in defining an item, aspect, component or process, rather than its reference numeral. Any similarity in reference numerals may be used to infer a similarity in the text, but not to confuse aspects where the text or other context indicates otherwise.

Claim 1:
A wearable cardioverter defibrillator (WCD) system, comprising:
a support structure (<NUM>) configured to be worn by an ambulatory patient
an energy storage module (<NUM>) configured to store an electrical charge
a discharge circuit (<NUM>) coupled to the energy storage module; electrodes (<NUM>) configured to sense an Electrocardiogram (ECG) signal of the patient;
a processor (<NUM>) configured to:
set a noise-detected flag responsive to the sensed ECG signal meeting a High-Amplitude (H-A) noise criterion, and unset the noise-detected flag responsive to the sensed ECG signal meeting a High-Amplitude (H-A) quiet criterion, wherein the H-A noise criterion is met when a noise fraction of a group of ECG portions in a sensed ECG signal comprising a number of potential R peaks exceeding a threshold amplitude exceeds a threshold noise fraction and the H-A quiet criterion is met responsive to the H-A noise criterion no longer being met,
determine, from the sensed ECG signal, whether or not a shock criterion is met, and
control, responsive to the shock criterion being met and the noise-detected flag being unset, the discharge circuit to discharge the stored electrical charge through the patient while the support structure is worn by the patient so as to deliver a shock to the patient, but the discharge circuit is controlled to not thus discharge when the noise-detected flag is set even if it is thus determined that the shock criterion is met.