A weak current signal acquisition circuit, and a seat (10) and a seat cover (100) having the circuit. The weak current signal acquisition circuit uses two signal acquisition units as front input electrodes of an amplification circuit, and uses an in-phase differential input mode, so that the ratio of amplitudes of a differential mode signal sent to a subsequent-stage operational amplifier to a common mode signal is improved, thereby achieving the purpose of improving the signal-to-noise ratio of a weak current signal extracted by a signal acquisition unit. When people use a seat cover (100) in which a weak current signal acquisition circuit is mounted, thighs are in contact with a signal acquisition unit provided on the seat (10), such that the weak current signal acquisition circuit can acquire a human body's electrocardiosignal more effectively.

An electrocardiographic detection device for a vehicle includes: a steering wheel electrode provided at a lower layer of a covering material that covers a surface of a steering wheel; a steering wheel electrode provided at a lower layer of the covering material of the steering wheel and an insulating material of a predetermined thickness; a waveform generator detecting a differential voltage between the steering wheel electrode and a ground region; a waveform generator detecting a differential voltage between the steering wheel electrode and a ground region; and a signal processing section that generates an electrocardiographic signal on the basis of the differential voltage detected at the waveform generator and the differential voltage detected at the waveform generator.

A system for providing a standard electrocardiogram (ECG) signal for a human body using contactless ECG sensors for outputting to exiting medical equipment or for storage or viewing on a remote device. The system comprises a digital processing module (DPM) adapted to connect to an array of contactless ECG sensors provided in a fabric or the like. A selection mechanism is embedded into the DPM which allows the DPM to identify body parts using the ECG signals of the different ECG sensors and select for each body part the best sensor lead. The DPM may then produce the standard ECG signal using the selected ECG signals for the different body parts detected. The system is adapted to continuously re-examine the selection to ensure that the best leads are selected for a given body part following a movement of the body part, thereby, allowing for continuous and un-interrupted ECG monitoring of the patient.

A system for providing a standard electrocardiogram (ECG) signal for a human body using contactless ECG sensors for outputting to exiting medical equipment or for storage or viewing on a remote device. The system comprises a digital processing module (DPM) adapted to connect to an array of contactless ECG sensors provided in a fabric or the like. A selection mechanism is embedded into the DPM which allows the DPM to identify body parts using the ECG signals of the different ECG sensors and select for each body part the best sensor lead. The DPM may then produce the standard ECG signal using the selected ECG signals for the different body parts detected. The system is adapted to continuously re-examine the selection to ensure that the best leads are selected for a given body part following a movement of the body part, thereby, allowing for continuous and un-interrupted ECG monitoring of the patient.

A method for evaluation of electrical propagation in the heart includes receiving a pacing signal applied to a heart of a patient, the pacing signal including a sequence of normal and shorter, abnormal, pacing stimuli. A responsive cardiac signal is received, that is sensed by electrodes at a location in the heart and on the body surface of the patient. A model response is found and annotated from evoked potentials caused by the normal pacing stimuli. A correlation is made between the model response along the different signal sections to find and calculate a normal and decremental time delays between the pacing stimuli and respectively resulting evoked potentials at a tissue location. A time difference is calculated, between the normal time delay and the decremental time delay. An EP map of at least a portion of the heart is presented to a user, with a graphical indication of the time difference presented at the tissue location.

A method for evaluation of electrical propagation in the heart includes receiving a pacing signal applied to a heart of a patient, the pacing signal including a sequence of normal and shorter, abnormal, pacing stimuli. A responsive cardiac signal is received, that is sensed by electrodes at a location in the heart and on the body surface of the patient. A model response is found and annotated from evoked potentials caused by the normal pacing stimuli. A correlation is made between the model response along the different signal sections to find and calculate a normal and decremental time delays between the pacing stimuli and respectively resulting evoked potentials at a tissue location. A time difference is calculated, between the normal time delay and the decremental time delay. An EP map of at least a portion of the heart is presented to a user, with a graphical indication of the time difference presented at the tissue location.

Techniques for switching an implantable medical device (IMD) from a first mode to a second mode in relation to signals obtained from internal sensors are described. The internal sensors may include a temperature sensor and a biosensor. In some examples, processing circuitry of the IMD may make a first preliminary determination that the IMD is implanted based on a first signal from the temperature sensor. In response to the first preliminary determination being that the IMD is implanted, the processing circuitry may make a second preliminary determination that the IMD is implanted based on a second signal from the biosensor. The processing circuitry may switch the IMD from a first mode to a second mode based on both the first preliminary determination and the second preliminary determination being that the IMD is implanted.

A connector may include a first housing configured to detachably secure a first input cable of a first sensor configured to generate a first signal, and a second housing configured to detachably secure a second input cable of a second sensor configured to generate a second signal. The second housing may be configured to transmit the second signal from the second input cable to the first housing. The first housing may be configured to transmit at least one of the first signal and the second signal to an output cable. A coupling of the first housing may be configured to mate with a coupling of the second housing such that the first housing and the second housing are configured to be detachably secured to each other. The coupling may be mechanical, electro-mechanical, or magnetic. Either sensor may be an electrocardiogram sensor or a pulse oximetry sensor.

A connector may include a first housing configured to detachably secure a first input cable of a first sensor configured to generate a first signal, and a second housing configured to detachably secure a second input cable of a second sensor configured to generate a second signal. The second housing may be configured to transmit the second signal from the second input cable to the first housing. The first housing may be configured to transmit at least one of the first signal and the second signal to an output cable. A coupling of the first housing may be configured to mate with a coupling of the second housing such that the first housing and the second housing are configured to be detachably secured to each other. The coupling may be mechanical, electro-mechanical, or magnetic. Either sensor may be an electrocardiogram sensor or a pulse oximetry sensor.

Provided is a biological electrode including: a polarizable electrode layer; and a non-polarizable electrode layer laminated on the polarizable electrode layer, in which the non-polarizable electrode layer includes a resin, silver, and silver chloride supported by silica, a content of the silver is 150 to 300 mass parts based on 100 mass parts of the resin, a ratio between the silver and the silver chloride is 97:3 to 95:5, and the non-polarizable electrode layer has a thickness of 3 to 5 μm.