Abstract: Described herein is a fully-differential preamplifier comprising an input differential pair, an output current load, and a current source. The current source is coupled between the input differential pair and a low voltage rail and configured to control whether the fully-differential preamplifier is operating in a first mode or a second mode, wherein the preamplifier draws more current when operating in the second mode compared to when operating in the first mode. The input differential pair is coupled between the output current load and the current source. The output current load is coupled between a high voltage rail and the input differential pair. The input differential pair comprise positive and negative inputs of the fully-differential preamplifier. Nodes where the input differential pair and the output current load are coupled to one another comprise positive and negative outputs of the fully-differential preamplifier.

Abstract: Described herein is a fully-differential receiver for use with an implantable medical device (IMD) and configured to receive conducted communication signals that are transmitted by another IMD or an external device. The fully-differential receiver includes a fully-differential preamplifier, a fully-differential buffer, a first comparator, a second comparator, and an AC coupling network coupled between differential outputs of the fully-differential buffer and a coupled together differential pair of inputs of the first and second comparators. A differential pair of inputs of the fully-differential receiver comprise the differential pair of inputs of the fully-differential preamplifier, and a differential pair of outputs of the fully-differential receiver comprise a first output of the first comparator and a second output of the second comparator. In order to conserve power, the fully-differential receiver is selectively changed from operating in a first mode to operating in a second mode, and vice versa.

Abstract: Described herein is a fully-differential preamplifier comprising an input differential pair, an output current load, and a current source. The current source is coupled between the input differential pair and a low voltage rail and configured to control whether the fully-differential preamplifier is operating in a first mode or a second mode, wherein the preamplifier draws more current when operating in the second mode compared to when operating in the first mode. The input differential pair is coupled between the output current load and the current source. The output current load is coupled between a high voltage rail and the input differential pair. The input differential pair comprise positive and negative inputs of the fully-differential preamplifier. Nodes where the input differential pair and the output current load are coupled to one another comprise positive and negative outputs of the fully-differential preamplifier.

Abstract: Described herein are implantable medical devices (IMDs), and methods for use therewith, that enable monitoring of impedance associated with a pathway (e.g., including a lead) used to selectively deliver stimulation pulses to patient tissue. A method involves measuring or storing a first voltage indicative of the energy stored on a reservoir capacitor (Cres) just prior to a stimulation pulse being delivered via the pathway, as well as measuring or storing a second voltage indicative of the energy stored on the Cres just after the stimulation pulse is delivered via the pathway. The method also includes monitoring the impedance associated with the pathway based on a difference between the first and second voltages, which may involve determining a count value indicative of how long it takes to discharge the first voltage to drop to the second voltage, wherein the count value is a surrogate of the impedance associated with the pathway.

Abstract: Described herein are implantable medical devices (IMDs), and methods for use therewith, that enable monitoring of impedance associated with a pathway (e.g., including a lead) used to selectively deliver stimulation pulses to patient tissue. A method involves measuring or storing a first voltage indicative of the energy stored on a reservoir capacitor (Cres) just prior to a stimulation pulse being delivered via the pathway, as well as measuring or storing a second voltage indicative of the energy stored on the Cres just after the stimulation pulse is delivered via the pathway. The method also includes monitoring the impedance associated with the pathway based on a difference between the first and second voltages, which may involve determining a count value indicative of how long it takes to discharge the first voltage to drop to the second voltage, wherein the count value is a surrogate of the impedance associated with the pathway.

Abstract: A power supply circuit includes a line voltage forming circuit and a supply voltage forming circuit. The line voltage forming circuit forms a voltage that is proportional to a line voltage provided by a telecommunication line, and the supply voltage forming circuit forms a second voltage from the first voltage. A sensing circuit senses the telecommunication line and provides a sensor signal that is representative of the power provided by the telecommunication line. The line voltage forming circuit is controlled by the sensor signal such that the slope of a load line characteristic of the line voltage forming circuit is modified when the sensor signal is above a predetermined threshold signal. The load line characteristic defines an increase of the line voltage with an increase of the line current provided by the telecommunication line.

Abstract: A current distribution circuit for application in a communication device, such as a telephone subscriber circuit comprises a first current sinking branch, which is connected in parallel to a second current sinking branch. Both branches sink at least the DC current on the telephone line, whereas an excess current in the DC line is taken up by the second current sinking branch, which is provided with a current sinking transistor, whose collector/emitter voltage is relatively large. This leads to a reduced effectively needed chip area. The DC line-current can be measured by means of a low pass filter, preferable connected to a current mirror means.