Abstract: Techniques are provided for estimating electrical conduction delays with the heart of a patient based on measured immittance values. In one example, impedance or admittance values are measured within the heart of a patient by a pacemaker or other implantable medical device, then used by the device to estimate cardiac electrical conduction delays. A first set of predetermined conversion factors may be used to convert the measured immittance values into conduction delay values. In some examples, the device then uses the estimated conduction delay values to estimate LAP or other cardiac pressure values. A second set of predetermined conversion factors may be used to convert the estimated conduction delays into pressure values. Techniques are also described for adaptively adjusting pacing parameters based on estimated LAP.

Abstract: Systems and methods for regional item recommendations are provided. In example embodiments, an indication of a destination geolocation from a user device of a user is received. Destination data corresponding to the destination geolocation is retrieved. A destination characteristic from the destination data is extracted. The destination characteristic indicates an affinity for apparel associated with the destination geolocation. A candidate apparel item is determined based on the extracted destination characteristic. An item listing corresponding to the candidate apparel item is identified. The item listing is presented on a user interface of the user device.

Abstract: Techniques are provided for estimating left atrial pressure (LAP) or other cardiac performance parameters based on measured conduction delays. In particular, LAP is estimated based interventricular conduction delays. Predetermined conversion factors stored within the device are used to convert the various the conduction delays into LAP values or other appropriate cardiac performance parameters. The conversion factors may be, for example, slope and baseline values derived during an initial calibration procedure performed by an external system, such as an external programmer. In some examples, the slope and baseline values may be periodically re-calibrated by the implantable device itself. Techniques are also described for adaptively adjusting pacing parameters based on estimated LAP or other cardiac performance parameters. Still further, techniques are described for estimating conduction delays based on impedance or admittance values and for tracking heart failure therefrom.

Abstract: Techniques for an omni-channel approach for displaying simulated digital apparel content are presented herein. A machine can detect an available amount of a computing resource on a client device. A determination that the client device is to render only a three-dimensional body model, among a set of models that includes the three-dimensional body model and a three-dimensional garment model, and that a server is to render the three-dimensional garment model, may occur based on the detected available amount of the computing resource on the client device. The machine can provide the client device with the three-dimensional garment model draped on the three-dimensional body model. The machine can cause the server to render at least a portion of the three-dimensional garment model in accordance with the determination. The machine can cause the client device to render at least a portion of the three-dimensional body model in accordance with the determination.

Abstract: Techniques for three-dimensional garment simulation are presented herein. An access module can be configured to access a three-dimensional garment model of a garment. The garment model can include garment points that represent a surface of the garment. Additionally, a three-dimensional body model can be generated based on body measurements, body scanning, or garment information. A processor can be configured by a garment module to position at least a portion of the generated three-dimensional body model inside the garment points, and calculate one or more simulated forces acting on a subset of the garment points. Moreover, a rendering module can be configured to generate an image of the three-dimensional garment model draped on the three-dimensional body model based on the calculated one or more simulated forces. Furthermore, a display module can be configured to present the generated image on a display of a device.

Abstract: Techniques for extraction of body parameters, dimensions and shape of a customer are presented herein. A model descriptive of a garment, a corresponding calibration factor and reference garment shapes can be assessed. A garment shape corresponding to the three-dimensional model can be selected from the reference garment shapes based on a comparison of the three-dimensional model with the reference garment shapes. A reference feature from the plurality of reference features may be associated with the model feature. A measurement of the reference feature may be calculated based on the association and the calibration factor. The computed measurement can be stored in a body profile associated with a user. An avatar can be generated for the user based on the body profile and be used to show or indicate fit of a garment, as well as make fit and size recommendations.

Abstract: Techniques for three-dimensional garment simulation using parallel computing are presented herein. An access module can be configured to access a three-dimensional garment model of a garment. The garment model can include garment points that represent a surface of the garment. A processor, having a plurality of cores, can be configured by a garment simulation module to calculate one or more exerted forces on a subset of garment points. Additionally, the garment simulation module can generate cross pairs and apportion the generated cross pairs among the plurality of cores. Moreover, the garment simulation module can determine, using the plurality of vector execution units in parallel based on an organized data layout, whether boundaries of the first subgroup of cross pairs are overlapping based on the one or more exerted forces. Subsequently, the garment simulation module can calculate one or more simulated forces acting on the garment points based on the determination.

Abstract: Techniques for generating and presenting a three-dimensional garment model are presented herein. A communication interface can be configured to receive images, where all visible parts of the garment may be captured by the received images. A garment creation module can be configured to generate partial shapes of the garment based on the received images. Additionally, the garment creation module can determine a type of garment by comparing the generated partial shapes to a database of reference garment shapes. Furthermore, the garment creation module can generate a three-dimensional garment model by joining the partial shapes based on the determined type of garment, and can tessellate the generated three-dimensional garment model. A user interface can be configured to present the tessellated three-dimensional garment model on a three-dimensional body model.

Abstract: Techniques are provided for estimating left atrial pressure (LAP) or other cardiac performance parameters based on measured conduction delays. In particular, LAP is estimated based interventricular conduction delays. Predetermined conversion factors stored within the device are used to convert the various the conduction delays into LAP values or other appropriate cardiac performance parameters. The conversion factors may be, for example, slope and baseline values derived during an initial calibration procedure performed by an external system, such as an external programmer. In some examples, the slope and baseline values may be periodically re-calibrated by the implantable device itself. Techniques are also described for adaptively adjusting pacing parameters based on estimated LAP or other cardiac performance parameters. Still further, techniques are described for estimating conduction delays based on impedance or admittance values and for tracking heart failure therefrom.

Abstract: In specific embodiments, one or more cardiogenic impedance signal template is stored, where each template has a corresponding morphology. Additionally, one or more cardiogenic impedance signal is obtained using electrodes implanted within a patient, where each signal has a corresponding morphology. The morphology of one or more obtained cardiogenic impedance signal is compared to the morphology of one or more stored template, to determine one or more metric indicative of similarity between the compared morphologies. The one or more metric indicative of similarity is used to analyze the patient's cardiac condition, to discriminate among arrhythmias and/or to adjust a cardiac pacing parameter.

Abstract: An implantable device monitors and treats heart failure, pulmonary edema, and hemodynamic conditions and in some cases applies therapy. In one implementation, the implantable device applies a high-frequency multi-phasic pulse waveform over multiple-vectors through tissue. The waveform has a duration less than the charging time constant of electrode-electrolyte interfaces in vivo to reduce intrusiveness while increasing sensitivity and specificity for trending parameters. The waveform can be multiplexed over multiple vectors and the results cross-correlated or subjected to probabilistic analysis or thresholding schemata to stage heart failure or pulmonary edema. In one implementation, a fractionation morphology of a sensed impedance waveform is used to trend intracardiac pressure to stage heart failure and to regulate cardiac resynchronization therapy. The waveform also provides unintrusive electrode integrity checks and 3-D impedancegrams.

Abstract: An implantable device monitors and treats heart failure, pulmonary edema, and hemodynamic conditions and in some cases applies therapy. In one implementation, the implantable device applies a high-frequency multi-phasic pulse waveform over multiple-vectors through tissue. The waveform has a duration less than the charging time constant of electrode-electrolyte interfaces in vivo to reduce intrusiveness while increasing sensitivity and specificity for trending parameters. The waveform can be multiplexed over multiple vectors and the results cross-correlated or subjected to probabilistic analysis or thresholding schemata to stage heart failure or pulmonary edema. In one implementation, a fractionation morphology of a sensed impedance waveform is used to trend intracardiac pressure to stage heart failure and to regulate cardiac resynchronization therapy. The waveform also provides unintrusive electrode integrity checks and 3-D impedancegrams.

Abstract: Testing lead conditions in an implantable medical device includes continuously sampling the impedance values of a lead associated with the implantable medical device. The sampling is conducted over a predetermined period of time. An impedance histogram is then generated using the sampled impedance values by separating each measured impedance value into a specific bin assigned to contain a particular range of impedance levels. The lead condition of the tested lead can then be determined based on one or more characteristics of the impedance histogram.

Abstract: Techniques are provided for estimating left atrial pressure (LAP) or other cardiac performance parameters based on measured conduction delays. In particular, LAP is estimated based interventricular conduction delays. Predetermined conversion factors stored within the device are used to convert the various the conduction delays into LAP values or other appropriate cardiac performance parameters. The conversion factors may be, for example, slope and baseline values derived during an initial calibration procedure performed by an external system, such as an external programmer. In some examples, the slope and baseline values may be periodically re-calibrated by the implantable device itself. Techniques are also described for adaptively adjusting pacing parameters based on estimated LAP or other cardiac performance parameters. Still further, techniques are described for estimating conduction delays based on impedance or admittance values and for tracking heart failure therefrom.

Abstract: Techniques are provided for estimating left atrial pressure (LAP) or other cardiac performance parameters based on measured conduction delays. In particular, LAP is estimated based interventricular conduction delays. Predetermined conversion factors stored within the device are used to convert the various the conduction delays into LAP values or other appropriate cardiac performance parameters. The conversion factors may be, for example, slope and baseline values derived during an initial calibration procedure performed by an external system, such as an external programmer. In some examples, the slope and baseline values may be periodically re-calibrated by the implantable device itself. Techniques are also described for adaptively adjusting pacing parameters based on estimated LAP or other cardiac performance parameters. Still further, techniques are described for estimating conduction delays based on impedance or admittance values and for tracking heart failure therefrom.

Abstract: Techniques are provided for estimating electrical conduction delays with the heart of a patient based on measured immittance values. In one example, impedance or admittance values are measured within the heart of a patient by a pacemaker or other implantable medical device, then used by the device to estimate cardiac electrical conduction delays. A first set of predetermined conversion factors may be used to convert the measured immittance values into conduction delay values. In some examples, the device then uses the estimated conduction delay values to estimate LAP or other cardiac pressure values. A second set of predetermined conversion factors may be used to convert the estimated conduction delays into pressure values. Techniques are also described for adaptively adjusting pacing parameters based on estimated LAP.

Abstract: Techniques are provided for estimating electrical conduction delays with the heart of a patient based on measured immittance values. In one example, impedance or admittance values are measured within the heart of a patient by a pacemaker or other implantable medical device, then used by the device to estimate cardiac electrical conduction delays. A first set of predetermined conversion factors may be used to convert the measured immittance values into conduction delay values. In some examples, the device then uses the estimated conduction delay values to estimate LAP or other cardiac pressure values. A second set of predetermined conversion factors may be used to convert the estimated conduction delays into pressure values. Techniques are also described for adaptively adjusting pacing parameters based on estimated LAP.

Abstract: Testing lead conditions in an implantable medical device includes continuously sampling the impedance values of a lead associated with the implantable medical device. The sampling is conducted over a predetermined period of time. An impedance histogram is then generated using the sampled impedance values by separating each measured impedance value into a specific bin assigned to contain a particular range of impedance levels. The lead condition of the tested lead can then be determined based on one or more characteristics of the impedance histogram.

Abstract: Techniques are provided for detecting problems involving electrode/tissue contact with extracardiac electrodes of subcutaneous monitoring devices, such as atrial fibrillation (AF) monitors. Briefly, subcutaneous impedance signals are detected using extracardiac sensing electrodes of the subcutaneous device. Problems involving poor electrode/tissue contact are then detected within the subcutaneous impedance signals. Depending upon its programming, the device can then inhibit the recording of subcutaneous electrocardiogram (ECG) data during periods of poor contact. Additionally, the device can identify the particular contact problem based on the impedance signals. In one example, the device identifies one or more of: acute instability of impedance indicative of intermittent electrode/tissue contact; impedance signal saturation indicative of loss of electrode/tissue contact; and impedance signal dropout indicative of the presence of liquids surrounding the electrodes (such as blood or edema accumulation.

Abstract: Methods and systems of noise detection and response for use when monitoring for arrhythmias are described herein. At least two electrodes are used to obtain a signal indicative of cardiac electrical activity. The signal is bandpass filtered to obtain a filtered signal. Ventricular depolarizations are monitored for based on comparisons of the filtered signal to a first threshold. Arrhythmias are monitored for based on ventricular depolarization detections that occur as a result of monitoring for ventricular depolarizations. During one or more noise detection windows, noise is monitored for and a likelihood that monitoring for arrhythmias is adversely affected by noise is determined based on results thereof. Whether and/or how the monitoring for arrhythmias is performed is modified when it is determined that monitoring for arrhythmias is likely adversely affected by noise.