Wearable device with physiological parameters monitoring

Description

FIELD

The present disclosure relates to a wearable health monitoring device incorporating a plurality of sensors worn on the wrist.

BACKGROUND

Spectroscopy is a common technique for measuring the concentration of organic and some inorganic constituents of a solution. The theoretical basis of this technique is the Beer-Lambert law, which states that the concentration c_iof an absorbent in solution can be determined by the intensity of light transmitted through the solution, knowing the pathlength d_λ, the intensity of the incident light I_0,λ, and the extinction coefficient ε_i,λ at a particular wavelength λ.

In generalized form, the Beer-Lambert law is expressed as:

I_λ=I_0,λe^−d^λ^·μ^a,λ (1)

$\begin{matrix} μ_{a, λ} = \sum_{i = 1}^{n} ε_{i, λ} \cdot c_{i} & (2) \end{matrix}$

where μ_a,λ is the bulk absorption coefficient and represents the probability of absorption per unit length. The minimum number of discrete wavelengths that are required to solve equations 1 and 2 is the number of significant absorbers that are present in the solution.

A practical application of this technique is pulse oximetry or plethysmography, which utilizes a noninvasive sensor to measure oxygen saturation and pulse rate, among other physiological parameters. Pulse oximetry or plethysmography relies on a sensor attached externally to the patient (typically for example, at the fingertip, foot, ear, forehead, or other measurement sites) to output signals indicative of various physiological parameters, such as a patient's blood constituents and/or analytes, including for example a percent value for arterial oxygen saturation, among other physiological parameters. The sensor has at least one emitter that transmits optical radiation of one or more wavelengths into a tissue site and at least one detector that responds to the intensity of the optical radiation (which can be reflected from or transmitted through the tissue site) after absorption by pulsatile arterial blood flowing within the tissue site. Based upon this response, a processor determines the relative concentrations of oxygenated hemoglobin (HbO₂) and deoxygenated hemoglobin (Hb) in the blood so as to derive oxygen saturation, which can provide early detection of potentially hazardous decreases in a patient's oxygen supply, and other physiological parameters.

A patient monitoring device can include a plethysmograph sensor. The plethysmograph sensor can calculate oxygen saturation (SpO₂), pulse rate, a plethysmograph waveform, perfusion index (PI), pleth variability index (PVI), methemoglobin (MetHb), carboxyhemoglobin (CoHb), total hemoglobin (tHb), respiration rate, glucose, and/or otherwise. The parameters measured by the plethysmograph sensor can display on one or more monitors the foregoing parameters individually, in groups, in trends, as combinations, or as an overall wellness or other index.

A pulse oximetry sensor is described in U.S. Pat. No. 6,088,607 entitled Low Noise Optical Probe; pulse oximetry signal processing is described in U.S. Pat. Nos. 6,650,917 and 6,699,194 entitled Signal Processing Apparatus and Signal Processing Apparatus and Method, respectively; a pulse oximeter monitor is described in U.S. Pat. No. 6,584,336 entitled Universal/Upgrading Pulse Oximeter; all of which are assigned to Masimo Corporation, Irvine, Calif., and each is incorporated by reference herein in its entirety.

SUMMARY

A draw back to current pulse oximetry sensors is a need to be located near significant capillary beds on the body, including fingers, ears, toes, nose and forehead. Such locations are often inconvenient for monitoring a user during normal activities, outside of a healthcare facility. Further, although measuring through motion oxygen saturation technology exists, it is directed to the healthcare facility context and is not reliable for normal routines, which include sporting activities or other significant daily movement. Accordingly, the present disclosure provides a sensor which allows for measuring pulse oximetry at sparse capillary bed locations, including the wrist. The present disclosure also provides algorithms for measuring pulse oximetry though higher exertion everyday motion.

A physiological monitoring sensor or module, also referred to herein as a physiological parameter measurement sensor or module, or a module, can be integrated into a wearable device that is secured to a wrist of a person (the “wearer”), such as a wristwatch or watch. The sensor on the watch can be used to monitor the wearer's physiological parameters. The sensor can detect pulse rate, oxygen saturation, hydration status, respiratory rate, and/or other parameters, such as the parameters disclosed herein, of the wearer. The sensor can include a convex protrusion to improve pressure and contact, and therefore optical coupling, between the wearer's skin and the physiological parameter measurement sensor. The curvature of the sensor can be designed to balance the desired pressure by the watch on the wearer's wrist and the wearer's comfort. The sensor can include a light barrier between emitters and detectors of the module and/or light diffusing materials surrounding the emitters and the detectors, among other features, to improve signal strength and reduce noise. The sensor or the watch can include a connection port to receive another sensor, which can be configured to be coupled to the wearer at a different measurement site of the wearer's body than the wrist. The sensor can be configured to continuously, at certain time intervals, and/or upon the wearer's request, measure one or more of the physiological parameters. For example, the sensor can be configured to continuously measure the wearer's oxygen saturation and/or pulse rate when the watch is worn on the wearer's wrist.

In some configurations, the one or more surface materials can comprise at least a portion of the one or more light blocks and a light transmission material.

In some configurations, the emitters in the first or second emitter groupings may not be electrically connected to one another.

In some configurations, the first or second emitter groupings can define a group of emitters located in close proximity.

In some configurations, the plurality of detectors can be individually both a near detector and far detector for each emitter grouping.

In some configurations, the first and second emitter groups can be located at non-central locations of a printed circuit board (PCB) of the sensor.

In some configurations, the one or more light blocks can extend from a surface of the sensor positioning the first and second pluralities of LEs towards a tissue of the wearer when the watch is worn.

In some configurations, each of the first or second emitter grouping can be surrounded by its own diffusing material.

In some configurations, the light diffusing material surrounding the first emitter grouping can be different from the light diffusing material surrounding the second emitter grouping.

In some configurations, at least some of the plurality of detectors can extend around a circumference of the sensor.

In some configurations, the plurality of detectors can be positioned in a grid pattern and/or across from one another.

In some configurations, locations of the emitter groupings can be interleaved with the plurality of detectors.

In some configurations, at least one of the plurality of detectors can be located between the first plurality of LEDs and the second plurality of LEDs, and at least one of the plurality of detectors can be located on each of at least two sides of each of the first plurality of LEDs and the second plurality of LEDs.

In some configurations, the sensor can further comprise a processor configured to determine an oxygen saturation measurement based on signals from the optical physiological sensor.

An example optical physiological sensor of the present disclosure can be integrated into a watch configured to monitor health of a wearer. The optical physiological sensor can be configured to face tissue of the wearer when the watch is worn by the wearer and to measure physiological parameters of the wearer using information from the optical physiological sensor. The optical physiological sensor can comprise a plurality of emitters, the emitters configured to emit light of a plurality of different wavelengths, the plurality of different wavelengths comprising at least three different wavelengths; a plurality of detectors, the detectors configured to detect light emitted by the plurality of emitters and attenuated by tissue of the user when the watch is worn on the wrist of the wearer and output signals to a sensor processor for determining the physiological parameters of the wearer; and a sensor housing, the plurality of emitters and the plurality of detectors enclosed within the housing, wherein the sensor housing can comprise: a convex skin-facing light transmissive cover extending over the plurality of emitters and the plurality of detectors, the cover located at a first side of sensor housing, and a printed circuit board (PCB) located at a second side of the sensor housing opposite the first side, the plurality of emitters and detectors located on a skin-facing side of the PCB; and a plurality of light barriers extending from the PCB to the cover, the plurality of light barriers configured to form walls of chambers to block light or substantially all the light between the chambers, each chamber enclosing one or more emitters without detectors, or one or more detectors without emitters, wherein a skin-facing surface of the cover and at least one of the light barriers can define a skin-facing surface of the sensor, a surface area of the cover extending over the chambers that enclose one or more detectors is at least 50% of a surface area of the skin-facing surface of the sensor.

In some configurations, the surface area of the cover extending over the chambers that enclose one or more detectors can be at least 100 mm².

In some configurations, the surface area of the cover extending over the chambers that enclose one or more detectors can be at least 150 mm².

In some configurations, the surface area of the cover extending over the chambers that enclose one or more detectors can be at least 165 mm².

In some configurations, a surface area of the light transmissive cover that extends over the chambers that enclose one or more emitters can be at least 25 mm².

In some configurations, the surface area of the light transmissive cover that extends over the chambers that enclose one or more detectors can be at least 35 mm².

In some configurations, the skin-facing surface of the sensor can have a longer side and a shorter side, the longer side configured to be along a width of the wearer's wrist when the watch is worn.

In some configurations, more of the plurality of detectors can be located along the longer side than along the shorter side.

In some configurations, the plurality of emitters can comprise a first group of emitters and a second group of emitters, the chambers comprising a first emitter chamber enclosing the first group and a second emitter chamber enclosing the second group.

In some configurations, the plurality of detectors can comprise a first ring of detectors and a second ring of detectors, the first ring of detectors surrounding the first group of emitters and the second ring of detectors surrounding the second group of emitters.

In some configurations, at least one of the plurality of detectors can be located between the first and second group of emitters and can be shared by the first and second rings of detectors.

In some configurations, some of the plurality of detectors can be closer to the first group of emitters than a remainder of the plurality of detectors and some of the plurality of detectors can be closer to the second group of emitters than a remainder of the plurality of detectors.

In some configurations, the plurality of light barriers can extend to a skin-facing surface of the cover.

An example optical physiological sensor of the present disclosure can be integrated into a watch configured to monitor health of a wearer. The optical physiological sensor can be configured to face tissue of the wearer when the watch is worn by the wearer and to measure physiological parameters of the wearer using information from the optical physiological sensor. The optical physiological sensor can comprise a plurality of emitters, the emitters configured to emit light of a plurality of different wavelengths, the plurality of different wavelengths comprising at least three different wavelengths; a plurality of detectors, the detectors configured to detect light emitted by the plurality of emitters and attenuated by tissue of the user when the watch is worn on the wrist of the wearer and output signals to a sensor processor for determining the physiological parameters of the wearer; and a sensor housing, the plurality of emitters and the plurality of detectors enclosed within the housing, wherein the sensor housing can comprise: a convex skin-facing light transmissive cover extending over the plurality of emitters and the plurality of detectors, the cover located at a first side of sensor housing, and a printed circuit board (PCB) located at a second side of the sensor housing opposite the first side, the plurality of emitters and detectors located on a skin-facing side of the PCB; and a plurality of light barriers extending from the PCB to the cover, the plurality of light barriers configured to form walls of chambers to block light or substantially all the light between the chambers, each chamber enclosing one or more emitters without detectors, or one or more detectors without emitters, wherein at least one of the plurality of light barriers can extend to a skin-facing surface of the cover.

In some configurations, all of the plurality of light barriers can extend to the skin-facing surface of the cover.

In some configurations, the skin-facing surface of the cover and the at least one of the light barriers can define a skin-facing surface of the sensor.

In some configurations, the skin-facing surface of the sensor can comprise a continuous curvature.

In some configurations, the cover can be a single lens or cover.

In some configurations, the cover can comprise individual lenses, each lens or cover covering a single chamber.

In some configurations, the cover can comprise a lens or cover covering all the chambers that extend over one or more detectors.

In some configurations, the lens or cover covering all the chambers that extend over one or more detectors may not cover a chamber that extends over one or more emitters.

In some configurations, the plurality of light barriers can comprise colored sapphire glass.

In some configurations, the first light barrier can comprise one or more portions that together extend from the surface of the substrate to the curved surface.

In some configurations, the sensor can further comprise: a second emitter comprising a second plurality of LEDs positioned on the surface of the substrate; a second photodiode positioned on the surface of the substrate; a second light barrier positioned between (i) both the first and second emitters and (ii) the second photodiode, and extending from the surface of the substrate to the curved surface, wherein the curved surface can extend over all the second plurality of LEDs and the second photodiode.

In some configurations, the second light barrier can comprise one or more portions that together extend from the surface of the substrate to the curved surface.

In some configurations, portions of the curved surface positioned above the first and second emitters can comprise at least a first material, portions of the curved surface positioned and the first and second photodiodes can comprise at least a second material, and portions of the first and second barriers extending to the curved surface can comprise at least a third material different from the first and second materials.

In some configurations, at least the first, second, and third materials together can make up the curved surface.

In some configurations, the first and second materials can comprise the same material.

An example optical physiological sensor of the present disclosure can be integrated into a watch configured to monitor health of a wearer. The optical physiological sensor can be configured to face tissue of the wearer when the watch is worn by the wearer and to measure physiological parameters of the wearer using information from the optical physiological sensor. The optical physiological sensor can comprise a plurality of emitters, the emitters configured to emit light of a plurality of different wavelengths, the plurality of different wavelengths comprising at least three different wavelengths; a plurality of detectors, the detectors configured to detect light emitted by the plurality of emitters and attenuated by tissue of the user when the watch is worn on the wrist of the wearer and output signals to a sensor processor for determining the physiological parameters of the wearer; and a sensor housing, the plurality of emitters and the plurality of detectors enclosed within the housing, wherein the sensor housing can comprise: a convex skin-facing light transmissive cover extending over the plurality of emitters and the plurality of detectors, the cover located at a first side of sensor housing, and a printed circuit board (PCB) located at a second side of the sensor housing opposite the first side, the plurality of emitters and detectors located on a skin-facing side of the PCB; and a plurality of light barriers extending from the PCB to the cover, the plurality of light barriers configured to form walls of chambers to block light or substantially all the light between the chambers, each chamber enclosing one or more emitters without detectors, or one or more detectors without emitters, wherein the plurality of detectors can comprise a plurality of far detectors that are further from at least some of the plurality of emitters than a remainder of the plurality of detectors.

In some configurations, at least one of the plurality of detectors can be located between the first and second group of emitters and is shared by the first and second rings of detectors.

In some configurations, some of the plurality of detectors can be closer to the first group of emitters than a remainder of the plurality of detectors and some of the plurality of detectors are closer to the second group of emitters than a remainder of the plurality of detectors.

In some configurations, the sensor can further comprise the sensor processor, wherein the sensor processor is configured to determine a hydration status of a user based on signals from the plurality of far detectors.

In some configurations, at least one of the emitters can be configured to emit light of a wavelength more sensitive to water than a remainder of the different wavelengths.

In some configurations, the wavelength more sensitive to water can be about 970 nm.

In some configurations, the sensor processor can be configured to compare signals of the reflected light of the wavelength more sensitive to water and another wavelength less sensitive to water from the plurality of far detectors.

In some configurations, the sensor processor can be configured to selectively drive some of the plurality of emitters and/or activate or deactivate some of the plurality of detectors.

An example optical physiological sensor of the present disclosure can be integrated into a watch configured to monitor health of a wearer. The optical physiological sensor can be configured to face tissue of the wearer when the watch is worn by the wearer and to measure physiological parameters of the wearer using information from the optical physiological sensor. The optical physiological sensor can comprise a plurality of emitters, the emitters configured to emit light of a plurality of different wavelengths, wherein at least one of the emitters can be configured to emit light of a reference wavelength; a plurality of detectors, the detectors configured to detect light emitted by the plurality of emitters and attenuated by tissue of the user when the watch is worn on the wrist of the wearer; a sensor processor, wherein the plurality of detectors can be configured to output signals to the sensor processor for determining at least some of the physiological parameters of the wearer based in part on a signal of the reflected light of the reference wavelength; and a sensor housing, the plurality of emitters and the plurality of detectors enclosed within the housing, wherein the sensor housing can comprise: a convex skin-facing light transmissive cover extending over the plurality of emitters and the plurality of detectors, the cover located at a first side of sensor housing, and a printed circuit board (PCB) located at a second side of the sensor housing opposite the first side, the plurality of emitters and detectors located on a skin-facing side of the PCB; and a plurality of light barriers extending from the printed circuit board to the cover, the plurality of light barriers configured to form walls of chambers to block light or substantially all the light between the chambers, each chamber enclosing one or more emitters without detectors, or one or more detectors without emitters.

In some configurations, the reference wavelength can be about 525 nm.

In some configurations, the light of the reference wavelength can be green or yellow.

In some configurations, the sensor processor can be configured to extract features from signals of other wavelengths based on the signal of the reflected light of the reference wavelength and calculate the at least some of the physiological parameters based on the extracted features.

In some configurations, at least one of the emitters can be configured to emit light of a wavelength more sensitive to oxygen saturation.

In some configurations, at least one of the emitters can be configured to emit light of a wavelength more sensitive to water.

In some configurations, at least one of the emitters can be configured to emit light of a normalizing wavelength.

In some configurations, the sensor processor can be configured to determine a hydration status of a user based on signals of the reflected light of the wavelength more sensitive to water and of the normalizing wavelength.

In some configurations, one or more physiological parameters can comprise a pulse rate, respiration rate, SpO2, PVI, PI, RRP, hydration, or a combination thereof.

In some configurations, the sensor can further comprise a thermistor located near the plurality of emitters.

In some configurations, the sensor can further comprise an accelerometer and/or gyroscope.

In some configurations, the sensor processor can be configured to selectively drive some of the plurality of emitters and/or activate or deactivate some of the plurality of detectors.

An example optical physiological sensor of the present disclosure can be integrated into a watch configured to monitor health of a wearer. The optical physiological sensor can be configured to face tissue of the wearer when the watch is worn by the wearer and to measure physiological parameters of the wearer using information from the optical physiological sensor. The optical physiological sensor can comprise a plurality of emitters, the emitters configured to emit light of a plurality of different wavelengths, the plurality of different wavelengths comprising at least three different wavelengths; a plurality of detectors, the detectors configured to detect light emitted by the plurality of emitters and attenuated by tissue of the user when the watch is worn on the wrist of the wearer and output signals to a sensor processor for determining the physiological parameters of the wearer; and a sensor housing, the plurality of emitters and the plurality of detectors enclosed within the housing, wherein the sensor housing can comprise: a convex skin-facing light transmissive cover extending over the plurality of emitters and the plurality of detectors, the cover located at a first side of sensor housing, and a printed circuit board (PCB) located at a second side of the sensor housing opposite the first side, the plurality of emitters and detectors located on a skin-facing side of the PCB; a plurality of light barriers extending from the PCB to the cover, the plurality of light barriers configured to form walls of chambers to block light or substantially all the light between the chambers, each chamber enclosing one or more emitters without detectors, or one or more detectors without emitters, wherein each chamber that encloses one or more emitters can be filled with a diffusing material such that there is no air gap between the plurality of emitters and the cover.

In some configurations, the light diffusing material can comprise glass microspheres.

In some configurations, the cover can comprise glass microspheres.

In some configurations, the sensor housing can comprise one or more openings configured to receive a flow of light diffusing solution.

In some configurations, the light diffusion solution can be UV-cured after being injected into each chamber that encloses one or more emitters.

In some configurations, the sensor housing can comprise one or more air vent openings configured to receive air displaced from the chamber(s) by the flow of light diffusing solution.

In some configurations, each chamber that encloses one or more detectors can be filled with the diffusing material such that there is no air gap between the plurality of detectors and the cover.

In some configurations, the diffusing material in each chamber that encloses one or more emitters can be configured to improve mixing of light such that light emitted by one of the emitter in the same chamber appears to be emitted from the entire same chamber.

An example watch of the present disclosure can be configured to monitor physiological parameters of a wearer. The watch can comprise any of the optical sensor or physiological parameter measurement sensor configurations disclosed above; a watch processor separate from and in electrical communication with the sensor processor; a power source configured to power the watch and the sensor, and a display in communication with the processor, the display configured to display the plurality of physiological parameters monitored by the sensor.

In some configurations, the display can be configured to display the wearer's SpO2 and pulse rate that are monitored by the sensor.

In some configurations, the sensor can be configured to continuously monitor the wearer's SpO2 and pulse rate.

In some configurations, the display can be configured to continuously display the wearer's SpO2 and pulse rate.

In some configurations, the watch can further comprise an ECG sensor.

In some configurations, the ECG sensor can comprise a reference electrode, a negative electrode, and a positive electrode.

In some configurations, the reference and negative electrodes can be located on the sensor.

In some configurations, a portion of a housing of the watch can form the positive electrode.

In some configurations, the ECG sensor can be in electrical communication with the sensor processor.

In some configurations, the watch can further comprise a wireless transmitter such that the watch is configured to wireless connect to external devices and/or external sensors.

In some configurations, the wireless transmitter can be a Bluetooth chip.

In some configurations, the external devices and/or external sensors can comprise a bedside monitor, a mobile communication device, a tablet, a nurses' station system, or a different medical device.

An health monitoring watch of the present disclosure can comprise a strap and a housing. The housing can comprise: a first chamber comprising a first well comprising a first depth below a first surface configured to be in contact with a skin of a user; a first plurality of light emitting diodes positioned at the first depth inside the first well, said first plurality of light emitting diodes comprising a first light emitting diode configured to emit light at a first wavelength, a second light emitting diode configured to emit light at a second wavelength different than the first wavelength, and a third light emitting diode configured to emit light at a third wavelength different than the first wavelength and the second wavelength, and a first wall surrounding the first well; a second chamber comprising a second well comprising a second depth below a second surface configured to be in contact with the skin of the user, a second plurality of light emitting diodes positioned at the second depth inside the second well, said second plurality of light emitting diodes comprising a fourth light emitting diode configured to emit light at the first wavelength, a fifth light emitting diode configured to emit light at the second wavelength different than the first wavelength, and a sixth light emitting diode configured to emit light at the third wavelength different than the first wavelength and the second wavelength, and a second wall surrounding the second well; and four or more light sensors.

An wearable health monitoring device can be configured to be worn on a wrist of a user and monitor one or more physiological parameters indicative of the user's health. The wearable health monitoring device can comprise: a first emitter grouping, the first emitter grouping comprising a first plurality of light-emitting diodes (LEDs) configured to emit light of one or more wavelengths, wherein the first emitter grouping can be arranged at a first location, the first location being spaced from an axis extending through a center of the wearable health monitoring device; a second emitter grouping, the second emitter grouping comprising a second plurality of LEDs configured to emit light of one or more wavelengths, wherein the second emitter grouping can be arranged at a second location, the second location being spaced from the first location and spaced from the axis extending through the center of the wearable health monitoring device; one or more light blocks separating the first emitter grouping from the second emitter grouping; a first light diffusing material, the first light diffusing material configured to be positioned between the first emitter grouping and tissue of the user when the wearable health monitoring device is in use, wherein the first light diffusing material can be configured to spread light emitted from one or more of the first plurality of LEDs before the emitted light reaches the tissue; a second light diffusing material, the second light diffusing material configured to be positioned between the second emitter grouping and the tissue of the user when the wearable health monitoring device is in use, wherein the second light diffusing material can be configured to spread light emitted from one or more of the second plurality of LEDs before the emitted light reaches the tissue; a plurality of photodiodes configured to detect at least a portion of the light emitted from one or more of the first plurality of LEDs or one or more of the second plurality of LEDs after attenuation through the user's tissue, the plurality of photodiodes configured to output one or more signals responsive to the detected light; and a processor configured to receive and process one or more signals responsive to the one or more signals outputted by the plurality of photodiodes and further configured to determine a physiological parameter of the user based on the received and processed one or more signals.

It is noted that “plethysmograph” as used herein (commonly referred to as “photoplethysmograph”), encompasses its broad ordinary meaning known to one of skill in the art, which includes at least data representative of a change in the absorption of particular wavelengths of light as a function of the changes in body tissue resulting from pulsing blood. Moreover, “oximetry” as used herein encompasses its broad ordinary meaning known to one of skill in the art, which includes at least those noninvasive procedures for measuring parameters of circulating blood through spectroscopy.

For purposes of summarization, certain aspects, advantages and novel features are described herein. Of course, it is to be understood that not necessarily all such aspects, advantages or features need to be present in any particular embodiment.

BRIEF DESCRIPTION OF THE DRAWINGS

The drawings and the associated descriptions are provided to illustrate embodiments of the disclosure and not to limit the scope of the claims. In the present disclosure, “bottom” refers to the side facing a wearer's wrist when an example wearable device disclosed herein is worn on the wearer's wrist and “top” refers to the side facing away from the wearer's wrist.

FIG. 1A illustrates a first view of an example wearable device including a physiological parameter measurement sensor or module worn on a wrist using straps.

FIG. 1B illustrates a second view of the example wearable device of FIG. 1A worn on the wrist.

FIG. 1C illustrates an example fingertip sensor that can be coupled to the wearable device of the present disclosure.

FIG. 1D illustrates a top perspective view of the example wearable device of FIGS. 1A-1C with a partial view of the straps.

FIG. 1E illustrates a bottom perspective view of the example wearable device of FIG. 1D.

FIG. 1F illustrates a side view of an example wearable device without the straps when the device is interfacing with a wearer's skin.

FIG. 1G illustrates a top perspective view of the example wearable device of FIG. 1F.

FIG. 1H illustrates a bottom perspective view of an example wearable device.

FIG. 1I illustrates a perspective view of an example strap configured to secure the wearable device disclosed herein to a wearer's wrist.

FIG. 2 is a diagram illustrating schematically a network of non-limiting examples of devices that can communicate with the wearable device disclosed herein.

FIG. 3 illustrates an example display of physiological parameter measurements on the wearable device disclosed herein.

FIG. 4 illustrates an example physiological parameter measurement module of the wearable device.

FIG. 5A illustrates a side view of an example wearable device incorporating an example physiological parameter measurement module.

FIG. 5B illustrates a cross-sectional view of the example wearable device of FIG. 5A.

FIG. 5C illustrates a perspective view of the wearable device of FIG. 5A.

FIG. 5D illustrates a bottom view of the wearable device of FIG. 5A.

FIG. 6 illustrates schematically arteries and capillaries of a human hand and a proximal portion of a human forearm.

FIG. 7A illustrates a schematic system diagram of a wearable device including a physiological parameter measurement module.

FIG. 7B illustrates a partially exploded view of an example wearable device.

FIG. 7C illustrates an example light transmissive cover of the physiological parameter measurement module of FIG. 7B.

FIG. 7D illustrate an exploded view of ECG electrodes, light transmissive cover(s), and a opaque frame of the physiological parameter measurement module of FIG. 7B.

FIG. 7E illustrates a bottom perspective view of a physiological parameter measurement module incorporating the ECG electrodes, light transmissive cover(s), and a opaque frame of FIG. 7C or 7D.

FIG. 7F illustrates a top perspective view of the example physiological parameter measurement module of FIG. 7E.

FIGS. 7G and 7H illustrate schematically top and bottom views of an example device processor board of the wearable device disclosed herein.

FIGS. 8A and 8B illustrate schematically top and bottom views of an example sensor or module processor board of an example physiological parameter measurement module.

FIGS. 8C-8E illustrate various view of bonding of detectors to a PCB substrate of a physiological parameter measurement module.

FIG. 8F illustrates a perspective view of a PCB substrate of a physiological parameter measurement module with different wire bonding arrangements than shown in FIGS. 8C-8E.

FIGS. 9A and 9B illustrate light diffusing material fill channels and air venting channels in a opaque frame of an example physiological parameter measurement module.

FIG. 10 illustrates a longitudinal cross-sectional view of an example physiological parameter measurement module and example light paths between emitters and detectors of the module.

FIG. 11A illustrates a schematic system diagram of an example wearable device including a physiological parameter measurement module.

FIG. 11B illustrate a schematic diagram of an example device processor shown in FIG. 11A.

FIG. 11C illustrates a schematic system diagram of an example sensor or module processor shown in FIG. 11A.

FIG. 11D illustrates a block diagram of an example front end circuitry of the sensor or module processor of FIG. 11C.

FIG. 12A illustrates a bottom view of an example physiological parameter measurement module with first and second ECG electrodes.

FIG. 12B illustrates a top perspective view of the example wearable device including a third ECG electrode.

FIG. 12C illustrates a partial top perspective view of the example wearable device of FIG. 12B with the third ECG electrode shown as transparent to illustrate contact springs underneath the third ECG electrode.

FIG. 13A illustrates an example block diagram of LED drive circuitry of the physiological parameter measurement module disclosed herein.

FIG. 13B illustrates an example block diagram of emitters circuitry of the physiological parameter measurement module disclosed herein.

FIG. 13C illustrates an example block diagram of detectors circuitry of the physiological parameter measurement module disclosed herein.

FIG. 13D illustrates an example block diagram of temperature sensors circuitry of the physiological parameter measurement module disclosed herein.

FIGS. 14A and 14B are example block diagrams illustrating signal processing of a conventional plethysmograph sensor.

FIGS. 15A and 15B illustrate example schematic input and output flow diagrams of a physiological parameter measurement module disclosed herein.

FIG. 15C illustrates an example schematic input and output flow diagram of the gyroscope and accelerometer of a physiological parameter measurement module disclosed herein.

FIG. 15D illustrates an example schematic block diagram for determining pulse rate using a physiological parameter measurement module disclosed herein.

FIG. 15E illustrates an example decision logic for determining pulse rate using a physiological parameter measurement module disclosed herein.

FIG. 15F illustrates an example schematic input and output flow diagram for determining oxygen saturation using a physiological parameter measurement module disclosed herein.

FIG. 15G illustrates an example decision logic for determining oxygen saturation using a physiological parameter measurement module disclosed herein.

FIG. 16A illustrates schematically an example plethysmograph sensor arrangement on a sensor or module processor board of a physiological parameter measurement module of a wearable device.

FIG. 16B illustrates a bottom view of an example physiological parameter measurement module incorporating the plethysmograph sensor arrangement of FIG. 16A.

FIG. 16C illustrates a side view of the example physiological parameter measurement module of FIG. 16B.

FIG. 16D illustrates a bottom perspective view of the example physiological parameter measurement module of FIG. 16B.

FIG. 16E illustrates a bottom view of a variation of the example physiological parameter measurement module of FIG. 16B including ECG electrodes.

FIG. 16F illustrates a side view of the example physiological parameter measurement module of FIG. 16E.

FIG. 16G illustrates a bottom perspective view of the example physiological parameter measurement module of FIG. 16E with the opaque frame and light transmissive cover hidden to show ECG electrodes assembled with the sensor or module processor board.

FIG. 17A illustrates a bottom perspective view of an example physiological parameter measurement module incorporating the plethysmograph sensor arrangement of FIG. 16A.

FIG. 17B illustrates a bottom view of the example physiological parameter measurement module of FIG. 17A.

FIG. 17C illustrates a side view of the example physiological parameter measurement module of FIG. 17A.

FIG. 18A illustrates schematically an example plethysmograph sensor arrangement on a sensor or module processor board of a physiological parameter measurement module of a wearable device.

FIG. 18B illustrate schematically an example plethysmograph sensor arrangement on a sensor or module processor board of a physiological parameter measurement module of a wearable device.

FIG. 19A illustrate schematically an example plethysmograph sensor arrangement on a sensor or module processor board of a physiological parameter measurement module of a wearable device.

FIG. 19B illustrates a bottom view of an example physiological parameter measurement module incorporating the plethysmograph sensor arrangement of FIG. 19A.

FIG. 19C illustrates a side view of the physiological parameter measurement module of FIG. 19B.

FIG. 20A illustrates a bottom view of an example physiological parameter measurement module of a wearable device as worn on a schematic representation of a wearer's wrist.

FIG. 20B illustrates a side view of the physiological parameter measurement module of FIG. 20A.

FIGS. 20C and 20D illustrate exploded views of the physiological parameter measurement module of FIG. 20A.

FIG. 20E illustrates a first side view of an example wearable device incorporating the physiological parameter measurement module of FIGS. 20A-20D.

FIG. 20F illustrates a bottom view of the wearable device of FIG. 20E.

FIG. 20G illustrates a second side view of the wearable device of FIG. 20E.

FIG. 20H illustrates a third side view of the wearable device of FIG. 20E.

FIG. 20I illustrates a bottom perspective view of the wearable device of FIG. 20E.

FIG. 20J illustrates a top perspective view of the wearable device of FIG. 20E.

FIGS. 21A and 21B illustrate perspective views of an example physiological parameter measurement module with alternative light transmissive cover curvatures from the module in FIG. 20A.

FIG. 21C illustrates a longitudinal cross-sectional view of the physiological parameter measurement module of FIGS. 21A and 21B.

FIGS. 22A and 22B illustrate perspective views of an example physiological parameter measurement module with another alternative light transmissive cover curvatures from the module in FIG. 20A.

FIG. 22C illustrates a longitudinal cross-sectional view of the physiological parameter measurement module of FIGS. 22A and 22B.

FIG. 23A illustrates a bottom perspective view of an example wearable device incorporating the physiological parameter measurement module of FIGS. 20A-20D.

FIG. 23B illustrates a side view of the wearable device of FIG. 23A.

FIG. 23C illustrates a top perspective view of the wearable device of FIG. 23A.

FIG. 23D illustrates a top view of the wearable device of FIG. 23A.

FIG. 23E illustrates a bottom view of the wearable device of FIG. 23A.

FIG. 24A illustrates a bottom view of another example physiological parameter measurement module of a wearable device.

FIG. 24B illustrates a side view of the physiological parameter measurement module of FIG. 24A.

FIG. 25A illustrates a bottom view of another example physiological parameter measurement module of a wearable device.

FIG. 25B illustrates a side view of the physiological parameter measurement module of FIG. 25A.

FIG. 25C illustrates a first side view of another example wearable device incorporating the physiological parameter measurement module of FIGS. 25A-25B.

FIG. 25D illustrates a bottom view of the wearable device of FIG. 25C.

FIG. 25E illustrates a second side view of the wearable device of FIG. 25C.

FIG. 25F illustrates a top perspective view of the wearable device of FIG. 25C.

FIG. 25G illustrates a third side view of the wearable device of FIG. 25C.

FIG. 25H illustrates a bottom perspective view of the wearable device of FIG. 25C.

FIG. 26A illustrates schematically a microneedle inserted into skin of a wearer.

FIG. 26B illustrates schematically a microneedle patch coupled to a body of the wearable device disclosed herein.

FIG. 26C illustrates schematically a microneedle patch coupled to a strap of the wearable device disclosed herein.

FIG. 26D illustrates schematically a simplified system diagram of the microneedle patch and the wearable device.

DETAILED DESCRIPTION

Although certain embodiments and examples are described below, those of skill in the art will appreciate that the disclosure extends beyond the specifically disclosed embodiments and/or uses and obvious modifications and equivalents thereof based on the disclosure herein. Thus, it is intended that the scope of the disclosure herein disclosed should not be limited by any particular embodiments described below.

Overview of Wearable Device Including a Physiological Parameter Measurement Sensor or Module

Daily use of a wearable healthcare monitoring device, which can include oximetry- or plethmosmograph-based and/or ECG physiological parameters, can be beneficial to the wearer. The device, such as a device 10 as shown in FIGS. 1A-1H, can be a wristwatch incorporating a physiological parameter measurement sensor 100 or a wrist-worn physiological parameter measurement sensor with built-in watch or time-indicating functions. The device 10 can include an adjustable strap 30. Accordingly, the wearer needs not wear an additional sensor when going about daily activities and the appearance of the device attracts less attention from the general public so that the wearer may feel less self-conscious about wearing a pulse oximeter sensor on the wearer's body. The wearer can also connect additional sensors (for example, a fingertip plethysmograph sensor shown in FIG. 1C) and/or other physiological monitoring devices to the wearable device to expand the functionality of the wearable device.

The wearer can be informed of physiological parameters, such as vital signs including but not limited to heart rate (or pulse rate), and oxygen saturation by the wearable device 10. The device 10 can display one or more of the measured physiological parameters on its display 12. The information can be helpful in providing feedback to the wearer and/or a third party user, for example, a healthcare professional or the wearer's family member, when the wearer is exercising, or otherwise for warning the wearer of possible health-related conditions, including but not limited to changes in the wearer's physiological parameters in response to medication that is being administered to the wearer.

As shown in FIGS. 1A-1H, the wearable device 10 can be a watch, which can include a physiological parameter measurement sensor or module 100 configured to measure an indication of the wearer's physiological parameters, which can include, for example, pulse rate, respiration rate, oxygen saturation (SpO2), Pleth Variability Index (PVI), Perfusion Index (PI), Respiration from the pleth (RRp), hydration, glucose, blood pressure, and/or other parameters. The physiological parameter measurement sensor or module 100 can be an optical sensor. Additionally, the sensor or module 100 can optionally calculate a wellness index based on more than one individual physiological parameter measured by the module and/or received by the sensor or module 100 based on externally connected sensors and/or patient monitoring devices. The sensor or module 100 can perform intermittent and/or continuous monitoring of the measured parameters. The sensor or module 100 can additionally and/or alternatively perform a spot check of the measured parameters, for example, upon request by the wearer.

As shown in FIGS. 1E and 1H, a bottom side of a device (or watch) housing 101 can include an opening sized to retain the physiological parameter measurement module 100 while still allowing the tissue-facing surface of the sensor or module 100 to be exposed. The retaining of the sensor or module 100 in the device housing 101 can be aided by any suitable retaining mechanisms. As shown in FIGS. 1F and 1H, the physiological parameter measurement module 100 can include a skin-interfacing light transmissive cover 102 that encloses a plurality of light emitters 104 (such as LEDs) and one or more photodetectors (also referred to as “detectors”) 106. Additionally, the sensor or module 100 can optionally include an electrocardiogram (ECG) sensor, which can include a plurality of ECG electrodes 124, 125. As shown in FIGS. 1G and 1H, some of the ECG electrodes 125 can be located away from the sensor or module 100 and some of the ECG electrodes 124 can be located on the sensor or module 100. The cover 102 can include a plurality of lenses or covers or a single construct of lens or cover. The physiological parameter measurement module 100 is designed to reduce noise in the signals detected by the detectors 106, for example, by reducing mixing of the emitted light and the reflected light using light barriers that are substantially opaque. As shown in FIG. 1F, the light barrier 120 can include a first light barrier which can be placed between the emitters and the detectors of the sensor or module 100. The first light barrier can extend (for example, entirely extend) along an inner portion of the cover 102. The first light barrier can also suppress light emitted by the emitters at an angle. The sensor or module 100 can include additional light barriers, including for example, a side perimeter wall and additional light barriers to separate the detectors from the emitters, and/or separate different detector groups from one another.

FIG. 1F illustrates the device 10 being worn on the wrist 2 of the wearer, with the physiological parameter measurement module 100 facing the wrist 2. The physiological parameter measurement module 100 on the device 10 is designed so as to reduce and/or eliminate a gap between a surface of the physiological parameter measurement module 100 and the wearer's skin at the measurement site where the device 10 is worn. At the wrist, if the device 10 is worn too loosely (which can be the case when the device 10 is able to slide over the skin when the device 10 is moved), the gap between the tissue-facing surface of the physiological parameter measurement module 100 and the wearer's skin can cause inaccurate measurements. This is because the gap can result in both light-piping and in the emitted light not penetrating deep enough into the wearer's tissue, for example, by going no deeper than within a top skin layer (for example, the epidermis) of the wearer's tissue, which typically does not have any blood vessels present. Therefore, light cannot reach and or interact with tissues, such as the arterial blood in the dermis, located below the top skin layer. The gap can also result in loss of the attenuated and reflected light through the gap so that less of the attenuated and reflected light can arrive at the detectors 106.

The tightness of the device 10 on the wearer's body (for example, the wrist) can be adjusted by adjusting any suitable strap(s) 30 used to secure the device to the wearer's body. The strap(s) can be connected to the device 10 using any suitable strap connections 22. For example, the strap connections 22 can be compatible with third party watch bands, wearable blood pressure monitors, and/or the like. As shown in FIG. 1I, an example strap 30 can be stretchable and evenly distribute the pressure of the device 10 around the wrist so as to provide better contact between the sensor or module 100 and the wrist 2 while not compromising the comfort of the wearer and/or reducing the blood flow across the wrist 2 in a way that reduces the accuracy of the measurement by the sensor or module 100. As shown in FIG. 1L, a rubber base 302 can be molded through a plurality of metal loops 304 arranged along a length of a strap 30 to form the strap 30. The metal loops 304 can include a thin (for example, less than about 1 mm) wall of metal forming a closed loop with a through-hole in a direction generally transverse to the length (that is, along a width) of the strap 30 and perpendicular to a thickness of the strap 30. During the overmolding process, the rubber material can fill up or substantially fill up the space in the through-hole. The metal loops 304 can be arranged in two rows along the length of the strap 30. Alternatively, the metal loops can include a partial loop with an opening, or the strap may include more than one partial metal loop snapped onto each other around the rubber base. Additional details of the strap 30 are described in U.S. Provisional Application No. 63/068,256, filed Aug. 20, 2020 and titled “WEARABLE PHYSIOLOGICAL MONITORING DEVICE WITH ADJUSTABLE STRAPS”, the entire of which is incorporated herein by reference.

Additionally, the gap between a surface of the physiological parameter measurement module 100 and the wearer's skin at the measurement site can be reduced by the design of the light transmissive cover 102. As shown in FIG. 1F, a cover 102 of the physiological parameter measurement module 100 can include a convex curvature or convex protrusion on its skin-interfacing cover 102. As will be described in greater detail below, the curvature of the cover 102 of the sensor or module 100, which can include a plurality of lenses or covers or a single lens or cover, can be discontinuous or continuous.

As shown in FIG. 1F, when the device 10 is worn by the wearer, the convex cover 102 can be pressed onto the skin and the tissue 2 of the wearer can conform around the convex curvature. The contact between the convex cover 102 and the tissue 2 of the wearer can leave no air gaps between the tissue 2 and the convex cover 102. And as the emitters and/or detectors can be surrounded by a light-diffusing material (as will be described below), the physiological parameter measurement module 100 may leave no air gap between the tissue 2 and any of the emitters and/or detectors. Optionally, certain portion(s) of the cover 102 can protrude more into the skin than the remainder of the cover. The pressure exerted by the curvature of the cover 102 on the skin and/or the absence of air gap can increase a light illuminated and/or detection area, improve the optical coupling of the emitted light and the blood vessels and/or of the reflected light and the detectors, reduce light piping, and/or reduce stagnation of the blood. The cover curvature can be configured so as to balance the pressure needed to improve contact between the cover 102 and the skin, and the comfort of the wearer.

The wearable device 10 can be used in a standalone manner and/or in combination with other devices and/or sensors. As shown in FIG. 2, the device 10 can connect (for example, wirelessly) with a plurality of devices, including but not limited to a patient monitor 202 (for example, a bedside monitor such as Masimo's Radical-7®, Rad-97® (optionally with noninvasive blood pressure or NomoLine capnography), and Rad-8® bedside monitors, a patient monitoring and connectivity hub such as Masimo's Root® Platform, any handheld patient monitoring devices, and any other wearable patient monitoring devices), a mobile communication device 204 (for example, a smartphone), a computer 206 (which can be a laptop or a desktop), a tablet 208, a nurses' station system 201, and/or the like. The wireless connection can be based on Bluetooth technology, near-field communication (NFC) technology, and/or the like. Additionally, the wearable device 10 can connect to a computing network 212 (for example, via any of the connected devices disclosed herein, or directly). The wearable device 10 can establish connection via the network 212 to one or more electronic medical record system 214, a remote server with a database 216, and/or the like.

Optionally, the device 10 can be integrated with more sensors and/or configured to connect to a plurality of external sensors, wirelessly or with a connecting cable. The connecting cable can be a universal connector configured to connect to any of the medical devices and/or sensors disclosed herein to provide communication between the wearable device 10 and the connected medical devices and/or sensors. The cable can optionally include a board-in-cable device that includes its own processor, but may not include its own display.

The device 10 can act as hub for the external sensors, for example, the sensors described in U.S. Patent Publication No. 2020/0138288, published on May 7, 2020 (the entirety of which is hereby incorporated herein by reference). The sensors described in U.S. Patent Publication No. 2020/0138288 can collect patient physiological data and provide power for a reusable pairing device. The reusable pairing device can establish wireless communication with a patient monitoring device. The wearable device 10 can replace the patient monitoring device in U.S. Patent Publication No. 2020/0138288. As another example, the device 10 can replace a patient monitor device described in U.S. Patent Publication No. 2020/0329993, published on Oct. 22, 2020, the entirety of which is hereby incorporated herein by reference. By replacing the patient monitor device in U.S. Patent Publication No. 2020/0329993, the wearable device 10 performs all the computations based on the sensor data so that the connected external sensors, for example, the ECG sensors disclosed in U.S. Patent Publication No. 2020/0329993, do not require heavy computing power.

The device 10 can include open architecture to allow connection of third party wireless sensor, and/or allow third party access to a plurality of sensors on the wearable device 10 or connected to the wearable device 10. The plurality of sensors can include, for example, a temperature sensor, an altimeter, a gyroscope, an accelerometer, emitters, LEDs, etc. Third party applications can be installed on the wearable device 10 and can use data from one or more of the sensors on the wearable device 10 and/or in electrical communication with the wearable device.

Optionally, the wearable device 10 can communicate with any other suitable noninvasive sensor, such as an acoustic sensor, a blood pressure sensor, temperature sensor, movement sensor, ECG sensor, etc. Examples of some of these devices include Masimo's Radius PPG™ sensor, Radius T™ sensor, and Centroid™ sensor, or otherwise. One or more of those sensors, for example, the Centroid™ sensor, can be used for stroke detection. The wearable device 10 can output an alert of stroke detection of the wearer and/or automatically initiate communication with a first respondent and/or the wearer's guardian or next-of-kin upon stroke detection.

The wearable device 10 can optionally communicate with chemical sensors, which can detect, for example, chemicals on the wearer's skin, and/or sweat, and/or the odor of certain chemicals in the air. The chemical sensors can include electrochemical sensors or any other suitable types of chemical sensors. A chemical sensor configured to analyze compositions of sweat can output measurements aiding the wearable device 10 in detecting stress and/or the wearer's hydration status. The wearable device 10 can optionally communicate with a skin impedance sensor, which can be used for monitoring the hydration status of the wearer.

Another example sensor that can be integrated into or connected to the device 10 and/or the sensor or module 100 can include a toxin and/or radiation detector configured to detect toxins in air (for example, pollution or contaminant particulates, carbon monoxide, smoke, and the like in the air). The toxin detection can aid care providers and/or firefighters who wear the device 10. Alternatively, the device 10 can be connected wirelessly to an external toxin and/or radiation detector. The toxin and/or radiation detector can be used with a smart mask. For example, the external toxin and/or radiation detector can be located on the mask, which can allow the mask to output a warning to the wearer of the mask when the mask filter or cartridge needs replacement.

Optionally, the wearable device 10 can communicate with glucose monitors, which can be invasive or minimally invasive such as finger prick type of glucose monitors, or a continuous noninvasive glucose monitor. The wearable device 10 can receive and display the wearer's glucose level from the glucose monitor. The wearable device 10 can also optionally be in communication with an insulin pump. The wearable device 10 can send a control signal to dispense insulin from the insulin pump to the wearer based on the monitored glucose level of the wearer.

As shown in FIG. 3, the device 10 can include a display screen 12 positioned at a top side of the device housing 101. In addition to time and date indicators, one display layout (for example, the default display layout) of the display screen 12 can display the wearer's SpO2 measurement, the pulse rate (PR) measurement, the respiration rate (RR) measurement, and/or hydration status (H2O). The format of the measurement displayed is not limiting. For example, some measurements, such as the SpO2 measurement and the PR measurements, can be displayed as numerical values. As another example, some measurements, such as the RR measurements and hydration status, can be displayed as a sliding scale. In the illustrated example, the hydration status can be displayed as having three levels from low (L) to high (H). In the illustrated example, the respiration rate can be displayed as ranging from 5 bpm to 25 bpm. The wearer can optionally view individual display layouts for each measurements or a group of measurements by tapping on the display screen 12, which can be a touch screen, and/or pressing a button on the device 10. Each of the measurements can be displayed constantly, at certain intervals, and/or upon receiving instructions for display (for example, by the wearer tapping on the display screen 12 and/or pressing a button on the device 10). Each of the measurements can be configured to be displayed with different or the same frequencies. Time and certain physiological parameters (for example, SpO2 and pulse rate) can be immediately and/or intermittently available, and/or continuously measured (for example, at least every 5 to 10 measurements per minute or more) and the displayed values constantly updated. Optionally, the display can further show a trend line for some parameters, such as SpO2 and pulse rate. In one example, the display of the wearable device can be configured to display only time, SpO2, and pulse rate.

As shown in FIG. 4, the physiological parameter measurement module 100 can be preassembled before being integrated into the device 10. The physiological parameter measurement module 100 can be characterized before being assembled with the rest of the device 10. The preassembled physiological parameter measurement module 100 can be secured within the device housing 101 using various mechanical assembly mechanisms, for example, one or more screws or other fasteners. The sensor or module 100 of a wearable device 10 can be interchangeable and be replaced without replacing the memory in the device 10. For example, the sensor or module 100 can include a quick-connect (and/or quick-release) feature for attaching the sensor or module 100 to the remainder of the device 10, such as being attachable to the device 10 by magnets. An electrical connection can be established between the physiological parameter measurement sensor or module processor board and the circuit of the rest of the device 10, including for example, a device processor and the display 12. Optionally, the electrical connection can include a connector 32 on the sensor or module 100. The connector 32 is configured to be electrically connected to a flex circuit. The wearable device 10 and the sensor or module 100 are portable and can be moved from place to place. As described above, the functionality of the wearable device 10 can be integrated and/or interchangeable with various other patient monitoring devices, displays, etc.

The sensor or module 100 can be applied to locations on the body other than the wrist. Alternatively or additionally, multiple modules 100 can be applied to different locations of the body of the wearer. Other types of straps or fastening mechanism may be used to attach the multiple modules 100 onto other parts of the body. The other types of straps or fastening mechanism can optionally include a power source (for example, battery) to power a module 100 that is not integrated into the wearable device 10, but may not have its own display. For example, an optical sensor can be placed on the wearer's neck to measure arterial and venous oxygen saturation, which can be transmitted to and displayed on the wearable device 10. The wearer can view his or her oxygen consumption information on the wearable device 10 based on the signals from the optical sensor on the neck and/or the signals from the sensor or module 100 that is located on the wearable device 10.

As shown in FIGS. 5A-5D, an example wearable device 500 can include a watch housing 501. Features of the device 500 can be incorporated into features of the device 10 and features of the device 10 can be incorporated into features of the device 500. The watch housing 501 can have a length, for example, between about 40 mm and 50 mm, or between about 42 mm and 46 mm. The watch housing can have a width, for example, between about 32 mm to about 40 mm, or between about 35 mm to about 38 mm. When fully assembled, the watch 500 can have a thickness or height, for example, between 10 mm to about 15 mm, or between 12 mm to about 14 mm.

As described above, the physiological parameter measurement module can include a plurality of emitters and a plurality of detectors. The emitters can transmit optical radiation of a plurality of wavelengths into a tissue site (near the wrist of the wearer) and the detectors can respond to the intensity of the optical radiation (which can be reflected from the tissue site) after absorption by pulsatile arterial blood flowing within the tissue site. In addition to the light being attenuated by blood in the arteries, light interaction also happens at the capillary level. Arteries are located deeper below the skin surface than the capillaries, requiring LED emitters of greater light intensity and thus greater power consumption in order for the emitted light to reach the arteries. Moreover, measuring the light intensities signal of the light after attenuation by blood in the artery requires more selective placement of the emitters and detectors directly above the arteries to capture the pulsation of the blood. The physiological parameter measurement module disclosed herein is designed to utilize attenuation by blood in the capillaries and is not reliant on the blood flow in arteries. The patient parameter measurements made by the module disclosed herein can be accurate enough for clinical use. The module disclosed herein can provide plethysmograph-based patient parameter measurements with an accuracy of within about 4% error, or about 2% error. As shown in FIG. 6, the wrist 62 has fewer capillaries per volume than the fingertip 64. Accordingly, the module is designed to have a width to provide greater coverage area of the wearer's wrist, which can boost the signal from the sensors located on the module (which will be described in greater detail below).

When measuring oxygen saturation based on attenuation by blood in the capillaries, it is desirable to avoid veins. Because venous blood contains less oxygen, intensity signals of light attenuated by venous blood can cause errant readings oxygen saturation measurement. Optionally, the sensor or module processor of the physiological parameter measurement modules disclosed herein can reduce the effect of pulsing vein on the signal by comparing the signals from the plurality of detectors to determine which detectors receive better and/or clearer signals and deactivating the detectors that are more likely to cover and/or be around the pulsing veins. The sensor or module processor can dynamically adjust which detectors to deactivate. Deactivating the detectors can include deactivating operation of that detector and/or ignoring signals from that detector.

Optionally, the sensor or module processor of the physiological parameter measurement module can map the physiological parameter measurements calculated from signals received at the detectors and/or clusters of detectors located at different regions of the module. Variations (for example, if outside a certain range) in the mapped measurements can be an indication that the pressure distribution of the wearable device on the body of the wearer is unbalanced, and therefore the pressure of the device on the wearer is either too high or too low and/or the wearable device is tilted on the wrist. The wearable device can output an instruction to the wearer to readjust the tightness of the straps and/or to re-center of the wearable device on the wrist. Variations (for example, if outside a certain range) in the mapped measurements can additionally or alternatively provide an indication that a certain detector or cluster of detectors is/are placed over a large pulsing vein as described above. Readings from that certain detector or cluster of detectors can be ignored or the detector(s) suspected to be cover a pulsing vein may be deactivated. When two or more physiological parameter measurements, such as oxygen saturation measurements, do not agree among two or more detectors (for example, having a variation exceeding a certain range), the sensor or module processor can use the higher or highest measurement value, or alternatively use a combination of the measurement values from the two or more detectors (for example, using one of the two measurement values at different times or otherwise).

Alternatively or additionally, the mapped measurements can be compared with experimentally determined data at the same detector location or detector cluster location. The experimentally determined data can be obtained using, for example, a conventional reflectance type pulse oximeter taped over the corresponding detector location, or any other suitable known methods for making the same measurements, including the same wrist-based sensor arrangements described herein. The comparison between the mapped measurements and the experimentally determined data can provide indication of whether the device has achieved a desired pressure on the body of the wearer, whether certain detectors and/or clusters of detectors are placed over or near a pulsing vein, which may interfere with the physiological parameter measurements, or otherwise. For example, if the difference between the mapped measurements and the experimental data at a certain location falls outside a predetermined range, the sensor or module processor can determine that pressure is too high or too low at that location, and/or that the pressure distribution over the body is not sufficiently balanced to make accurate measurements, and/or a detector or cluster of detectors is/are placed over the wearer's pulsing vein. The experimental data can be stored in a memory device of the sensor or module processor.

The comparison among the mapped measurements and/or between the mapped measurements and the experimental data can be performed when the wearer first puts on the device and/or at certain time intervals in the duration when the device is worn on the wearer. Additionally, running the comparison-based diagnostics can allow the sensor or module processor to determine, at the start of the measurement and/or dynamically during use of the device, which detector(s) provide the most accurate and/or reliable measurements.

Various Example Components of the Wearable Device

Components of the wearable device will now be described. As shown in FIGS. 7A and 7B, the device 10 can include its own device processor 14, which can be a digital/analog chip or other processor(s), such as a digital watch processor or a smartwatch processor. As shown in FIGS. 7B, 7G, and 7H, the device processor 14 can be located on a PCB. FIGS. 7G and 7H illustrate example layouts of the PCB for the device processor 14. As shown in FIGS. 7A and 7B, the device 10 can include a power source 16, which can be a battery, for powering the device processor 14, the display screen 12, and/or the physiological parameter measurement module 100. The battery 16 can last at least 10 hours, or at least 12 hours, or at least 14 hours, or at least about 16 hours after each charge, with continuous measurements and/or displaying of certain physiological parameters, such as SpO2 and pulse rate.

The device 10 can be configured to display time after the battery 16 has been depleted, even if other features (for example, measuring physiological parameters using the module) may not be available when the battery 16 has been depleted. Additionally, when the device to is used clinically, the display 12 can also continue displaying critical patient information (for example, the patient's name, date of admission, etc.) after the battery 16 has been depleted. The device 10 may include nonvolatile memory to store the critical patient information. The device 10 can include a dual-battery configuration with a main battery and a backup battery. Power management of the device 10 may switch automatically for the device 10 to be powered by the backup battery when the main battery has been depleted. The device can additionally or alternatively be configured to be solar-powered, for example, by including a solar panel on the dial or elsewhere of the wearable device 10. The display 12 of the device 10 can use e-ink or ULP (ultra low power screen) technology, which draws little amount of current for displaying information. The display 12 may automatically adjust the brightness, being brighter when outdoors and dimmer when indoors to further prolong battery life.

As shown in FIGS. 7A and 7B, the sensor or module 100 of the wearable device 10 can include a sensor or module processor 108 (which can include a memory and/or other electronics, such as shown in FIG. 11C). The sensor or module processor 108 can process signals from one or more of the sensors in the sensor or module 100 (or optionally other sensors in communication with the device 10) to determine a plurality of physiological parameters. All the processing of the raw sensor data of the sensors in communication (via a wired and/or wireless connection) with the sensor or module processor 108 is performed by the sensor or module processor 108. The sensor or module processor 108 can be configured to drive the emitters 104 to emit light of different wavelengths and/or to process signals of attenuated light after absorption by the body tissue of the wearer from the detectors 106. The sensor or module processor 108 can determine and output for display on the device display screen 12 the physiological parameters based on the detected signals. Optionally, the sensor or module 100 can send the signals from the detectors 106 (for example, preprocessed signals) to the device processor 14, which can determine and output for display the physiological parameters based on the detected signals. The absorption of light can be via transreflectance by the wearer's body tissue, for example, by the pulsatile arterial blood flowing through the capillaries (and optionally also the arteries) within a tissue site where the device 10 is worn (for example, the wrist). The sensor or module processor 108 can be located on a PCB 116, such as shown in FIG. 7B.

The sensor or module 100 can include more than one group or cluster of light emitters (such as LEDs) 104 and more than one group of photodetectors (also referred to as “detectors”) 106. Each group of emitters 104 can be configured to emit four (or three) different wavelengths described herein. The sensor or module 100 can include one or more thermistors 110 or other types of temperature sensors. The thermistor(s) 110 can be placed near one or more groups of emitters 104. There can be at least one thermistor 110 near each group of emitters 104. The thermistor(s) 110 can provide for wavelength correction of the light emitted by the emitters 104. Optionally, the thermistor(s) 110 can additionally measure a temperature of the wearer of the device 10. Optionally there can be one or more thermistors 110 located at other places of the sensor or module 100. The emitters 104, the thermistor(s) 110, and/or the detectors 106 can be positioned on the PCB 116.

As shown in FIG. 7A, the device 100 can include a gyroscope 112, an accelerometer 114, and/or other position and/or posture detection sensor(s). The gyroscope 112 and/or the accelerometer 114 can be in electrical communication with the sensor or module processor 108. The sensor or module processor 108 can determine motion information from signals from the gyroscope 112 and/or the accelerometer 114. The motion information can provide noise reference for analysis of the pleth information and other signal processing (for example, processing of ECG signals) performed by the sensor or module processor 108. The gyroscope 112 and/or the accelerometer 114 can be located on the PCB 116.

FIG. 8A illustrates example layouts of a top side of the PCB 116. FIG. 8B illustrates example layouts of a bottom side of the PCB 116. The first or bottom side of the PCB 116 can include the emitters 104, the detectors 106, the temperature sensor 110, and any other sensors, for example, the gyroscope, the accelerometer, and/or the like. FIGS. 8C-8E illustrate the detectors 106 being connected electrically to the PCB 116 via wire bonds 107. The module can include wires 105 extending over the detector 106 for shielding purposes. The number of wires 105 extending over the detector 106 may vary. The manner in which the wires 105 extend over the detector 106 may vary. The wires 105 may not extend all the way over the detectors 106 across the detector's width or length. For example, as shown in FIG. 8F, the detectors of detector groups 106a, 106b, 106a/b can each be connected electrically to the first side of the PCB 816 via wire bonds 107. A wire 105 can extend along each side of the detector for noise shielding. In the illustrated example, the wire 105 can extend along each long side of the detector. The wire 105 may extend parallel with the length of the detector. The wire 105 may not extend over the body of the detector 106a, 106b, 106a/b. The emitters in the emitter groups 104a, 104b can each be electrically connected to the first side of the PCB 816 via wire bonds 107. The thermistors 110 at each of the emitter groups 104a, 104b can be electrically connected to the first side of the PCB 816 via wire bonds 107. The detectors, emitters, and/or thermistor can alternatively be electrically connected to the PCB 116 via other suitable types of electrical connectors.

The second or top side of the PCB 116 can include the sensor or module processor 108 and other circuit hardware. The second side of the PCB 116 can be electrically noisy and is isolated from the sensors on the first side of the PCB 116 by the board. Electronics on the same side of the PCB 116 can be substantially entirely overmoulded to reduce or avoid components shifting in place or being damaged during use. On the second side of the PCB 116, which faces away from the light transmissive cover 102, the PCB 116 can be covered by melt plastic or other suitable electronics protective material 130, such as shown in FIGS. 7B and 7F. As shown in FIG. 7F, the electronic components on the second side of the PCB 116 can be generally sealed by the protective material 130 except that a connector 132 can extend from the second side of the PCB 116 and be exposed. The connector 132 can electronically connect the sensor or module 100 to circuitry of the wearable device 10.

Optionally, as shown in FIGS. 7A, 7B, and 7D, the device 10 can include an electrocardiogram (ECG) sensor including a plurality of electrodes 124, 125 configured to make contact with the wearer's skin. One or more ECG electrodes 124 may be located on the sensor or module 100 (such as shown in FIGS. 7B and 7E). One or more ECG electrodes 125 may be located elsewhere on the device (for example, an ECG electrode 125 can form a part of the housing of the wearable device 10 as shown in FIG. 7B). The ECG sensor can be in electrical communication with the sensor or module processor 108 via an ECG connector.

As shown in FIGS. 7B-7E, the physiological parameter measurement module 100 can include a skin-interfacing light transmissive cover 102 that encloses the first side of the PCB 116, which positions the plurality of light emitters 104 and detectors 106. The sensor or module 100 can include a light barrier construct 120 that is configured to divide the emitters 104 and the detectors 106 into different chambers such that light cannot travel or substantially cannot travel between the chambers. The light transmissive cover 102 can extend over the various emitter and detector chambers formed by the light barrier construct 120 and the PCB 116. The light transmissive cover 102 can include individual lenses or covers such as shown in FIG. 7D, a single lens or cover such as shown in FIGS. 17A-17C, or a combination of individual emitter chamber covering lenses or covers and a single lens or cover covering a plurality of detector chambers, such as shown in FIG. 7C. In the example lens or cover 102b shown in FIG. 7C, the individual lenses or covers that are configured to cover the detector chambers such as shown in FIG. 7D can be interconnected with bridging portions 103 between the detector chambers, forming a single piece of lens or cover. The lens or cover 102b can be combined with the lenses or covers 102a covering the emitter chambers to cover all the openings in the light barrier construct 120 for forming sealed emitter and detector chambers. The light barrier construct 120 can be overmoulded to the lens or cover 102b and the lenses or covers 120a. The lens or cover 102b may not be configured to cover the emitter chambers, which can be covered by individual lenses, so as to avoid any light traveling between an emitter chamber and a detector chamber.

As shown in FIG. 7B, the physiological parameter measurement module 100 can include a opaque frame 126. The opaque frame 126 can accommodate the light barrier construct 120. Alternatively, the opaque frame 126 and the light barrier construct 120 can form an integral piece, such as shown in FIG. 7D. The opaque frame 126 can include indentations having the shape and size to accommodate the ECG electrodes 124 or other components with a suitable shape and size. A front side of the electrodes 124 can have one or more posts 137 extending past openings in the opaque frame 124 into corresponding openings on the PCB 116. The posts 137 of the electrodes 124 can establish an electrical connection with the corresponding openings of the PCB 116. A plurality of screws (or other types of fasteners) can extend into the corresponding openings of the PCB 116 from the front side of the PCB 116 to secure the electrodes 124 to the sensor or module 100 by threadedly mating or otherwise with the posts 137. When a wearer puts the wearable device incorporating the sensor or module 100 onto the wearer's wrist, the electrodes 124 can made contact with the wearer's skin.

The physiological parameter measurement module 100 can include diffusing materials or encapsulant, which can include, for example, microspheres or glass microspheres. As described above, the encapsulant can eliminate air gaps between the surface of the light transmissive cover 102 and the emitters 104 and/or the detectors 106. The encapsulant can be included around the emitters 104 to more evenly spread the emitted light, which appears to be emitted from an entire emitter chamber rather than from a point source (that is, a single LED emitter) if the encapsulant is absent. The encapsulant can allow the emitted light to travel through a greater volume of the tissue at the tissue site. The diffusing material can act as a beam shaper that can homogenize the input light beam from the emitter, shape the output intensity profile of the received light, and define the way (for example, the shape or pattern) the emitted light is distributed to a tissue measurement site. Such diffuser materials can, for example, deliver substantially uniform illumination over a specified target area in an energy-efficient manner. According to the Beer-Lambert law, the amount of light absorbed by a substance is proportional to the concentration of the light-absorbing substance in the irradiated solution (for example, the arterial blood). Therefore, by irradiating a larger volume of tissue and/or by increasing the amount of detected light, a larger sample size of light attenuated by the wearer's tissue can be measured. The larger sample size provides a data set that can be more representative of the complete interaction of the emitted light as it passes through the patient's blood as compared to a smaller sample size.

The diffusing materials can be any suitable materials, for example, glass, ground glass, glass beads, opal glass, greyed glass, polytetrafluoroethylene, or a microlens-based, band-limited, engineered diffuser that can deliver efficient and uniform illumination UV-cured flow glass microspheres injected into one or more openings on the sensor or module 100 (for example, after the sensor or module 100 has been assembled). Examples of engineered diffusers can include molded plastics with specific shapes, patterns, and/or textures designed to diffuse the emitter light across the entirety of a tissue surface. The diffusing material can be made of ground glass, which spreads the emitted light with a Gausian intensity profile. The diffusing material can include glass beads. The diffusing material can be constructed so as to diffuse the emitted light in a Lambertian pattern. A Lambertian pattern is one in which the radiation intensity is substantially constant throughout the area of dispersion. One such diffusing material can be made from opal glass. Opal glass is similar to ground glass, but has one surface coated with a milky white coating to diffuse light evenly. The diffusing material can be capable of distributing the emitted light on the surface of a plane (for example, the surface of the tissue measurement site) in a predefined geometry (for example, a rectangle, square, circle, or otherwise), and with a substantially uniform intensity profile and energy distribution. The efficiency, or the amount of light transmitted by the diffusing material, can be greater than 70% of the light emitted by the emitter. The efficiency can be greater than 90% of the emitted light. Additional examples of the diffusing material are described in U.S. Pat. No. 10,448,871, the entirety of which is hereby incorporated herein by reference and should be considered part of the disclosure.

Additionally or alternatively, the physiological parameter measurement module 100 can include encapsulant or light diffusing materials in the detector chambers to more evenly spread the reflected light to so as to increase the amount of the reflected light reaching the detectors. The module can include light diffusing materials positioned around the detectors to scatter and/or deflect the reflected light so that more reflected light can be detected by the detectors. For example, the reflected light can keep bouncing off the diffusing materials until the reflected light reaches the detector. Accordingly, the light detecting surface area in the module can be greater than the surface area of the detectors. Having the light diffusing materials can reduce the power needed to drive the LEDs of the emitters and/or the number of detectors at a particular location of the module, which can reduce the power consumption of the module.

As shown in FIG. 9A, the opaque frame 126 of the sensor or module 100 can include a plurality of light diffusing material(s) (or encapsulant) fill holes 144. Light diffusing material(s) or encapsulant (for example, a flow of glass microspheres) can be injected into the plurality of chambers via the fill holes 144, and be directed to the respective emitter or detector chambers as illustrated by the arrows in FIG. 9A along a plurality of the fill channels 446 (see FIG. 9B) which are interconnected with the fill holes 144. The fill channels 146 can be located at a side of the opaque frame 126 facing away from the tissue of the wearer. As shown in FIG. 9B, the side of the opaque frame 126 facing away from the tissue of the wearer can further include a plurality of air vent channels 145. Air can escape into the vent channels 145 as the diffusing material solution or encapsulant is injected into the respective chambers via the fill holes 144, making it easier for the injected solution to flow into the respective chamber. As shown in FIG. 9B, the module 401 may not have air vent channels or fill channels between emitter and detector chambers to avoid light piping along such a channel. The encapsulant can be UV-cured after being injected into the respective chambers.

The opaque frame 126 may be configured such that the fill holes 144 and channels 146 allow the light diffusing materials to fill only the emitter chambers, or only the detector chambers, or both the emitter and detector chambers. Optionally, in addition or alternative to the light diffusing materials, the detector chamber can include light transmissive lens(es) or covers on the surface of the PCB that is not occupied by the detectors. The light transmissive lens(es) or covers inside the detector chamber can help in focusing the reflected light onto the detectors inside the detector chamber.

In FIG. 10, a cross-sectional view of the sensor or module 100 illustrates some of the emitter and detector chambers. The chambers illustrated in FIG. 10 include a first emitter chamber 136a enclosing a first emitter group 104a, a second emitter chamber 136b enclosing a second emitter group 104b, a first detector chamber 140 enclosing one of first groups of detectors 106a that surround the first emitter group 104a, a second detector chamber 142 enclosing one of second groups of detectors 106b that surround the second emitter group 104b, and a third detector chamber 138 enclosing one of shared groups of detectors 106a/b that surround both the first and second emitter groups 104a, 104b on opposite sides of the third detector chamber 138.

As shown in FIG. 10, light from the first emitter group 104a can travel a shorter path, as indicated by the shorter arrows, to the first group of detectors 106a or the shared group of detectors 106a/b; and light from the first emitter group 104a can travel a longer path, as indicated by the longer arrows, to the second group of detectors 106b. The reverse is true for light from the second emitter group 104b, which can travel a shorter path to the second group of detectors 106b or the shared group of detectors 106a/b and a longer path to the first group of detectors 106a. As described herein, the different groups of emitters 104a, 104b and/or detectors 106a, 106b, 106a/b can be run independently and/or simultaneously. Signals outputted by the different groups of detectors 106a, 106b, 106a/b based on light emitted from the first emitter group 104a and/or the second emitter group 104b can provide different information due to the different light paths, which can travel through different areas of the tissue. The longer path penetrates deeper into the tissue and through a greater volume of the tissue to reach the “far” groups of detectors than the shorter path, which penetrates less deep into the tissue and travels through a smaller volume of tissue to reach the “near” group of detectors. The different information can be separated and/or combined to calculate a plurality of physiological parameters of the wearer of the sensor or module 100, for example, an indication of the wearer's hydration status, which will be described in greater detail below.

FIG. 11A illustrates schematically an example wearable device 10 disclosed herein. As described above, the device processor 14 can be connected to the module sensor 108 of the physiological parameter measurement module 100, which includes the emitters, the detectors, the thermistors, and other sensors disclosed herein. The electrical connection between the device processor 14 and the sensor or module processor 108 can be establish optionally via a flex connector 32. The sensor or module processor 108 can be coupled to the ECG electrodes 124, 125, optionally via an ECG flex connector 123.

The device processor 14 can be connected to a display 12, which can include the display screen and touch input from the wearer. The device processor 14 can include a battery 16, and optionally one or more wireless charging coils 17 to enable wireless charging of the battery 16. The device processor 14 can be connected to an antenna 19 for extending signals transmitted wirelessly, for example, to an external device as described with reference to FIG. 2. The device processor 14 can include connection to a first user interface (UI 1) 13a and a second user interface (UI 2) 13b on the device 10 to receive input from the wearer. As shown in FIG. 1F, example first and second user interface 13a, 13b can be in the form of buttons 13. Additionally or alternatively, the device 10 can include a microphone. The device 10 can receive user inputs via the user interfaces, which can be the buttons, the microphone, and/or the touchscreen. The user inputs can command the device 10 to turn on and/or off certain measurements, and/or to control externally connected devices, such as an insulin pump, a therapeutics delivery device, or otherwise. The device processor 14 can be connected to a user feedback output 15 to provide feedback to the wearer, for example, in the form of vibration, an audio signal, and/or otherwise. The device processor 14 can optionally be connected to an accelerometer and/or a gyroscope 42 located on the device 10 that is different from the accelerometer 114 and gyroscope 112 on the physiological parameter measurement module 100. The accelerometer and/or gyroscope 42 can measure position and/or orientation of the wearer for non-physiological parameter measurement functions, for example, for sensing that the wearer has woken up, rotating the display 12, and/or the like.

FIG. 11B illustrates example components of the device processor 14 PCB board. As shown in FIG. 11B, the device processor 14 can include a Bluetooth co-processor 1400 and a system processor 1402. The system processor 1402 can run the peripheral functions of the device 10, receive user (that is, the wearer) input and communicate to the sensor or module processor 108. The Bluetooth co-processor 1400 can focus on managing Bluetooth communication so as to allow the system processor 1402 to focus on the high memory utilization tasks, such as managing the display screen 12. The Bluetooth co-processor 1400 can be activated when there is incoming and/or outgoing Bluetooth communication. Alternatively, the Bluetooth co-processor 1400 can be replaced by a different wireless co-processor configured to manage wireless communication using a different wireless communication protocol.

FIG. 11C illustrates example components of the module processor PCB board 116. As shown in FIG. 11C, the sensor or module processor 108 can include a calculation processor 1080 and a system processor 1082. The calculation processor 1080 can manage host communication with the device processor 14 via a host connector 1084. The calculation processor 1080 can perform algorithm computations to calculate the physiological parameters based on the signals received from the ECG electrodes 124/125 and the optical sensor including the emitters 104, the detectors 106, and the temperature sensors 110, and optionally from other sensors in communication with the sensor or module processor 108. The calculation processor 1080 can have relatively large memory suitable for running algorithm computations. The system processor 1082 can be in communication with a power management integrated circuit (PMIC) 1090. The system processor 1082 can run the physical system of the sensor or module 100 (for example, including turning on and off the emitter LEDs, changing gain, setting current, reading the accelerometer 114 and/or the gyroscope 112, and the like) and decimate data to a lower sampling rate. The system processor 1082 can focus on data processing, taking measurements and diagnostics, and basic functions of the sensor or module processor 108. The system processor 1082 can allow the calculation processor 1082 to sleep (being inactive) most of the time, and only wake up when there is enough measurement data to perform calculations.

FIG. 11D illustrates an example front-end analog signal conditioning circuitry 1088 of the module PCB 116 shown in FIG. 11C. The entire front end circuitry 1088 can be located on a single application-specific integrated circuit (ASIC).

The front-end circuitry 1088 can include a transimpedance amplifier 1092 configured to receive analog signals from the optical sensor including the emitters 104, the detectors 106, and the temperature sensors 110, which can be preprocessed (for example, via a low pass filter 1094 and a high pass filter 1096) before being sent to an analog-digital converter 1098. The analog-digital converter 1098 can output a digital signal based on the analog signals from the optical sensor including the emitters 104, the detectors 106, and the temperature sensors 110 to the system processor 1082 and the calculation processor 1080. The front end circuitry 1088 can include a detector cathode switch matrix 1083 configured to activate the cathode of the detectors that are selected to be activated. The matrix 1082 can be further configured to deactivate (for example, by short-circuiting) anodes of the detectors that are selected to be deactivated in configurations in which the detectors share a common cathode and have different cathodes.

The front-end circuitry 1088 can include an ECG amplifier 1091 configured to receive analog signals from the ECG electrodes 124/125, which can output the amplified analog signals to the analog-digital converter 1096. The amplified analog signals can include an ECG differential between the positive and negative electrodes. The analog-digital converter 1098 can output a digital signal based on the analog signals from the ECG electrodes 124/125 to the system processor 1082 and the calculation processor 1080.

The ECG electrodes 124 can include a negative electrode, a positive electrode, and a reference electrode. As shown in FIG. 12A, the two electrodes 124 located on the sensor or module 100 can act as a reference electrode and a negative (or positive) electrode respectively. As shown in FIGS. 12B and 12C, a portion of the device housing 101 that surrounds the display screen 12 can function as another ECG electrode 125. An electrically insulating material 127 can separate the ECG electrode 125 from the remainder of the housing 101 so that an electrical current between the ECG electrode 125 and the ECG electrodes 124 would travel through the wearer's body. When the wearer wants to make a measurement using the ECG sensor that includes the ECG electrodes 124, 125, the wearer can press on or touch the electrode 125 using the wearer's finger or another part of the wearer's body such that the wearer's skin makes contact with the electrode 125.

In the illustrated examples, the ECG electrode 125 can be positive (or negative if one of the electrodes 124 servers as a positive electrode) electrode. As shown in FIG. 12C, the electrode 125 is illustrated as being transparent to show one or more spring contacts 131 located underneath the electrode 125. The shape, size, and/or number of the spring contacts 131 can vary from the example shown in FIG. 12C. The spring contacts 131 can establish an electrical connection between the electrode 125 and the electrode 125 and the sensor or module processor 108 of the sensor or module 100. For example, the spring contacts 131 can establish an electrical connection between the electrode 125 and the connector 132. The spring contacts 131 can be biased toward the electrode 525 to ensure a firm electrical connection between the spring contacts 131 and the electrode 125. Readings from the electrodes 124, 125 can allow the sensor or module processor 108 to obtain the wearer's ECG signal and optionally to make physiological measurements based on the obtained ECG, for example, the heart rate, the respiratory rate, and/or otherwise. The sensor or module processor 108 can communicate the ECG signals and/or ECG-related measurements to the wearable device processor 14. The wearer's ECG waveform and/or the measurements made from the ECG can be displayed on the display screen 12.

FIG. 13A illustrates an example LED driver circuitry 1086 of the module PCB 116 shown in FIG. 11C. The entire LED driver circuitry 1086 can be located on the single ASIC with the front end circuitry 1088. As described above, the system processor 1802 can output a control signal to turn on and off the emitter LEDs. As shown in FIG. 13A, the LED driver circuitry 1086 can include an emitter switch matrix 1085 configured to drive any of the emitters (or emitter groups) that are selected to be turned on or turn off any of the emitters (or emitter groups) that are selected to be turned off.

FIG. 13B illustrates an example emitter circuitry including eight different emitter LEDs 104. The number of LEDs may vary and be greater than eight. The emitters of the physiological parameter measurement module can be configured to emit a plurality of (for example, three, four, or more) wavelengths. Each of the emitters can be configured to emit light of a different wavelength than the other emitters. Alternatively, one or more of the emitters can emit light of more than one wavelength. In the illustrated example, the emitter circuitry can include four drivers to drive the eight emitter LEDs. Alternatively, the module can include more than four LEDs per emitter group. Each LED Drive can drive an LED to emit light of a different wavelength. The device or the module can grant access of some of the LEDs to a third party device, for example, for measurement purposes. The LED drivers can selectively drive some but not all the LEDs.

The emitters can be configured to emit light of a first wavelength providing an intensity signal that can act as a reference signal. The first wavelength can be more absorbent by the human body than light of other wavelengths emitted by the emitters. The reference signal can be stronger and less likely to be affected by noise than the signals from other wavelengths emitted by the emitters. The reference signal can be used by the physiological parameter measurement sensor or module processor to extract information from the other signals, for example, information relevant to and/or indicative of the pulsing rate, harmonics, or otherwise. The physiological parameter measurement sensor or module processor can focus the analysis on the extracted information for calculating physiological parameters of the wearer. Including the reference signal can reduce power consumption and saving the battery life of the device. The first wavelength can be from about 525 nm to about 650 nm, or from about 580 nm to about 585 nm, or from about 645 nm to about 650 nm, or about 525 nm, or about 580 nm, or about 645 nm. The light providing the reference signal can have an orange or yellow color. Alternatively, the light providing the reference signal can have a green color.

The emitters can be configured to emit light having a second wavelength having a red color. The second wavelength can be from about 620 nm to about 660 nm. Light of the second wavelength can be more sensitive to changes in oxygen saturation (SpO2) than light of other wavelengths emitted by the emitters. The second wavelength is preferably closer to 620 nm (for example, about 625 nm), which results in greater absorption by the body tissue of the wearer, and therefore a stronger signal and/or a steeper curve in the signal, than a wavelength that is closer to 660 nm. The physiological parameter measurement sensor or module processor 108 can extract information such as the pleth waveform from signals of the second wavelength.

The emitters can be configured to emit light having a third wavelength of about 900 nm to about 910 nm, or about 905 nm, or about 907 nm. The third wavelength can be in the infrared range. The sensor or module processor can use the third wavelength as a normalizing wavelength when calculating ratios of the intensity signals of the other wavelengths, for example, a ratio of the intensity signals of the second wavelength (red) to the third wavelength (infrared).

Additionally or optionally, the emitters can be configured to emit light having a fourth wavelength that is more sensitive to changes in water than the rest of the emitted wavelengths. The fourth wavelength can be in the infrared range and about 970 nm. The physiological parameter measurement sensor or module processor can determine physiological parameters such as a hydration status of the wearer based at least in part on a comparison of the intensity signals of the fourth wavelength and a different wavelength detected by certain detectors. The detectors used for hydration monitoring can be located a predetermined distance away from the emitters (that is, being a “far” detector disclosed herein) so that light travels through a certain depth of the tissue before being detected by those detectors.

The emitters in the physiological parameter measurement sensor or module can be placed in two emitter groups. Each emitter group can include four emitter LEDs configured to emitter the first, second, third, and fourth wavelengths described above. The emitters in the same emitter group can be located in the same emitter chamber disclosed herein. Each of the four drivers are configured to drive the emitters to emit one of the four wavelengths described above.

FIG. 13C illustrates an example detector circuitry including fourteen detectors 106. The total number of detectors on a module can vary. The fourteen detectors can form seven detector groups, each group including two detectors. The number of detectors in each group may vary. Detectors of the same detector group can be located in the same detector chamber disclosed herein. Each detector group can output one signal, which can be a combined signal of the two detectors in the same group. As shown in FIG. 13C, the detectors can share a common anode but have seven different cathodes, corresponding to the seven detector groups.

FIG. 13C illustrates an example thermistor circuitry. In the illustrated example, the physiological parameter measurement module can include two thermistors 110. The two thermistors can be located in the two emitter chambers near the two emitter groups respectively.

Example Signal Processing of the Physiological Parameter Measurement Module

FIGS. 14A and 14B depict functional block diagrams of the operations of a conventional pulse oximeter carried out by the digital signal processing system. The signal processing functions described below are carried out by a digital signal processor (DSP) with a microcontroller providing system management. As shown in FIG. 14A, an analog signal from the detector(s) of the conventional pulse oximeter is digitized, filtered and normalized, and further processed using conventional pulse oximetry signal processing algorithms. Parallel signal processing engines—DST®, FST®, SST™, and MST™ are used to separate the arterial signal from sources of noise (including the venous signal) to measure SpO2 and pulse rate accurately, even during motion. FIG. 14B depicts a generalized functional block diagram for the operations performed on the 20 Khz sample data entering the digital signal processing system from an analog to digital converter (ADC). As illustrated in FIG. 14B, the DSP first performs a demodulation, as represented in a demodulation module 400. The processor performs decimation, as represented in a decimation module 402 on the resulting data from the demodulation. The processor calculates certain statistics, as represented in a statistics module 404, and performs a saturation transform, as represented in a saturation transform module 406, on the data resulting from the decimation operation. The processor forwards data subjected to the statistics operations and the data subjected to the saturation transform operations to saturation operations, as represented by a saturation calculation module 408 to output an oxygen saturation measurement and pulse rate operations, as represented in a pulse rate calculation module 410 to output a pulse rate value.

FIGS. 15A-15G illustrate example signal processing of the physiological parameter measurement sensor or module disclosed herein. As shown in FIG. 15A, the sensor or module processor can receive intensity signals from the detectors in response to detected reflected light of the first (reference signal or signal of green or yellow light), second (signal of red light), third (signal of infrared light), and fourth (signal of infrared light with a wavelength of 970 nm) wavelengths described above, and signals from the gyroscope and accelerometer. The sensor or module processor can output a plurality of physiological parameters based on the input signals from the sensors described above. The plurality of physiological parameters can include, for example, SpO2 (Sat), pulse rate (PR), perfusion index (PI), pleth variability index (PVI), respiration rate from the pleth (RRp), and a hydration index.

As shown in greater detail in FIG. 15B, the sensor or module processor can process the intensity signal in response to detected light of the first, second, and third wavelengths in the unnormalized form and a normalized form (in normalization modules “Norm” 1500, “Norm 1” 1502, and “Norm 2” 1504). As described above, the signal of the third wavelength can be used as the normalizing signal. The sensor or module processor can extract various information from the intensity signals in response to detected light of the first, second, and third wavelengths and signals from the accelerometer and the gyroscope, such as the PR (which can be output as the PR measurement), time domain (TD) saturation information, frequency domain (FD) saturation information, PI information, and PVI information, in a pulse rate determination module 1506.

FIG. 15C illustrates example processing of the raw signals from the accelerometer and the gyroscope to output the gyroscope and accelerometer signals. The sensor or module processor can combine each of the raw gyroscope and accelerometer signals (which can be raw signals from any axis of the gyroscope and/or accelerometer) with gyroscope/accelerometer time instants and pleth time instants signals in an interpolation module 1518 or interpolation 1 module 1520 respectively. The sensor or module processor can further process the outputs from the interpolation module 1518 or interpolation 1 module 1520 in a low pass filter and decimation module 1522 or low pass filter and decimation 1 module 1524 respectively to output a gyrol signal and an accelerometer 1 signal. The output gyre 1 and accelerometer 1 signals can be sent to the ASIC described above.

As shown in FIG. 15D, the sensor or module processor can extract motion information from the gyroscope and accelerometer input and the normalized signals of the first, second, and third wavelengths in an interference mitigation (IM) and motion analysis module 1526. As also shown in FIG. 15D, the sensor or module processor can obtain time domain pulse rate (TDPR) information, TD saturation information, PI information, and PVI information in a time domain pulse rate determination module 1528 from the intensity signals of the first, second, and third wavelengths. The sensor or module processor can obtain frequency domain pulse rate (FDPR) information and FD saturation information in a frequency domain pulse rate determination module 1530 based on normalized signals of the first, second, and third wavelengths. The sensor or module processor can determine and output a pulse rate in a pulse rate decision logic 1532 based on the TDPR information, FDPR information, interference mitigation (IM) PR information (output by the interference mitigation and motion analysis module 1526), and motion information.

FIG. 15E illustrates an example pulse rate determination decision logic. In this example, a decision logic stage 2 module 1534 can receive as input raw pulse rate calculations from individual pulse rate determination engines (for example, the time domain pulse rate determination module 1528, the frequency domain pulse rate determination module 1530 and the interference mitigation and motion analysis module 1526 as shown in FIG. 15D), pleth features including time domain and frequency domains from N channels (for example, N=4 or more) of pleth signals, and motion features obtained from a motion analysis module 1536. The motion analysis module 1536 can assess the amount of motion, define the type of motion, and calculate a motion rate (for example, per minute) if the motion is determined to be periodic, and/or the like based on motion information from a 6DOF (degree-of-freedom) inertia measurement unit (IMU). The IMU can include the accelerometer and the gyroscope on the physiological parameter measurement module.

With continued reference to FIG. 15B, the sensor or module processor can determine the oxygen saturation measurement based on the normalized signal of the third wavelength, the normalized signal of the second wavelength, the TD saturation information, the FD saturation information, the PR, and the motion information in an oxygen saturation determination module 1508. FIG. 15F illustrates an oxygen saturation determination module including a plurality of parallel signal processing engines, such as a Seed saturation module 1538, an SST saturation module 1540, a DST saturation module 1542, an interference mitigation (IM) saturation module 1544, and a signal/noise reference saturation module 1546, configured to feed individual raw oxygen saturation (SpO2) values to a decision logic 1548. The decision logic 1548 can further receive as input the motion information and output a final oxygen saturation measurement based on the motion information and the raw oxygen saturation values determined by the parallel engines.

FIG. 15E illustrates an example oxygen saturation determination decision logic. In this example, a saturation decision logic stage 2 module 1550 can receive as input raw oxygen saturation calculations from the parallel engines described above, pleth features, pulse rate, and motion features obtained from a motion analysis module 1552. The pleth features received by the module 1550 can include the features in the pulse rate decision logic shown in FIG. 15E. Additionally, the pleth features received by the module 1550 can include features related to saturation, for example, the DC ratio of the second and third wavelengths. The motion analysis module 1552 can receive the same features as the pulse rate decision logic shown in FIG. 15E.

With continued reference to FIG. 15B, the sensor or module processor can determine the PI measurement based on the normalized signal of the third wavelength and the PI information in a perfusion index determination module 1510. The sensor or module processor can determine the PVI measurement based on the PVI information in a pleth variability index determination module 1512. The sensor or module processor can determine the RRp measurement based on the intensity signals of the first and second wavelength in a respiration rate determination module 1514. The sensor or module processor can determine the hydration index in a hydration determination module 1516 based on the intensity signals (for example, from the “far detectors” disclosed herein) of the fourth wavelength, which is more sensitive to changes in water in the measurement site and another wavelength (for example, the third wavelength or about 905 nm) that is less sensitive to changes in water. The sensor or module processor can focus on the DC component of the signals for hydration status monitoring.

Various example physiological parameter measurement modules and wearable devices incorporating the same will be described below. Each of the example modules and devices can incorporate any of the features of the physiological parameter measurement module 100 and the device 10 described above, all of which are not repeated for brevity. Features of the example modules and devices disclosed herein can be incorporated into one another.

Examples of Physiological Parameter Measurement Modules with Double Emitter Groups

FIG. 16A illustrates schematically an example arrangement of an optical sensor, including emitters, detectors, and thermistors, on a sensor or module processor PCB 116. As shown in FIG. 16A, the PCB 116 can include a first group of emitters 104a and a second group of emitters 104b. Each group of emitters can include four emitters. The emitters in each group 404a, 404b can emit at least the first, second, third, and fourth wavelengths as described above. The first and second groups of emitters 404a, 404b can be located a distance from each other on a first side of a PCB 116. The PCB 116 can include a temperature sensor (such as a thermistor) 110 as described above located on the first side of the PCB 416. One temperature sensor 110 can be near the first group of emitters 404a. Another temperature sensor 110 can be near the second group of emitters 404b.

The PCB 116 can be elliptical in shape, although the shape of the PCB is not limiting. The two groups of the emitters 104a, 104b can be located on different parts of the first side of the PCB 116 divided along the minor diameter of the ellipse. Each of the two groups of the emitters 104a, 104b can be surrounded by a first light barrier and form an emitter chamber.

The first and second groups of emitters 104a, 104b can be surrounded by two rings of detectors 106a, 106b that are separated from the first and second groups of emitters 104a, 104b respectively by a distance. The two rings of detectors 106a, 106b can share a plurality of (for example, two or more) detectors 106a/b common to both rings. The detectors 106a/b common to both rings can be located along the minor axis of the ellipse. In the illustrated example, the PCB 116 can include fourteen detectors coupled to the PCB 116, but the total number of detectors can vary.

The detectors 106b can be the far detectors for the first group of emitters 104a and the detectors 106a, 106a/b can be the near detectors for the first group of emitters 104a. The detectors 106a can be the far detectors for the second group of emitters 104b and the detectors 106b, 106a/b can be the near detectors for the second group of emitters 104b. Accordingly, each detector 106a, 106b, 106a/b can receive two signals for each wavelength emitted by the first and second groups of emitters 104a, 104b respectively. As described above, signals outputted by the far and near detectors can provide different information due to the different light paths, which can travel through different areas of the tissue. In addition, the far detectors for each group of emitters 104a, 104b can detect the light emitted by the respective group of emitters 104a, 104b, for example, light of the fourth wavelength and another wavelength, and attenuated by tissue to provide an indication of the wearer's hydration status as described herein.

The detectors 106a, 106b, 106a/b can be separated or partitioned into seven detector regions. Each detector region can include two detectors, or any other number of detectors. Each detector region can form a detector chamber surrounded by light barriers. As described above, the sensor or module processor can process signals from a particular emitter and received at the detectors within the same detector region as one signal source. Accordingly, for each wavelength, the sensor or module processor can receive data from a total of fourteen signal sources, two from each detector region acting as the far and near detectors for the different groups of emitters respectively.

FIGS. 16B-16D illustrate an example physiological parameter measurement module 400 of a wearable device. The module 400 can incorporate any of the features of the module examples described herein.

As shown in FIG. 16B, the physiological parameter measurement module 400 can include a first group of emitters 404a and a second group of emitters 404b incorporating the arrangement shown in FIG. 16A. Each group of emitters can include four emitters (or optionally a different number of emitters, such as six or eight emitters). The emitters in each group 404a, 404b can emit at least the first, second, third, and fourth wavelengths as described above. Each of the two groups of the emitters 404a, 404b can be surrounded by a first light barrier 420 and form an emitter chamber.

The first and second groups of emitters 404a, 404b in the module 400 can be surrounded by two rings of detectors 406a, 406b that are separated from the first and second groups of emitters 404a, 404b by the first light barrier 420. The two rings of detectors 406a, 406b can share a plurality of (for example, two or more) detectors 406a/b common to both rings. The detectors 406a, 406b, 406a/b can have the same arrangement as the detectors shown in FIG. 16A. In the illustrated example, the module 400 can include fourteen detectors, but the module 400 can also include a different total number of detectors.

As shown in FIGS. 16B and 16D, the detectors 406a, 406b, 406a/b can be separated or partitioned into seven detector chambers by a portion of the first light barrier 420 and second light barriers 422. Each detector region can include two detectors, or any other number of detectors. Along an outer perimeter of the module 400, the detectors 406a, 406b, 406a/b can be enclosed within a module side wall 424. A sensor or module processor of the module 400 can process signals from a particular emitter and received at the detectors within the same detector region as one signal source as described above. The arrangement of emitters 104a, 104b and detectors 106a, 106b, 106a/b and the light diffusing materials encapsulating the emitters 104a, 104b and/or detectors 106a, 106b, 106a/b can improve the sensing coverage on the wearer's wrist, which has fewer capillaries per volume than the fingertip as described above. The aggregate light detecting area of the 106a, 106b, 106a/b in FIG. 16B, that is, the aggregate surface area of all the detector chambers, can occupy about 50% or more of the tissue-facing surface of the physiological parameter measurement module. The aggregate light detecting area in FIG. 16B can be, for example, greater than about 100 mm², or greater than about 125 mm², or about 150 mm², or about 165 mm². The aggregate light emitting area in FIG. 16B, that is, the aggregate surface area of both emitters chambers, can be, for example, greater than about 25 mm², or about 30 mm², or about 35 mm². Any other physiological parameter measurement module examples disclosed herein can have the same or substantially similar aggregate light detecting area and/or light emitting area as the module 400 shown in FIG. 16B.

On the first side of the PCB 416, the module 400 can be enclosed by a curved light transmissive cover 402 with a convex protrusion. As shown in FIG. 16C, the cover 402 can have a continuous curvature. The first and second light barriers 420, 422 are configured to be in contact with the first side of the PCB 416 at one end. At the other end, the height of the first and second light barriers 420, 422, and of the side wall 424 can generally follow the curvature of the cover 402. The side wall 424 can be shorter than the second light barrier 422. The height of the second light barrier 422 can increase from the perimeter of the module 400 toward a center of the module 400 until the second light barrier 422 merges with the first light barrier 420, which is the highest among the light barriers. The light barriers 420, 422 can extend to the tissue-facing surface of the cover 402 so that when the module 400 is pressed into the skin of the wearer of a device incorporating the module 400, the tissue-facing surfaces of the first and second light barriers 420, 422, and of the side wall 424 can be configured to contact the skin of the wearer. The cover 402 can include individual lenses or covers such as shown in FIG. 7D or a combination of individual emitter chamber covering lenses or covers and a lens or cover covering a plurality of detector chambers, such as shown in FIG. 7C. The tissue-facing surface of the module 400 can include a continuous convex curvature.

The first and second light barriers 420, 422 and the side wall 424 can optionally form a single light barrier construct. The single light barrier construct can be formed by any suitable manufacturing techniques and any suitable materials, for example, plastic, colored, or opaque sapphire glass, or others. The single light barrier construct can include at one end a recess that is shaped and sized to receive the PCB 416, including the electronics on the PCB 416. The first side of the PCB 416 can include the emitters 404a, 404b, detectors 406a, 406b, 406a/b, temperature sensor 410, and any other sensors, for example, the gyroscope, the accelerometer, and/or the like. The second side of the PCB 416 can include the sensor or module processor and other circuit hardware.

As described above, the module 400 can include a plurality of chambers such that light cannot travel between the chambers because of the various light barriers extending from the PCB 416 to the tissue-facing surface of the cover 402 as described herein. The light diffusing materials described above can be added above (for example, via the fill holes described herein) and around the emitters 404a, 404b, and/or optionally above and around the detectors 406a, 406b, 406a/b, to improve distribution of emitted lighted and/or detected light after attenuation by the tissue. The light diffusing materials can include a flow of glass microsphere solution, which can be injected into the chambers after the module 400 has been assembled. After being injected into the respective chamber, the solution can be UV-cured. Air can escape via the vent openings disclosed herein as the diffusing material solution is injected into the respective chambers via the injection openings, making it easier for the glass microsphere solution to flow into the respective chamber. The cover 402 can also include glass microspheres. The light diffusing materials in the cover 402 and inside the emitter chambers and/or the first light barrier 420 can make the emitted light leave the emitter chambers enclosing the emitters 404a, 404b in a direction generally parallel to the height of the first light barrier 420. The light diffusing materials in the cover 402 and the detector chambers can increase the amount of reflected light being directed to and detected by the detectors 406a, 406b, 406a/b.

FIGS. 16E-16G illustrate an example physiological parameter measurement modules 401 of a wearable device. The module 401 can include the same optical sensor arrangements as shown in FIGS. 16A-16D and have any of the features of the module 400 in FIGS. 16B-16D with the differences noted in the description of FIGS. 16E-16G. The module 401 can have any of the features of the other physiological parameter measurement module examples described herein.

The module 401 can include a generally circular outer shape. The generally circular outer shape can be defined by an opaque frame 426 extending over of the PCB 416 from a first side of the PCB 416. The opaque frame 426 can have a height such that a top side of the opaque frame 426 can be generally level with (or receding or protruding slightly from) a second side of the PCB 416. As shown in FIG. 16G, the PCB 416 can be generally circular in shape. The opaque frame 426 can be generally concentric with the PCB 416. The opaque frame 426 and the PCB 416 are not transmissive to light. The opaque frame 426 in FIGS. 16E and 16F can include the first light barrier 420 and second light barriers 422 as an integral piece.

The module 401 can include one or more (for example, two or otherwise) ECG electrodes 424. In the illustrated examples of FIGS. 16E-16G, one of the ECG electrodes 424 can be a reference electrode and the other one of the ECG electrode 424 can be a negative or positive electrode. The opaque frame 426 can have indentations having the shape and size to accommodate the electrodes 424, similar to the indentations on the opaque frame 126 shown in FIG. 7D. As shown in FIG. 16F, a bottom surface of the electrodes 424 can have a curvature that is generally continuous with the curvature of the opaque frame 426 and the light-transmissive cover 402. As shown in FIG. 16G, a top side of the electrodes 424 can have one or more posts 437 extending past openings in the opaque frame 426 into corresponding openings on the PCB 416. The posts 437 of the electrodes 424 can establish an electrical connection with the corresponding openings of the PCB 416. A plurality of screws (or other types of fasteners) can extend into the corresponding openings of the PCB 416 from the front side of the PCB 416 to secure the electrodes 424 to the module 401 by threadedly mating with the posts. When a wearer puts the wearable device incorporating the module 401 onto the wearer's wrist, the electrodes 424 can make contact with the wearer's skin. The electrodes 424 can have the same polarity as the electrodes 124 disclosed herein. As disclosed herein, the wearable device incorporating the module 401 can include another ECG electrode 125 located on the housing of the wearable device configured to make contact with the wearer's skin.

On the second side of the PCB 416, which faces away from the cover 402, the PCB 416 can be covered by melt plastic or other suitable electronics protective material 430 (similar to the protective material 130 disclosed herein) except that a flex connector 432 can remain exposed. The flex connector 432 can be configured to connect the module 401 electrically to the wearable device incorporating the module 401.

FIGS. 17A-17C illustrate an example physiological parameter measurement modules 403 of a wearable device. The module 403 can include the same optical sensor arrangements as shown in FIGS. 16A-16G and have any of the features of the module 400 in FIGS. 16B-16D and any of the features of the module 401 in FIGS. 16E-16G with the differences noted in the description of FIGS. 17A-17C. The module 401 can have any of the features of the other physiological parameter measurement module examples described herein.

As shown in FIGS. 17A-17C, the opaque frame 426 can include an opening fitted with the light transmissive cover 402. The cover 402 extending over emitter chambers or detector chambers formed by the light barriers 420, 422, 423 and the PCB 415 can include a single lens or cover. The cover 402 can be elliptical in shape. The cover 402 can have a continuous convex curvature. As shown in FIG. 17C, the light barriers 420, 422, 423 may not extend to the tissue-facing surface of the cover 402 and can extend to below the cover 402 such that when a wearer puts on a wearable device incorporating the module 402, the wearer's tissue comes into contact with the cover 402 and the electrodes 424, but not with any of the light barriers 420, 422, 423.

FIGS. 18A-19C illustrate other non-limiting examples of a physiological parameter measurement module with two emitter groups in two separate emitter chambers formed by a light barrier. In those configurations, the perimeter of the module can have a different shape. For example, FIG. 19A illustrates schematically a module 300 having an outer shape of two circles partially overlapped with each other. The circle in the module 300 can have a radius, for example, between about 6 mm and about 12 mm, or between about 8 mm and about 10 mm. The module 300 can have any of the features of the other modules disclosed herein. The module 300 can include the substantially the same arrangement of emitters 300a, 300b and detectors 306a, 306b, 306a/b as the module 400, 401, 403 described above except that each emitter group 304a, 304b includes three emitters. The module 300 can include a thermistor near each emitter group 304a, 304b. The module 300 can have a length of, for example, between about 22 mm and about 28 mm, or between about 24 mm and about 26 mm.

FIG. 18B illustrates a physiological parameter measurement module 301 including a variation of the arrangement of emitters and detectors of the module 300 in FIG. 18A, and can include any of the features of the module 300 except for the differences described herein. The module 301 differs from the module 300 by not sharing detectors located between the two groups of emitters 304a, 304b. The first group of emitters 304a can be surrounded by a first ring of detectors 306a on a first side of the minor axis A2 and the second group of emitters 304b can be surrounded by a second ring of detectors 306b that are on a second side of the minor axis A2.

FIG. 19A illustrates a physiological parameter measurement module 201 including a variation of the arrangement of emitters and detectors of the module 300 in FIG. 18A. The physiological parameter measurement module 201 can have any of the features of the modules 300, with the differences noted in the description of FIG. 19A. The module 201 can have any of the features of the other modules disclosed herein. In the module 201, the two overlapping circles of detectors 206a, 206b are closer to each other than in the module 300. The detectors 206a/b can be further away from each other than in the module 300 and may not be located between or separating the two emitter groups 204a, 204b. The module 201 can include two groups of emitters that are separated from each other by one light barrier. Each of the detectors in the module 201 can form its own detector chamber with one or more light barriers. The circle can have a radius, for example, between about 6 mm and about 12 mm, or between about 8 mm and about 10 mm. The module 300 can have a length of, for example, between about 18 mm and about 24 mm, or between about 20 mm and about 22 mm.

FIGS. 19B and 19C illustrate a variation of the module 201 in FIG. 19A with the differences noted in the description of FIGS. 19B and 19C. The module 200 in FIGS. 19B and 19C can have any of the features of the module examples described herein. In FIGS. 19B and 19C, a physiological parameter measurement module 200 can include two groups of emitters 204a, 204b surrounded by one ring of detectors 206. The module 200 can have a width, for example, between about 16 mm and about 22 mm, or between about 18 mm and about 20 mm. The module 200 can have a length, for example, between about 20 mm and about 28 mm, or between about 22 mm and about 25 mm.

Each group of the emitters 204a, 204b can include three of emitters. Each group of the emitters 204a, 204b can emit at least the first, second, and third wavelength described above. Optionally, each emitter group 204a, 204b can include a fourth emitter configured to emit the fourth wavelength that is more sensitive to water. The emitters can be located at or near a center portion of a PCB 216 of the module 200. The module 200 can include a temperature sensor located on the PCB 216 near each group of the emitters 204a, 204b.

The emitters can be covered by an inner lens or cover 202a. In the illustrated example, the inner lens or cover 202a can be generally elliptical. In other examples, the inner lens or cover may have any other shapes. The two groups of the emitters 204a, 204b can be located on two parts of the central portion of the PCB divided along the minor diameter of the ellipse. The two groups of the emitters 204a, 204b can be divided by an opaque divider barrier 228, which can reduce mixing of light emitted by the two groups of the emitters 204a, 204b. As shown in FIG. 19C, the divider barrier 228 can have a same or substantially the same height as the highest point of the inner lens or cover 202a when assembled in the module 200. The inner lens or cover 202a can include two components divided by the divider barrier 228.

The module 200 can include a plurality of detectors 206 (for example, about six, eight, ten, or more) that can be arranged on the PCB so that the detectors 206 are spaced apart around the emitters 204a, 204b. The emitters groups 204a, 204b and the detectors 206 can be separated by a first light barrier 220. The first light barrier 220 can extend along and surround the inner lens or cover 202a. The divider barrier 228 and the first light barrier 220 can form two emitter chambers 234a, 234b, each enclosing one of the two emitter groups 204a, 204b. The first light barrier 220 and the divider barrier 228 can also suppress light emitted by the emitters 204a, 204b at an angle so the light emitted by each group of emitters 204a, 204b can exit the inner lens or cover 202a in a direction generally parallel to the height of the first light barrier 220. The detectors 206 can be enclosed within a module side wall 224. The module side wall 224 can define a perimeter of the module 200. As shown in FIG. 19B, the perimeter of the module 200 can have a generally elliptical outer shape. The detectors 206 can be further separated from one another by a plurality of divider barriers 226, forming detector chambers 236, each containing one detector 206.

As shown in FIG. 19C, the first light barrier 220 can protrude slightly from, that is, proud of the edge of the inner lens or cover 202a and the other lenses or covers that will be described below. The detectors 206 can be covered by an outer lens or cover 202b. The outer lens or cover 202b can be generally concentric with the inner lens or cover 202a. In the illustrated examples, the outer lens or cover 202b can be an elliptical disc as shown in FIG. 19B. In other examples such as those disclosed herein, the outer lens or cover can have other shapes. As shown in FIG. 19C, the outer lens or cover 202b can have a smaller curvature than the inner lens or cover 202a such that the inner lens or cover 202a protrudes more than if the inner lens or cover had the same curvature as the outer lens or cover 202b.

As shown in FIG. 19C, the side wall 224 can be shorter than the first light barrier 220. The height of the side wall 224 can be configured such that the tissue-facing end of the side wall 224 is generally continuous with the curvature of outer lenses or covers 202b. The divider barriers 226 can have a height lower than the first light barrier 220. The height of the divider barriers 226 can be configured to accommodate the outer lens or cover 202b such that when assembled, the outer lens or cover 202b forms a substantially smooth surface with the module side wall 224. The tissue-facing ends of the first light barrier 220 and the side wall 224, and the tissue-facing surfaces of the inner lens or cover 202a and the outer lens or cover 202b can form the tissue-facing surface of the module 200. The slightly protruding first light barrier 220 and/or inner lens or cover 202a can be pressed into the wearer's skin at a higher pressure than the remainder of the lens or cover or light barriers.

The light diffusing materials described above can be included in one or more of the chambers 234a, 234b, 236 of the module 200 to improve distribution of emitted lighted and/or detected light. As shown in FIG. 19B, one or more of the lenses or covers 202a, 202b can include an injection opening 244 so that the light diffusing materials, which can include a flow of glass microsphere solution, can be injected into the respective chambers 234a, 234b, 236 after the module 200 has been assembled. After the injection, the solution can be UV-cured. The lenses or covers 202a, 202b can include one or more venting openings that are smaller than the injection openings 244. Air can optionally escape via separate vent openings as the diffusing material solution is injected into the respective chambers 234a, 234b, 236 via the injection openings 244. The inner lens or cover 202a and the outer lens or cover 202b can also include glass microspheres so as to act as light diffusers.

Examples of Physiological Parameter Measurement Modules with Inner and Outer Detector Groups and Examples of Wearable Devices Incorporating the Same

FIGS. 20A-20D illustrate an example physiological parameter measurement module 600 of a wearable device. The module 600 can have any of the features of the module examples described herein, with the differences noted in the description of FIGS. 20A-20D. The physiological parameter measurement module 600 can include a single emitter group having a plurality of emitters 604, such as four emitters as shown in FIG. 20A, six emitters, or eight emitters. The emitters 604 of the module 600 can emit at least the first, second, third, and fourth wavelengths as described above. The emitters 604 can be located at or near a center portion of a PCB 616 of the module 600. The module 600 can include a temperature sensor 610 located on the PCB 616 near the emitters 604.

The module 600 can include a plurality of detectors 606 that can be arranged on the PCB 616 as an inner group of detectors 606 and an outer group of detectors 606. The inner group 606c of detectors 606, which can include, for example, about ten (or a different number of) detectors 606, can surround the emitters 604 and be spaced apart from one another.

The outer group of detectors 606 can be located further away from the emitters 604 than the inner group of detectors 606. The outer group of detectors 606 can be separated into a first outer group 606a and a second outer group 606b of detectors 606. As shown in FIG. 20A, the module 600 can have a first axis A1 and a second axis A2. The outer groups 606a, 606b of detectors 606 can be located further away from the emitters 204 than the inner group of detectors 606 generally along the first axis A1. The two outer groups 606a, 606b of detectors 606 are on opposite sides of the inner group of detectors along the first axis A1. The first and second outer groups 606a, 606b of detectors 606 can be generally symmetrical about the first axis A2 and the second axis A2. Each of the first or second outer groups 606a, 606b of detectors 606 can include about five (or a different number) of detectors 606 that are spaced apart from one another generally along the second axis A2. The outer groups 606a, 606b of detectors 606 can be arranged to be generally concentric with the inner group 606c of detectors 606.

The module 600 can be longer in the first axis A1 than in the second axis A2. The module 600 can have a dimension of about 25.4 mm (1 inch) along the first axis A1. The module can have a dimension of about 19.1 mm (0.75 inch) along the second axis A2. As shown in FIG. 20A, when a watch incorporating the module 600 is worn on the wrist of a wearer, the first axis A1 can be generally parallel to the width of the wrist and generally perpendicular to the direction of blood flow along the wrist (that is, along a direction between the hand and the forearm) and the second axis A2 can be generally perpendicular to the width of the wrist and generally parallel to the direction of blood flow along the wrist. The distribution of the detectors 606 along the first axis A1 can improve detection of the light attenuated by the pulsing arterial blood in the capillaries as the detectors 606 are arranged to cover a greater cross-section of the blood flow through the wrist. Similarly, in the other example modules described herein, such as the sensor or module 100, 400, 401, 403, 300, 301, 200, 201, the physiological parameter measurement module is incorporated in the wearable device such that the longer side of the module is generally perpendicular to the direction of the blood flow along the wrist (see, for example, FIG. 1B) when the wearable device is worn on the wrist.

As shown in FIG. 20A, the emitters 604 can be covered by an inner lens or cover 602a. In the illustrated example, the inner lens or cover 602a can be generally circular. In other examples such as disclosed herein, the inner lens or cover may not be generally circular, but can have other shapes, for example, elliptical, rectangular, square, diamond, or otherwise. The inner group 606c of detectors 606 can be covered by a first outer lens or cover 602b. The first outer lens or cover 602b can be generally concentric with the inner lens or cover 602a. In the illustrated example, the first outer lens or cover 602b can be disc shaped. The first and second outer groups 606a, 606b of detectors 606 can be covered by a second outer lens or cover 606c and a third outer lens or cover 606d respectively. The second and third outer lenses or covers 606c, 606d can be symmetrical about the second axis A2. As shown in FIG. 20B, the first, second, and third outer lenses or covers 602b, 602c, 602d can have substantially the same curvature. The inner lens or cover 602a can be more curved than the outer lenses or covers 602b, 602c, 602d such that the inner lens or cover 602a protrudes more than if the inner lens or cover 602a had same curvature as the outer lenses or covers 602b, 602c, 602d.

The inner group 606c of detectors 606 and the emitters 604 can be separate by a first light barrier 620. The first light barrier 620 can extend along and surround the inner lens or cover 602a, forming an emitter chamber. The first and second outer groups 606a, 606b of detectors 606 can be separated from the inner group 606c of detectors 606 by a second light barrier 622. The second light barrier 622 can be shorter than the first light barrier 620. The first and second outer groups 606a, 606b of detectors 606 can be enclosed within a module side wall 624 enclosing a perimeter of the module 600. The perimeter of the module 600 can be elliptical or any other shape. The side wall 624 can be shorter than the second light barrier 622. The height of the first and second light barriers 620, 622, and of the side wall 624 can generally follow or be substantially continuous with the curvature of the first, second, and third outer lenses or covers 602b, 602c, 602d. The first and second light barriers 620, 622, and of the side wall 624 can have a height so as to be configured to contact the skin of the wearer. Accordingly, the tissue-facing surface of the module 600 can be defined by the tissue-facing side of the first and second light barriers 620, 622, and of the side wall 624 and tissue-facing surfaces of the inner lens or cover 602a and the first, second, and third outer lenses or covers 602b, 602c, 602d.

In the illustrated example, the inner group 606c of detectors 606 can be separated by a third light barrier 626 and a fourth light barrier 628 (see FIGS. 20C and 20D). The third and fourth light barriers 626, 628 can have a height lower than the first light barrier 620 or the second light barrier 622. The height of the third and fourth light barriers 626, 628 can be configured to accommodate the first outer lens or cover 602b such that when assembled, the first outer lens or cover 602b forms a substantially smooth surface with the second and third outer lenses or covers 602c, 602d. The first outer lens or cover 602b can sit on top of the third and fourth light barriers 626, 628.

The first light barrier 620 can protrude slightly from, that is, sit proud of the edge of the inner lens or cover 602a and the outer lenses or covers 602b, 602c, 602d. The slightly protruding first light barrier 620 and/or inner lens or cover 602a can be pressed into the wearer's skin at a higher pressure than the remainder of the lenses or covers or light barriers. The first light barrier 620 can also reduce mixing of the emitted and reflected light and/or suppress light emitted by the emitters 604 at an angle so that the emitted light exits the inner lens or cover 602a generally in a direction parallel to the height of the first light barrier 620.

As shown in FIGS. 20C and 20D, the first, second, third, and fourth light barriers 620, 622, 626, 628 and the side wall 624 can optionally form a single light barrier construct 630. The single light barrier construct 630 can be formed by any suitable manufacturing techniques. The single light barrier construct 630 can include at one end a recess 632 (see FIG. 20C) that is configured to receive the PCB 616 (and the emitters 604, detectors 606, temperature sensor 610, and any other sensors, for example, the gyroscope, the accelerometer, and/or the like, and the sensor or module processor, which are located on the PCB 616). The single light barrier construct 630 can receive the lenses, including the inner lens or cover 602a, the first, second, and third outer lenses or covers 602b, 602c, 602d at another end that is opposite to the end including the recess 632.

The module housing can include a plurality of chambers such that light cannot travel between the chambers because of the various light barriers described herein. As described above, the first chamber can be enclosed by the inner lens or cover 602a, the first light battier 620, and a portion of the PCB 616. The first chamber 634 enclose the emitters 604. A second chamber and a third chamber can be enclosed by the first outer lens or cover 602b, the first light barrier 620, the second light barrier 622, the third light barrier 626, the fourth light barrier 628, and a portion of the PCB 616. The second and third chambers can enclose the inner group 606c of detectors 606, with half of the inner group 606c of detectors enclosed by each of the second and third chambers. A fourth chamber can be closed by the second outer lens or cover 602c, the second light barrier 622, the side wall 624, and part of the PCB 616. A fifth chamber can be enclosed by the third outer lens or cover 602d, the second light barrier 622, the side wall 624, and part of the PCB 616. The fourth and fifth chambers can enclose the first and second outer groups 606a, 606b of detectors 606 respectively.

Light from the emitters 604 can travel a shorter path to the inner group 606c of detectors 606 and a longer path to the first and second outer groups 606a, 606b of detectors 606. The inner group 606c of detectors 606 and the first and second outer groups 606a, 606b of detectors 606 can be run independently and/or simultaneously. Signals outputted by the inner and outer groups 606a, 606b of detectors 606 can provide different information due to the different light paths, which can travel through different areas of the tissue. The longer path penetrates deeper into the tissue and through a greater volume of the tissue to reach one of the outer groups 606a, 606b of detectors 606 than the short path, which penetrates less deep into the tissue and travels through a smaller volume of tissue to reach one of the inner group 606c of detectors 606. The different information can be separated and/or combined to calculate a plurality of physiological parameters of the wearer of the module 600, for example, an indication of the wearer's hydration status, which will be described in greater detail below.

The light diffusing materials described above can be included in one or more chambers of the module 600 to improve distribution of emitted lighted and/or detected light after attenuation by the tissue. As shown in FIG. 20A, one or more of the lenses or covers 602a, 602b, 602c, 602d can include an injection opening 644 so that the light diffusing materials, which can include a flow of glass microsphere solution, can be injected into the respective chambers after the module 600 has been assembled. After being injected into the respective chamber, the solution can be UV-cured. The lenses or covers 602a, 602b, 602c, 602d can include one or more venting openings 645 that are smaller than the injection openings 644. Each of the lenses or covers can include at least one venting opening 645. Air can escape via the vent openings 645 as the diffusing material solution is injected into the respective chambers via the injection openings 644, making it easier for the glass microsphere solution to flow into the respective chamber. The inner lens or cover 602a and/or the outer lenses or covers 602b, 602c, 602d can also include glass microspheres. The light diffusing materials in the inner lens or cover 602a and the UV-cured material in the first chamber 634 and/or the first light barrier 620 can make the emitted light leave the first chamber 634 in a direction generally parallel to the height of the first light barrier 620. The light diffusing materials in the outer lenses or covers 602b, 602c, 602d and the UV-cured material in the other chambers 636, 638, 640, 642 can increase the amount of reflected light being directed to the detectors 606.

The module 600 shown in FIGS. 20A-20D can be incorporated in a wearable device disclosed herein, such as a watch 900 shown in FIGS. 20E-20J. The watch processor 914 and power source can be enclosed within the watching housing 901. The watch housing 901 can include a connection port opening 950 configured to allow access to a connection port 952 that is in electrical communication with the watch processor 914 and/or the power source. The connection port opening 950 can be located at one end of the watch housing 901 transverse to the first axis A1 of the module 600. The connection port 952 can allow for charging of the power source and/or data transfer to and from the watch processor 914. Optionally, as shown in FIGS. 20F and 20I, the watch 900 can include a cable connector 945 extending outward from the watch housing 901. The cable connector 945 can be located adjacent to or near the connection port opening 950.

The watch 900 can include a display screen 912 positioned at a first side of the watch housing 901. The watch housing 901 has a second side that is opposite the first side. The second side of the watch housing 901 can include an opening sized to retain the physiological parameter measurement module 600 while still allowing the tissue-facing surface of the module 600 to be exposed. The second side of the watch housing 901 can be removably attached to the first side of the watch housing 901 without using external fasteners or alternatively via one or more fasteners. An electrical connection can be established between the physiological parameter measurement module PCB and the watch circuit, for example, using a flex connector as disclosed herein.

The watch housing 901 can include strap coupling extensions 948 on opposing sides of the watch 900 along the length of the housing 901 (that is, along the first axis A1 of the module 600). The extensions 948 can include a bar 946 for coupling to any suitable watch straps.

FIGS. 21A-21C and 22A-22C illustrate alternative lens or cover curvatures of the physiological parameter measurement module 600 of FIGS. 20A-20D and can incorporate any of the features of the module 600 of FIGS. 20A-20D except the differences described below. As shown in FIGS. 21A-21C, the first outer lens or cover 602b of the module 601 can be more convex (that is, protrude more) than the inner lens or cover 602a the second and third outer lenses or covers 602c, 602d. The curvatures of the tissue-facing side of the second light barrier 622 and of the side wall 624 can be substantially continuous with the curvature of the second and third outer lenses or covers 602c, 602d. The second light barrier 622 can be shorter than the first light barrier 620. The first light barrier 620 can be higher than an outer edge of the inner lens or cover 602a, which can facilitate separation of light emitted by the emitters 604 and light being detected by the detectors 606 before the light is attenuated by the wearer's body tissue. In the FIGS. 22A-22C, the module 603 can be different from the module 601 in FIGS. 21A-21C in that the inner lens or cover 602a can have the same height as the first light barrier 620 and the first outer lens or cover 602b. The inner lens or cover 602a can have a generally flat surface or a slight curvature that can be substantially continuous from the curvature of the first outer lens or cover 602b. The module 601, 603 in FIGS. 21A-22C can facilitate pressing the first outer lens or cover 602b or the first outer lens or cover 602b and the inner lens or cover 602a into the skin of the wearer more than the remainder of the tissue-facing surface of the module 600.

FIGS. 23A-23E illustrate a watch 700 that can incorporate the physiological parameter measurement module 600. The watch 700 can have any of the features of the watch 900 with the differences noted in the description of FIGS. 23A-23E. As shown in FIGS. 23A-23E, the watch housing 701 of the watch 700 can include a flap 750 on a side of the housing 701 along a length of the watch housing 701, which is along the first axis A1 of the physiological parameter measurement module (see FIG. 23E). The flap 750 can be opened to give access to a connection port (such as the connection port in the watch 900) in electrical communication with the watch processor 714 and/or the power source 716. The connection port can allow for charging of the power source 716 and/or data transfer to and from the watch processor 714. The flap 750 can be closed when the connection port 752 is not in use.

The watch 700 can include a display screen positioned at a first side of the watch housing 701. The watch housing 701 has a second side that is opposite the first side. The second side of the watch housing 701 can include an opening sized to retain the physiological parameter measurement module 600 while still allowing the tissue-facing surface of the module 600 to be exposed. The second side of the watch housing 701 can be removably attached to the first side of the watch housing 701 via one or more screws 718 or other fasteners. When fully assembled, the watch 700 can have a thickness or height, for example, between 10 mm to about 15 mm, or between 12 mm to about 14 mm.

The watch housing 701 can include suitable strap connections configured to couple to watch strap(s). The strap connections in the watch housing 701 can be different from the strap connections shown in the watch 900. In an example, a plurality of strap openings can be at opposite ends of the watch and the watch housing can additionally and/or alternatively include strap slots on the same opposite ends of the watch as the strap openings. In this example, the strap slots can be configured to slidably receive ends of watch straps that include a shape corresponding to the shape of the strap slots. The strap openings can be configured to receive spring-biased buttons near the ends of the watch straps to releasably retain the straps after the ends of the watch straps are received into the strap slots. Alternatively, the watch may not include strap openings. The strap(s) coupled to the watch examples disclosed herein can be configured to allow adjusting of tightness around the wearer's wrist, for example, using a buckle connector, a Velcro connector, and/or the like.

Hydration Monitoring by Wearable Devices Incorporating Examples Physiological Parameter Measurement Modules with “Near” and “Far” Detectors or Detector Groups

The physiological parameter measurement module examples disclosed herein can monitor a hydration status of the wearer. This is because water in the body tissue can allow a greater portion of the light of the third (or first or second) wavelength disclosed herein to go through (that is, acting as a light pipe), but can bulk absorb the light of the fourth wavelength disclosed herein. The physiological parameter measurement processor can compare intensity signals of the fourth wavelength and another wavelength that is less sensitive to changes in water from the same detector(s). When the wearer's hydration status is in a normal range such that the wearer is not considered dehydrated in a medical sense, the signals of the fourth wavelength and the other wavelength can show opposite trends, that is, one is increasing when the other one is decreasing. When the wearer becomes dehydrated in a medical sense, the opposite trends can become less distinct, for example, by falling below a threshold.

Hydration monitoring can be performed when the physiological parameter measurement module, such as the sensor or module 100, is configured such that at least some of the detectors 106 are located further away (far detector) from one of the emitters 104 (or emitter groups than the other detectors 106 (near detector), such as illustrated in FIG. 10. In configurations where there are two emitter groups, each detector 106 or detector region (which can include more than one detector 106 placed enclosed in the same detector chamber) can act as a near (or shallow) detector or detector region for the group of emitters that are closer to that detector 106 or detector region and as a far (or deeper) detector or detector region for the group of emitters that are further away from that detector 106 or detector region.

The physiological parameter measurement module 400, 401, 403 illustrates an example configuration for hydration monitoring of the wearer. The detectors 406a can be the far detectors for the second group of emitters 404b and the detectors 406b, 406a/b can be the near detectors for the second group of emitters 404b. The detectors 406b can be the far detectors for the first group of emitters 404a and the detectors 406a, 406a/b can be the near detectors for the first group of emitters 404a. The physiological parameter measurement modules 300, 301 illustrate similar detector arrangements in configurations (except that in the module 301, there are no shared detectors between the two groups of emitters 304a, 304b) where the modules 300, 301 include a fourth emitter in at least one of the emitter groups configured to emit light of the four wavelength.

The physiological parameter measurement modules 200, 201 illustrate additional example detectors configurations that can include “near” detectors for one emitter group and “far” detectors for another emitter group, in configurations where the modules 200, 201 include a fourth emitter configured to emit light of the fourth wavelength. For example, the detectors 206 on the far side of each group of emitters 204a, 204b can act as “far” detectors for detecting the light emitted by the respective group of emitters 204a, 204b, for example, light of the fourth wavelength and another wavelength, and attenuated by tissue to provide an indication of the wearer's hydration status

The physiological parameter measurement module 600 illustrates an example configuration for hydration monitoring of the wearer, with the inner group 606c of detectors 606 acting as the “near” detectors and the outer groups 606a, 606b of the detectors acting as the “far” detectors.

In the above-described configurations, each detector or detector region can provide two measurements calculated from the signals received from the closer emitter group and the signals from the further emitter group respectively. Signals detected at the far detectors can provide indication of the hydration status of the wearer as light travels through a deeper portion of the tissue of the wearer to reach the far detectors than to reach the near detectors). Signals detected at the near detectors can optionally be used as reference or for comparison with the signals detected at the far detectors when the physiological parameter measurement sensor or module processor determines the wearer's hydration status. The sensor or module processor of the physiological parameter measurement module disclosed herein can compare intensity signals of the fourth wavelength and another wavelength (for example, the third wavelength or about 905 nm) that is less sensitive to changes in water from one of the “far” detectors. The module processor can focus on the DC component, or the DC bulk absorption measurement of the signals detected by the “far” detectors for hydration status monitoring. At the DC level, water can act as a light block (that is, less transmissive of light) for the fourth wavelength and as a lens or cover (that is, more transmissive of light) for the other wavelength.

Additionally and/or alternatively, any of the modules disclosed herein can monitor the wearer's hydration status by monitoring the wearer's PVI values. The module can determine a baseline PVI value of the wearer, and can output a notification that the wearer is dehydrated or hydrated based on fluctuations in the PVI value from the baseline.

The module can further combine the hydration status monitoring by the optical detectors and other sensors (such as a sweat sensor or a skin impedance sensors) in outputting a final hydration status indication of the wearer. The module can calculate an average, a weight average or otherwise of raw hydration index values calculated based on signals from the different sensors, and/or rely on the different hydration monitoring sensors for redundancy.

As a person's hydration status is not expected to change rapidly, the physiological parameter measurement module can optionally make a measurement of the hydration status less frequently than making measurements related to the wearer's pulse rate or SpO2 or other parameters. For example, the physiological parameter measurement sensor or module processor can make a measurement of hydration status every 5 minutes, or longer, and/or upon (for example, only upon) a request by the wearer, such as when the wearer presses a button (a physical button and/or a touch button on the display) on the device or otherwise instructs the device using voice commands, hand gestures, and/or the like.

Examples of Generally Circular Physiological Parameter Measurement Modules and Examples of Wearable Devices Incorporating the Same

A physiological parameter measurement module can alternatively include an inner portion of emitters and an outer ring of detectors as shown in FIGS. 24A-24B and FIGS. 25A-25B. The sensor or module 1000 in FIGS. 24A-24B and the module 1100 in FIGS. 25A-25B can have any of the features of the module examples described herein, with the differences noted in the description of FIGS. 24A-24B and 25A-25B. Such a physiological parameter measurement module can have a generally circular outer shape. The sensor or module 1000 in FIGS. 24A-24B can be smaller than the module 1100 in FIGS. 25A-25B. For example, the sensor or module 1000 can have an outer diameter between about 12 mm and about 16 mm, or between about 14 mm and about 15 mm. For example, the module 1100 can have an outer diameter between about 16 mm and about 22 mm, or between about 18 mm and about 20 mm.

The physiological parameter measurement module 1000, 1100 can each include a single emitter group having a plurality of emitters 1004, 1104, such as three emitters. The emitters 1004, 1104 of the sensor or module 1000, 1100 can emit at least the first, second, and third wavelengths as described above. The emitters 1004, 1104 can be located at or near a center portion of a PCB of the sensor or module 1000, 1100. The sensor or module 1000, 1100 can include a temperature sensor located on the PCB near the emitters 1004, 1104.

The sensor or module 1000, 1100 can include a plurality of detectors 1006, 1106 (for example, about six, eight, or more) that can be arranged on the PCB so that the detectors 1006, 1106 are spaced apart around the emitters 1004, 1006. The emitters 1004, 1104 and the detectors 1006, 1106 can be separated by a first light barrier 1020, 1120. The first light barrier 1020, 1120 can surround the emitters 1004, 1104. The first light barrier 1020, 1120 can also suppress light emitted by the emitters 1004, 1104 at an angle so that the emitted light exits the inner lens or cover 1002a, 1102a in a direction generally parallel to the height of the first light barrier 1020, 1120.

The emitters 1004, 1104 can be covered by an inner lens or cover 1002a, 1102a. In the illustrated example, the inner lens or cover 1002a, 1102a can be generally circular. The detectors 1006, 1106 can be covered by an outer lens or cover 1002b, 1102b. The outer lens or cover 1002b, 1102b can be generally concentric with the inner lens or cover 1002a, 1102a. In the illustrated examples, the outer lens or cover 1002b, 1102b can be a disc when viewed directly above from the sensor or module 1000, 1100. In other examples such as those disclosed herein, the outer lens or cover can have other shapes, for example, being elliptical or otherwise. The outer lens or cover 1002b, 1102b can have a smaller curvature than the inner lens or cover 1002a, 1102a such that the inner lens or cover 1002a, 1102a protrudes more than if the inner lens or cover had the same curvature as the outer lens or cover 1002b, 1102b. As shown in FIGS. 24B and 25B, the first light barrier 1020, 1120 can protrude slightly from, that is, proud of the outer edge of the inner lens or cover 1002a, 1102a. The slightly protruding first light barrier 1020, 1120 and/or inner lens or cover 1002a, 1102a can be pressed into the wearer's skin at a higher pressure than the remainder of the light barriers or lenses or covers of the sensor or module 1000, 1100.

The detectors 1006, 1106 can be enclosed within a module side wall 1024, 1124 that defines a perimeter of the sensor or module 1000, 1100. The perimeter can be generally circular or of any other shape. The side wall 1024, 1124 can be shorter than the first light barrier 1020, 1120. The height of the side wall 1024, 1124 can be such that the tissue-facing end of the side wall 1024, 1124 is generally continuous with the curvature of outer lenses or covers 1002b, 1102b. In the illustrated example, the detectors 1006, 1106 can be separated from one another by a plurality of generally opaque divider barriers 1026, 1126. The divider barriers 1026, 1126 can have a height lower than the first light barrier 1020, 1120. The height of the divider barriers 1026, 1126 can be configured to accommodate the outer lens or cover 1002b, 1102b such that when assembled, the outer lens or cover 1002b, 1102b forms a substantially smooth surface with the module side wall 1024, 1124. The outer lens or cover 1002b, 1102b can sit on top of the divider barriers 1026, 1126. The tissue-facing end of the first light barrier 1020, 1120 and the side wall 1024, 1124, and the tissue-facing surfaces of the inner lens or cover 1002a, 1102a and the outer lens or cover 1002b, 1102b can be configured to contact the skin of the wearer and form the tissue-facing surface of the sensor or module 1000, 1100.

The first light barrier 1020, 1120, the side wall 1024, 1124, and the divider barriers 1026, 1126 can optionally form a single light barrier construct. The single light barrier construct can receive the PCB of the sensor or module 1000, 1100, and the emitters 1004, 1104, detectors 1006, 1106, temperature sensor, and any other sensors, for example, the gyroscope, the accelerometer, and/or the like, and the sensor or module processor that are located on the PCB. The single light barrier construct can receive the lenses, including the inner lens or cover 1002a, 1102a and the outer lens or cover 1002b, 1102b on another end that is opposite the end receiving the PCB. As shown in FIGS. 25A and 25B, the light barrier construct of the module 1100 or the PCB can additionally include a plurality of (for example, four or otherwise) extension prongs 1152. The plurality of extension prongs 1152 can be generally equally spaced around the side wall 1124.

The sensor or module 1000, 1100 can include a plurality of chambers such that light cannot travel between the chambers because of the various light barriers described herein. A first chamber 1034, 1134 can be enclosed by the inner lens or cover 1002a, 1102a, the first light battier 1020, 1120, and a portion of the PCB. The first chamber 1034, 1134 can enclose the emitters 1004, 1104. A plurality of second chambers 1036, 1136 can be enclosed by the outer lens or cover 1002b, 1102b, the first light barrier 1020, 1120, the divider barriers 1026, 1126, the side wall 1024, 1124, and part of the PCB. Each of the second chambers 1036, 1136 can enclose one detector 1006, 1106.

The light diffusing materials described above can be included in one or more of the chambers 1034, 1134, 1036, 1136 of the module housing to improve distribution of emitted lighted and/or detected light. The inner lens or cover 1002a, 1102a and the outer lens or cover 1002b, 1102b can also include glass microspheres as described above.

The watch 1200 in FIGS. 25C-25H is illustrated as incorporating the module 1100 shown in FIGS. 25A-25B. However, any of the example watches disclosed herein can incorporate the physiological parameter measurement module 1000, 1100 shown in FIGS. 24A-24B or FIGS. 25A-25B. The watch 1200 can have any of the features of the wearable devices disclosed herein, such as the watch 700, 900, all of which are not repeated for brevity. The watch processor 1214 and power source can be enclosed within the watching housing 1201. The watch housing 1201 can include a connection port opening 1250 configured to allow access to a connection port 1252 in electrical communication with the watch processor 1214 and/or the power source. The opening 1250 can be on one side of the watch 1200 perpendicular to the first axis A1 of the module 1100, closer to the strap coupling mechanisms. The connection port 1252 can allow for charging of the power source and/or data transfer to and from the watch processor 1214. Optionally, as shown in FIGS. 25D, 25F, and 25H, the watch 1200 can include a cable connector 845 extending outward from the watch housing 1201. The cable connector 1245 can be located adjacent to or near the connection port opening 1250.

The watch 1200 can include a display screen 1212 positioned at a first side of the watch housing 1201. The watch housing 1201 has a second side that is opposite the first side. The second side of the watch housing 1201 can include an opening sized to retain the physiological parameter measurement module 1100 while still allowing the tissue-facing surface of the module 1100 to be exposed. The extension prongs 1152 of the module 1100 can be received into corresponding structures, for example, recesses, on the second side of the watch housing 1201, which can prevent rotation of the module 1100 when being installed in the watch 1200. The second side of the watch housing 1201 can be removably attached to the first side of the watch housing 1201 without using external fasteners or via one or more fasteners as described above. An electrical connection can be established between the physiological parameter measurement module circuit and the watch circuit. Optionally, the electrical connection can include a flex circuit.

The watch housing 1201 can include strap coupling extensions 1248 on opposite sides of the watch 1200 along the first axis A1 of the module 1100. The extensions 1248 can include a bar 1246 for coupling to any suitable watch straps.

Example Second Sensor Connection on Physiological Parameter Measurement Modules for Preventing Opioid Overdose

The physiological parameter measurement module examples disclosed herein can include an optional connector 118 (see FIG. 7A) for receiving a second sensor, which can be a plethysmograph sensor or other suitable sensors. The connector 118 can be oriented such that the second sensor can extend from a housing of the device 10 with reduced or no impingement of the tissue at the device/tissue interface, resulting in less or no effect of the connection of a second sensor to the connector 118 on the blood flow through the device measurement site. The second plethysmograph sensor can include any suitable plethysmograph sensors, for example, a fingertip sensor configured to monitor opioid overdose as described in U.S. Pub. No. 20190374173, the entirety of which is incorporated herein by reference and should be considered part of the disclosure. FIG. 1C illustrates a non-limiting example of the second sensor 119 that is a fingertip sensor. The second sensor 119 can extend from a wearable device as shown in FIG. 1C or any of the wearable device examples disclosed herein.

Alternative to the connection to a wearable device as shown in FIG. 1C, the connector from the watch disclosed herein can extend from an opening on a tissue-facing side of the device housing, for example, on a raised platform 703, 903 (FIGS. 20I and 23A). The connector can be coupled to the PCB 616 via a cable, which can optionally have a length configured to extend around the raised platform 703, 903, for example, in a groove of the raised platform 703, 903, or otherwise. Having the cable extending around the raised platform 703, 903 can allow adjustment of the slack of the cable when the connector connects to the second sensor. Having the connector extending from an opening on the raised platform 703, 903 can also avoid the connector and/or the cable impinging on the tissue at the watch/tissue interface as described above. The connector can alternatively be located at other suitable locations on the watch 700, 900.

The second plethysmograph sensor can have a higher measurements accuracy than the physiological parameter measurement module disclosed herein. The wearer can disconnect and/or deactivate the second sensor while the wearer is awake and/or moving about. The wearer can connect and activate the second sensor, for example, when going to sleep or resting. The sensor or module processor can ignore signals from the detectors of the module when the second sensor is activated so that the sensor or module processor can output physiological parameters based on the readings from the second sensor. Alternatively, the sensor or module processor can output physiological parameters based on a combination of the readings from the second sensor and the detectors of the module. The wearer can have the flexibility of choosing to use the physiological parameter measurement module and/or the second sensor, depending on the wearer's need.

The second plethysmograph sensor can aid in detection of opioid overdose in a wearer who uses opioid (for example, for medical reasons), in particular, by detecting low saturation of oxygen in the blood of the wearer. Depressed breathing is the most dangerous side effect of opioid overdose. Lack of oxygen to the brain can not only result in permanent neurologic damage, but may also be accompanied by the widespread failure of other organ systems, including the heart and kidneys. If a person experiencing an opioid overdose is left alone and asleep, the person could easily die as the respiratory depression worsens. The second plethysmograph sensor can be configured to detect depressed breathing by detecting decreased oxygen saturation in the blood of the wearer. The wearable device can be configured to automatically notify a first responder and/or the wearer's family or guardian in response to detecting opioid overdose of the wearer.

Optionally, the device processor of the wearable device can be in communication (for example, via Bluetooth or NFC communication, or via the network) with a processor of a drug delivery apparatus that is wearable by the wearer and configured to deliver one or more doses of a therapeutic drug, such as opioid. The drug delivery apparatus can include a delivery device that includes a dose of a therapeutic drug stored in a reservoir, a drug delivery channel, a dispensing device to dispense the therapeutic drug from the reservoir through the drug delivery channel, and activation circuitry to activate the dispensing device. The processor of the drug delivery apparatus can receive the parameters measured by the second plethysmograph sensor of the wearable device disclosed herein. The processor of the drug delivery apparatus can store memory-storing instructions and be configured to execute the instructions to at least compare the received parameters from the wearable device to a threshold that is indicative of opioid overdose. The processor of the drug delivery apparatus can determine whether an overdose event is occurring or likely to occur based on the comparison and send at least one activation signal to the drug delivery apparatus to dispense at least one dose of the therapeutic drug based on the determination.

Alternatively, the sensor or module processor of the physiological parameter measurement module can perform the comparison of the parameters measured by the second plethysmograph sensor to the predetermined opioid overdose threshold. Optionally, a microneedle patch may be used for providing a medication that can counteract opioid overdose. The wearer can apply the microneedle patch containing the medication to the skin when the wearable device outputs an alert that the wearer's physiological parameters (for example, SpO2) has exceeded a threshold (which may be indicative of opioid overdose).

Alternatively or additionally, the second sensor can be any other suitable noninvasive sensor disclosed herein. Alternatively or additionally, the physiological parameter measurement module examples disclosed herein can connect to a second sensor via wireless connection, for example, using Bluetooth technology. The module can receive measured parameters from the connected second sensor and/or process the sensor data received from the second sensor to calculate additional physiological parameters.

Example Microneedle Patch

In addition and/or alternative to delivering medication to prevent opioid overdose as described herein, a microneedles patch can be used for other purposes in combination with the wearable device. Microneedles have been used in recent years as a painless alternative to hypodermic needles to deliver drugs to the body. Microneedles on a patch can be placed on an arm or leg, or other parts of the body, which then create small holes in the skin's outermost layer, allowing the drugs coated on each needle to diffuse into the body. Microneedles can be made from silicon, metals, synthetic polymers, or natural, biodegradable materials such as silk and chitin.

Because of the small size, microneedles are minimally invasive and cause less pain compared to larger needles (for example, hypodermic needles). Additionally, the microneedle patch are easier to apply by the wearer than a hypothermal needle. In comparison, larger needles may require correct injection depth and injection angle to ensure that the drugs are injected at a right location.

FIG. 26A illustrates schematically a microneedle 3100 of a microneedle patch that has penetrated the tissue surface 2 of the wearer. Depending on its height, the microneedle 3100 may have varying injection depths. For example, the microneedle 3100 may puncture just the epidermis (including the stratum corneum, which is the outer layer of the epidermis) 42. In other examples, the microneedle 102 may puncture the epidermis 42 and dermis 44, with a tip of the microneedle 3102 terminating in the dermis 44. In other examples such as shown in FIG. 26A, the microneedle 3100 may puncture the epidermis 42 and dermis 44, with the tip 3102 end in the subcutaneous tissues 46.

Depending on the use, the microneedles 3100 with different heights may be used for delivery of medication and/or irrigation fluid 3104 into different parts of the wearer's tissue. The microneedles 3100 can be used to deliver a broad range of drugs, biotherapeutics, and vaccines. The microneedles 3100 can be hollow with internal reservoirs to store and deliver drugs or irrigation fluid 3104. Alternatively, the microneedles 3100 can be solid and coated with drugs 3104, and optionally other surfactant/thickening agents. Optionally, the microneedle 3100 can be dissolvable and encapsulate the drug in a nontoxic polymer that can dissolve once inside the skin.

Alternatively or additionally, the microneedles 3100 can be used to extract a tissue fluid sample 3104 (for example, the interstitial fluid of the wearer) for detection and/or analysis of analytes in the sample 3104. Optionally, the microneedle 3100 can irrigate the tissue of the wearer with a fluid before extracting the fluid (which, for example, may have equilibrated with the chemical composition of the wearer's bodily fluid sample) back into the microneedles 3100. The microneedles 3100 can be hollow and can extract a fluid sample via surface tension. The analyte detection and/or analysis can provide information such as the hydration status, glucose concentration, hemoglobin concentration, and/or orthogonal information about the fluid. The analyte detection and/or analysis can provide additional information related to, for example, sodium, potassium, glucose, chloride, bicarbonate, blood urea nitrogen, magnesium, creatinine, LDL cholesterol, HDL cholesterol, triglyceride, pH, and the like.

A microneedle patch may be located under one of the straps or the body of the wearable device, or be applied remotely (anywhere else on the wearer's body) from the wearable device without contacting the device. A plurality of microneedle patches can be applied to the wearer at different locations on the wearer's body. As shown in FIGS. 26B and 26C, the microneedles 3100 may be connected to a patch body 3106, forming a microneedle patch 3108. The patch body 3106 may be circular, oval, rectangular, square, triangular, tear-drop shaped, or of any other shape. The size of the patch body 3106 is not limiting. A surface of the patch body 3106 that is not connected to the microneedles 3100 can include an adhesive layer for releasably attach the patch 3108 to the wearable device. The adhesive layer may be covered by a back layer, which can be peeled off before applying the patch 3108 to the wearable device.

As shown in FIG. 26B, the microneedle patch 3108 can be placed on the body of the device 10. The patch 3108 can be applied under the skin-facing surface of the physiological parameter measurement sensor or module 100. The microneedles 3100 of the microneedle patch 3108 can face the skin of the wearer of the device 10 when the device 10 is worn. Accordingly, when the device 10 is worn, for example, on the wrist of the wearer with the straps wrapped around the wearer's wrist, the microneedles 3100 can puncture the skin on the wrist.

Additionally or alternatively, the microneedle patch 3108 may be integrated or releasably secured to an inner side of the adjustable strap 30 of the wearable device 10, such as shown in FIG. 26C. The microneedles 3100 can be pointing toward the skin around the wrist of the wearer when the device 10 is worn. When the strap 30 is wrapped around the wrist of the wearer, the microneedle patch 3108 may come in contact with the skin around the wrist of the wearer and the microneedles 3100 can penetrate the skin of the wearer.

As shown in FIG. 26D, the microneedle patch 3108 can communicate with the wearable device 10, using the wearable device 10 as a platform or hub to detect and/or analyze analytes in the fluid sample collected in the microneedles patch 3108. The patch 3108 can optionally include a sensor 3110, for example, an electrochemical sensor (with electrodes built into the microneedles), a colorimetric sensor, or otherwise. Alternatively, the patch 3108 can be brought to an external sensor for analyte detection and analysis. The patch 3108 can include an antenna 3112, which may be an NFC antenna or otherwise. The sensor 3100 can output a signal via the antenna 3112. The wearable device can receive the signal from the sensor 3100 via the antenna 19. The device processor 14 (or optionally the sensor or module processor of the physiological parameter measurement sensor or module on the device 10) can process the signal from the sensor 3100 to determine the presence and/or concentration of certain analyte(s) in the fluid sample.

Examples Device Tightness Monitoring Systems and Methods

A desired tightness and/or pressure of the device on the body can be indicated by the skin interfacing with the wearable device moving with the device when the device is moved. If there is insufficient tightness and/or pressure of the device on the body of the wearer, ambient light entering the device-skin interface can result in noises in the signals detected by the detectors, and therefore inaccurate measurements made by the device. If the device is worn too tight (and/or the pressure exerted by the device on the body is too high), blood pulsation and circulation at the wrist can be restricted, which can lead to a decrease in oxygen saturation readings of the wearer of the device. Optionally, the device can output a warning that the device is worn too tight (which can include a message displayed on the device to the wearer to loosen the straps) when the device has determined that the wearer's oxygen saturation readings are decreasing by a certain percentage, at a certain rate, and/or at a certain rate within a predetermined amount of time.

The device 10 can include an optional strain gauge 20 (see FIG. 7A) to measure a pressure of the device 10 on the wearer. The strain gauge 20 can be located in a device housing 101 between the physiological parameter measurement module 100 and other components of the device 10, for example, the power source 16, the device processor 14, or otherwise. For example, the strain gauge 20 can be flanged between the physiological parameter measurement module 100 and the device processor 14. When the device 10 is worn on the wearer, for example, on the wrist, the pressure exerted by the module, particularly by the convex protrusion of the cover 102 against the tissue can be transmitted to and measured by the strain gauge 20. The strain gauge 20 can also be incorporated in the other wearable device examples disclosed herein.

Readings from the strain gauge 20 can be communicated to the device processor 14, which can process the readings and output an indication of the pressure asserted by the device 10 on the wearer to be displayed on the display 12. The indication can be in a variety of suitable forms, for example, using different colors to indicate whether the pressure is too low, appropriate, or too high for obtaining accurate or reliable measurements using the physiological parameter measurement module 100. In one example, the device 10 can display a green light when the pressure on the wearer is suitable for using the physiological parameter measurement module 100 and display a red or other colored light for a pressure that is too high or too low than the desired pressure or pressure range. The physiological parameter measurement module 100 may not be activated unless the readings from the strain gauge 20 indicate that the desired pressure or pressure range has been achieved. Optionally, the device processor can also deactivate the physiological parameter measurement module 100, and/or any other sensors on or attached to the device 10, in response to not detecting any readings from the strain gauge 20, indicating that the device 10 is not worn on the wearer. Automatically turning on and/or off the sensors on or attached to the device 10 can reduce power consumption and increase battery life of the device 10.

Optionally, the wearable device 10 can include a motor to adjust tightness of the straps based on a monitored tightness of the straps and/or pressure exerted by the sensor or module 100 on the wearer's skin.

Example Additional Features of the Wearable Device

The wearable device examples disclosed herein can provide protection of the wearer's safety by sending an alert to a first responder (for example, a hospital emergency room, a firefighter, 911, security at the facility where the wearer is located, or otherwise) and/or the wearer's family or guardian when the wearer is in danger, for example, when the wearer is drowning. The wearable device can include a swim mode, which the wearer can activate when going swimming. The physiological parameter measurement module of the wearable device can monitor one or more parameters to determine that the wearer is likely drowning (such as drowning of a child in water), for example, by determining that the wearer's respiratory rate has become irregular (such as showing fluctuations greater than a predetermined number per minute), or the wearer's SpO2 value declines by a predetermined amount, or otherwise. Alternatively, the module processor can determine that wearer is likely drowning based on the gyroscope and/or accelerometer readings, which can further be combined with the parameters monitored by the other sensors. In response to determining that the wearer is likely drowning, the module can send a notification to the processor of the wearable device, which can send an alert to a first responder and/or the wearer's family or guardian. Additionally or alternatively, the wearable device can include a distress button that the wearer can push in an emergency, such as when the wearer is drowning, has sustained a fall (which can alternatively or additionally be determined using the gyroscope and/or accelerometer readings, which can further be combined with the parameters monitored by the other sensors) while being alone, or otherwise.

The physiological parameters (for example but not limited to, SpO2, PR, PI, PVI, RR, Hydration, ECG-related parameters, etc.) measured by the module disclosed herein can be reliable enough for healthcare or medical purposes, for example, in hospitals. The module can be configured to take measurements at the same time every day. The wearable device (or the physiological parameter measurement module of the device) can further include a hospital patient ID tag on a near-field communication (NFC) or Bluetooth chip, or a watch strap or band. Essential patient information, such as the patient's name, admission date, reason for admission, blood type, drug allergies, etc. can be stored on the memory device of the watch or the physiological parameter measurement module. The patient ID tag cannot be easily removed and/or may include special tools like theft prevention devices, for example, requiring the patient to cut the watch strap off. Alternatively, the wearable device can display the patient information (for example, name, admission date, etc.) on the screen when the patient is admitted to the hospital. The patient ID tag can be either disposable after the patient is discharged or reusable after disinfection. The physiological parameter measurement module can be removed and replaced when the patient ID tag (for example, the watch band) is changed. If the wearable device is worn by a caregiver, the caregiver can use the wearable device for communications with other caregivers (for example, to share critical, real-time information about patients, update changes in patient status, and/or the like), replacing the need for specialized communication tools, for example, Vocera®, Spok®, etc.

Terminology

Many other variations than those described herein will be apparent from this disclosure. For example, certain acts, events, or functions of any of the algorithms described herein can be performed in a different sequence, can be added, merged, or left out altogether (for example, not all described acts or events are necessary for the practice of the algorithms). Moreover, acts or events can be performed concurrently, for example, through multi-threaded processing, interrupt processing, or multiple processors or processor cores or on other parallel architectures, rather than sequentially. In addition, different tasks or processes can be performed by different machines and/or computing systems that can function together.

It is to be understood that not necessarily all such advantages can be achieved in accordance with any particular example of the examples disclosed herein. Thus, the examples disclosed herein can be embodied or carried out in a manner that achieves or optimizes one advantage or group of advantages as taught herein without necessarily achieving other advantages as may be taught or suggested herein.

The various illustrative logical blocks, modules, and algorithm steps described in connection with the examples disclosed herein can be implemented as electronic hardware, computer software, or combinations of both. To clearly illustrate this interchangeability of hardware and software, various illustrative components, blocks, modules, and steps have been described above generally in terms of their functionality. Whether such functionality is implemented as hardware or software depends upon the particular application and design constraints imposed on the overall system. The described functionality can be implemented in varying ways for each particular application, but such implementation decisions should not be interpreted as causing a departure from the scope of the disclosure.

The various illustrative logical blocks and modules described in connection with the examples disclosed herein can be implemented or performed by a machine, such as a general purpose processor, a digital signal processor (DSP), an application specific integrated circuit (ASIC), a field programmable gate array (FPGA) or other programmable logic device, discrete gate or transistor logic, discrete hardware components, or any combination thereof designed to perform the functions described herein. A general purpose processor can be a microprocessor, but in the alternative, the processor can be a controller, microcontroller, or state machine, combinations of the same, or the like. A processor can include electrical circuitry or digital logic circuitry configured to process computer-executable instructions. In another example, a processor can include an FPGA or other programmable device that performs logic operations without processing computer-executable instructions. A processor can also be implemented as a combination of computing devices, for example, a combination of a DSP and a microprocessor, a plurality of microprocessors, one or more microprocessors in conjunction with a DSP core, or any other such configuration. A computing environment can include any type of computer system, including, but not limited to, a computer system based on a microprocessor, a mainframe computer, a digital signal processor, a portable computing device, a device controller, or a computational engine within an appliance, to name a few.

The steps of a method, process, or algorithm described in connection with the examples disclosed herein can be embodied directly in hardware, in a software module stored in one or more memory devices and executed by one or more processors, or in a combination of the two. A software module can reside in RAM memory, flash memory, ROM memory, EPROM memory, EEPROM memory, registers, hard disk, a removable disk, a CD-ROM, or any other form of non-transitory computer-readable storage medium, media, or physical computer storage known in the art. An example storage medium can be coupled to the processor such that the processor can read information from, and write information to, the storage medium. In the alternative, the storage medium can be integral to the processor. The storage medium can be volatile or nonvolatile. The processor and the storage medium can reside in an ASIC.

Conditional language used herein, such as, among others, “can,” “might,” “may,” “for example,” and the like, unless specifically stated otherwise, or otherwise understood within the context as used, is generally intended to convey that certain examples include, while other examples do not include, certain features, elements and/or states. Thus, such conditional language is not generally intended to imply that features, elements and/or states are in any way required for one or more examples or that one or more examples necessarily include logic for deciding, with or without author input or prompting, whether these features, elements and/or states are included or are to be performed in any particular example. The terms “comprising,” “including,” “having,” and the like are synonymous and are used inclusively, in an open-ended fashion, and do not exclude additional elements, features, acts, operations, and so forth. Also, the term “or” is used in its inclusive sense (and not in its exclusive sense) so that when used, for example, to connect a list of elements, the term “or” means one, some, or all of the elements in the list. Further, the term “each,” as used herein, in addition to having its ordinary meaning, can mean any subset of a set of elements to which the term “each” is applied.

Disjunctive language such as the phrase “at least one of X, Y, or Z,” unless specifically stated otherwise, is otherwise understood with the context as used in general to present that an item, term, etc., may be either X, Y, or Z, or any combination thereof (for example, X, Y, and/or Z). Thus, such disjunctive language is not generally intended to, and should not, imply that certain examples require at least one of X, at least one of Y, or at least one of Z to each be present.

Unless otherwise explicitly stated, articles such as “a” or “an” should generally be interpreted to include one or more described items. Accordingly, phrases such as “a device configured to” are intended to include one or more recited devices. Such one or more recited devices can also be collectively configured to carry out the stated recitations. For example, “a processor configured to carry out recitations A, B and C” can include a first processor configured to carry out recitation A working in conjunction with a second processor configured to carry out recitations B and C.

While the above detailed description has shown, described, and pointed out novel features as applied to various examples, it will be understood that various omissions, substitutions, and changes in the form and details of the devices or algorithms illustrated can be made without departing from the spirit of the disclosure. As will be recognized, the inventions described herein can be embodied within a form that does not provide all of the features and benefits set forth herein, as some features can be used or practiced separately from others.

Additionally, all publications, patents, and patent applications mentioned in this specification are herein incorporated by reference to the same extent as if each individual publication, patent, or patent application was specifically and individually indicated to be incorporated by reference.

Claims

1. An optical physiological sensor integrated into a watch configured to monitor health of a wearer, the optical physiological sensor configured to face a tissue of the wearer when the watch is worn by the wearer, the optical physiological sensor configured to measure physiological parameters of the wearer using information from the optical physiological sensor, the optical physiological sensor comprising: a first emitter grouping comprising a first plurality of light emitting diodes (LEDs);a second emitter grouping comprising a second plurality of LEDs, wherein the second emitter grouping comprises a same number and type of LEDs as the first emitter grouping, and wherein the first emitter grouping and the second emitter grouping are adjacent to each other;one or more light blocks separating the first emitter grouping from the second emitter grouping;light diffusing material configured to diffuse light emitted by each of the first and second pluralities of LEDs;a plurality of detectors including four or more photodiodes; anda surface configured to be positioned between (i) the tissue of the wearer and (ii) all of the first and second emitter groupings and the four or more photodiodes, the surface comprising one or more surface materials.
2. The optical physiological sensor of claim 1, wherein the one or more surface materials comprise at least a portion of the one or more light blocks and a light transmission material.
3. The optical physiological sensor of claim 1, wherein the LEDs in the first or second emitter grouping are not electrically connected to one another.
4. The optical physiological sensor of claim 1, wherein the first or second emitter grouping defines a group of emitters located in close proximity.
5. The optical physiological sensor of claim 1, wherein the plurality of detectors are individually both a near detector and far detector for each of the first emitter grouping and the second emitter grouping.
6. The optical physiological sensor of claim 1, wherein the first and second emitter groupings are located at non-central locations of a printed circuit board (PCB) of the optical physiological sensor.
7. The optical physiological sensor of claim 1, wherein the one or more light blocks extend from a surface of the optical physiological sensor positioning the first and second pluralities of LEDs and past the first and second pluralities of LEDs towards the tissue of the wearer when the watch is worn.
8. The optical physiological sensor of claim 1, wherein each of the first or second emitter grouping is surrounded by its own diffusing material.
9. The optical physiological sensor of claim 1, wherein at least some of the plurality of detectors extend around a circumference of the optical physiological sensor.
10. The optical physiological sensor of claim 9, wherein the plurality of detectors are positioned in a grid pattern and/or across from one another.
11. The sensor optical physiological of claim 9, wherein locations of the first and second emitter groupings are interleaved with the plurality of detectors.
12. A watch comprising the optical physiological sensor of claim 1, further comprising a processor configured to determine an oxygen saturation measurement based on signals from the optical physiological sensor.
13. The watch of claim 12, further comprising one or more of an ECG sensor; one or more temperature sensors; or an accelerometer.
14. The watch of claim 12, further comprising a display screen to display one or both of the oxygen saturation measurement or a heart rate measurement.
15. The optical physiological sensor of claim 1, further comprising light diffusing material positioned around each of the plurality of detectors.
16. The optical physiological sensor of claim 1, wherein the surface is a convex surface.
17. An optical physiological sensor integrated into a watch configured to monitor health of a wearer, the optical physiological sensor configured to face a tissue of the wearer when the watch is worn by the wearer, the optical physiological sensor configured to measure physiological parameters of the wearer using information from the optical physiological sensor, the optical physiological sensor comprising: a first emitter grouping comprising a first plurality of light emitting diodes (LEDs) at a first location;a second emitter grouping comprising a second plurality of LEDs at a second location different from the first location, wherein the second emitter grouping comprises a same number and type of LEDs as the first emitter grouping;one or more light blocks separating the first emitter grouping from the second emitter grouping;a plurality of detectors including four or more photodiodes;light diffusing material positioned between the plurality of detectors and the tissue of the wearer; anda surface configured to be positioned between (i) the tissue of the wearer and (ii) all of the first and second emitter groupings and the four or more photodiodes, the surface comprising one or more surface materials.
18. The optical physiological sensor of claim 17, wherein the first location is adjacent to the second location.
19. The optical physiological sensor of claim 17, wherein the one or more surface materials comprise at least a portion of the one or more light blocks and a light transmission material.
20. The optical physiological sensor of claim 17, wherein the one or more light blocks extend from a surface of the optical physiological sensor positioning the first and second pluralities of LEDs and past the first and second pluralities of LEDs towards the tissue of the wearer when the watch is worn.
21. The optical physiological sensor of claim 17, wherein the plurality of detectors are individually both a near detector and far detector for each of the first emitter grouping and the second emitter grouping.
22. The optical physiological sensor of claim 17, wherein at least some of the plurality of detectors extend around a circumference of the optical physiological sensor.
23. The optical physiological sensor of claim 17, wherein each of the first or second emitter grouping is surrounded by its own diffusing material.
24. The optical physiological sensor of claim 17, wherein the surface is a convex surface.

INCORPORATION BY REFERENCE TO ANY PRIORITY APPLICATIONS

The present application claims priority benefit under 35 U.S.C. § 119(e) to U.S. Provisional Application No. 62/960,610, filed Jan. 13, 2020, U.S. Provisional Application No. 62/984,243, filed Mar. 2, 2020, and U.S. Provisional Application No. 63/023,156, filed May 11, 2020, the entirety of each of which is hereby incorporated by reference. Any and all applications for which a foreign or domestic priority claim is identified in the Application Data Sheet as filed with the present application are hereby incorporated by reference under 37 CFR 1.57.

US Referenced Citations (1438)

Number	Name	Date	Kind
3452215	Alessio	Jun 1969	A
3514538	Chadwick et al.	May 1970	A
3638640	Shaw	Feb 1972	A
3704706	Herczfeld et al.	Dec 1972	A
3760582	Thiess et al.	Sep 1973	A
3769974	Smart et al.	Nov 1973	A
3789601	Bergey	Feb 1974	A
3910701	Henderson et al.	Oct 1975	A
4015595	Benjamin	Apr 1977	A
4063551	Sweeny	Dec 1977	A
4086916	Freeman et al.	May 1978	A
4120294	Wolfe	Oct 1978	A
4129124	Thalmann	Dec 1978	A
4163447	Orr	Aug 1979	A
4216462	McGrath et al.	Aug 1980	A
4224948	Cramer et al.	Sep 1980	A
4248244	Charnitski et al.	Feb 1981	A
4295472	Adams	Oct 1981	A
4375219	Schmid	Mar 1983	A
4409470	Shepard et al.	Oct 1983	A
4414980	Mott	Nov 1983	A
4447150	Heinemann	May 1984	A
4448199	Schmid	May 1984	A
4541439	Hon	Sep 1985	A
4547075	Fei	Oct 1985	A
4606352	Geddes et al.	Aug 1986	A
4635646	Gilles et al.	Jan 1987	A
4648892	Kittrell et al.	Mar 1987	A
4700708	New, Jr. et al.	Oct 1987	A
4759369	Taylor	Jul 1988	A
4802486	Goodman et al.	Feb 1989	A
4859057	Taylor et al.	Aug 1989	A
4865038	Rich et al.	Sep 1989	A
4867557	Takatani et al.	Sep 1989	A
4869253	Craig, Jr. et al.	Sep 1989	A
4890619	Hatschek	Jan 1990	A
4892101	Cheung et al.	Jan 1990	A
4903701	Moore et al.	Feb 1990	A
4928692	Goodman et al.	May 1990	A
4933545	Saaski et al.	Jun 1990	A
4938218	Goodman et al.	Jul 1990	A
4941236	Sherman et al.	Jul 1990	A
4945239	Wist et al.	Jul 1990	A
4955379	Hall	Sep 1990	A
4960128	Gordon et al.	Oct 1990	A
4960314	Smith et al.	Oct 1990	A
4964408	Hink et al.	Oct 1990	A
5007423	Branstetter et al.	Apr 1991	A
5025791	Niwa	Jun 1991	A
5069680	Grandjean	Dec 1991	A
5099842	Mannheimer et al.	Mar 1992	A
5137364	Mccarthy	Aug 1992	A
5158082	Jones	Oct 1992	A
5158091	Butterfield et al.	Oct 1992	A
5176137	Erickson et al.	Jan 1993	A
5184620	Cudahy et al.	Feb 1993	A
5190038	Polson et al.	Mar 1993	A
5191891	Righter	Mar 1993	A
5203329	Takatani et al.	Apr 1993	A
5209230	Swedlow et al.	May 1993	A
5218962	Mannheimer et al.	Jun 1993	A
5228449	Christ et al.	Jul 1993	A
5251011	Fujiwara et al.	Oct 1993	A
5254388	Melby et al.	Oct 1993	A
5254992	Keen et al.	Oct 1993	A
5259381	Cheung et al.	Nov 1993	A
5299570	Hatschek	Apr 1994	A
5316008	Suga et al.	May 1994	A
5319355	Russek	Jun 1994	A
5334916	Noguchi	Aug 1994	A
5337744	Branigan	Aug 1994	A
5341805	Stavridi et al.	Aug 1994	A
5351695	Mills et al.	Oct 1994	A
5365924	Erdman	Nov 1994	A
D353195	Savage et al.	Dec 1994	S
D353196	Savage et al.	Dec 1994	S
5372135	Mendelson et al.	Dec 1994	A
5377676	Vari et al.	Jan 1995	A
5413100	Barthelemy et al.	May 1995	A
D359546	Savage et al.	Jun 1995	S
5431170	Mathews	Jul 1995	A
5436499	Namavar et al.	Jul 1995	A
D361840	Savage et al.	Aug 1995	S
D362063	Savage et al.	Sep 1995	S
D363120	Savage et al.	Oct 1995	S
5456252	Vari et al.	Oct 1995	A
5462051	Oka et al.	Oct 1995	A
5477853	Farkas et al.	Dec 1995	A
5479934	Imran	Jan 1996	A
5482036	Diab et al.	Jan 1996	A
5490505	Diab et al.	Feb 1996	A
5490523	Issacson et al.	Feb 1996	A
5494043	O'Sullivan et al.	Feb 1996	A
5497771	Rosenheimer	Mar 1996	A
5533511	Kaspari et al.	Jul 1996	A
5542146	Hoekstra et al.	Aug 1996	A
5555882	Richardson et al.	Sep 1996	A
5561275	Savage et al.	Oct 1996	A
5562002	Lalin	Oct 1996	A
5564429	Bornn et al.	Oct 1996	A
5581069	Shepard et al.	Dec 1996	A
5584296	Cui et al.	Dec 1996	A
5590649	Caro et al.	Jan 1997	A
5601079	Wong et al.	Feb 1997	A
5602924	Durand et al.	Feb 1997	A
5623925	Swenson et al.	Apr 1997	A
5623926	Weiss	Apr 1997	A
5632272	Diab et al.	May 1997	A
5635700	Fazekas	Jun 1997	A
5638816	Kiani-Azarbayjany et al.	Jun 1997	A
5638818	Diab et al.	Jun 1997	A
5645440	Tobler et al.	Jul 1997	A
5671914	Kalkhoran et al.	Sep 1997	A
5673692	Shulze et al.	Oct 1997	A
5699808	John	Dec 1997	A
5702429	King	Dec 1997	A
5719557	Rattman et al.	Feb 1998	A
5720284	Aoyagi et al.	Feb 1998	A
5726440	Kalkhoran et al.	Mar 1998	A
5729203	Oka et al.	Mar 1998	A
D393830	Tobler et al.	Apr 1998	S
5738104	Lo et al.	Apr 1998	A
5743262	Lepper, Jr. et al.	Apr 1998	A
5746697	Swedlow et al.	May 1998	A
5747806	Khalil et al.	May 1998	A
5750994	Schlager	May 1998	A
5758644	Diab et al.	Jun 1998	A
5760910	Lepper, Jr. et al.	Jun 1998	A
5782756	Mannheimer	Jul 1998	A
5782757	Diab et al.	Jul 1998	A
5792052	Isaacson et al.	Aug 1998	A
5797841	Delonzor et al.	Aug 1998	A
5800348	Kaestle	Sep 1998	A
5800349	Isaacson et al.	Sep 1998	A
5817008	Rafert et al.	Oct 1998	A
5830137	Scharf	Nov 1998	A
5838451	Mccarthy	Nov 1998	A
5854706	Alb	Dec 1998	A
5860932	Goto et al.	Jan 1999	A
5890929	Mills et al.	Apr 1999	A
5893364	Haar et al.	Apr 1999	A
5911689	Smith et al.	Jun 1999	A
5916155	Levinson et al.	Jun 1999	A
5919134	Diab	Jul 1999	A
5923021	Dvorkis et al.	Jul 1999	A
5924979	Swedlow et al.	Jul 1999	A
5936986	Cantatore et al.	Aug 1999	A
5952084	Anderson et al.	Sep 1999	A
5963333	Walowit et al.	Oct 1999	A
5983122	Jarman et al.	Nov 1999	A
5987343	Kinast	Nov 1999	A
5991467	Kamiko	Nov 1999	A
5997343	Mills et al.	Dec 1999	A
6002952	Diab et al.	Dec 1999	A
6010937	Karam et al.	Jan 2000	A
6014576	Raley	Jan 2000	A
6018403	Shirakura et al.	Jan 2000	A
6022321	Amano et al.	Feb 2000	A
6027452	Flaherty et al.	Feb 2000	A
6035223	Baker	Mar 2000	A
6040578	Malin et al.	Mar 2000	A
6041247	Weckstrom et al.	Mar 2000	A
6058331	King	May 2000	A
6066204	Haven	May 2000	A
6069653	Hudson	May 2000	A
6070092	Kazama et al.	May 2000	A
6075755	Zarchan	Jun 2000	A
6083156	Lisiccki	Jul 2000	A
6088607	Diab et al.	Jul 2000	A
6091530	Duckworth	Jul 2000	A
6102856	Groff et al.	Aug 2000	A
6115673	Malin et al.	Sep 2000	A
6124597	Shehada et al.	Sep 2000	A
6126595	Amano et al.	Oct 2000	A
6128521	Marro et al.	Oct 2000	A
6129675	Jay	Oct 2000	A
6133871	Krasner	Oct 2000	A
6144868	Parker	Nov 2000	A
6152754	Gerhardt et al.	Nov 2000	A
6158245	Savant	Dec 2000	A
6167303	Thompson	Dec 2000	A
6178343	Bindszus et al.	Jan 2001	B1
6184521	Coffin, IV et al.	Feb 2001	B1
6185454	Thompson	Feb 2001	B1
6198951	Kosuda et al.	Mar 2001	B1
6212210	Serizawa	Apr 2001	B1
6223063	Chaiken et al.	Apr 2001	B1
6226539	Potratz	May 2001	B1
6232609	Snyder et al.	May 2001	B1
6241680	Miwa	Jun 2001	B1
6241683	Macklem et al.	Jun 2001	B1
6253097	Aronow et al.	Jun 2001	B1
6255708	Sudharsanan et al.	Jul 2001	B1
6265789	Honda et al.	Jul 2001	B1
6270223	Del Bon et al.	Aug 2001	B1
6278889	Robinson	Aug 2001	B1
6280381	Malin et al.	Aug 2001	B1
6285896	Tobler et al.	Sep 2001	B1
6293915	Amano et al.	Sep 2001	B1
6297906	Allen et al.	Oct 2001	B1
6308089	von der Ruhr et al.	Oct 2001	B1
6317627	Ennen et al.	Nov 2001	B1
6321100	Parker	Nov 2001	B1
6330468	Scharf	Dec 2001	B1
6331063	Kamada et al.	Dec 2001	B1
6334065	Al-Ali et al.	Dec 2001	B1
6343223	Chin et al.	Jan 2002	B1
6351217	Kuhn	Feb 2002	B1
6356203	Halleck et al.	Mar 2002	B1
6356774	Bernstein et al.	Mar 2002	B1
6360114	Diab et al.	Mar 2002	B1
6368283	Xu et al.	Apr 2002	B1
6393311	Edgar et al.	May 2002	B1
6396873	Goldstein et al.	May 2002	B1
6398727	Bui et al.	Jun 2002	B1
6402690	Rhee et al.	Jun 2002	B1
6411373	Garside et al.	Jun 2002	B1
6415166	Van Hoy et al.	Jul 2002	B1
6415167	Blank et al.	Jul 2002	B1
6430423	Delonzor et al.	Aug 2002	B2
6430437	Marro	Aug 2002	B1
6430525	Weber et al.	Aug 2002	B1
6463311	Diab	Oct 2002	B1
6470199	Kopotic et al.	Oct 2002	B1
6473008	Kelly et al.	Oct 2002	B2
6483976	Shie et al.	Nov 2002	B2
6487429	Hockersmith et al.	Nov 2002	B2
6505059	Kollias et al.	Jan 2003	B1
6505061	Larson	Jan 2003	B2
6522915	Ceballos et al.	Feb 2003	B1
6525386	Mills et al.	Feb 2003	B1
6526300	Kiani et al.	Feb 2003	B1
6527711	Stivoric et al.	Mar 2003	B1
6527729	Turcott	Mar 2003	B1
6529754	Kondo	Mar 2003	B2
6534012	Hazen et al.	Mar 2003	B1
6542764	Al-Ali et al.	Apr 2003	B1
6553242	Sarussi	Apr 2003	B1
6556852	Schulz et al.	Apr 2003	B1
6560352	Rowe et al.	May 2003	B2
6580086	Schulz et al.	Jun 2003	B1
6584336	Ali et al.	Jun 2003	B1
6587196	Stippick et al.	Jul 2003	B1
6587199	Luu	Jul 2003	B1
6595316	Cybulski et al.	Jul 2003	B2
6596016	Vreman et al.	Jul 2003	B1
6597932	Tian et al.	Jul 2003	B2
6605045	Ohsaki et al.	Aug 2003	B2
6606511	Ali et al.	Aug 2003	B1
6608562	Kimura et al.	Aug 2003	B1
6635559	Greenwald et al.	Oct 2003	B2
6639668	Trepagnier	Oct 2003	B1
6640116	Diab	Oct 2003	B2
6640117	Makarewicz et al.	Oct 2003	B2
6650917	Diab et al.	Nov 2003	B2
6654624	Diab et al.	Nov 2003	B2
6658276	Kiani et al.	Dec 2003	B2
6661161	Lanzo et al.	Dec 2003	B1
6671526	Aoyagi et al.	Dec 2003	B1
6697656	Al-Ali	Feb 2004	B1
6697658	Al-Ali	Feb 2004	B2
RE38476	Diab et al.	Mar 2004	E
6699194	Diab et al.	Mar 2004	B1
6707476	Hochstedler	Mar 2004	B1
6714803	Mortz	Mar 2004	B1
RE38492	Diab et al.	Apr 2004	E
6738652	Mattu et al.	May 2004	B2
6760607	Al-Ali	Jul 2004	B2
6775566	Nissilä	Aug 2004	B2
6785568	Chance	Aug 2004	B2
6788965	Ruchti et al.	Sep 2004	B2
6801798	Geddes et al.	Oct 2004	B2
6801799	Mendelson	Oct 2004	B2
6815694	Sfez et al.	Nov 2004	B2
6816241	Grubisic	Nov 2004	B2
6822564	Al-Ali	Nov 2004	B2
6831266	Paritsky et al.	Dec 2004	B2
6843771	Lo et al.	Jan 2005	B2
6847836	Sujdak	Jan 2005	B1
6922241	Kramer	Jan 2005	B2
6850787	Weber et al.	Feb 2005	B2
6850788	Al-Ali	Feb 2005	B2
6853304	Reisman	Feb 2005	B2
6871089	Korzinov et al.	Mar 2005	B2
6876931	Lorenz et al.	Apr 2005	B2
6889153	Dietiker	May 2005	B2
6920345	Al-Ali et al.	Jul 2005	B2
6934570	Kiani et al.	Aug 2005	B2
6943348	Coffin, IV	Sep 2005	B1
6956649	Acosta et al.	Oct 2005	B2
6961598	Diab	Nov 2005	B2
6970792	Diab	Nov 2005	B1
6982930	Hung	Jan 2006	B1
6985764	Mason et al.	Jan 2006	B2
6990364	Ruchti et al.	Jan 2006	B2
6998247	Monfre et al.	Feb 2006	B2
6999685	Kawase et al.	Feb 2006	B1
7003338	Weber et al.	Feb 2006	B2
7008380	Rees et al.	Mar 2006	B1
7015451	Dalke et al.	Mar 2006	B2
7018338	Vetter et al.	Mar 2006	B2
7019338	Ballon	Mar 2006	B1
7027849	Al-Ali	Apr 2006	B2
7031728	Beyer, Jr.	Apr 2006	B2
7035736	Nissila	Apr 2006	B2
7060963	Maegawa et al.	Jun 2006	B2
7072700	Yamamoto et al.	Jul 2006	B2
D526719	Richie, Jr. et al.	Aug 2006	S
7088040	Ducharme et al.	Aug 2006	B1
7092735	Osann, Jr.	Aug 2006	B2
7096052	Mason et al.	Aug 2006	B2
7096054	Abdul-Hafiz et al.	Aug 2006	B2
7107706	Bailey, Sr. et al.	Sep 2006	B1
D529616	Deros et al.	Oct 2006	S
7130672	Pewzner et al.	Oct 2006	B2
7133710	Acosta et al.	Nov 2006	B2
7142901	Kiani et al.	Nov 2006	B2
7155273	Taylor	Dec 2006	B2
7171251	Sarussi et al.	Jan 2007	B2
7190986	Hannula et al.	Mar 2007	B1
7225006	Al-Ali et al.	May 2007	B2
RE39672	Shehada et al.	Jun 2007	E
7227156	Colvin, Jr. et al.	Jun 2007	B2
7251513	Kondoh et al.	Jul 2007	B2
7252385	Engle et al.	Aug 2007	B2
7254429	Schurman et al.	Aug 2007	B2
7254431	Al-Ali et al.	Aug 2007	B2
7254434	Schulz et al.	Aug 2007	B2
7261690	Teller et al.	Aug 2007	B2
7274955	Kiani et al.	Sep 2007	B2
D554263	Al-Ali et al.	Oct 2007	S
7280858	Al-Ali et al.	Oct 2007	B2
7285090	Stivoric et al.	Oct 2007	B2
7289835	Mansfield et al.	Oct 2007	B2
7292883	De Felice et al.	Nov 2007	B2
7315632	Spycher et al.	Jan 2008	B2
7341559	Schulz et al.	Mar 2008	B2
7341560	Henderson et al.	Mar 2008	B2
7343186	Lamego et al.	Mar 2008	B2
D566282	Al-Ali et al.	Apr 2008	S
7355284	Negley	Apr 2008	B2
7356365	Schurman	Apr 2008	B2
7371981	Abdul-Hafiz	May 2008	B2
7372778	Klopfenstein et al.	May 2008	B2
7373193	Al-Ali et al.	May 2008	B2
7377794	Al-Ali et al.	May 2008	B2
7378647	Nishikawa et al.	May 2008	B2
7383105	Conroy, Jr.	Jun 2008	B2
7385874	Vuilleumier et al.	Jun 2008	B2
7395104	Mouradian et al.	Jul 2008	B2
7395158	Monfre et al.	Jul 2008	B2
7399277	Saidara et al.	Jul 2008	B2
7415297	Al-Ali et al.	Aug 2008	B2
7415298	Casciani et al.	Aug 2008	B2
7438683	Al-Ali et al.	Oct 2008	B2
7455423	Takenaka	Nov 2008	B2
7483729	Al-Ali et al.	Jan 2009	B2
D587657	Al-Ali et al.	Mar 2009	S
7500950	Al-Ali et al.	Mar 2009	B2
7502643	Farringdon et al.	Mar 2009	B2
7509494	Al-Ali	Mar 2009	B2
7510849	Schurman et al.	Mar 2009	B2
7514725	Wojtczuk et al.	Apr 2009	B2
7519327	White	Apr 2009	B2
7519406	Blank et al.	Apr 2009	B2
D592507	Wachman et al.	May 2009	S
7530942	Diab	May 2009	B1
7558622	Tran	Jul 2009	B2
7572508	Lutz et al.	Aug 2009	B2
7593230	Abul-Haj et al.	Sep 2009	B2
7596398	Al-Ali et al.	Sep 2009	B2
7601123	Tweed et al.	Oct 2009	B2
7606608	Blank et al.	Oct 2009	B2
7613490	Sarussi et al.	Nov 2009	B2
7613504	Rowe	Nov 2009	B2
7620212	Allen et al.	Nov 2009	B1
7620674	Ruchti et al.	Nov 2009	B2
D606659	Kiani et al.	Dec 2009	S
7629039	Eckerbom et al.	Dec 2009	B2
7640140	Ruchti et al.	Dec 2009	B2
D608225	Giroud	Jan 2010	S
7647083	Al-Ali et al.	Jan 2010	B2
D609193	Al-Ali et al.	Feb 2010	S
7656393	King et al.	Feb 2010	B2
7658613	Griffin et al.	Feb 2010	B1
7676253	Raridan, Jr.	Mar 2010	B2
7682070	Burton	Mar 2010	B2
7683926	Schechterman et al.	Mar 2010	B2
D614305	Al-Ali et al.	Apr 2010	S
7695680	Unlu et al.	Apr 2010	B2
7697966	Monfre et al.	Apr 2010	B2
7698105	Ruchti et al.	Apr 2010	B2
7698909	Hannula et al.	Apr 2010	B2
RE41317	Parker	May 2010	E
RE41333	Blank et al.	May 2010	E
7726209	Ruotoistenmäki	Jun 2010	B2
7729733	Al-Ali et al.	Jun 2010	B2
7740588	Sciarra	Jun 2010	B1
7740589	Maschke et al.	Jun 2010	B2
7761127	Al-Ali et al.	Jul 2010	B2
7764982	Dalke et al.	Jul 2010	B2
D620884	Lee et al.	Aug 2010	S
D621516	Kiani et al.	Aug 2010	S
7778118	Lyons et al.	Aug 2010	B2
7791155	Diab	Sep 2010	B2
D626147	Goddard	Oct 2010	S
RE41912	Parker	Nov 2010	E
D628110	Boulangeot	Nov 2010	S
D630961	Ciuchindel et al.	Jan 2011	S
7862523	Ruotoistenmaki	Jan 2011	B2
7869849	Ollerdessen et al.	Jan 2011	B2
7876274	Hobson et al.	Jan 2011	B2
7880626	Al-Ali et al.	Feb 2011	B2
7890158	Rowe et al.	Feb 2011	B2
7899510	Hoarau	Mar 2011	B2
7899518	Trepagnier et al.	Mar 2011	B2
7904130	Raridan, Jr.	Mar 2011	B2
7909772	Popov et al.	Mar 2011	B2
7918779	Haber et al.	Apr 2011	B2
7919713	Al-Ali et al.	Apr 2011	B2
7937128	Al-Ali	May 2011	B2
7937129	Mason et al.	May 2011	B2
7941199	Kiani	May 2011	B2
7946758	Mooring	May 2011	B2
7957780	Lamego et al.	Jun 2011	B2
7962188	Kiani et al.	Jun 2011	B2
7976472	Kiani	Jul 2011	B2
7978062	LaLonde et al.	Jul 2011	B2
7990382	Kiani	Aug 2011	B2
8008088	Bellott et al.	Aug 2011	B2
RE42753	Kiani-Azarbayjany et al.	Sep 2011	E
D645818	Guccione et al.	Sep 2011	S
8028701	Al-Ali et al.	Oct 2011	B2
8040758	Dickinson	Oct 2011	B1
8048040	Kiani	Nov 2011	B2
8050728	Al-Ali et al.	Nov 2011	B2
8071935	Besko et al.	Dec 2011	B2
RE43169	Parker	Feb 2012	E
8118620	Al-Ali et al.	Feb 2012	B2
8130105	Al-Ali et al.	Mar 2012	B2
8162804	Tagliabue	Apr 2012	B2
8177720	Nanba et al.	May 2012	B2
8182443	Kiani	May 2012	B1
8190223	Al-Ali et al.	May 2012	B2
8203438	Kiani et al.	Jun 2012	B2
8203704	Merritt et al.	Jun 2012	B2
8219172	Schurman et al.	Jul 2012	B2
8224411	Al-Ali et al.	Jul 2012	B2
8228181	Al-Ali	Jul 2012	B2
8229532	Davis	Jul 2012	B2
8229535	Mensinger et al.	Jul 2012	B2
8233955	Al-Ali et al.	Jul 2012	B2
8255026	Al-Ali	Aug 2012	B1
8265723	McHale et al.	Sep 2012	B1
8274360	Sampath et al.	Sep 2012	B2
8280469	Baker, Jr. et al.	Oct 2012	B2
8280473	Al-Ali	Oct 2012	B2
8285010	Rowe	Oct 2012	B2
8289130	Nakajima et al.	Oct 2012	B2
8311514	Bandyopadhyay et al.	Nov 2012	B2
8315682	Such et al.	Nov 2012	B2
8315683	Al-Ali et al.	Nov 2012	B2
RE43860	Parker	Dec 2012	E
8343026	Gardiner et al.	Jan 2013	B2
8346330	Lamego	Jan 2013	B2
8353842	Al-Ali et al.	Jan 2013	B2
8355766	MacNeish, III et al.	Jan 2013	B2
8364389	Dorogusker et al.	Jan 2013	B2
8374665	Lamego	Feb 2013	B2
8374825	Vock et al.	Feb 2013	B2
8388353	Kiani et al.	Mar 2013	B2
8401602	Kiani	Mar 2013	B2
8414499	Al-Ali et al.	Apr 2013	B2
8418524	Al-Ali	Apr 2013	B2
8428967	Olsen et al.	Apr 2013	B2
8430817	Al-Ali et al.	Apr 2013	B1
8437825	Dalvi et al.	May 2013	B2
8452364	Hannula et al.	May 2013	B2
8455290	Siskavich	Jun 2013	B2
8457707	Kiani	Jun 2013	B2
8463345	Kuhn et al.	Jun 2013	B2
8471713	Poeze et al.	Jun 2013	B2
8473020	Kiani et al.	Jun 2013	B2
D685367	Akana et al.	Jul 2013	S
8487256	Kwong et al.	Jul 2013	B2
8496595	Jornod	Jul 2013	B2
8509867	Workman et al.	Aug 2013	B2
8515509	Bruinsma et al.	Aug 2013	B2
8515511	Boutelle	Aug 2013	B2
8515515	Mckenna et al.	Aug 2013	B2
8523781	Al-Ali	Sep 2013	B2
D692145	Al-Ali et al.	Oct 2013	S
8552989	Hotelling et al.	Oct 2013	B2
8562489	Burton et al.	Oct 2013	B2
8564544	Jobs et al.	Oct 2013	B2
8571617	Reichgott et al.	Oct 2013	B2
8571618	Lamego et al.	Oct 2013	B1
8571619	Al-Ali et al.	Oct 2013	B2
D694182	Lee et al.	Nov 2013	S
8577431	Lamego et al.	Nov 2013	B2
8584345	Al-Ali et al.	Nov 2013	B2
8588880	Abdul-Hafiz et al.	Nov 2013	B2
8591426	Onoe et al.	Nov 2013	B2
D694745	Akana et al.	Dec 2013	S
8600494	Schroeppel et al.	Dec 2013	B2
8611095	Kwong et al.	Dec 2013	B2
8615290	Lin et al.	Dec 2013	B2
D697027	Ho	Jan 2014	S
8624836	Miller et al.	Jan 2014	B1
8630691	Lamego et al.	Jan 2014	B2
8641631	Sierra et al.	Feb 2014	B2
8652060	Al-Ali	Feb 2014	B2
8655004	Prest et al.	Feb 2014	B2
8666468	Al-Ali	Mar 2014	B1
8668643	Kinast	Mar 2014	B2
8670811	O'Reilly	Mar 2014	B2
8670819	Iwamiya et al.	Mar 2014	B2
RE44823	Parker	Apr 2014	E
RE44875	Kiani et al.	Apr 2014	E
8688183	Bruinsma et al.	Apr 2014	B2
8690799	Telfort et al.	Apr 2014	B2
8700111	Leboeuf et al.	Apr 2014	B2
8702627	Telfort et al.	Apr 2014	B2
8712494	MacNeish, III et al.	Apr 2014	B1
D704634	Eidelman et al.	May 2014	S
8715206	Telfort et al.	May 2014	B2
8723677	Kiani	May 2014	B1
8734343	Lin et al.	May 2014	B2
8740792	Kiani et al.	Jun 2014	B1
8755535	Telfort et al.	Jun 2014	B2
8755872	Marinow	Jun 2014	B1
8760517	Sarwar et al.	Jun 2014	B2
D709873	Aumiller et al.	Jul 2014	S
D709874	Aumiller et al.	Jul 2014	S
8764671	Kiani	Jul 2014	B2
8768423	Shakespeare et al.	Jul 2014	B2
8768426	Haisley et al.	Jul 2014	B2
8771204	Telfort et al.	Jul 2014	B2
8781544	Al-Ali et al.	Jul 2014	B2
8787984	Murakami et al.	Jul 2014	B2
8790268	Al-Ali	Jul 2014	B2
D711372	Aumiller et al.	Aug 2014	S
D711873	Aumiller et al.	Aug 2014	S
8801613	Al-Ali et al.	Aug 2014	B2
8814802	Iijima et al.	Aug 2014	B2
D712930	Lee et al.	Sep 2014	S
8821397	Al-Ali et al.	Sep 2014	B2
8821415	Al-Ali et al.	Sep 2014	B2
8830449	Lamego et al.	Sep 2014	B1
8838210	Wood et al.	Sep 2014	B2
8840549	Al-Ali et al.	Sep 2014	B2
8852094	Al-Ali et al.	Oct 2014	B2
8852994	Wojtczuk et al.	Oct 2014	B2
D718233	Aumiller et al.	Nov 2014	S
D718234	Rautiainen	Nov 2014	S
D718236	Murray	Nov 2014	S
D718324	Lee et al.	Nov 2014	S
8888701	Leboeuf et al.	Nov 2014	B2
8897847	Al-Ali	Nov 2014	B2
D720289	Chiang et al.	Dec 2014	S
8911377	Al-Ali	Dec 2014	B2
8920332	Hong et al.	Dec 2014	B2
8929967	Mao et al.	Jan 2015	B2
8948832	Hong et al.	Feb 2015	B2
8954135	Yuen et al.	Feb 2015	B2
8958859	Petersen et al.	Feb 2015	B2
D724103	Akana et al.	Mar 2015	S
8979762	Ma et al.	Mar 2015	B2
8989831	Al-Ali et al.	Mar 2015	B2
D727316	Song	Apr 2015	S
8998809	Kiani	Apr 2015	B2
8998815	Venkatraman et al.	Apr 2015	B2
9001047	Forstall et al.	Apr 2015	B2
9005129	Venkatraman et al.	Apr 2015	B2
D729238	Song	May 2015	S
D729796	Song	May 2015	S
D730347	Jung et al.	May 2015	S
9036970	Guyon et al.	May 2015	B2
D732527	Kim et al.	Jun 2015	S
D732528	Kim et al.	Jun 2015	S
D733132	Kim et al.	Jun 2015	S
D733133	Kim et al.	Jun 2015	S
9063160	Stamler et al.	Jun 2015	B2
9066666	Kiani	Jun 2015	B2
9066680	Al-Ali et al.	Jun 2015	B1
D735131	Akana et al.	Jul 2015	S
D735190	Song	Jul 2015	S
9072437	Paalasmaa	Jul 2015	B2
9081889	Ingrassia, Jr. et al.	Jul 2015	B2
9095316	Welch et al.	Aug 2015	B2
9106038	Telfort et al.	Aug 2015	B2
9107625	Telfort et al.	Aug 2015	B2
9131881	Diab et al.	Sep 2015	B2
9138180	Coverston et al.	Sep 2015	B1
9153112	Kiani et al.	Oct 2015	B1
9173578	Miettinen	Nov 2015	B2
9192329	Al-Ali	Nov 2015	B2
9192351	Telfort et al.	Nov 2015	B1
9195385	Al-Ali et al.	Nov 2015	B2
D745513	Jung et al.	Dec 2015	S
D745514	Jung et al.	Dec 2015	S
9210566	Ziemianska et al.	Dec 2015	B2
9211095	Al-Ali	Dec 2015	B1
9218454	Kiani et al.	Dec 2015	B2
D746868	Akana et al.	Jan 2016	S
9245668	Vo et al.	Jan 2016	B1
9267572	Barker et al.	Feb 2016	B2
D751069	Choi et al.	Mar 2016	S
D752580	Choi et al.	Mar 2016	S
D752582	Jung et al.	Mar 2016	S
9277880	Poeze et al.	Mar 2016	B2
D753510	Puttorngul et al.	Apr 2016	S
9307928	Al-Ali et al.	Apr 2016	B1
9311382	Varoglu et al.	Apr 2016	B2
9314173	Gu et al.	Apr 2016	B2
9314197	Eisen et al.	Apr 2016	B2
9323894	Kiani	Apr 2016	B2
D755176	Jung et al.	May 2016	S
D755392	Hwang et al.	May 2016	S
D757819	Akana et al.	May 2016	S
9326712	Kiani	May 2016	B1
9339236	Frix et al.	May 2016	B2
9351645	Irisawa	May 2016	B2
9357665	Myers et al.	May 2016	B2
D759120	Akana et al.	Jun 2016	S
D760220	Aumiller et al.	Jun 2016	S
9392945	Al-Ali et al.	Jul 2016	B2
9392946	Sarantos et al.	Jul 2016	B1
9392976	Rodriguez-Llorente et al.	Jul 2016	B2
9408542	Kinast et al.	Aug 2016	B1
9423952	Tamegai	Aug 2016	B2
D766115	Ma	Sep 2016	S
D766235	Song	Sep 2016	S
9436645	Al-Ali et al.	Sep 2016	B2
9445759	Lamego et al.	Sep 2016	B1
D768622	Kim et al.	Oct 2016	S
D768724	Akana et al.	Oct 2016	S
9460846	Graham et al.	Oct 2016	B2
9474474	Lamego et al.	Oct 2016	B2
D770533	Akana et al.	Nov 2016	S
D771624	Aumiller et al.	Nov 2016	S
D772228	Jung et al.	Nov 2016	S
9480435	Olsen	Nov 2016	B2
9489081	Anzures et al.	Nov 2016	B2
9497534	Prest et al.	Nov 2016	B2
9504405	Conrad et al.	Nov 2016	B2
9510779	Poeze et al.	Dec 2016	B2
9517024	Kiani et al.	Dec 2016	B2
9526430	Srinivas et al.	Dec 2016	B2
9532722	Lamego et al.	Jan 2017	B2
9553625	Hatanaka et al.	Jan 2017	B2
D780223	Kim	Feb 2017	S
9560996	Kiani	Feb 2017	B2
9579039	Jansen et al.	Feb 2017	B2
9583256	Lapetina et al.	Feb 2017	B2
D782537	Akana et al.	Mar 2017	S
9593969	King	Mar 2017	B2
9622692	Lamego et al.	Apr 2017	B2
D787714	Wang et al.	May 2017	S
D788079	Son et al.	May 2017	S
D788312	Al-Ali et al.	May 2017	S
9636059	Cinbis et al.	May 2017	B2
9649054	Lamego et al.	May 2017	B2
9651405	Gowreesunker et al.	May 2017	B1
9664556	Chu et al.	May 2017	B2
9666764	Bergmann et al.	May 2017	B2
9668676	Culbert	Jun 2017	B2
9681812	Presura	Jun 2017	B2
9683894	Uematsu et al.	Jun 2017	B2
9684900	Motoki et al.	Jun 2017	B2
9697928	Al-Ali et al.	Jul 2017	B2
9699546	Qian et al.	Jul 2017	B2
9700249	Johnson et al.	Jul 2017	B2
9716937	Qian et al.	Jul 2017	B2
9717448	Frix et al.	Aug 2017	B2
9717458	Lamego et al.	Aug 2017	B2
9723997	Lamego	Aug 2017	B1
9724016	Al-Ali et al.	Aug 2017	B1
9724024	Al-Ali	Aug 2017	B2
9724025	Kiani et al.	Aug 2017	B1
9749232	Sampath et al.	Aug 2017	B2
D797809	Akana et al.	Sep 2017	S
D797810	Akana et al.	Sep 2017	S
9750442	Olsen	Sep 2017	B2
9750461	Telfort	Sep 2017	B1
9752925	Chu et al.	Sep 2017	B2
D800172	Akana et al.	Oct 2017	S
9775545	Al-Ali et al.	Oct 2017	B2
9775548	Sarantos et al.	Oct 2017	B2
9778079	Al-Ali et al.	Oct 2017	B1
9781984	Baranski et al.	Oct 2017	B2
9782077	Lamego et al.	Oct 2017	B2
9787568	Lamego et al.	Oct 2017	B2
9801547	Yuen et al.	Oct 2017	B2
9808188	Perea et al.	Nov 2017	B1
9814399	Takahashi et al.	Nov 2017	B2
9820658	Tran	Nov 2017	B2
D806063	Kim	Dec 2017	S
9838775	Qian et al.	Dec 2017	B2
9839379	Al-Ali et al.	Dec 2017	B2
9839381	Weber et al.	Dec 2017	B1
9847749	Kiani et al.	Dec 2017	B2
9848787	White et al.	Dec 2017	B2
9848800	Lee et al.	Dec 2017	B1
9848823	Raghuram et al.	Dec 2017	B2
D807351	Bang et al.	Jan 2018	S
9861298	Eckerbom et al.	Jan 2018	B2
9861305	Weber et al.	Jan 2018	B1
9866671	Thompson et al.	Jan 2018	B1
9867575	Maani et al.	Jan 2018	B2
9877650	Muhsin et al.	Jan 2018	B2
D809512	Mistry et al.	Feb 2018	S
9883824	Tiao et al.	Feb 2018	B2
9891079	Dalvi	Feb 2018	B2
9891590	Shim et al.	Feb 2018	B2
9898049	Myers et al.	Feb 2018	B2
D812607	Mistry et al.	Mar 2018	S
9918646	Singh Alvarado et al.	Mar 2018	B2
9924874	Sato	Mar 2018	B2
9924897	Abdul-Hafiz	Mar 2018	B1
9936917	Poeze et al.	Apr 2018	B2
9952095	Hotelling et al.	Apr 2018	B1
D816524	Akana et al.	May 2018	S
D819021	Mistry et al.	May 2018	S
9955919	Leboeuf et al.	May 2018	B2
9955937	Telfort	May 2018	B2
9965946	Al-Ali et al.	May 2018	B2
D820865	Muhsin et al.	Jun 2018	S
9986952	Dalvi et al.	Jun 2018	B2
9993200	Jeong	Jun 2018	B2
D822215	Al-Ali et al.	Jul 2018	S
D822216	Barker et al.	Jul 2018	S
D823301	Bang et al.	Jul 2018	S
10010276	Al-Ali et al.	Jul 2018	B2
10024655	Raguin et al.	Jul 2018	B2
10039080	Miller et al.	Jul 2018	B2
10039491	Thompson et al.	Aug 2018	B2
10052850	Weiss et al.	Aug 2018	B2
10055121	Chaudhri et al.	Aug 2018	B2
10058254	Fei	Aug 2018	B2
10060788	Fei	Aug 2018	B2
D827831	Fong et al.	Sep 2018	S
10066970	Gowreesunker et al.	Sep 2018	B2
10076257	Lin et al.	Sep 2018	B2
10078052	Ness et al.	Sep 2018	B2
10080499	Kuhn	Sep 2018	B2
10085656	Sato	Oct 2018	B2
10086138	Novak, Jr.	Oct 2018	B1
10090712	Jabori et al.	Oct 2018	B2
10092197	Han	Oct 2018	B2
10092244	Chuang et al.	Oct 2018	B2
10104219	Thompson et al.	Oct 2018	B2
10108151	Cardinali et al.	Oct 2018	B2
10111591	Dyell et al.	Oct 2018	B2
D833624	DeJong et al.	Nov 2018	S
10117587	Han	Nov 2018	B2
10123729	Dyell et al.	Nov 2018	B2
D835282	Barker et al.	Dec 2018	S
D835283	Barker et al.	Dec 2018	S
D835284	Barker et al.	Dec 2018	S
D835285	Barker et al.	Dec 2018	S
10149616	Al-Ali et al.	Dec 2018	B2
10154789	Raghuram et al.	Dec 2018	B2
10154815	Al-Ali et al.	Dec 2018	B2
10159412	Lamego et al.	Dec 2018	B2
10164688	Rothkopf et al.	Dec 2018	B2
10165954	Lee	Jan 2019	B2
10188348	Al-Ali et al.	Jan 2019	B2
RE47218	Al-Ali	Feb 2019	E
RE47244	Kiani et al.	Feb 2019	E
RE47249	Kiani et al.	Feb 2019	E
D839753	Domke et al.	Feb 2019	S
10201286	Waydo	Feb 2019	B2
10205291	Scruggs et al.	Feb 2019	B2
10206623	Harrison-Noonan et al.	Feb 2019	B2
10215698	Han et al.	Feb 2019	B2
10219754	Lamego	Mar 2019	B1
10226187	Al-Ali et al.	Mar 2019	B2
10231629	Pei et al.	Mar 2019	B1
10231657	Al-Ali et al.	Mar 2019	B2
10231670	Blank et al.	Mar 2019	B2
RE47353	Kiani et al.	Apr 2019	E
10244948	Pham et al.	Apr 2019	B2
10247670	Ness et al.	Apr 2019	B2
10265024	Lee et al.	Apr 2019	B2
10271746	Jeanne et al.	Apr 2019	B2
10279247	Kiani	May 2019	B2
10285626	Kestelli et al.	May 2019	B1
10285645	Bushnell et al.	May 2019	B2
10292664	Al-Ali	May 2019	B2
10299720	Brown et al.	May 2019	B2
10302465	Gowreesunker et al.	May 2019	B2
10303219	Myers et al.	May 2019	B2
10318716	Nakajima et al.	Jun 2019	B2
10327337	Schmidt et al.	Jun 2019	B2
10327713	Barker et al.	Jun 2019	B2
10332630	Al-Ali	Jun 2019	B2
10368799	Sannholm et al.	Aug 2019	B2
10383520	Wojtczuk et al.	Aug 2019	B2
10383527	Al-Ali	Aug 2019	B2
10388120	Muhsin et al.	Aug 2019	B2
10390716	Shimuta	Aug 2019	B2
10398383	Van Dinther et al.	Sep 2019	B2
10406445	Vock et al.	Sep 2019	B2
10416079	Magnussen et al.	Sep 2019	B2
D861676	Mistry et al.	Oct 2019	S
D864120	Forrest et al.	Oct 2019	S
10433043	Hankey et al.	Oct 2019	B2
10441181	Telfort et al.	Oct 2019	B1
10441196	Eckerbom et al.	Oct 2019	B2
10447844	Ma et al.	Oct 2019	B2
10448844	Al-Ali et al.	Oct 2019	B2
10448871	Al-Ali et al.	Oct 2019	B2
10448876	Hutchinson	Oct 2019	B2
10456038	Lamego et al.	Oct 2019	B2
D866350	Park et al.	Nov 2019	S
10463340	Telfort et al.	Nov 2019	B2
10466889	Tyler	Nov 2019	B2
10471159	Lapotko et al.	Nov 2019	B1
10478075	Martin et al.	Nov 2019	B2
10492726	Dusan et al.	Dec 2019	B2
10499821	Pi et al.	Dec 2019	B2
10503254	Allec et al.	Dec 2019	B2
10503379	Al-Ali et al.	Dec 2019	B2
10504380	Thompson et al.	Dec 2019	B2
10505311	Al-Ali et al.	Dec 2019	B2
10512406	Martinez et al.	Dec 2019	B2
10512432	Shahparnia et al.	Dec 2019	B2
10512436	Muhsin et al.	Dec 2019	B2
10517489	Narasimhan et al.	Dec 2019	B2
10521900	Bartula et al.	Dec 2019	B2
10524670	Raghuram et al.	Jan 2020	B2
10524671	Lamego	Jan 2020	B2
10524706	Telfort et al.	Jan 2020	B2
10524735	Waydo et al.	Jan 2020	B2
10524738	Olsen	Jan 2020	B2
10531811	Al-Ali et al.	Jan 2020	B2
10531819	Diab et al.	Jan 2020	B2
10531835	Al-Ali et al.	Jan 2020	B2
10532174	Al-Ali	Jan 2020	B2
10536768	Wagner et al.	Jan 2020	B2
10537284	Ruh et al.	Jan 2020	B1
10537285	Shreim et al.	Jan 2020	B2
10542903	Al-Ali et al.	Jan 2020	B2
10542920	Sato	Jan 2020	B2
D875092	Akana et al.	Feb 2020	S
10548561	Telfort et al.	Feb 2020	B2
10555678	Dalvi et al.	Feb 2020	B2
10568514	Wojtczuk et al.	Feb 2020	B2
10568516	Yang et al.	Feb 2020	B2
10568553	O'Neil et al.	Feb 2020	B2
RE47882	Al-Ali	Mar 2020	E
10575766	Sato	Mar 2020	B2
10575779	Poeze et al.	Mar 2020	B2
10588518	Kiani	Mar 2020	B2
10588556	Kiani et al.	Mar 2020	B2
10593186	Hankey et al.	Mar 2020	B2
10595747	Al-Ali et al.	Mar 2020	B2
10603690	Zadesky et al.	Mar 2020	B2
10608817	Haider et al.	Mar 2020	B2
D880477	Forrest et al.	Apr 2020	S
D882565	Akana et al.	Apr 2020	S
10610157	Pandya et al.	Apr 2020	B2
10617302	Al-Ali et al.	Apr 2020	B2
10617335	Al-Ali et al.	Apr 2020	B2
10617912	Narasimha Rao et al.	Apr 2020	B2
10620591	Rothkopf	Apr 2020	B2
10627783	Rothkopf	Apr 2020	B2
10637181	Al-Ali et al.	Apr 2020	B2
D883279	Akana et al.	May 2020	S
10653327	Lijima	May 2020	B2
D886849	Muhsin et al.	Jun 2020	S
D887548	Abdul-Hafiz et al.	Jun 2020	S
D887549	Abdul-Hafiz et al.	Jun 2020	S
10667764	Ahmed et al.	Jun 2020	B2
10687707	Tan et al.	Jun 2020	B2
10687718	Allec et al.	Jun 2020	B2
10687752	Pham et al.	Jun 2020	B2
10694994	Alvarado et al.	Jun 2020	B2
10699594	Mermel et al.	Jun 2020	B2
D890708	Forrest et al.	Jul 2020	S
10702171	Narasimhan et al.	Jul 2020	B2
10702211	Clavelle et al.	Jul 2020	B2
10709933	Tan et al.	Jul 2020	B2
10721785	Al-Ali	Jul 2020	B2
10722157	Bower et al.	Jul 2020	B2
10726731	Arney et al.	Jul 2020	B2
10736518	Al-Ali et al.	Aug 2020	B2
10736543	Chen et al.	Aug 2020	B2
10750984	Pauley et al.	Aug 2020	B2
D897098	Al-Ali	Sep 2020	S
10758133	Shapiro	Sep 2020	B2
10772512	Klaassen et al.	Sep 2020	B2
10779098	Iswanto et al.	Sep 2020	B2
10779738	Sullivan et al.	Sep 2020	B2
10799128	Paulussen et al.	Oct 2020	B2
10827961	Iyengar et al.	Nov 2020	B1
10828007	Telfort et al.	Nov 2020	B1
10832818	Muhsin et al.	Nov 2020	B2
10849554	Shreim et al.	Dec 2020	B2
10856750	Indorf	Dec 2020	B2
D906970	Forrest et al.	Jan 2021	S
D908213	Abdul-Hafiz et al.	Jan 2021	S
10912501	Poeze et al.	Feb 2021	B2
10912502	Poeze et al.	Feb 2021	B2
10918281	Al-Ali et al.	Feb 2021	B2
10918322	Shao et al.	Feb 2021	B2
10930452	Weaver	Feb 2021	B2
10932705	Muhsin et al.	Mar 2021	B2
10932729	Kiani et al.	Mar 2021	B2
10939878	Kiani et al.	Mar 2021	B2
10942491	Rothkopf et al.	Mar 2021	B2
10945648	Poeze et al.	Mar 2021	B2
10956950	Al-Ali et al.	Mar 2021	B2
D916135	Indorf et al.	Apr 2021	S
D917046	Abdul-Hafiz et al.	Apr 2021	S
D917550	Indorf et al.	Apr 2021	S
D917564	Indorf et al.	Apr 2021	S
D917704	Al-Ali et al.	Apr 2021	S
10987054	Pandya et al.	Apr 2021	B2
10987066	Chandran et al.	Apr 2021	B2
10991135	Al-Ali et al.	Apr 2021	B2
D919094	Al-Ali et al.	May 2021	S
D919100	Al-Ali et al.	May 2021	S
11006867	Al-Ali	May 2021	B2
11009390	Hotelling et al.	May 2021	B2
D921202	Al-Ali et al.	Jun 2021	S
11024064	Muhsin et al.	Jun 2021	B2
11026604	Chen et al.	Jun 2021	B2
11033189	Verkruijsse et al.	Jun 2021	B2
11033708	Blahnik et al.	Jun 2021	B2
D925597	Chandran et al.	Jul 2021	S
11069255	Blahnik et al.	Jul 2021	B2
D927699	Al-Ali et al.	Aug 2021	S
11076771	Allec et al.	Aug 2021	B2
11076777	Lee et al.	Aug 2021	B2
11106352	Tyler	Aug 2021	B2
11107578	Nag	Aug 2021	B2
11114188	Poeze et al.	Sep 2021	B2
D933232	Al-Ali et al.	Oct 2021	S
D933233	Al-Ali et al.	Oct 2021	S
D933234	Al-Ali et al.	Oct 2021	S
11134854	Presura	Oct 2021	B2
11145408	Sampath et al.	Oct 2021	B2
11147518	Al-Ali et al.	Oct 2021	B1
11185262	Al-Ali et al.	Nov 2021	B2
11191484	Kiani et al.	Dec 2021	B2
11210583	Mathew et al.	Dec 2021	B2
D946596	Ahmed	Mar 2022	S
D946597	Ahmed	Mar 2022	S
D946598	Ahmed	Mar 2022	S
D946617	Ahmed	Mar 2022	S
11272839	Al-Ali et al.	Mar 2022	B2
11289199	Al-Ali	Mar 2022	B2
RE49034	Al-Ali	Apr 2022	E
D947842	Akana et al.	Apr 2022	S
D949144	Akana et al.	Apr 2022	S
D949145	Akana et al.	Apr 2022	S
11298021	Muhsin et al.	Apr 2022	B2
11298075	Paalasmaa et al.	Apr 2022	B2
D950580	Ahmed	May 2022	S
D950599	Ahmed	May 2022	S
D950738	Al-Ali et al.	May 2022	S
D953324	Akana et al.	May 2022	S
11331013	Al-Ali et al.	May 2022	B2
D957648	Al-Ali	Jul 2022	S
11382567	O'Brien et al.	Jul 2022	B2
11389093	Triman et al.	Jul 2022	B2
11406286	Al-Ali et al.	Aug 2022	B2
11417426	Muhsin et al.	Aug 2022	B2
D962933	Akana et al.	Sep 2022	S
D962934	Akana et al.	Sep 2022	S
D962936	Akana et al.	Sep 2022	S
11439329	Lamego	Sep 2022	B2
11445948	Scruggs et al.	Sep 2022	B2
D965789	Al-Ali et al.	Oct 2022	S
D967433	Al-Ali et al.	Oct 2022	S
11464410	Muhsin	Oct 2022	B2
11474483	Rothkopf et al.	Oct 2022	B2
11478258	Chien et al.	Oct 2022	B2
11504057	Clavelle et al.	Nov 2022	B2
11504058	Sharma et al.	Nov 2022	B1
11504066	Dalvi et al.	Nov 2022	B1
D971933	Ahmed	Dec 2022	S
D973072	Ahmed	Dec 2022	S
D973685	Ahmed	Dec 2022	S
D973686	Ahmed	Dec 2022	S
D974193	Forrest et al.	Jan 2023	S
D979516	Al-Ali et al.	Feb 2023	S
D980091	Forrest et al.	Mar 2023	S
11596363	Lamego	Mar 2023	B2
11627919	Kiani et al.	Apr 2023	B2
11637437	Al-Ali et al.	Apr 2023	B2
D985498	Al-Ali et al.	May 2023	S
11653862	Dalvi et al.	May 2023	B2
D989112	Muhsin et al.	Jun 2023	S
D989327	Al-Ali et al.	Jun 2023	S
11678829	Al-Ali et al.	Jun 2023	B2
11679579	Al-Ali	Jun 2023	B2
11684296	Vo et al.	Jun 2023	B2
11692934	Normand et al.	Jul 2023	B2
11701043	Al-Ali et al.	Jul 2023	B2
D997365	Hwang	Aug 2023	S
11721105	Ranasinghe et al.	Aug 2023	B2
11730379	Ahmed et al.	Aug 2023	B2
D998625	Indorf et al.	Sep 2023	S
D998630	Indorf et al.	Sep 2023	S
D998631	Indorf et al.	Sep 2023	S
D999244	Indorf et al.	Sep 2023	S
D999245	Indorf et al.	Sep 2023	S
D999246	Indorf et al.	Sep 2023	S
11766198	Pauley et al.	Sep 2023	B2
D1000975	Al-Ali et al.	Oct 2023	S
11803623	Kiani et al.	Oct 2023	B2
11832940	Diab et al.	Dec 2023	B2
11872156	Telfort et al.	Jan 2024	B2
11879960	Ranasinghe et al.	Jan 2024	B2
11883129	Olsen	Jan 2024	B2
20010017970	Shie et al.	Aug 2001	A1
20010034477	Mansfield et al.	Oct 2001	A1
20010039483	Brand et al.	Nov 2001	A1
20010056243	Ohsaki et al.	Dec 2001	A1
20020010401	Bushmakin et al.	Jan 2002	A1
20020015034	Malmborg	Feb 2002	A1
20020019586	Teller et al.	Feb 2002	A1
20020042558	Mendelson	Apr 2002	A1
20020058864	Mansfield et al.	May 2002	A1
20020133080	Apruzzese et al.	Sep 2002	A1
20020156353	Larson	Oct 2002	A1
20020161291	Kianl et al.	Oct 2002	A1
20020184055	Naghavi et al.	Dec 2002	A1
20020188210	Aizawa	Dec 2002	A1
20030013975	Kiani	Jan 2003	A1
20030018243	Gerhardt et al.	Jan 2003	A1
20030033102	Dietiker	Feb 2003	A1
20030036689	Diab et al.	Feb 2003	A1
20030065269	Vetter et al.	Apr 2003	A1
20030088162	Yamamoto et al.	May 2003	A1
20030125612	Fox et al.	Jul 2003	A1
20030144582	Cohen et al.	Jul 2003	A1
20030156288	Barnum et al.	Aug 2003	A1
20030212312	Coffin, IV et al.	Nov 2003	A1
20030212316	Leiden et al.	Nov 2003	A1
20040039272	Abdul-Hafiz et al.	Feb 2004	A1
20040054290	Chance	Mar 2004	A1
20040106163	Workman, Jr. et al.	Jun 2004	A1
20040138568	Lo et al.	Jul 2004	A1
20040152957	Stivoric et al.	Aug 2004	A1
20050007582	Villers et al.	Jan 2005	A1
20050007589	Kramer	Jan 2005	A1
20050030518	Nishi et al.	Feb 2005	A1
20050030629	Kursawe et al.	Feb 2005	A1
20050033284	Hooven et al.	Feb 2005	A1
20050047455	Tanaka	Mar 2005	A1
20050055276	Kiani et al.	Mar 2005	A1
20050116820	Goldreich	Jun 2005	A1
20050197555	Mouradian et al.	Sep 2005	A1
20050212405	Negley	Sep 2005	A1
20050234317	Kiani	Oct 2005	A1
20050274971	Wang et al.	Dec 2005	A1
20050276164	Amron	Dec 2005	A1
20050277819	Kiani et al.	Dec 2005	A1
20050279949	Oldham et al.	Dec 2005	A1
20060009698	Banet et al.	Jan 2006	A1
20060033724	Chaudhri et al.	Feb 2006	A1
20060073719	Kiani	Apr 2006	A1
20060115128	Mainguet	Jun 2006	A1
20060189871	Al-Ali et al.	Aug 2006	A1
20060226992	Al-Ali et al.	Oct 2006	A1
20070021677	Markel	Jan 2007	A1
20070073116	Kiani et al.	Mar 2007	A1
20070093717	Nagar et al.	Apr 2007	A1
20070093786	Goldsmith et al.	Apr 2007	A1
20070145255	Nishikawa et al.	Jun 2007	A1
20070180140	Welch et al.	Aug 2007	A1
20070228404	Tran et al.	Oct 2007	A1
20070232880	Siddiqui et al.	Oct 2007	A1
20070244377	Cozad et al.	Oct 2007	A1
20070276270	Tran	Nov 2007	A1
20070282478	Al-Ali et al.	Dec 2007	A1
20080030468	Ali et al.	Feb 2008	A1
20080064965	Jay et al.	Mar 2008	A1
20080094228	Welch et al.	Apr 2008	A1
20080103375	Kiani	May 2008	A1
20080122796	Jobs et al.	May 2008	A1
20080147147	Griffiths et al.	Jun 2008	A1
20080165063	Schlub et al.	Jul 2008	A1
20080194932	Ayers et al.	Aug 2008	A1
20080208009	Shklarski	Aug 2008	A1
20080221418	Al-Ali et al.	Sep 2008	A1
20080242958	Al-Ali et al.	Oct 2008	A1
20080269619	Lindberg et al.	Oct 2008	A1
20080287758	Benaron et al.	Nov 2008	A1
20090018452	Sugiura et al.	Jan 2009	A1
20090036759	Ault et al.	Feb 2009	A1
20090054112	Cybart et al.	Feb 2009	A1
20090054751	Babashan et al.	Feb 2009	A1
20090093687	Telfort et al.	Apr 2009	A1
20090095926	MacNeish, III	Apr 2009	A1
20090190198	Kwon	Jul 2009	A1
20090247984	Lamego et al.	Oct 2009	A1
20090275810	Ayers et al.	Nov 2009	A1
20090275844	Al-Ali	Nov 2009	A1
20100004518	Vo et al.	Jan 2010	A1
20100030040	Poeze et al.	Feb 2010	A1
20100099964	O'Reilly et al.	Apr 2010	A1
20100113948	Yang et al.	May 2010	A1
20100193804	Brown et al.	Aug 2010	A1
20100234718	Sampath et al.	Sep 2010	A1
20100270257	Wachman et al.	Oct 2010	A1
20100324384	Moon et al.	Dec 2010	A1
20110003665	Burton et al.	Jan 2011	A1
20110028806	Merritt et al.	Feb 2011	A1
20110028809	Goodman	Feb 2011	A1
20110040197	Welch et al.	Feb 2011	A1
20110082711	Poeze et al.	Apr 2011	A1
20110087081	Kiani et al.	Apr 2011	A1
20110118561	Tari et al.	May 2011	A1
20110137297	Kiani et al.	Jun 2011	A1
20110172498	Olsen et al.	Jul 2011	A1
20110230733	Al-Ali	Sep 2011	A1
20110237969	Eckerbom et al.	Sep 2011	A1
20110288383	Diab	Nov 2011	A1
20110301444	Ai-Ali	Dec 2011	A1
20120041316	Al-Ali et al.	Feb 2012	A1
20120046557	Kiani	Feb 2012	A1
20120078069	Melker	Mar 2012	A1
20120088984	Al-Ali et al.	Apr 2012	A1
20120104999	Teggatz et al.	May 2012	A1
20120123231	O'Reilly	May 2012	A1
20120129495	Chae et al.	May 2012	A1
20120150052	Buchheim et al.	Jun 2012	A1
20120165629	Merritt et al.	Jun 2012	A1
20120209084	Olsen et al.	Aug 2012	A1
20120221254	Kateraas et al.	Aug 2012	A1
20120226117	Lamego et al.	Sep 2012	A1
20120271121	Della Torre et al.	Oct 2012	A1
20120283524	Kiani et al.	Nov 2012	A1
20120288230	Polonge et al.	Nov 2012	A1
20130006076	McHale	Jan 2013	A1
20130023775	Lamego et al.	Jan 2013	A1
20130041591	Lamego	Feb 2013	A1
20130060147	Welch et al.	Mar 2013	A1
20130096405	Garfio	Apr 2013	A1
20130227418	Sa et al.	Aug 2013	A1
20130239058	Yao et al.	Sep 2013	A1
20130262730	Al-Ali et al.	Oct 2013	A1
20130264592	Bergmann et al.	Oct 2013	A1
20130267804	Al-Ali	Oct 2013	A1
20130274572	Al-Ali et al.	Oct 2013	A1
20130296672	O'Neil et al.	Nov 2013	A1
20130296713	Al-Ali et al.	Nov 2013	A1
20130305351	Narendra et al.	Nov 2013	A1
20130317370	Dalvi et al.	Nov 2013	A1
20130345921	Al-Ali et al.	Dec 2013	A1
20140051943	Gillette	Feb 2014	A1
20140066783	Kiani et al.	Mar 2014	A1
20140101597	Bamford et al.	Apr 2014	A1
20140107493	Yuen et al.	Apr 2014	A1
20140117926	Hwu et al.	May 2014	A1
20140135594	Yuen et al.	May 2014	A1
20140139486	Mistry et al.	May 2014	A1
20140166076	Kiani et al.	Jun 2014	A1
20140180160	Brown et al.	Jun 2014	A1
20140187973	Brown et al.	Jul 2014	A1
20140189577	Shuttleworth et al.	Jul 2014	A1
20140221854	Wai	Aug 2014	A1
20140275852	Hong et al.	Sep 2014	A1
20140275871	Lamego et al.	Sep 2014	A1
20140275872	Merritt et al.	Sep 2014	A1
20140276013	Muehlemann et al.	Sep 2014	A1
20140276115	Dalvi et al.	Sep 2014	A1
20140278229	Hong	Sep 2014	A1
20140316217	Purdon et al.	Oct 2014	A1
20140316218	Purdon et al.	Oct 2014	A1
20140323897	Brown et al.	Oct 2014	A1
20140323898	Purdon et al.	Oct 2014	A1
20140361147	Fei	Dec 2014	A1
20140371548	Al-Ali et al.	Dec 2014	A1
20140371632	Al-Ali et al.	Dec 2014	A1
20140378784	Kiani et al.	Dec 2014	A1
20150005600	Blank et al.	Jan 2015	A1
20150011907	Purdon et al.	Jan 2015	A1
20150012231	Poeze et al.	Jan 2015	A1
20150018647	Mandel et al.	Jan 2015	A1
20150025406	Al-Ali	Jan 2015	A1
20150045637	Dalvi	Feb 2015	A1
20150045685	Al-Ali et al.	Feb 2015	A1
20150051462	Olsen	Feb 2015	A1
20150065889	Gandelman et al.	Mar 2015	A1
20150073241	Lamego	Mar 2015	A1
20150080754	Purdon et al.	Mar 2015	A1
20150095819	Hong et al.	Apr 2015	A1
20150097701	Al-Ali et al.	Apr 2015	A1
20150099324	Wojtczuk et al.	Apr 2015	A1
20150099950	Al-Ali et al.	Apr 2015	A1
20150099951	Al-Ali et al.	Apr 2015	A1
20150099955	Al-Ali et al.	Apr 2015	A1
20150112151	Muhsin et al.	Apr 2015	A1
20150116076	Al-Ali et al.	Apr 2015	A1
20150126830	Schurman et al.	May 2015	A1
20150133755	Smith et al.	May 2015	A1
20150135310	Lee	May 2015	A1
20150140863	Al-Ali et al.	May 2015	A1
20150141781	Weber et al.	May 2015	A1
20150153843	Lee	Jun 2015	A1
20150165312	Kiani	Jun 2015	A1
20150196237	Lamego	Jul 2015	A1
20150201874	Diab	Jul 2015	A1
20150208966	Al-Ali	Jul 2015	A1
20150214749	Park et al.	Jul 2015	A1
20150230755	Al-Ali et al.	Aug 2015	A1
20150245773	Lamego et al.	Sep 2015	A1
20150245793	Al-Ali et al.	Sep 2015	A1
20150245794	Al-Ali	Sep 2015	A1
20150250396	Ahmed et al.	Sep 2015	A1
20150255001	Haughav et al.	Sep 2015	A1
20150272514	Kiani et al.	Oct 2015	A1
20150282739	Nishida et al.	Oct 2015	A1
20150346976	Karunamuni et al.	Dec 2015	A1
20150355604	Fraser et al.	Dec 2015	A1
20160019360	Pahwa et al.	Jan 2016	A1
20160041531	Mackie et al.	Feb 2016	A1
20160042162	Newell	Feb 2016	A1
20160051147	Cohen et al.	Feb 2016	A1
20160051158	Silva	Feb 2016	A1
20160058356	Raghuram et al.	Mar 2016	A1
20160058375	Rothkopf	Mar 2016	A1
20160073914	Lapetina et al.	Mar 2016	A1
20160098137	Kim et al.	Apr 2016	A1
20160103985	Shim et al.	Apr 2016	A1
20160106367	Jorov et al.	Apr 2016	A1
20160157780	Rimminen et al.	Jun 2016	A1
20160166182	Al-Ali et al.	Jun 2016	A1
20160166183	Poeze et al.	Jun 2016	A1
20160196388	Lamego	Jul 2016	A1
20160206221	Kim et al.	Jul 2016	A1
20160206251	Kwon et al.	Jul 2016	A1
20160228064	Jung et al.	Aug 2016	A1
20160233632	Scruggs et al.	Aug 2016	A1
20160234944	Schmidt et al.	Aug 2016	A1
20160240721	Chu et al.	Aug 2016	A1
20160256082	Ely et al.	Sep 2016	A1
20160287090	Al-Ali et al.	Oct 2016	A1
20160287107	Szabados et al.	Oct 2016	A1
20160287181	Han et al.	Oct 2016	A1
20160296169	McHale et al.	Oct 2016	A1
20160296173	Culbert	Oct 2016	A1
20160296174	Isikman et al.	Oct 2016	A1
20160310052	Al-Ali et al.	Oct 2016	A1
20160331332	Al-Ali	Nov 2016	A1
20160334332	Magnussen	Nov 2016	A1
20160338598	Kegasawa	Nov 2016	A1
20160367173	Dalvi et al.	Dec 2016	A1
20170007134	Al-Ali et al.	Jan 2017	A1
20170007198	Al-Ali et al.	Jan 2017	A1
20170010858	Prest et al.	Jan 2017	A1
20170011210	Cheong et al.	Jan 2017	A1
20170014084	Al-Ali et al.	Jan 2017	A1
20170024748	Haider	Jan 2017	A1
20170046024	Dascola et al.	Feb 2017	A1
20170055851	Al-Ali	Mar 2017	A1
20170079594	Telfort et al.	Mar 2017	A1
20170086689	Shui et al.	Mar 2017	A1
20170086743	Bushnell et al.	Mar 2017	A1
20170094450	Tu et al.	Mar 2017	A1
20170119262	Shim et al.	May 2017	A1
20170164884	Culbert et al.	Jun 2017	A1
20170172476	Schilthuizen	Jun 2017	A1
20170173632	Al-Ali	Jun 2017	A1
20170187146	Kiani et al.	Jun 2017	A1
20170188919	Al-Ali et al.	Jul 2017	A1
20170202505	Kirenko et al.	Jul 2017	A1
20170215743	Meer et al.	Aug 2017	A1
20170224262	Al-Ali	Aug 2017	A1
20170251974	Shreim et al.	Sep 2017	A1
20170258403	Abdul-Hafiz et al.	Sep 2017	A1
20170290552	Naruse	Oct 2017	A1
20170293727	Klaassen et al.	Oct 2017	A1
20170311851	Schurman et al.	Nov 2017	A1
20170311891	Kiani et al.	Nov 2017	A1
20170325728	Al-Ali et al.	Nov 2017	A1
20170325744	Allec et al.	Nov 2017	A1
20170367632	Al-Ali et al.	Dec 2017	A1
20180049656	Paulussen et al.	Feb 2018	A1
20180049694	Singh Alvarado et al.	Feb 2018	A1
20180055385	Al-Ali	Mar 2018	A1
20180069776	Lamego et al.	Mar 2018	A1
20180103874	Lee et al.	Apr 2018	A1
20180110469	Maani et al.	Apr 2018	A1
20180110478	Al-Ali	Apr 2018	A1
20180116575	Perea et al.	May 2018	A1
20180130325	Kiani et al.	May 2018	A1
20180132770	Lamego	May 2018	A1
20180153418	Sullivan et al.	Jun 2018	A1
20180167806	Boyd	Jun 2018	A1
20180174679	Sampath et al.	Jun 2018	A1
20180174680	Sampath et al.	Jun 2018	A1
20180182484	Sampath et al.	Jun 2018	A1
20180192955	Al-Ali et al.	Jul 2018	A1
20180235542	Yun et al.	Aug 2018	A1
20180242924	Barker et al.	Aug 2018	A1
20180242926	Muhsin et al.	Aug 2018	A1
20180247353	Al-Ali et al.	Aug 2018	A1
20180247712	Muhsin et al.	Aug 2018	A1
20180249933	Schurman et al.	Sep 2018	A1
20180256087	Al-Ali et al.	Sep 2018	A1
20180256113	Weber et al.	Sep 2018	A1
20180289337	Al-Ali et al.	Oct 2018	A1
20180310823	Al-Ali et al.	Nov 2018	A1
20180360326	Lee et al.	Dec 2018	A1
20190021638	Al-Ali et al.	Jan 2019	A1
20190038143	Al-Ali	Feb 2019	A1
20190059821	Pekonen et al.	Feb 2019	A1
20190090748	Al-Ali	Mar 2019	A1
20190090766	Block et al.	Mar 2019	A1
20190090806	Clavelle	Mar 2019	A1
20190104973	Poeze et al.	Apr 2019	A1
20190110719	Poeze et al.	Apr 2019	A1
20190117070	Muhsin et al.	Apr 2019	A1
20190150800	Poeze et al.	May 2019	A1
20190167114	Islam	Jun 2019	A1
20190196411	Yuen	Jun 2019	A1
20190239787	Pauley et al.	Aug 2019	A1
20190320906	Olsen	Oct 2019	A1
20190324593	Chung et al.	Oct 2019	A1
20190357813	Poeze et al.	Nov 2019	A1
20190357823	Reichgott et al.	Nov 2019	A1
20190357824	Al-Ali	Nov 2019	A1
20190358524	Kiani	Nov 2019	A1
20190365294	Poeze et al.	Dec 2019	A1
20190374139	Kiani et al.	Dec 2019	A1
20190374173	Kiani et al.	Dec 2019	A1
20190374713	Kiani et al.	Dec 2019	A1
20190386908	Lamego et al.	Dec 2019	A1
20190388039	Al-Ali	Dec 2019	A1
20200000338	Lamego et al.	Jan 2020	A1
20200000415	Barker et al.	Jan 2020	A1
20200020493	Weaver	Jan 2020	A1
20200021930	Iswanto et al.	Jan 2020	A1
20200037453	Triman et al.	Jan 2020	A1
20200037891	Kiani et al.	Feb 2020	A1
20200037966	Al-Ali	Feb 2020	A1
20200046257	Eckerbom et al.	Feb 2020	A1
20200054253	Al-Ali et al.	Feb 2020	A1
20200060591	Diab et al.	Feb 2020	A1
20200060628	Al-Ali et al.	Feb 2020	A1
20200060629	Muhsin et al.	Feb 2020	A1
20200060869	Telfort et al.	Feb 2020	A1
20200074819	Muhsin et al.	Mar 2020	A1
20200111552	Ahmed	Apr 2020	A1
20200113435	Muhsin	Apr 2020	A1
20200113488	Al-Ali et al.	Apr 2020	A1
20200113496	Scruggs et al.	Apr 2020	A1
20200113497	Triman et al.	Apr 2020	A1
20200113520	Abdul-Hafiz et al.	Apr 2020	A1
20200121941	Kwon et al.	Apr 2020	A1
20200138288	Al-Ali et al.	May 2020	A1
20200138368	Kiani et al.	May 2020	A1
20200163597	Dalvi et al.	May 2020	A1
20200196877	Vo et al.	Jun 2020	A1
20200196882	Kiani et al.	Jun 2020	A1
20200221980	Poeze et al.	Jul 2020	A1
20200253474	Muhsin et al.	Aug 2020	A1
20200253544	Belur Nagaraj et al.	Aug 2020	A1
20200275841	Telfort et al.	Sep 2020	A1
20200288983	Telfort et al.	Sep 2020	A1
20200321793	Al-Ali et al.	Oct 2020	A1
20200329983	Al-Ali et al.	Oct 2020	A1
20200329984	Al-Ali et al.	Oct 2020	A1
20200329993	Al-Ali et al.	Oct 2020	A1
20200330037	Al-Ali et al.	Oct 2020	A1
20210022628	Telfort et al.	Jan 2021	A1
20210104173	Pauley et al.	Apr 2021	A1
20210113121	Diab et al.	Apr 2021	A1
20210117525	Kiani et al.	Apr 2021	A1
20210118581	Kiani et al.	Apr 2021	A1
20210121582	Krishnamani et al.	Apr 2021	A1
20210161465	Barker et al.	Jun 2021	A1
20210236729	Kiani et al.	Aug 2021	A1
20210256267	Ranasinghe et al.	Aug 2021	A1
20210256835	Ranasinghe et al.	Aug 2021	A1
20210275101	Vo et al.	Sep 2021	A1
20210290060	Ahmed	Sep 2021	A1
20210290072	Forrest	Sep 2021	A1
20210290080	Ahmed	Sep 2021	A1
20210290120	Al-Ali	Sep 2021	A1
20210290177	Novak, Jr.	Sep 2021	A1
20210290184	Ahmed	Sep 2021	A1
20210296008	Novak, Jr.	Sep 2021	A1
20210330228	Olsen et al.	Oct 2021	A1
20210358700	Weaver	Nov 2021	A1
20210386382	Olsen et al.	Dec 2021	A1
20210402110	Pauley et al.	Dec 2021	A1
20220026355	Normand et al.	Jan 2022	A1
20220039707	Sharma et al.	Feb 2022	A1
20220053892	Al-Ali et al.	Feb 2022	A1
20220071562	Kiani	Mar 2022	A1
20220096603	Kiani et al.	Mar 2022	A1
20220151521	Krishnamani et al.	May 2022	A1
20220218244	Kiani et al.	Jul 2022	A1
20220219311	Duthaler et al.	Jul 2022	A1
20220287574	Telfort et al.	Sep 2022	A1
20220296161	Al-Ali et al.	Sep 2022	A1
20220361819	Al-Ali et al.	Nov 2022	A1
20220379059	Yu et al.	Dec 2022	A1
20220392610	Kiani et al.	Dec 2022	A1
20230028745	Al-Ali	Jan 2023	A1
20230038389	Vo	Feb 2023	A1
20230045647	Vo	Feb 2023	A1
20230058052	Al-Ali	Feb 2023	A1
20230058342	Kiani	Feb 2023	A1
20230069789	Koo et al.	Mar 2023	A1
20230087671	Telfort et al.	Mar 2023	A1
20230110152	Forrest et al.	Apr 2023	A1
20230111198	Yu et al.	Apr 2023	A1
20230115397	Vo et al.	Apr 2023	A1
20230116371	Mills et al.	Apr 2023	A1
20230135297	Kiani et al.	May 2023	A1
20230138098	Telfort et al.	May 2023	A1
20230145155	Krishnamani et al.	May 2023	A1
20230147750	Barker et al.	May 2023	A1
20230210417	Al-Ali et al.	Jul 2023	A1
20230222805	Muhsin et al.	Jul 2023	A1
20230222887	Muhsin et al.	Jul 2023	A1
20230226331	Kiani et al.	Jul 2023	A1
20230284916	Telfort	Sep 2023	A1
20230284943	Scruggs et al.	Sep 2023	A1
20230301562	Scruggs et al.	Sep 2023	A1
20230346993	Kiani et al.	Nov 2023	A1
20230368221	Haider	Nov 2023	A1
20230371893	Al-Ali et al.	Nov 2023	A1
20230389837	Krishnamani et al.	Dec 2023	A1
20240016418	Devadoss et al.	Jan 2024	A1
20240016419	Devadoss et al.	Jan 2024	A1
20240047061	Al-Ali et al.	Feb 2024	A1
20240049310	Al-Ali et al.	Feb 2024	A1
20240049986	Al-Ali et al.	Feb 2024	A1

Foreign Referenced Citations (261)

Number	Date	Country
7426381	Feb 1983	AU
2014200060	Oct 2016	AU
2105681	Oct 1992	CA
2264029	Mar 1998	CA
2137878	Apr 2007	CA
1270793	Oct 2000	CN
1482448	Mar 2004	CN
201033073	Mar 2008	CN
100518630	Jul 2009	CN
101564290	Oct 2009	CN
201481421	May 2010	CN
201542615	Aug 2010	CN
201578231	Sep 2010	CN
201585989	Sep 2010	CN
101484065	Nov 2011	CN
302687306	Dec 2013	CN
103906468	Jul 2014	CN
203732900	Jul 2014	CN
302942795	Sep 2014	CN
302972990	Oct 2014	CN
302864470	Nov 2014	CN
303285726	Jul 2015	CN
303285726	Jul 2015	CN
303296619	Jul 2015	CN
303306604	Jul 2015	CN
303327831	Aug 2015	CN
303518893	Dec 2015	CN
205041396	Feb 2016	CN
303646405	Apr 2016	CN
303737075	Jul 2016	CN
106236051	Dec 2016	CN
104181809	Jan 2017	CN
304027493	Feb 2017	CN
106527106	Mar 2017	CN
304385323	Dec 2017	CN
304481666	Jan 2018	CN
105379306	Feb 2020	CN
202004017631	Mar 2005	DE
102008002741	Dec 2009	DE
202007019341	Jan 2012	DE
001383434-0008	Sep 2013	EM
001383434-0009	Sep 2013	EM
002743575-0001	Jul 2015	EM
004428274-0003	Oct 2017	EM
005940459-0005	Dec 2018	EM
005940459-0011	Dec 2018	EM
005940459-0013	Dec 2018	EM
005940459-0014	Dec 2018	EM
005940459-0015	Dec 2018	EM
006302279-0001	Mar 2019	EM
006302279-0002	Mar 2019	EM
007127113-0001	Oct 2019	EM
0102816	Mar 1984	EP
0419223	Mar 1991	EP
0 505 627	Sep 1992	EP
0630208	Dec 1994	EP
0724860	Aug 1996	EP
0665727	Jan 1997	EP
0760223	Mar 1997	EP
0770349	May 1997	EP
0781527	Jul 1997	EP
0880936	Dec 1998	EP
0922432	Jun 1999	EP
0985373	Mar 2000	EP
1080683	Mar 2001	EP
1518494	Mar 2005	EP
1526805	May 2005	EP
1124609	Aug 2006	EP
1213037	Nov 2006	EP
1860989	Dec 2007	EP
1875213	Jan 2008	EP
1880666	Jan 2008	EP
2165196	Mar 2010	EP
2277440	Jan 2011	EP
14163114.3	Apr 2014	EP
2194842	Apr 2015	EP
3015062	May 2016	EP
3316779	May 2018	EP
3430980	Jan 2019	EP
3 459 447	Mar 2019	EP
3488776	May 2019	EP
3626159	Mar 2020	EP
3033992	Apr 2020	EP
2243691	Nov 1991	GB
4032616	Jan 2014	GB
S57-037438	Mar 1982	JP
05325705	Dec 1993	JP
H0666633	Sep 1994	JP
H07124138	May 1995	JP
08185864	Jul 1996	JP
H09173322	Jul 1997	JP
H09257508	Oct 1997	JP
H10314133	Dec 1998	JP
H1170086	Mar 1999	JP
2919326	Jul 1999	JP
H11197127	Jul 1999	JP
H11235320	Aug 1999	JP
3107630	Nov 2000	JP
3116255	Dec 2000	JP
2001066990	Mar 2001	JP
2001087250	Apr 2001	JP
2002500908	Jan 2002	JP
2003024276	Jan 2003	JP
2003508104	Mar 2003	JP
2003210438	Jul 2003	JP
2003265444	Sep 2003	JP
2004031485	Jan 2004	JP
2004119515	Apr 2004	JP
2004-298606	Oct 2004	JP
2004329406	Nov 2004	JP
2004337605	Dec 2004	JP
2004344668	Dec 2004	JP
2005160641	Jun 2005	JP
3710570	Oct 2005	JP
2005270543	Oct 2005	JP
3741147	Feb 2006	JP
2006102159	Apr 2006	JP
2006102164	Apr 2006	JP
2006177837	Jul 2006	JP
3803351	Aug 2006	JP
2006198321	Aug 2006	JP
2006288835	Oct 2006	JP
2006296564	Nov 2006	JP
2007289463	Nov 2007	JP
2007319232	Dec 2007	JP
2008099222	Apr 2008	JP
2008119026	May 2008	JP
2008126017	Jun 2008	JP
2009106373	May 2009	JP
2010136921	Jun 2010	JP
D1400735	Nov 2010	JP
2011147746	Aug 2011	JP
D1436448	Mar 2012	JP
5056867	Oct 2012	JP
2013009710	Jan 2013	JP
2013515528	May 2013	JP
2013118978	Jun 2013	JP
2013-212315	Oct 2013	JP
D1489271	Dec 2013	JP
5756752	Jun 2015	JP
2015112488	Jun 2015	JP
2016054822	Apr 2016	JP
2016-154754	Sep 2016	JP
D1568369	Dec 2016	JP
2018524073	Aug 2018	JP
20-0195400	Sep 2000	KR
10-2016-0089718	Nov 2003	KR
10-2006-0083552	Jul 2006	KR
10-2006-0111159	Oct 2006	KR
10-2007-0011685	Jan 2007	KR
10-2007-0058900	Jun 2007	KR
2007-0061122	Jun 2007	KR
100755079	Sep 2007	KR
10-2007-0102089	Oct 2007	KR
2007-0102089	Oct 2007	KR
10-2007-0056925	Apr 2008	KR
10-2008-0048010	May 2008	KR
2010-0091592	Aug 2010	KR
30-0645410	May 2012	KR
10-2013-0107833	Oct 2013	KR
30-0740673	Apr 2014	KR
30-0817671	Sep 2015	KR
10-2016-0041623	Apr 2016	KR
10-2016-0044811	Apr 2016	KR
10-2016-0058476	May 2016	KR
10-2016-0069623	Aug 2016	KR
10-2016-0096902	Aug 2016	KR
10-2017-0049279	May 2017	KR
10-2018-0038206	Apr 2018	KR
10-2019-0115313	Oct 2019	KR
10-2136836	Aug 2020	KR
2020-0093247	Aug 2020	KR
WO 82000088	Jan 1982	WO
WO 93012712	Jul 1993	WO
WO 94021173	Sep 1994	WO
WO 94023643	Oct 1994	WO
WO 95000070	Jan 1995	WO
WO 96013208	May 1996	WO
WO 96027325	Sep 1996	WO
WO 96041566	Dec 1996	WO
WO 97000923	Jan 1997	WO
WO 97001985	Jan 1997	WO
WO 97009923	Mar 1997	WO
WO 99000053	Jan 1999	WO
WO 99001704	Jul 1999	WO
WO 99063883	Dec 1999	WO
WO 00018290	Apr 2000	WO
WO 00025112	May 2000	WO
WO 00028892	May 2000	WO
WO 01009589	Feb 2001	WO
WO 01024700	Apr 2001	WO
WO 01050433	Jul 2001	WO
WO 01050955	Jul 2001	WO
WO 02028274	Apr 2002	WO
WO 02062213	Aug 2002	WO
WO 02097324	Dec 2002	WO
WO 03031961	Apr 2003	WO
WO 03068060	Aug 2003	WO
WO 2004082472	Sep 2004	WO
WO 2005009221	Feb 2005	WO
WO 2005092182	Oct 2005	WO
WO 2005094667	Oct 2005	WO
WO 2006016366	Feb 2006	WO
WO 2006017117	Feb 2006	WO
WO 2006060949	Jun 2006	WO
WO 2006079862	Aug 2006	WO
WO 2006090371	Aug 2006	WO
WO 2006110488	Oct 2006	WO
WO 2006113070	Oct 2006	WO
WO 2007004083	Jan 2007	WO
WO 2007017266	Feb 2007	WO
WO 2007048039	Apr 2007	WO
WO 2007144817	Dec 2007	WO
WO 2008002405	Jan 2008	WO
WO 2008035076	Mar 2008	WO
WO 2008040736	Apr 2008	WO
WO 2008107238	Sep 2008	WO
WO 2008133394	Nov 2008	WO
WO 2008149081	Dec 2008	WO
WO 2009001988	Dec 2008	WO
WO 2009137524	Nov 2009	WO
WO 2010003134	Jan 2010	WO
WO 2010107913	Sep 2010	WO
WO 2011033628	Mar 2011	WO
WO 2011051888	May 2011	WO
WO 2011069122	Jun 2011	WO
WO 2011076886	Jun 2011	WO
WO 2012092221	Jul 2012	WO
WO 2012140559	Oct 2012	WO
WO 2013027357	Feb 2013	WO
WO 2013030744	Mar 2013	WO
WO 2013066642	May 2013	WO
WO 2013076656	May 2013	WO
WO 2013106607	Jul 2013	WO
WO 2013124750	Aug 2013	WO
WO 2013181368	Dec 2013	WO
WO D083678-002	Jun 2014	WO
WO 2014115075	Jul 2014	WO
WO 2014149781	Sep 2014	WO
WO 2014153200	Sep 2014	WO
WO 2014158820	Oct 2014	WO
WO 2014178793	Nov 2014	WO
WO 2014184447	Nov 2014	WO
WO 2015034149	Mar 2015	WO
WO D086018-0001	Mar 2015	WO
WO D086018-0002	Mar 2015	WO
WO 2015046624	Apr 2015	WO
WO 2015049108	Apr 2015	WO
WO D086693-004	Jul 2015	WO
WO 2015116111	Aug 2015	WO
WO 2015150199	Oct 2015	WO
WO 2015187732	Dec 2015	WO
WO 2016066312	May 2016	WO
WO 2017004260	Jan 2017	WO
WO 2017165532	Sep 2017	WO
WO 2018112401	Jun 2018	WO
WO 2019198991	Oct 2019	WO
WO 2020006477	Jan 2020	WO
WO 2021146333	Jul 2021	WO
WO 2023287789	Jan 2023	WO
WO 2023034879	Mar 2023	WO

Non-Patent Literature Citations (681)

Entry
US 8,845,543 B2, 09/2014, Diab et al. (withdrawn)
US 2022/0192529 A1, 06/2022, Al-Ali et al. (withdrawn)
US 2024/0016391 A1, 01/2024, Lapotko et al. (withdrawn)
International Search Report and Written Opinion in corresponding International Patent Application No. PCT/US2021/013299, dated Jun. 21, 2021, in 23 pages.
Invitation to Pay Additional Fees from International Application No. PCT/US2021/013299, dated Apr. 29, 2021, 16 pages.
U.S. Appl. No. 62/691,822, filed Jun. 29, 2018, Weaver.
International Search Report and Written Opinion received in International Application No. PCT/US2022/036823, dated Oct. 21, 2022, 13 pages.
International Search Report and Written Opinion received in International Application No. PCT/US2022/07578, dated Dec. 13, 2022, 12 pages.
Jung, Scott, “Medgadget Joins the Verily Baseline Project Study, Part 2: The Tech”, MedGadget.com, https://www.medgadget.com/2017/10/medgadget-joins-verily-baseline-project-study-part-2-tech.html, Oct. 27, 2017, pp. 6.
U.S. Appl. No. 61/932,258, filed Jan. 28, 2014, Park et al.
U.S. Appl. No. 61/976,388, filed Apr. 7, 2014, Fei.
Aldinger et al., “Advanced Ceramics and Future Materials: An Introduction to Structure, Properties, Technologies, Methods”, Wiley-VCH GmbH & Co., 2010, pp. 17.
Francis, Johnson, “ECG monitoring leads and special leads”, Indian Pacing and Electrophysiology Journal, vol. 16, 2016, pp. 92-95.
Kingery, W.D., “Introduction to Ceramics”, John Wiley & Sons, Inc., 1960, pp. 23.
Ling et al., “The effects of link format and screen location on visual search of web pages,” Ergonomics, vol. 47, No. 8, Jun. 22, 2004, pp. 18.
Loehman et al., “Characterization of Ceramics”, Materials Characterization Series; Surfaces, Interfaces, Thin Films, Butterworth-Heinemann, 1993, pp. 13.
McCarthy et al., “Could I have the Menu Please? An Eye Tracking Study of Design Conventions”, People and Computers XVII—Designing for Society, 2003, pp. 20.
Nielsen, Jakob, “Do Interface Standards Stifle Design Creativity?”, Alertbox, https://web.archive.org/web/19991128143803/http://www.useit.com/alertbox/990822.html, Aug. 22, 1999, pp. 2.
Nielsen, Jakob, “Enhancing the Explanatory Power of Usability Heuristics”, Human Factors in Computing Systems, CHI '94 Conference Proceedings, Aug. 1994, pp. 14.
Norman, Donald A., “The Design of Everyday Things”, Double Day, 1988, pp. 37.
Santa-Maria et al., “The effect of violating visual conventions of a website on user performance and disorientation. How bad can it be?,” SIGDOC'08, Sep. 22-24, 2008, pp. 8.
Shackelford et al., “Ceramic and Glass Materials: Structure, Properties and Processing”, Springer, 2008, pp. 33.
Shi, Feng, “Ceramic Materials—Progress in Modern Ceramics”, InTech, Apr. 2012, p. 6.
Matthes, K. & W. Hauss, Lichtelektrische Plethysomgramme Klinische Wochenschrift No. 17 (5):I211-1213, 1938.
Bagha et al., “A Real Time Analysis of PPG Signal for Measurement of Sp02 and Pulse Rate,” International Journal of Computer Applications, vol. 36, No. 11, Dec. 2011, pp. 45-50.
N. Phattraprayoon et al., “Accuracy of pulse oximeter readings from probe placement on newborn wrist and ankle,” Journal of Perinatology, vol. 32, 2012, pp. 276-280.
R. Stojanovic et al., “Design of an Oximeter Based on LED-LED Configuration and FPGA Technology,” Sensors vol. 13, 2013, pp. 574-586.
T. Tamura et al., “Wearable Photoplethysmographic Sensors—Past and Present,” Electronics vol. 3, 2014, pp. 282-302.
S. Vogel et al., “In-Ear Vital Signs Monitoring Using a Novel Microoptic Reflective Sensor,” IEEE Transactions on Information Technology in Biomedicine, vol. 13, No. 6, Nov. 2009, pp. 882-889.
Y. Mendelson, et al., “Design and Evaluation of a New Reflectance Pulse Oximeter Sensor”, Worcester Polytechnic Institute, Biomedical Engineering Program, Worcester, MA 01609, Association for the Advancement of Medical Instrumentation, vol. 22, No. 4, 1988, pp. 167-173, Abstract, 1 page.
P.B. Crilly et al., “An Integrated Pulse Oximeter System for Telemedicine Applications,” IEEE Instrumentation and Measurement Technology Conference Sensing, Processing, Networking, IMTC Proceedings, 1997, pp. 102-104.
Y. Zhai, “A Wireless Sensor Network For Hospital Patient Monitoring,” Thesis for University of Calgary Department of Eletrical and Computer Engineering, Apr. 2007, 134 pages.
Y. Lee et al., “Development of a Wristwatch-Type PPG Array Sensor Module,” 2011 IEEE International Conference on Consumer Electronics (ICCE-Berlin), 2011, pp. 168-171.
J. Heerlein et al., ‘LED-based sensors for wearable fitness tracking products,’ published Dec. 16, 2014, retrieved from https://www.edn.com/design/led/4437996/1/LED-based-sensors-for-fitness-tracking-wearables, accessed Nov. 25, 2019, 6 pages.
Love et al., Personal Status Monitor, Sandia National Laboratories, Feb. 1997, 211 p. [uploaded in 2 parts].
137 pages of images, identified by bates numbers “APL_MAS_ITC_00378839” to “APL_MAS_ITC_00378975”. Undated. [uploaded in 3 parts].
54 pages of images, identified by bates numbers “APL_MAS_ITC_00383217” to “APL_MAS_ITC_00383270”. Undated. [uploaded in 3 parts].
12 pages of images, identified by bates numbers “APL_MAS_ITC_00383288” to “APL_MAS_ITC_00383299”. Undated.
7 pages of images, identified by bates numbers “APL_MAS_ITC_00383308” to “APL_MAS_ITC_00383314”. Undated.
Jun. 30, 2021 Complaint under Section 337 of the Tariff Act of 1930, as Amended, and including Exhibits 11- 40 (Exhibits 1-10 comprise copies of publicly available U.S. patents, and are not included herein for ease of transmission), Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., United States International Trade Commission, Investigation No. 337-TA-1276, 736 pages. [uploaded in 13 parts].
Jul. 7, 2021 First Amended Complaint under Section 337 of the Tariff Act of 1930, as Amended, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., United States International Trade Commission, Investigation No. 337-TA-1276, 44 pages.
Sep. 23, 2021 Response of Apple Inc. to First Amended Complaint and Notice of Investigation, and including Exhibit A and Appendix A, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., United States International Trade Commission, Investigation No. 337-TA-1276, 664 pages.
Dec. 3, 2021 Respondent Apple Inc.'s Preliminary Invalidity Contentions for U.S. Patent Nos. 10,912,501, 10,912,502, 10,945,648, 10,687,745, and 7,761,127, and including Exhibits A1-A6, B1-B6, and C1-C6 related to Patent Nos. 10,912,501, 10,912,502, 10,945,648 (Exhibits D1-D16 and E1-E13 relate to Patent Nos. 10,687,745, and 7,761,127, and are not included herein but are available upon request), Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., United States International Trade Commission, Investigation No. 337-TA-1276, 443 pages.
Dec. 3, 2021 Respondent Apple Inc.'s Preliminary Invalidity Contentions for U.S. Pat. Nos. 10,912,501, 10,912,502, 10,945,648, 10,687,745, and 7,761,127, and including Exhibits D1-D16 related to Patent No. 10,687,745 (Exhibits A1-A6, B1-B6, C1-C6, and E1-E13 relate to Patent Nos. 10,912,501, 10,912,502, 10,945,648, and 7,761,127, and are not included herein but are available upon request), Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., United States International Trade Commission, Investigation No. 337-TA-1276, 443 pages.
Dec 3, 2021 Respondent Apple Inc.'s Preliminary Invalidity Contentions for U.S. Pat. Nos. 10,912,501, 10,912,502, 10,945,648, 10,687,745, and 7,761,127, Exhibits A-1 to A-6, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., United States International Trade Commission, Investigation No. 337-TA-1276, 1230 pages. [uploaded in 2 parts].
Dec. 3, 2021 Respondent Apple Inc.'s Preliminary Invalidity Contentions for U.S. Pat. Nos. 10,912,501, 10,912,502, 10,945,648, 10,687,745, and 7,761,127, Exhibits B-1 to B-6, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., United States International Trade Commission, Investigation No. 337-TA-1276, 1343 pages. [uploaded in 2 parts].
Dec. 3, 2021 Respondent Apple Inc.'s Preliminary Invalidity Contentions for U.S. Pat. Nos. 10,912,501, 10,912,502, 10,945,648, 10,687,745, and 7,761,127, Exhibits C-1 to C-6, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., United States International Trade Commission, Investigation No. 337-TA-1276, 1222 pages. [uploaded in 2 parts].
Jan. 13, 2022 Joint Proposed Claim Construction Chart, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., United States International Trade Commission, Investigation No. 337-TA-1276, 8 pages.
Jan. 27, 2022 Respondent Apple Inc.'s Opening Markman Brief, and including Exhibits 1-7, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., United States International Trade Commission, Investigation No. 337-TA-1276,144 pages.
Jan. 27, 2022 Complainant's Opening Claim Construction Brief, and including Exhibits 1-16, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., United States International Trade Commission, Investigation No. 337-TA-1276, 1019 pages. [uploaded in 9 parts].
Feb. 9, 2022 Respondent Apple Inc.'s Motion for Leave to File Amended Response to the First Amended Complaint, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., United States International Trade Commission, Investigation No. 337-TA-1276, 4 pages.
Feb. 9, 2022 Memorandum in support of Respondent Apple Inc.'s Motion for Leave to File Amended Response to the First Amended Complaint, and including Exhibits 1 (with Exhibits A-J) and 2, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., United States International Trade Commission, Investigation No. 337-TA-1276, 1477 pages. [uploaded in 2 parts].
Feb. 10, 2022 Complainants' Rebuttal Claim Construction Brief, and including Exhibits 17-21, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., United States International Trade Commission, Investigation No. 337-TA-1276, 59 pages.
Feb. 10, 2022 Respondent Apple Inc.'s Rebuttal Markman Brief, and including Exhibit 8, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., United States International Trade Commission, Investigation No. 337-TA-1276, 21 pages.
Feb. 15, 2022 Respondent Apple Inc.'s Notice of Prior Art, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., United States International Trade Commission, Investigation No. 337-TA-1276, 15 pages.
Feb. 17, 2022 Hearing Transcript, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., United States International Trade Commission, Investigation No. 337-TA-1276, 106 pages.
Feb. 18, 2022 Complainants' Opposition to Respondent's Motion for Leave to File Amended Response to the First Amended Complaint, and including Exhibits A-J, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., United States International Trade Commission, Investigation No. 337-TA-1276, 691 pages. [uploaded in 5 parts].
Feb. 18, 2022 Respondent Apple Inc.'s Rebuttal Claim Construction Evidence, and including Exhibit 9, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., United States International Trade Commission, Investigation No. 337-TA-1276, 12 pages.
Feb. 23, 2022 Respondent Apple Inc.'s Reply in support of its Motion for Leave to File Amended Response to First Amended Complaint (Motion No. 1276-018), and including Exhibit 3, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., United States International Trade Commission, Investigation No. 337-TA-1276, 65 pages.
Feb. 23, 2022 Updated Joint Proposed Claim Construction Chart, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., United States International Trade Commission, Investigation No. 337-TA- 1276, 6 pages.
Apr. 11, 2022 Order No. 24 Granting-in-Part and Denying-in-Part Respondent's Motion for Leave to File Amended Response to the Complaint to Add Affirmative Defenses, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., United States International Trade Commission, Investigation No. 337-TA- 1276, 10 pages.
May 13, 2022 Complainants' Pre-Hearing Brief, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., United States International Trade Commission, Investigation No. 337-TA-1276, 274 pages.
May 16, 2022 Respondent Apple Inc.'s Corrected Pre-Hearing Brief, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., United States International Trade Commission, Investigation No. 337-TA- 1276, 264 pages.
Jun. 27, 2022 Complainants' Initial Post-Hearing Brief and including Complainants' Final Exhibit Lists, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., United States International Trade Commission, Investigation No. 337-TA-1276, 434 pages. [uploaded in 3 parts].
Jun. 27, 2022 Respondent Apple Inc.'s Post-Hearing Brief and including Respondent's Final Exhibit Lists and Respondent's Corrected Final Exhibit Lists, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., United States International Trade Commission, Investigation No. 337-TA-1276, 338 pages.
Jul. 11, 2022 Respondent Apple Inc.'s Reply Post-Hearing Brief, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., United States International Trade Commission, Investigation No. 337-TA- 1276, 191 pages.
Jul. 11, 2022 Complainants' Reply Post-Hearing Brief, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., United States International Trade Commission, Investigation No. 337-TA-1276, 217 pages. [uploaded in 2 parts].
Aug. 19, 2022 Complainant's Corrected Initial Post-Hearing Brief, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., United States International Trade Commission, Investigation No. 337-TA-1276, 380 pages. [uploaded in 9 parts].
Sep. 19, 2022 Respondent's Corrected Reply Post-Hearing Brief, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., United States International Trade Commission, Investigation No. 337-TA- 1276, 191 pages.
Sep. 14, 2022 Respondent's Second Corrected Reply Post-Hearing Brief, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., United States International Trade Commission, Investigation No. 337-TA- 1276, 312 pages.
Feb. 22, 2022 Deposition Transcript of Robert Rowe, Ph.D., Masimo Corp et al. v. Apple Inc., ITC Inv. No 337-TA-1276, pp. 213.
Jun. 6, 2022 through Jun. 12, 2022 Masimo Corp et al. v. Apple Inc., Public Hearing Transcript, ITC Inv. No 337-TA-1276, pp. 670.
Jan. 10, 2023 Notice of Final Initial Determination on Violation of Section 337, Inv. No 337-TA-1276, pp. 2.
Jan. 10, 2023 Final Initial Determination on Violation of Section 337, Inv. No 337-TA-1276, pp. 342. [Submitted in 10 parts].
Jan. 23, 2023 Respondent Apple Inc.'s Summary of Petition for Review of the Initial Determination of Violation of Section 337, Inv. No 337-TA-1276, pp. 25.
Jan. 24, 2023 Recommended Determination in Remedy and Bonding, Inv. No 337-TA-1276, pp. 7.
Jan. 31, 2023 Respondent Apple Inc.'s Response to Complainants' Petition for Review, Inv. No 337-TA- 1276, pp. 105.
Jan. 31, 2023 Respondent Apple Inc.'s Summary of its Response to Complainants' Petition for Review, Inv. No 337-TA-1276, pp. 25.
Feb. 2, 2023 Complainants' Petition for Review of the Final Initial Determination on Violation of Section 337, Inv. No 337-TA-1276, pp. 104.
Feb. 2, 2023 Complainants' Summary of Petition for Review of the Final Initial Determination on Violation of Section 337, Inv. No 337-TA-1276, pp. 13.
Feb. 2, 2023 Respondent Apple Inc.'s Petition for Review of the Initial Determination of Violation of Section 337, Inv. No 337-TA-1276, pp. 120.
Feb. 10, 2023 Complainants' Response to Apple Inc.'s Petition for Review of the Final Initial Determination on Violation of Section 337, Inv. No 337-TA-1276, pp. 297.
Feb. 10, 2023 Complainants' Summary of Response to Apple's Petition for Review of the Final Initial Determination on Violation of Section 337, Inv. No 337-TA-1276, pp. 13.
May 15, 2023 Notice of a Commission Determination to Review in Part a Final Initial Determination; Request for Written Submissions on the Issues Under Review and on Remedy, The Public Interest, and Bonding, Inv. No 337-TA-1276, pp. 7.
International Trade Commission, Determination to Review, Federal Register, vol. 88, No. 97, May 19, 2023, Investigation No. 337-TA-1276, pp. 32243-32246.
Jun. 12, 2023 Complainant's Reply to Apple Inc.'s Response to the Comission's Notice to Review in Part a Final Initial Determination and Request for Written Submissions, Inv. No. 337-TA-1276, pp. 65.
Jun. 12, 2023 Exhibits 54-93 for Complainants' Reply to Apple Inc.'s Response to the Commission's Notice to Review in Part a Final Initial Determination and Request for Written Submissions, Inv. No 337-TA-1276, pp. 590.
Jun. 15, 2023 Complainants' Submission in Response to the Commission's May 15, 2023 Notice of Commission Determination to Review in Part, Inv. No 337-TA-1276, pp. 130.
Jun. 15, 2023 Exhibits 1-53 of Complainants' Submission in Response to the Commission's May 15, 2023 Notice of Commission Determination to Review in Part, Inv. No 337-TA-1276, pp. 781. [uploaded in 2 parts].
Jun. 15, 2023 Respondent Apple Inc.'s Response to the Commissions' Notice to Review in Part a Final Initial Determination and Request for Written Submissions, Inv. No 337-TA-1276, pp. 263.
Jun. 22, 2023 Respondent Apple Inc.'s Reply to Complainants' Response to the Commission's Notice to Review in Part a Final Initial Determination and Request for Written Submissions, Inv. No 337-TA-1276, pp. 60.
Jun. 23, 2023 Notice of Denial of Respondent Apple Inc.'s Request for Rehearing of Decisions Denying Institution of Inter Partes Review for U.S. Pat. No. 10,945,648, Inv. No 337-TA-1276, pp. 5.
Jun. 23, 2023 Exhibits A & B for Notice of Denial of Respondent Apple Inc.'s Request for Rehearing of Decisions Denying Institution of Inter Partes Review for U.S. Pat. No. 10,945,648, Inv. No 337-TA-1276, pp. 19.
Oct. 26, 2023 Notice of the Commission's Final Determination Finding a Violation of Section 337; Issuance of a Limited Exclusion Order and a Cease and Desist Order; Termination Of The Investigation, Inv. No 337- TA-1276, pp. 4.
Oct. 26, 2023 Limited Exclusion Order, Inv. No 337-TA-1276, pp. 4.
Oct. 30, 2023 Respondent Apple Inc.'s Motion to Stay Exclusion and Cease and Desist Orders Pending Appeal and/or in light of the Potential Government Shutdown, Inv. No 337-TA-1276, pp. 36.
International Trade Commission, Determination to Review, Federal Register, vol. 88, No. 210, Nov. 1, 2023, Investigation No. 337-TA-1276, pp. 75032-75033.
Nov. 9, 2023 Complainants' Opposition to Respondent Apple Inc.'s Motion to Stay Exclusion and Cease and Desist Orders Pending Appeal and/or in light of the Potential Government Shutdown, Inv. No 337-TA-1276, pp. 124.
Nov. 14, 2023 Commission Opinion [Public Version], Inv. No 337-TA-1276, pp. 124.
Dec. 26, 2023 Appellant Apple Inc.'s Non-Confidential Emergency Motion for an Immediate Interim Stay Pending Disposition of Motion for Stay Pending Appeal, Inv. No 337-TA-1276, pp. 15.
Dec. 26, 2023 Appellant Apple Inc.'s Non-Confidential Emergency Motion to Stay Enforcement of ITC's Orders Pending Review in Inter Partes Review, Inv. No 337-TA-1276, pp. 939. [Uploaded in 4 parts].
Dec. 26, 2023 Apple Inc.'s Petition for Review and Notice of Appeal Regarding U.S. Pat. Nos. 10,912,502 and 10,945,648, Inv. No 337-TA-1276, pp. 492. [Uploaded in 3 parts].
Jan. 3, 2024 Commission Opinion Denying Respondent's Motion to Stay the Remedial Orders [Public Version], Inv. No 337-TA-1276, pp. 14.
Jan. 10, 2024 Appellee International Trade Commission's Nonconfidential Response in Opposition to Appellant's Motion for a Stay Pending Appeal, Inv. No 337-TA-1276, pp. 137.
Jan. 10, 2024 Masimo Corporation and Cercacor Laboratories, Inc.'s Nonconfidential Opposition to Apple Inc.'s Emergency Motion to Stay Enforcement of ITC's Orders Pending Review, Inv. No 337-TA-1276, p. 34.
Jan. 10, 2024 Addendum, Declaration of Joe Kiani in Support of Masimo Corporation and Cercacor Laboratories, Inc.'s Opposition to Apple's Emergency Motion to Stay Enforcement Of ITC's Order Pending Review, Inv. No 337-TA-1276, pp. 67.
Jan. 10, 2024 Masimo Exhibits: Part 1 in Support of Opposition, Inv. No 337-TA-1276, pp. 468.
Jan. 10, 2024 Masimo Exhibits: Part 2 in Support of Opposition, Inv. No 337-TA-1276, pp. 138.
Jan. 12, 2024 Ruling; U.S. Customs and Border Protection; U.S. International Trade Commission; Limited Exclusion Order; Hq H335304, Inv. No. 337-TA-1276; pp. 31.
Jan. 15, 2024 Non-Confidential Reply in Support of Appellant Apple Inc.'s Emergency Motion to Stay Enforcement of ITC's Orders Pending Review, Inv. No 337-TA-1276, pp. 123.
Design of Pulse Oximeters, J.G. Webster, Institution of Physics Publishing, IOP Publishing Ltd, 1997, 131 pages (uploaded in 2 parts).
V. Konig et al., “Reflectance Pulse Oximetry—Principles and Obstetric Application in the Zurich System,” Journal of Clinical Monitoring and Computing, vol. 14, No. 6, Aug. 1998, pp. 403-412.
Y. Mendelson, et al., “A Wearable Reflectance Pulse Oximeter for Remote Physiological Monitoring”, Proceedings of the 28th IEEE Embs Annual International Conference, 2006, pp. 912-915.
Y. Mendelson, et al., “Measurement Site and Photodetector Size Considerations in Optimizing Power Consumption of a Wearable Reflectance Pulse Oximeter”, Proceedings of the 25th IEEE Embs Annual International Conference, 2003, pp. 3016-3019.
Y. Mendelson, et al., “Design and Evaluation of a New Reflectance Pulse Oximeter Sensor”, WorcesterPolytechnic Institute, Biomedical Engineering Program, Worcester, MA 01609, Association for the Advancement of Medical Instrumentation, vol. 22, No. 4, 1988, pp. 167-173.
Y. Mendelson, et al., “Skin Reflectance Pulse Oximetry: In Vivo Measurements from the Forearm and Calf”, Journal of Clinical Monitoring, vol. 7, No. 1, Jan. 1991, pp. 7-12.
G. Comtois et al., “A Comparative Evaluation of Adaptive Noise Cancellation Algorithms for Minimizing Motion Artifacts in a Forehead-Mounted Wearable Pulse Oximeter,” Proceedings of the 29th Annual International Conference of the IEEE EMBS, Aug. 2007, pp. 1528-1531.
Y. Mendelson et al., “A Multiwavelength VIS-NIR Spectrometer for Pulsatile Measurement of Hemoglobin Derivatives in Whole Blood,” 18th Annual International Conference of the IEEE Engineering in Medicine and Biology Society, 1996, pp. 134-135.
R. P. Dresher et al., “A New Reflectance Pulse Oximeter Housing to Reduce Contact Pressure Effects,” Proceedings of the IEEE 32nd Annual Northeast Bioengineering Conference, 2006, pp. 49-50.
G. Comtois et al., “A Noise Reference Input to an Adaptive Filter Algorithm for Signal Processing in a Wearable Pulse Oximeter,” IEEE 33rd Annual Northeast Bioengineering Conference, 2007, pp. 106-107.
Y. Mendelson et al., “An In Vitro Tissue Model for Evaluating the Effect of CarboxyhemoglobinConcentration on Pulse Oximetry,” IEEE Transactions on Biomedical Engineering, vol. 36, No. 6, Jun. 1989, pp. 625-627.
Y. Mendelson et al., Chapter 9: Biomedical Sensors, Introduction to Biomedical Engineering, Second Edition, Apr. 2005, pp. 505-548.
Y. Mendelson et al., “Blood Glucose Measurement by Multiple Attenuated Total Reflection and Infrared Absorption Spectroscopy,” IEEE Transactions on Biomedical Engineering, vol. 37, No. 5, May 1990, pp. 458-465.
Y. Mendelson et al., “Carbon dioxide laser based multiple ATR technique for measuring glucose in aqueous solutions,” Applied Optics, vol. 27, No. 24, Dec. 1988, pp. 5077-5081.
Y. Mendelson et al., “Evaluation of the Datascope ACCUSAT Pulse Oximeter in Healthy Adults,” Journal of Clinical Monitoring, vol. 4, No. 1, Jan. 1988, pp. 59-63.
W. S. Johnston et al., “Extracting Breathing Rate Information from a Wearable Reflectance Pulse Oximeter Sensor,” Proceedings of the 26th Annual International Conference of the IEEE Embs, Sep. 2004, pp. 5388-5391.
W. Johnston et al., “Extracting Heart Rate Variability from a Wearable Reflectance Pulse Oximeter,” Proceedings of the IEEE 31st Annual Northeast Bioengineering Conference, 2005, pp. 1-2.
W. S. Johnston et al., “Investigation of Signal Processing Algorithms for an Embedded Microcontroller-Based Wearable Pulse Oximeter,” Proceedings of the 28th IEEE Embs Annual International Conference, Sep. 2006, pp. 5888-5891.
P. C. Branche et al., “Measurement Reproducibility and Sensor Placement Considerations in Designinga Wearable Pulse Oximeter for Military Applications,” Proceedings of the IEEE 30th Annual Northeast Bioengineering Conference, 2004, pp. 216-217.
Y. Mendelson et al., “Multi-channel pulse oximetry for wearable physiological monitoring,” IEEE International Conference on Body Sensor Networks, 2013, pp. 1-6.
Y. Mendelson et al., “Noninvasive Pulse Oximetry Utilizing Skin Reflectance Photoplethysmography,” IEEE Transactions on Biomedical Engineering, vol. 35, No. 10, Oct. 1988, pp. 798-805.
Y. Mendelson et al., “Noninvasive Transcutaneous Monitoring of Arterial Blood Gases,” IEEE Transactions on Biomedical Engineering, vol. BME-31, No. 12, Dec. 1984, pp. 792-800.
M. Savage et al., “Optimizing Power Consumption in the Design of a Wearable Wireless Telesensor:Comparison of Pulse Oximeter Modes,” IEEE 29th Annual Proceedings of Bioengineering Conference, 2003, pp. 150-151.
C. Pujary et al., “Photodetector Size Considerations in the Design of a Noninvasive Reflectance PulseOximeter for Telemedicine Applications,” Proceedings of the IEEE 29th Annual Bioengineering Conference, 2003, pp. 148-149.
S. M. A. Salehizadeh et al., “Photoplethysmograph Signal Reconstruction based on a Novel MotionArtifact Detection-Reduction Approach. Part II: Motion and Noise Artifact Removal,” Annals of Biomedical Engineering, vol. 42, May 2014, pp. 2251-2263.
Y. Mendelson et al., Pulse Oximetry: Theory and Applications for Noninvasive Monitoring, Clinical Chemistry, vol. 38, No. 9, 1992, pp. 1601-1607.
Y. Mendelson, Pulse Oximetry, PowerPoint, UMass Center for Clinical and Translational Science Research Retreat, 2017, 22 pages.
E. Stohr et al., “Quantitative FT-IR Spectrometry of Blood Constituents,” 14th Annual International Conference of the IEEE Engineering in Medicine and Biology Society, 1992, pp. 173-174.
R. P. Dresher et al., “Reflectance Forehead Pulse Oximetry: Effects of Contact Pressure During Walking,” Proceedings of the 28th IEEE Embs Annual International Conference, Sep. 2006, pp. 3529-3532.
P. Branche et al., “Signal Quality and Power Consumption of a New Prototype Reflectance PulseOximeter Sensor,” Proceedings of the IEEE 31st Annual Northeast Bioengineering Conference, 2005, pp. 1-2.
C. Tamanaha et al., “Surface Modification of y-AI203 Filters by Chemisorption of Alkyltrichlorosilane Molecules,” 18th Annual International Conference of the IEEE Engineering in Medicine and Biology Society, 1996, pp. 2069-2070.
Y. Mendelson et al., “Variations in Optical Absorption Spectra of Adult and Fetal Hemoglobins and Its Effect on Pulse Oximetry,” IEEE Transactions on Biomedical Engineering, vol. 36, No. 8, Aug. 1989, pp. 844-848.
K. Chon et al., “Wearable Wireless Sensor for Multi-Scale Physiological Monitoring,” Worcester Polytechnic Institute, Oct. 2015, 142 pages.
S. Takatani et al., “Experimental and Clinical Evaluation of a Noninvasive Reflectance Pulse Oximeter Sensor,” Journal of Clinical Monitoring, vol. 8, No. 4, Oct. 1992, pp. 257-266.
B. F. Koegh et al., “Recent findings in the use of reflectance oximetry: a critical review,” Current Opinion in Anaesthesiology, vol. 18, 2005, pp. 649-654.
Oct. 20, 2020 Letter from B. K. Andrea to J. Re et al., Re: Masimo Corp, et al. v. Apple, Inc., C.A. 8:20-cv-00048 (C.D. Cal.), 19 pages.
3 pages of images, identified by bates numbers “APL-MAS_00057600”, “APL-MAS_00057601”, and “APL-MAS_00057602”. Undated.
2 pages of images, identified by bates numbers “APL-MAS_00057598” and “APL-MAS_00057599”. Undated.
Y. Mendelson et al., “A Mobile PDA-Based Wireless Pulse Oximeter,” Proceedings of the IASTED International Conference, Jul. 2005, pp. 1-6.
Y. Mendelson et al., A Wearable Reflectance Pulse Oximeter for Remote Physiological Monitoring, PowerPoint, The Bioengineering Institute, Worcester Polytechnic Institute, 18 pages. Undated.
Y. Mendelson et al., A Wireless Wearable Reflectance-Based Forehead Pulse Oximeter, PowerPoint, The Bioengineering Institute, Worcester Polytechnic Institute, 8 pages. Undated.
Y. Mendelson et al., “Accelerometery-Based Adaptive Noise Cancellation for Remote Physiological Monitoring by a Wearable Pulse Oximeter,” Proceedings of the 3rd IASTED International Conference on Telehealth, May 2007, pp. 28-33.
C. J. Pujary, “Investigation of Photodetector Optimization in Reducing Power Consumption by aNoninvasive Pulse Oximeter Sensor,” Master thesis, Worcester Polytechnic Institute, Jan. 2004, 133 pages.
Y. Mendelson et al., “Minimization of LED Power Consumption in the Design of a Wearable PulseOximeter,” Proceedings of the IASTED International Conference Biomedical Engineering, Jun. 2003, pp. 249-254.
Y. Mendelson et al., “The Feasibility of Measuring SpO2 from the Head Using a Reflectance Pulse Oximeter: Effect of Motion Artifacts,” Proceeding of the 3rd European Medical & Biological Engineering Conference, 2005, 5 pages.
R. Dresher, “Wearable Forehead Pulse Oximetry: Minimization of Motion and Pressure Artifacts,” Master thesis, Worcester Polytechnic Institute, May 2006, 93 pages.
Y. Mendelson, “Wearable, Wireless, Noninvasive Physiological Sensing,” The Bioengineering Institute, Worcester Polytechnic Institute, 2005, 2 pages.
Y. Mendelson et al., “Wireless Reflectance Pulse Oximetery for Remote Triage Application,” Worcester Polytechnic Institute, 1 page. Undated.
Jan. 9, 2020 Complaint for (1) Patent Infringement (2) Trade Secret Misappropriation and (3) Ownership of Patents and Demand for Jury Trial, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., Case No. 8:20-cv-00048, 64 pages.
Mar. 25, 2020 First Amended Complaint for (1) Patent Infringement (2) Trade Secret Misappropriation (3) Correction of Inventorship and (4) Ownership of Patents and Demand for Jury Trial, and including Exhibits 13-24 (Exhibits 1-12 and 25-31 comprise copies of publicly available U.S. patents and U.S. patent application publications, and are not included herein for ease of transmission), Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., Case No. 8:20-cv-00048, pp. 1-94, 983-1043 (total of 156 pages).
Jul. 24, 2020 Second Amended Complaint for (1) Patent Infringement (2) Trade Secret Misappropriation (3) Correction of Inventorship and (4) Ownership of Patents and Demand for Jury Trial, and including Exhibit 1, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., Case No. 8:20-cv-00048, 182 pages.
Jul. 27, 2020 Plaintiffs' Infringement Contentions, and including Exhibit 1 and Appendices A-P, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., Case No. 8:20-cv-00048, 305 pages.
Sep. 8, 2020 Apple's Preliminary Invalidity Contentions, and including Exhibits A-G, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., Case No. 8:20-cv-00048, 3960 pages. [uploaded in 15 parts].
Sep. 16, 2020 Public Order Regarding Masimo's Motion for Preliminary Injunction, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., Case No. SACV 20-00048, 14 pages.
Nov. 11, 2020 Third Amended Complaint for (1) Patent Infringement (2) Trade Secret Misappropriation (3) Correction of Inventorship and (4) Ownership of Patents and Demand for Jury Trial, and including Exhibit 1, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., Case No. 8:20-cv-00048, 196 pages. [uploaded in 2 parts].
Feb. 3, 2021 Defendant Apple Inc.'s Answer to Plaintiffs' Third Amended Complaint and Demand for Jury Trial, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., Case No. 8:20-cv-00048, 72 pages.
Feb. 5, 2021 Fourth Amended Complaint for (1) Patent Infringement (2) Trade Secret Misappropriation (3) Correction of Inventorship and (4) Ownership of Patents and Demand for Jury Trial, and including Exhibit 1, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., Case No. 8:20-cv-00048, 207 pages.
Feb. 24, 2021 Defendant Apple Inc.'s Amended Answer to Plaintiffs' Third Amended Complaint and\|Demand for Jury Trial, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., Case No. 8:20-cv-00048, 85 pages.
May 5, 2021 Defendant Apple Inc.'s Amended Answer to Plaintiffs' Fourth Amended Complaint and Demand for Jury Trial, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., Case No. 8:20-cv-00048, 90 pages.
Jun. 6, 2022 First Supplement to the Fourth Amended Complaint and Demand for Jury Trial, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., Case No. 8:20-cv-00048, 7 pages.
Jun. 27, 2022 Defendant Apple Inc.'s Answer to Plaintiffs' First Supplement to the Fourth Amended Complaint and Demand for Jury Trial, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., Case No. 8:20-cv-00048, 7 pages.
Jan. 29, 2024 Plaintiff's Memorandum in Support of Motion to Lift Patent Stay, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., Case No. 8:20-cv-00048, 10 pages.
Feb. 5, 2024 Defendant Apple Inc.'s Opposition to Plaintiffs' Motion to Lift the Patent Stay, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., Case No. 8:20-cv-00048, 23 pages.
Feb. 12, 2024 Plaintiff's Reply Memorandum in Support of Motion to Lift Patent Stay, Masimo Corporation and Cercacor Laboratories, Inc. v. Apple Inc., Case No. 8:20-cv-00048, 18 pages.
Bacchillone, et al. “A flexible home gateway system for telecare of patients affected by chronic heart failure,” APL_DEL00032311, 2011, in 4 pages.
Bailey, et al. “Development of a Remote Pulse Oximeter,” APL_DEL00032315, 2010, in 91 pages.
Chang, et al. “Microlens array diffuser for a light-emitting diode backlight system,” APL_DEL00030110, 2+B256006, in 4 pages.
Donati, et al. “A flexible home monitoring platform for patients affected by chronic heart failure directly integrated with the remote Hospital Information System,” APL_DEL00032456, 2011, in 8 pages.
Fantini, et al. “Frequency-domain multichannel optical detector for noninvasive tissue spectroscopy and oximetry,” APL_DEL00037609, 1995, in 12 pages.
Lin, et al. “Wireless PDA-Based Physiological Monitoring System for Patient Transport,” APL_DEL00031220, Dec. 2004, in 9 pages.
Moyle, “Pulse Oximetry,” APL_DEL00031253, 2002, in 192 pages.
Nogawa, et al. “New hybrid reflectance optical pulse oximetry sensor for lower oxygen saturation measurement and for broader clinical application,” APL_DEL00037781, 1997, in 11 pages.
Rodrigues, et al. “Using Discovery and Monitoring Services to Support Context-Aware Remote Assisted Living Applications,” APL_DEL00036886, 2009, in 6 pages.
Tablado, et al. “A Flexible Data Processing Technique for a Tele-assistance System of Elderly People,” APL_DEL00032254, 2004, in 24 pages.
“A New Family of Sensors for Pulse Oximetry,” Hewlett-Packard Journal, Feb. 1997 (APL_DEL00037653), in 17 pages. Apple alleges that this reference has a prior art date of 1997.
“A Technology Overview of the Nellcor OxiMax Pulse Oximetry System,” Nellcor Technical Staff, 2003 (APL_DEL00031781, APL_DEL00037976), in 8 pages. Apple alleges that this reference has a prior art date of 2003.
“Masimo Signal Extraction Technology,” Masimo Corp., 2001 (APL_DEL00037764), in 8 pages. Apple alleges that this reference has a prior art date of 2003.
“Masimo Signal Extraction Technology: Technical Bulletin 1,” Masimo Corp., 2001 (APL_DEL00037757), in 7 pages. Apple alleges that this reference has a prior art date of 2003.
“Non-Invasive Cardiac Output Monitor Model 7300: User's Manual,” Novametrix, 2001 (APL_DEL00031974), in 100 pages. Apple alleges that this reference has a prior art date of 2001.
“NPB-195 Pulse Oximeter: Home Use Guide,” Nellcor, 1997 (APL_DEL00032149), in 105 pages. Apple alleges that this reference has a prior art date of 1999.
“NPB-195 Pulse Oximeter: Operator's Manual,” Mallinckrodt, 1999 (APL_DEL00032074), in 75 pages. Apple alleges that this reference has a prior art date of 1999.
“OxiMax N-595 Pulse Oximeter Operator's Manual,” Nellcor, 2002 (APL_DEL00031597, APL_DEL00037792), in 184 pages. Apple alleges that this reference has a prior art date of 2003.
“Oxinet II Monitoring System Operator's Manual,” Nellcor, 2002 (APL_DEL00031789), in 132 pages. Apple alleges that this reference has a prior art date of 2003.
“Oxinet III Central Station and Paging System,” Nellcor, 2003 (APL_DEL00031921), in 2 pages. Apple alleges that this reference has a prior art date of 2003.
“Oxinet III Service Manual,” Nellcor, 2005 (APL_DEL00031535), in 62 pages. Apple alleges that this reference has a prior art date of 2003.
“Pulse Oximetry Sensors: LNOP & NR,” Masimo SET, 2003 (APL_DEL00037755), in 2 pages. Apple alleges that this reference has a prior art date of 2003.
“Radical Signal Extraction Pulse Oximeter: Operator's Manual,” Masimo, 2001 (APL_DEL00034347), in 78 pages. Apple alleges that this reference has a prior art date of 2001.
“Sotera Wireless,” Tuck School of Business at Dartmouth: Center for Digital Strategies Case Series,Sep. 4, 2012 (APL_DEL00037109), in 20 pages. Apple alleges that this reference has a prior art date of 2011.
A Decision Support Service Platform for Neurodegenerative Disease Patients, Sixth International Conference on Networking and Services, 2010 (APL_DEL00034343), in 4 pages. Apple alleges that this reference has a prior art date of 2010.
Android-based Healthcare Smartphone Packed with Medical Sensors, Jul. 5, 2012 (APL_DEL00038072), in 3 pages. Apple alleges that this reference has a prior art date of 2012.
Code-Stat 10 Basic Annotation Guide, 2015 (APL_DEL00032565), in 62 pages. Apple alleges that this reference has a prior art date of 2011.
Code-Stat data review software and service, Jun. 5, 2023 (APL_DEL00032627), in 4 pages. Apple alleges that this reference has a prior art date of 2011.
DC Rainmaker, Fitbit Surge In-Depth Review, Jan. 20, 2015 (“Surge Review”) (APL_DEL00030150), in 109 pages. Apple alleges that this reference has a prior art date of May 2015.
Dynamic Adaptive Remote Health Monitoring for Patients with Chronic Disease, University of California, LosAngeles, 2012 (APL_DEL00038075), in 127 pages. Apple alleges that this reference has a prior art date of 2012.
Fitbit, Fitbit Surge Fitness Super Watch User Manual Version 1.0 (“Surge Manual”) (APL_DEL00030259), in 49 pages. Apple alleges that this reference has a prior art date of May 2015.
Fitbit's New Fitness Watch Can Display Your Calls And Track Your Location While You Run, Oct. 27, 2014 (“Fitbit's New Fitness Watch”) (APL_DEL00030308), in 5 pages. Apple alleges that this reference has a prior art date of May 2015.
Hamamatsu, “Lens for Side-on Type Photomultiplier Tubes” (Mar. 1999) (APL_DEL00037641), in 4 pages. Apple alleges that this reference has a prior art date of Mar. 1999.
How ViSi Mobile Can Help With Infectious Disease / Sotera ViSi Mobile Brochures (APL_DEL00036979), in 1 page. Apple alleges that this reference has a prior art date of 2011.
https://www.stryker.com/US/en/emergencycare/products/lifepak-15.html (APL_DEL00033792), in 6 pages. Apple alleges that this reference has a prior art date of 2011.
Human-Centered Phone Oximeter Interface Design for the Operating Room, Proceedings of theInternational Conference on Health Informatics, SciTePress (APL_DEL00032489), in 6 pages. Apple alleges that this reference has a prior art date of 2011.
Ideal Life SpO2 Manager, 2011 (APL_DEL00038204), in 2 pages. Apple alleges that this reference has a prior art date of 2012.
IntelliVue MX40 Brochures, Mar. 2016 (APL_DEL00036603), in 8 pages. Apple alleges that this reference has a prior art date of Feb. 2012.
IntelliVue MX40 Brochures (APL_DEL00036821), in 3 pages. Apple alleges that this reference has a prior art date of Feb. 2012.
IntelliVue MX40 Brochures, Jan. 2020 (APL_DEL00036861), in 17 pages. Apple alleges that this reference has a prior art date of Feb. 2012.
IntelliVue MX40 Brochures (APL_DEL00036878), in 8 pages. Apple alleges that this reference has a prior art date of Feb. 2012.
IntelliVue MX40 Installation and Service, Jun. 2012 (APL_DEL00035983), in 158 pages. Apple alleges that this reference has a prior art date of Feb. 2012.
IntelliVue MX40 Instructions for Use, Feb. 2012 (APL_DEL00036141), in 246 pages. Apple alleges that this reference has a prior art date of Feb. 2012. [Uploaded in 2 parts].
IntelliVue MX40 Instructions for Use, Jun. 2011 (APL_DEL00036611), in 210 pages. Apple alleges that this reference has a prior art date of Feb. 2012.
IntelliVue MX40 with Masimo SET Reusable Adapter and Patient Cables Instructions for Use, 2020 (APL_DEL00036387), in 206 pages. Apple alleges that this reference has a prior art date of Feb. 2012.
LifePak 15 Monitor Defibrillator Operating Instructions, Jun. 2015 (APL_DEL00032631), in 284 pages. Apple alleges that this reference has a prior art date of 2011. [Uploaded in 2 parts].
LifePak 15 Monitor Defibrillator Power Module Upgrade (APL_DEL00032915), in 52 pages. Apple alleges that this reference has a prior art date of 2011.
LifePak 15 Monitor Defibrillator Service Manuals, Mar. 2019 (APL_DEL00032967), in 507 pages. Apple alleges that this reference has a prior art date of 2011. [Uploaded in 2 parts].
LifePak 15 Monitor Defibrillator Service Manuals, Jun. 2015 (APL_DEL00033798), in 527 pages. Apple alleges that this reference has a prior art date of 2011. [Uploaded in 2 parts].
LifePak 15 Operating Instructions, Jan. 2019 (APL_DEL00033474), in 318 pages. Apple alleges that this reference has a prior art date of 2011. [Uploaded in 3 parts].
LifeWatch V User Manual, 2012 (APL_DEL00038208), in 136 pages. Apple alleges that this reference has a prior art date of 2012.
LifeWatch V, A smartphone that connects to you, Jul. 7, 2012 (APL_DEL00038344), in 1 page. Apple alleges that this reference has a prior art date of 2012.
Lucas 3 Quick User Guide (APL_DEL00034325), 2020, in 5 pages. Apple alleges that this reference has a prior art date of 2011.
Microsoft HealthVault Drivers - Installation Quick Start Guide (APL_DEL00034971), in 4 pages. Apple alleges that this reference has a prior art date of 2008.
Microsoft HealthVault Service Specification, Mar. 27, 2009 (APL_DEL00034580), in 391 pages. Apple alleges that this reference has a prior art date of 2008.
Model 3150 WristOx2 Operator's Manual and 3150SC USB Cable Driver Software (APL_DEL00035230), in 699 pages. Apple alleges that this reference has a prior art date of 2011. [Uploaded in 6 parts].
Nellcor N-3000 Pulse Oximeter Service Manual, 1996 (APL_DEL00034470), in 110 pages. Apple alleges that this reference has a prior art date of 1996.
Nonin Comparative Accuracy Testing of Nonin PureSAT, Nov. 8, 2004 (APL_DEL00034975), in 6 pages. Apple alleges that this reference has a prior art date of 2008.
Nonin nVision Operator's Manual (APL_DEL00035127), 2017, in 54 pages. Apple alleges that this reference has a prior art date of 2008.
Nonin nVision SpO2 Data Management Software (APL_DEL00035111), 2009, in 4 pages. Apple alleges that this reference has a prior art date of 2008.
Nonin nVision User Guide (APL_DEL00035018), 2014, in 89 pages. Apple alleges that this reference has a prior art date of 2008.
Nonin OEM Family Brochure (APL_DEL00035115), 2005, in 12 pages. Apple alleges that this reference has a prior art date of 2008.
Nonin Onyx II 9560 User Manual (APL_DEL00035014), 2008, in 4 pages. Apple alleges that this reference has a prior art date of 2008.
Nonin Onyx II Model 9560 Finger Pulse Oximeter Instructions for Use—English (APL_DEL00034981), 2012, in 9 pages. Apple alleges that this reference has a prior art date of 2008.
Nonin Pulse Oximeter Avant 4100 Service Manual (APL_DEL00035929), 2005, in 44 pages. Apple alleges that this reference has a prior art date of 2008.
Nonin Sample nVision Report (APL_DEL00035107), in 4 pages. Apple alleges that this reference has a prior art date of 2008.
Nonin WristOx 3100 Operator's Manual (APL_DEL00035187), 2005, in 43 pages. Apple alleges that this reference has a prior art date of 2011.
Nonin WristOx2 3150 Bluetooth Connection Tutorial (APL_DEL00034990), in 20 pages. Apple alleges that this reference has a prior art date of 2011.
OxiMax N-595 Pulse Oximeter Home Use Guide APL_DEL00031445), in 90 pages. Apple alleges that this reference has a prior art date of 2003.
PAS: A Wireless-Enabled, Cell-Phone-Incorporated Personal Assistance System for Independent and Assisted Living, 28th International Conference on Distributed Computing Systems, 2008 (APL_DEL00035973), in 10 pages. Apple alleges that this reference has a prior art date of 2008.
Philips IntelliVue Information Center iX Brochures (APL_DEL00036593), 2014, in 2 pages. Apple alleges that this reference has a prior art date of Feb. 2012.
Philips IntelliVue Information Center iX Brochures (APL_DEL00036595), Nov. 2015, in 8 pages. Apple alleges that this reference has a prior art date of Feb. 2012.
Philips IntelliVue Information Center iX Brochures (APL_DEL00036824), Sep. 2019, in 16 pages. Apple alleges that this reference has a prior art date of Feb. 2012.
Philips IntelliVue Information Center iX Brochures, Jun. 2015 (APL_DEL00036842), in 4 pages. Apple alleges that this reference has a prior art date of Feb. 2012.
Philips IntelliVue Information Center iX Brochures, Apr. 2015 (APL_DEL00036846), in 4 pages. Apple alleges that this reference has a prior art date of Feb. 2012.
Philips IntelliVue Information Center iX Brochures, Jun. 2015 (APL_DEL00036850), in 4 pages. Apple alleges that this reference has a prior art date of Feb. 2012.
Philips IntelliVue Information Center iX Brochures, Jun. 2022 (APL_DEL00036854), in 7 pages. Apple alleges that this reference has a prior art date of Feb. 2012.
Philips IntelliVue Smart-Hopping Network Product Website (APL_DEL00036840), in 2 pages. Apple alleges that this reference has a prior art date of Feb. 2012.
Physio-Control Code-Stat 10.0 Data Review Software (APL_DEL00034330), in 2 pages. Apple alleges that this reference has a prior art date of 2011.
Sanofi-aventis and AgaMatrix Unveil iBGStar Plug-In Glucose Meter for the iPhone, Medgadget, Sep. 21, 2010 (APL_DEL00038345), in 4 pages. Apple alleges that this reference has a prior art date of 2010.
Sanofi-aventis to launch blood glucose monitoring devices, PharmaBiz.com, Sep. 22, 2010 (APL_DEL00038349), in 2 pages. Apple alleges that this reference has a prior art date of 2010.
Santa Barbara Cottage Hospital, Nonin's Onyx II Fingertip Pulse Oximeter, 2007 (APL_DEL00035181), in 4 pages. Apple alleges that this reference has a prior art date of 2008.
Sotera ViSi Mobile Brochures, Oct. 9, 2013 (APL_DEL00036984), in 2 pages. Apple alleges that this reference has a prior art date of 2011.
Sotera ViSi Mobile Brochures (APL_DEL00037129), in 6 pages. Apple alleges that this reference has a prior art date of 2011.
Sotera ViSi Mobile Brochures (APL_DEL00037305), Aug. 21, 2012, in 1 page. B258.
Sotera ViSi Mobile Brochures, 2018 (APL_DEL00037313), in 2 pages. Apple alleges that this reference has a prior art date of 2011.
Sotera ViSi Mobile Monitoring System Technical Reference Manual, Jul. 2015 (APL_DEL00036993), in 116 pages. Apple alleges that this reference has a prior art date of 2011.
Sotera ViSi Mobile Monitoring System User Manual, Aug. 2012 (APL_DEL00037135), in 170 pages. Apple alleges that this reference has a prior art date of 2011.
Sotera ViSi Mobile Technical Specifications, Oct. 9, 2013 (APL_DEL00036986), in 7 pages. Apple alleges that this reference has a prior art date of 2011.
SpO2 Accuracy of PureSAT Signal Processing Technology—The Onyx II, Aug. 8, 2006 (APL_DEL00035185), in 2 pages. Apple alleges that this reference has a prior art date of 2008.
ViSi Mobile Monitoring System 510(k) Summary, 2013 (APL_DEL00036980), in 4 pages. Apple alleges that this reference has a prior art date of 2011.
ViSi Mobile System General Information (APL_DEL00037307), in 6 pages. Apple alleges that this reference has a prior art date of 2011.
Wanda B.: Weight and Activity with Blood Pressure Monitoring System for Heart Failure Patients, 2010 (APL_DEL00038351), in 7 pages. Apple alleges that this reference has a prior art date of 2012.
Wayback Machine, Fitbit Surge Fitness Super Watch User Manual Version 1.0, May 2015 (“Wayback Machine: Fitbit Surge”) (APL_DEL00030689), in 1 page. Apple alleges that this reference has a prior art date of May 2015.
Wristox2, Model 3150 Wrist-worn Pulse Oximeter, 2011 (APL_DEL00035010), in 2 pages. Apple alleges that this reference has a prior art date of 2011.
Wristox2, Model 3150 Wrist-worn Pulse Oximeter, 2011 (APL_DEL00035012), in 2 pages. Apple alleges that this reference has a prior art date of 2011.
Screen captures from YouTube video clip entitled “LifeWatch V—Blood Oxygen Saturation Level Test Tutorial,” in 3 pages, uploaded on Jul. 8, 2013 by user “LifeWatchTech”. Retrieved from Internet: <https://www.youtube.com/watch?v=68UHtoo1KIY>. Corresponds to “LifeWatch V, Blood Oxygen Saturation Level Test Tutorial” (APL_DEL00038207). Apple alleges that this reference has a prior art date of 2012.
Screen captures from YouTube video clip entitled “LifeWatch V—A Smartphone that Connects to You,” in 9 pages, uploaded on Jul. 4, 2012 by user “LifeWatchTech”. Retrieved from Internet: <https://www.youtube.com/watch?v=A75GggZSWgc>. Corresponds to “LifeWatch V, A smartphone that connects to you” (APL_DEL00038206). Apple alleges that this reference has a prior art date of 2012.
Screen captures from YouTube video clip entitled “iBGStar REVIEW,” in 1 page, uploaded on Mar. 27, 2012 by user “Valerie Anne C”. Retrieved from Internet: < https://www.youtube.com/watch?v=OuGbNsh-pUc>. Corresponds to “Sanofi-aventis and AgaMatrix Unveil iBGStar Plug-In Glucose Meter for the iPhone, Medgadget” (APL_DEL00038203). Apple alleges that this reference has a prior art date of 2010.
Screen captures from YouTube video clip entitled “iBGStar bloedglucosemeter instructievideo,” in 5 pages, uploaded on Mar. 9, 2011 by user “gezondheidbovenalles”. Retrieved from Internet:\|<https://www.youtube.com/watch?v=ZIS-tTFfoUY>. Corresponds to “Sanofi-aventis and AgaMatrix Unveil iBGStar Plug-In Glucose Meter for the iPhone, Medgadget” (APL_DEL00038202). Apple alleges that this reference has a prior art date of 2010.
Screen captures from YouTube video clip entitled “Visi Mobile System for Vital Signs \| Sotera Wireless,” in 5 pages, uploaded on Aug. 29, 2012 by user “Eastman”. Retrieved from Internet: <https://www.youtube.com/watch?v=ug9U43bsn6g>. Corresponds to “ViSi Mobile Patient Monitoring System Promotional Video” (APL_DEL00037306). Apple alleges that this reference has a prior art date of 2011.
Mendelson et al., “A Wearable Reflectance Pulse Oximeter for Remote Physiological Monitoring”,Proceedings of the 28th IEEE Embs Annual International Conference, New York City, 2006, pp. 912-915. (APL_DEL00030452).
Webster, J G, “Design of Pulse Oximeters”, Medical Science Series, 1997, pp. 262. (APL_DEL00030690).
Ashley et al., “Cardiology Explained”, Remedica, 2004, pp. 257. [Uploaded in 2 parts].
Johns et al., “Adapting Qi-compliant wireless-power solutions to low-power wearable products”, Texas Instruments, Analog Applications Journal, 2Q, 2014, pp. 7.
“Android 4.2 Compatibility Definition”, Android Compatibility Program, chrome-extension://efaidnbmnnnibpcajpcglclefindmkaj/https://source.android.com/docs/compatibility/4.2/android-4.2-cdd.pdf, Jun. 10, 2013, pp. 36.
Chad, “Widget Tutorial Part 2—How to add lockscreen widgets on your device”,\|https://digibites.zendesk.com/hc/en-US/articles/200351831-Widget-tutorial-part-2-How-to-add-lockscreen-widgets-on-your-device, Jan. 25, 2016, pp. 11.
Ion et al., “Hands-on: Multiple users, lock screen widgets round out Android 4.2”, ARSTechnica,\|https://arstechnica.com/gadgets/2012/11/hands-on-multiple-users-lock-screen-widgets-round-out-android-4-2/, Nov. 14, 2012, pp. 12.
Samsung Galaxy S4, 4G LTE Smartphone, User Manual, 2013, pp. 260. [Uploaded in 3 parts].
Samsung GT-19500, User Manual, 2013, pp. 147.
Youtube, “Adidas MiCoach Smart Run review \| Engadget”, https://www.youtube.com/watch?v=k5LpMYOokVo, Nov. 20, 2013, pp. 4.
Youtube, “Agent Smartwatch”, https://www.youtube.com/watch?v=IsIEOILBuKM, Jun. 27, 2013, pp. 3.
Youtube, “Android 4.2 Lock Screen Widgets”, https://www.youtube.com/watch?v=ZpN8Wyu_z6Y, Nov. 12, 2012, pp. 6.
Youtube, “Galaxy S8 review, how does the home button feel? [4K]”, https://www.youtube.com/watch?v =_ DIHga3ByoE, Apr. 5, 2017, pp. 5.
Youtube, “Lg G Flex—How to reorganize page, app and widget”. https://www.youtube.com/watch?v=J_12W-MrkVM, Dec. 6, 2013, pp. 3.
Youtube, “LG G2 Quick Tips—Adding Widgets to the Home Screen”, https://www.youtube.com/watch?v=9xEwmiNoKok, Oct. 15, 2013, pp. 3.
Youtube, “Small, thin, and light LG Watch Style unboxing & review! (LG Watch Style Unboxing&Review)”, https://www.youtube.com/watch?v=IJYtazmdMI0, Mar. 24, 2017, pp. 5.
Youtube, “Samsung Galaxy S4 Lock Screen Widget Tutorial”, https://www.youtube.com/watch?v=oaWa905892s, Apr. 25, 2013, pp. 8.
Prior Use of Android Devices (“Android Prior Use”), Android versions: A living history from 1.0 to 14, available at https://www.computerworld.com/article/3235946/android-versions-a-living-history-from-1-0-to-today.html, pp. 18.
2012 LG Nexus 4 https://www.gsmarena.com/lg_nexus_4_e960-5048.php, pp. 4.
2013 Samsung Galaxy S4 https://www.gsmarena.com/samsung_i9500_galaxy_s4-5125.php, pp. 4.
2013 LG G2 https://www.gsmarena.com/lg_g2-5543.php, pp. 4.
2013 LG G Flex https://www.gsmarena.com/lg_g_flex-5806.php, pp. 4.
Apr. 2017 Samsung Galaxy S8, https://www.gsmarena.com/samsung_galaxy_s8-8161.php, pp. 3.
Android Device List Page https://www.androidheadlines.com/android-device-list-page. Sep. 13, 2023, pp. 8.
2014 LG G Watch W100 https://www.gsmarena.com/lg_g_watch_w100-7718.php, pp. 2.
2013 Adidas MiCoach Smart Run, https://www.cnet.com/reviews/adidas-micoach-smart-run-preview/, pp. 7.
Feb. 2017 LG Watch Style, https://www.gsmarena.com/lg_watch_style-8551.php, pp. 2.
Motorola, LG announce upcoming Android Wear smartwatches (Mar. 18, 2014), available at https://www.theverge.com/2014/3/18/5522340/motorola-Ig-announce-upcoming-android-wear-smartwatches, pp. 3.
Oranger Watch 2.0 from Oranger (Cheng Yi Family) Technology Co. Ltd.; May 31, 2015, pp. 5.
Y. Mendelson, “Wearable Wireless Pulse Oximetry for Physiological Monitoring,” PPL Workshop (2008), PPT Presentation, pp. 18.
Berbari, Edward J., “Principles of Electrocardiograma”, Biomedical Engineering Fundamentals, The Biomedical Engineering Handbook, 4th Ed., 2015, pp. 5.
Meziane et al., “Dry Electrodes for Electrocardiograma”, IOP Publishing, Physiological Measurement, 34 (2013) R47-R69.
Canfield, Douglas, “Drying and Curing Inks and Coatings on Glass”, Mar. 26, 2013, pp. 5. https://www.glassmagazine.com/article/drying-and-curing-inks-and-coatings-glass.
“Apple Watch Series 4: Beautifully redesigned with breakthrough communication, fitness and health capabilities,” archived on Sep. 12, 2018 by the Internet Organization's Wayback Machine at https://web.archive.org/web/20180912191250/https://www.apple.com/newsroom/2018/09/redesigned-apple-watch-series-4-revolutionizescommunication-fitness-and-health/, pp. 15.
“Your heart rate. What it means, and where on Apple Watch you'll find it,” archived on Jan. 23, 2019 by the Internet Organization's “Wayback Machine” at https://web.archive.org/web/20190123031906/https://support.apple.com/en-US/HT204666, pp. 4.
“Apple Watch Series 4—Health,” archived on Sep. 20, 2018 by the Internet Organization's “Wayback Machine” at https://web.archive.org/web/20180920103403/https:/www.apple.com/apple-watch-series-4/health/, pp. 18.
“Charge Apple Watch,” https://support.apple.com/guide/watch/chargeapple-watch-apd2b717523a/watchos (last visited Mar. 6, 2023), pp. 6.
“Apple Watch Magnetic Charging Cable (1 m),” https://www.apple.com/shop/product/MX2E2AM/A/apple-watchmagnetic-charging-cable-1m (last visited Mar. 6, 2023), pp. 4.
“Apple Watch Series 4 Teardown,”https://www.ifixit.com/Teardown/Apple+Watch+Series+4+Teardown/113044 (last visited Mar. 6, 2023), pp. 14.
Letter from Jennifer Shih to Verily Life Sciences LLC re 510(k) No. K192415, U.S. Food & Drug Administration, dated Jan. 17, 2020 in 7 pages. https://www.accessdata.fda.gov/cdrh_docs/pdf19/K192415.pdf.
“Agent: The World's Smartest Watch”, https://www.kickstarter.com/projects/secretlabs/agent-the-worlds-smartest-watch/faqs, Last updated Apr. 30, 2016, pp. 8.
“Introducing Verily Study Watch”, Verily, https://verily.com/blog/Introducing-Verily-Study-Watch/, Apr. 14, 2017, pp. 6.
CMS50K Wearable SpO2/ECG Monitor from Contec Medical Systems Co., Ltd. (“CMS50K Watch”), Per Apple: Date of Public Knowledge, Use, and/or Sale is No later than Apr. 2016, 1 page.
“Care for your pillow partner with all your heart, Oranger Snoring Monitor 2.0”, https://mp.weixin.qq.com/s/EkQ_fNfotpCMaoDt3xan9Q, Jul. 27, 2015, pp. 10 (21 total pages with Translation).
“An entry-level all-round watch that makes sports unique \| Aiwei P1 energy sports watch”, https://mp.weixin.qq.com/s/d6ACPZqrRpvqdLHmb7UOsQ, Jun. 10, 2018, pp. 36.
“Monitor heart rate and record sports, experience of Avery energy sports watch P1”, https://www.sohu.com/a/234524743_115300, Jun. 8, 2018, pp. 9 (26 total pages with Translation).
“Comprehensive functions and excellent cost-effectiveness, Aiwei energy sports watch P1 trial experience”,\|https://mp.weixin.qq.com/s/XvRdKBCYQWqZwBP-Cesz7g, Jun. 27, 2018, p. 11 (20 total pages with Translation).
Hanselman, Scott, “Exclusive Sneak Peek: The Agent Smart Watch Emulator and managed .NET code on\|my wrist!”, https://www.hanselman.com/blog/exclusive-sneak-peek-the-agent-smart-watch-emulator-and-managed-net-code-on-my-wrist, Jun. 18, 2013, pp. 2.
Luke, Jack, “Garmin VivoActive 3 brings new design, interface and features”, https://www.bikeradar.com/news/garmin-vivoactive-3-brings-new-design-interface-and-features, Sep. 1, 2017, pp. 6.
Bennett, Brian, “LG's WCP-300 easily charges sans wires (hands-on)”, https://www.cnet.com/reviews/lg-wcp-300-wireless-charger-preview/, Feb. 26, 2013, pp. 3.
Chang-Wook, Kim, “Mobile 11th Street, Mobile Phone Wireless Charger Unlimited Sale”, etnews, Mar. 11, 2013, pp. 2.
DC Rainmaker, “Garmin Vivoactive 3 In-Depth Review”, https://www.dcrainmaker.com/2017/10/garmin-vivoactive-3-in-depth-review.html, Oct. 18, 2017, pp. 119.
DC Rainmaker, “Garmin's Vivomove HR: Everything you need to know”, https://www.dcrainmaker.com/2017/09/garmins-vivomove-hr-everything.html, Sep. 6, 2017, pp. 27.
Youtube, “Magconn, Wireless Charger”, https://www.youtube.com/watch?v=qxEXCOChLNA, Aug. 22, 2012, 1 page.
Youtube, “VivoActive 3 REVIEW—Final Verdict after 30 days of use (EP4)”, https://www.youtube.com/watch?v=IDcakqddUCU, Oct. 15, 2017, pp. 5.
Stein, Scott, “Garmin Vivomove HR review: The best fitness tracker in disguise”, https://www.cnet.com/reviews/garmin-vivomove-hr-review/, Nov. 22, 2017, pp. 5.
Sumra, Husain, “Garmin Vivomove HR: Essential guide to the stylish hybrid fitness watch”,\|https://www.wareable.com/garmin/garmin-vivomove-hr-release-date-price-specs-4983, Sep. 5, 2017, pp. 5.
Mendelson, Yitzhak, “Invasive and Noninvasive Blood Gas Monitoring”, Bioinstrumentation and Biosensors, 1991, pp. 249-279.
Leslie Cromwell et al., Biomedical Instrumentation and Measurements (1973), pp. 31-32.
Adecro Plastics, ABS Plastic Properties, (last visited Mar. 13, 2023), www.adrecoplastics.co.uk/abs-\|plasticproperties/# :˜: text=Finally%2C%20ABS%20has%20low%20heat, absorb%20shock%20effectively%2Oand%20reliably, pp. 7.
Carl R. Nave, Conductors and Insulators, Hyperphysics (last visited Mar. 13, 2023), http://hyperphysics.phyastr.gsu.edu/hbase/electric/conins.html#c1, pp. 3.
Merriam-Webster's Collegiate Dictionary, 11th ed. 2004, Definition of “embedded” and “Pad”, pp. 406 & 890 (5 pgs. Total).
Random House Unabridged Dictionary (2nd ed. 1993), Definition of “embedded” pp. 635.
The American Heritage Dictionary of the English Language (4th ed. 2000) Definition of “embedded” pp. 583.
Steven M. Kaplan, Wiley Electrical and Electronics Engineering Dictionary (2004) Definition of “lead”, pp. 414-415 [Total pages 4].
Stedman's Medical Dictionary (28th ed. 2006) Definition of “lead” pp. 1062.
GOV.UK Designs Journal Entry for Lee-616, https://www.registereddesign.service.gov.uk/view/2013/11/215 (last visited Mar. 28, 2023), pp. 12.
Youtube, “GMYLE(R) Qi Wireless Charger Review (Nexus 5)”, https://www.youtube.com/watch?v=EvJ4Jkvj_R8, Nov. 28, 2013, pp. 10.
“Apple Watch Teardown—iFixit,” https://www.ifixit.com/Teardown/Apple+Watch+Teardown/40655 (last visited Apr. 3, 2023), pp. 18.
“Apple Unveils Apple Watch—Apple's Most Personal Device Ever,”\|https://www.apple.com/newsroom/2014/09/09Apple-Unveils-Apple-Watch-Apples-Most-Personal-Device-Ever/ (last visited Mar. 31, 2023), pp. 4.
“Apple Watch—Technology,” archived on Sep. 11, 2014 by the Internet Organization's “Wayback Machine” at https://web.archive.org/web/20140911003437/http://www.apple.com/watch/technology/, pp. 8.
Patancheru, Govardhan Reddy, “Wearable Heart Rate Measuring Unit”, Master's Thesis in Electronics Design, 30HP, Mid Sweden University, Nov. 5, 2014, pp. 75.
“Pulse Sensor, Easy to Use Heart Rate Sensor & Kit”, PulseSensor.com, World Famous Electronics LLC. NY, USA, pp. 2.
Oct. 20, 2022 Complaint for Patent Infringement and Demand for Jury Trial, Apple Inc. v. Masimo Corporation and Sound United, LLC, Case No. 1:22-cv-01377-UNA, 32 pages.
Oct. 20, 2022 Complaint for Patent Infringement and Demand for Jury Trial, Apple Inc. v. Masimo Corporation and Sound United, LLC, Case No. 1:22-cv-01378-UNA, 77 pages.
Letter from Jennifer Shih to Masimo Corporation re 510(k) Number K232512, U.S. Food & Drug Administration, dated Nov. 17, 2023, in 14 pages.
International Preliminary Report on Patentability and Written Opinion for International Application No. PCT/US2016/040190, dated Jan. 2, 2018, in 7 pages.
International Preliminary Report on Patentability and Written Opinion of the International Searching Authority issued in Application No. PCT US2009/049638, mailed Jan. 5, 2011 in 9 pages.
International Preliminary Report on Patentability and Written Opinion of the International Searching Authority issued in Application No. PCT/US2009/052756, mailed Feb. 8, 2011 in 8 pages.
International Search Report and Written Opinion for PCT/US2009/049638, mailed Jan. 7, 2010.
International Search Report issued in Application No. PCT/US2009/052756, mailed Feb. 10, 2009 in 14 pages.
International Search Report, App. No. PCT/US2010/047899, Date of Actual Completion of Search: Jan. 26, 2011, 4 pages.
“Acrylic: Strong, stiff, clear plastic available in variety of brilliant colors”, Copyright 2020. available at http://www.curbellplastics.com/Research-.
Heart Rate Measurement Technology, Seiko Epson Corporation, retrieved from\|https://global.epson.com/innovation/core_technology/wearable/vital_sensing.html, accessed Dec. 2, 2019, 6 pages.
“Introducing Easy Pulse: A DIY Photoplethysmographic Sensor For Measuring Heart Rate”, Embedded Lab, 2012.
“PerformTek Precision Biometrics”, ValenCell, 2013.
“Universal asynchronous receiver-transmitter”, Wikipedia, available at https://en.wikipedia.org/wiki/Universal_asynchronous_receiver-transmitter, accessed Aug. 27, 2020, 10 pages.
“Galaxy S5 Explained: The Heart Rate Sensor and S Health 3.0.” Samsung Global Newsroom, 2014.
“Withings Pulse: Activity Tracker—Sleep Analyzer Hear Rate Analyzer; Installation and Operating Instructions”, Withings, 2015.
A Wireless Wearable Reflectance Pulse Oximeter Printout, The Bioengineering Institute, Worcester Polytechnic Institute, 1 page. Undated.
A. C. M. Dassel et al., “Effect of location of the sensor on reflectance pulse oximetry,” British Journal of Obstetrics and Gynaecology, vol. 104, Aug. 1997, pp. 910-916.
A. C. M. Dassel et al., “Reflectance Pulse Oximetry at the Forehead Improves by Pressure on the Probe,” Journal of Clinical Monitoring, vol. 11, No. 4, Jul. 1995, pp. 237-244.
A. Domingues, “Development of a Stand-Alone Pulse Oximeter,” Thesis for Universidade de Coimbra Master of Biomedical Engineering, Sep. 2009, 120 pages.
A. Fontaine et al., “Reflectance-Based Pulse Oximetry for the Chest and Wrist”, Worcester Polytechnic Institute Digital WPI, Apr. 2013, 132 pages.
A. Gendler et al., “A PAB-Based Multi-Prefetcher Mechanism,” International Journal of Parallel Programming, vol. 34, No. 2, Apr. 2006, pp. 171-188.
A. Keikhosravi et al., “Effect of deep breath on the correlation between the wrist and finger photoplethysmograms,” Proceedings of the 19th Iranian conference on Biomedical Engineering (ICBME 2012), Dec. 21-22, 2012, pp. 135-138.
A. Lader et al., “An Investigative Study of Membrane-Based Biosensors,” Proceedings of the IEEE 17th Annual Northeast Bioengineering Conference, 1991, pp. 253-254.
A. Looney, “Respiratory System Monitoring: Basics of Pulse Oximetry and Capnography,” Atlantic Coast Veterinary Conference, 2001, retrieved from https://www.vin.com/doc/?id=3844121, 5 pages.
A. Nagre et al., “Effects of Motion Artifacts on Pulse Oximeter Readings from Different Facial Regions,” Proceedings of the IEEE 31st Annual Northeast Bioengineering Conference, 2005, pp. 1-3.
A. Tura et al., “A Wearable Device with Wireless Bluetooth-based Data Transmission,” Measurement Science Review, vol. 3, Sec. 2, 2003, pp. 1-4.
A.C. Dassel et al., “Reflectance pulse oximetry at the forehead of newborns: the influence of varying pressure on the probe,” Journal of Clinical Monitoring, vol. 12, No. 6, Nov. 1996, pp. 421-428.
Akira Sakane et al., “Estimating Arterial Wall Impedance using a Plethysmogram,” IEEE 2003, pp. 580-585.
Anliker et al., “AMON: a wearable multiparameter medical monitoring and alert system,” in IEEE Transactions on Information Technology in Biomedicine, vol. 8, No. 4, Dec. 2004.
Asada, et al. “Mobile Monitoring with Wearable Photoplethysmographic Biosensors”, IEEE Engineering in Medicine and Biology Magazine, 2003.
B. F. Keogh et al., “Recent findings in the use of reflectance oximetry: a critical review,” Current Opinion in Anaesthesiology, vol. 18, 2005, pp. 649-654.
B. Landon et al., “Master Visually Windows Mobile 2003”, Wiley Publishing, Inc., 2004, 335 pages (uploaded in two parts).
B. Mapar, “Wearable Sensor for Continuously Vigilant Blood Perfusion and Oxygenation Monitoring,” UCLA Electronic Theses and Dissertations, 2012, 112 pages.
B. McGarry et al., “Reflections on a candidate design of the user-interface for a wireless vital-signs monitor,” Proceedings of DARE 2000 on Designing Augmented Reality Environments, Jan. 2000, pp. 33-40.
B. Odegard et al., “An Analysis of Racewalking Styles Using a 2-Dimensional Mathematical Knee Model,” Proceedings of the IEEE 23rd Northeast Bioengineering Conference, 1997, pp. 73-74.
B. Yocum et al., “Design of a Reflectance Pulse Oximeter Sensor and its Evaluation in Swine,” Proceedings of the 15th Annual Northeast Bioengineering Conference, IEEE, 1989, pp. 239-240.
B.-H. Yang et al., “Development of the ring sensor for healthcare automation,” Robotics and Autonomous Systems, 2000, pp. 273-281.
Bagha, et al. “A Real Time Analysis of PPG Signal for Measurement of SpO2 and Pulse Rate”. International Journal of Computer Applications (0975-8887), vol. 36, No. 11, Dec. 2011, pp. 45-50.
B-H. Yang et al., “A Twenty-Four Hour Tele-Nursing System Using a Ringer Sensor,” Proceedings of 1998 IEEE International Conference on Robotics and Automation, May 16-20, 1998, 6 pages.
Branche, et al. “Measurement Reproducibility and Sensor Placement Considerations in Designing a Wearable Pulse Oximeter for Military Applications”, IEEE, 2004.
Branche, et al. “Signal Quality and Power Consumption of a New Prototype Reflectance Pulse Oximeter Sensor”, IEEE, 2005.
B-S. Lin et al., “RTWPMS: A Real-Time Wireless Physiological Monitoring System,” IEEE Transactions on Information Technology in Biomedicine, vol. 10, No. 4, Oct. 2006, pp. 647-656.
Burritt, Mary F.; Current Analytical Approaches to Measuring Blood Analytes; vol. 36; No. 8(B); 1990.
C. E. Darling et al., “Detecting Blood Loss With a Wearable Photoplethysmography Device,” Annals of Emergency Medicine, vol. 68, No. 45, Oct. 2016, p. S116.
C. Faulkner, “Apple Watch heart rate sensor: everything you need to know,” Apr. 24, 2015, 5 pages.
C. G. Scully et al., “Physiological Parameter Monitoring from Optical Recordings With a Mobile Phone,” IEEE Transactions on Biomedical Engineering, vol. 59, No. 2, Feb. 2012, pp. 303-306.
C. Gutierrez et al., “Non-Invasive Functional Mapping of the Brain Using Cerebral Oximeter,” Proceedings of the Second Joint EMBS/BMES Conference, Oct. 2002, pp. 947-948.
C. J. Pujary, “Investigation of Photodetector Optimization in Reducing Power Consumption by a Noninvasive Pulse Oximeter Sensor,” Worcester Polytechnic Institute, Jan. 16, 2004, 133 pages.
C. Pujary et al., “Photodetector Size Considerations in the Design of a Noninvasive Reflectance Pulse Oximeter for Telemedicine Applications,” Proceedings of IEEE Annual Northeast Bioengineering Conference, 2003, pp. 148-149.
C. Tamanaha et al., “An Inorganic Membrane Filter to Support Biomembrane-Mimetic Structures,” Proceedings of 17th International Conference of the Engineering in Medicine and Biology Society, Sep. 1995, pp. 1559-1560.
C. Tamanaha et al., “Feasibility Study of an Inorganic Membrane Filter as a Support for Biomembrane- Mimetic Structures,” Proceedings of the IEEE 21st Annual Northeast Bioengineering Conference, 1995, pp. 99-101.
C. Tamanaha et al., “Humidity and Cation Dependency of Purple Membrane Based Biosensors,” Proceedings of the 18th IEEE Annual Northeast Bioengineering Conference, Mar. 1992, pp. 107-108.
C. Tamanaha et al., “Surface Modification of y-A1203 Filters by Chemisorption of Alkyltrichlorosilane Molecules,” 18th Annual International Conference of the IEEE Engineering in Medicine and Biology Society, 1996, pp. 2069-2070.
C. W. Mundt et al., “A Multiparameter Wearable Physiologic Monitoring System for Space and Terrestrial Applications,” IEEE Transactions on Information Technology in Biomedicine, vol. 9, No. 3, Sep. 2005, pp. 382-391.
Cahill, Laser-Based Fibre-Optic Sensor for Measurement of Surface Properties, Thesis for Dublin City University Faculty of Engineering and Design, May 1998, 208 pages. [uploaded in 5 parts].
Celka, et al. “Motion resistant earphone located infrared based heart rate measurement device”, Research Gate, 2004.
Chang et al., “Microlens array diffuser for a light-emitting diode backlight system”, Optics Letters, vol. 31, No. 20, Oct. 15, 2006, pp. 3016-3018.
Comtois, et al. “A Comparative Evaluation of Adaptive Noise Cancellation Algorithms for Minimizing Motion Artifacts in a Forehead-Mounted Wearable Pulse Oximeter”, IEEE, 2007.
Comtois, et al. “A Noise Reference Input to an Adaptive Filter Algorithm for Signal Processing in a Wearable Pulse Oximeter”, IEEE, 2007.
Conway, et al. “Wearable computer as a multi-parametric monitor for physiological signals,” Proceedings IEEE International Symposium on Bio-Informatics and Biomedical Engineering, pp. 236-242, 2000.
Crilly, et al. “An Integrated Pulse Oximeter System for Telemedicine Applications”, IEEE Instrumentation and Measurement Technology Conference, 1997.
D. C. Zheng and Y. T. Zhang, “A ring-type device for the noninvasive measurement of arterial blood pressure,” Proceedings of the 25th Annual International Conference of the IEEE Engineering in Medicine and Biology Society (IEEE Cat. No.03CH37439), Sep. 17-21, 2003, Cancun, pp. 3184-3187 vol.4.
D. Dao et al., “A Robust Motion Artifact Detection Algorithm for Accurate Detection of Heart Rates FromPhotoplethysmographic Signals Using Time-Frequency Spectral Features,” IEEE Journal of Biomedical and Health Informatics, vol. 21, No. 5, Sep. 2017, pp. 1242-1253.
D. Konstantas et al., “Mobile Patient Monitoring: The MobiHealth System,” In Proceedings of International Conference on Medical and Care Compunetics, NCC'04, Feb. 2004, 8 pages.
D. Marculescu et al., “Ready to Ware,” IEEE Spectrum, vol. 40, Issue 10, Oct. 2003, pp. 28-32.
D. Sen et al., “A New Vision for Preventing Pressure Ulcers: Wearable Wireless Devices Could Help Solve a Common-and Serious-Problem,” IEEE Pulse, vol. 9, No. 6, Nov. 2018, pp. 28-31.
D. Sen et al., “Pressure Ulcer Prevention System: Validation in a Clinical Setting,” IEEE Life Sciences Conference (LSC), 2018, pp. 105-108.
D. Sen et al., “Time-Domain-Based Measurement Technique for Pressure Measurement in a Wearable Wireless Sensor Patch,” IEEE International Symposium on Circuits and Systems (ISCAS), 2018, pp. 1-5.
D. Sen et al., “Wireless Sensor Patch Suitable for Continuous Monitoring of Contact Pressure in a\|Clinical Setting,” 16th IEEE International New Circuits and Systems Conference (NEWCAS), 2018, pp. 91-95.
D. Thompson et al., “A Small, High-Fidelity Reflectance Pulse Oximeter,” American Society for Engineering Education, 2007, 14 pages.
D. Thompson et al., “Pulse Oximeter Improvement with an ADC-DAC Feedback Loop and a Radical Reflectance Sensor,” Proceedings of the 28th IEEE Embs Annual International Conference, 2006, pp. 815-818.
D. Thompson et al., “A Small, High-Fidelity Reflectance Pulse Oximeter”, American Society for Engineering Education, Jan. 2007, 15 pages.
D. Traviglia et al., “A Portable Setup for Comparing Transmittance and Reflectance Pulse Oximeters for Field Testing Applications,” Proceedings of the IEEE 30th Annual Northeast Bioengineering Conference, 2004, pp. 212-213.
D. Yang et al., “SpO2 and Heart Rate Measurement with Wearable Watch Based on PPG,” 2015 IET International Conference on Biomedical Image and Signal Processing (ICBISP 2015), Nov. 2015, pp. 1-5.
DC Rainmaker, 'Mio Alpha Optical Heart Rate Monitor in-Depth Review (Bluetooth Smart/ANT+)', published Feb. 12, 2013, retrieved from https://www.dcrainmaker.com/2013/02/monitor-bluetooth-smartant.html, 108 pages. [uploaded in 5 parts].
Definition of “cover”, excerpt from Merriam-Webster's Collegiate Dictionary (11th ed.), 2005, 3 pages.
Definition of “gap”, excerpt from Merriam-Webster's Collegiate Dictionary (11th ed.), 2005, 3 pages.
Definition of “processor”, excerpt from Merriam-Webster's Collegiate Dictionary (10th ed.), 1999, 6 pages.
Design of Pulse Oximeters, J.G. Webster, Institution of Physics Publishing, IOP Publishing Ltd, 1997, 262 pages (uploaded in three parts).
Dresher, et al. “A New Reflectance Pulse Oximeter Housing to Reduce Contact Pressure Effects”, IEEE, 2006.
Dresher, et al. “Reflectance Forehead Pulse Oximetry: Effects of Contact Pressure During Walking”, IEEE, 2006.
E. Geun et al., “Measurement Site and Applied Pressure Consideration in Wrist Photoplethysmography”, The 23rd International Technical Conference on Circuits/System, Computers and Communication, Jan. 2008, pp. 1129-1132.
E. Higurashi et al., “An integrated laser blood flowmeter,” Journal of Lightwave Technology, vol. 21, No. 3, pp. 591-595, Mar. 2003.
E. Kviesis-Kipge et al., “Miniature wireless photoplethysmography devices: integration in garments and test measurements,” Proc. SPIE vol. 8427, Biophotonics: Photonic Solutions for Better Health Care III, May 2012, 7 pages.
E. Morillo et al., “Multiwavelength Transmission Spectrophotometry in the Pulsatile Measurement of Hemoglobin Derivatives in Whole Blood,” Proceedings of the IEEE 23rd Northeast Bioengineering Conference, 1997, pp. 5-6.
E. Stohr et al., “Quantitative FTIR Spectrophotometry of Cholesterol and Other Blood Constituents and their Interference with the In-Vitro Measurement of Blood Glucose,” Proceedings of the 18th IEEE Annual Northeast Bioengineering Conference, 1992, pp. 105-106.
E. Tuite et al., “Design of Individual Balance Control Device Utilized during the Sit-to-Stand Task,” ISB 2011 Brussels, 2011, pp. 1-2.
Eiji Higurashi et al., “Hybrid integration technologies for optical micro-systems”, Proc. SPIE 5604, Optomechatronic Micro/Nano Components, Devices, and Systems, Oct. 25, 2004, pp. 67-73.
Eugene Hecht, Excerpts of Optics, Second Edition, Addition-Wesley Publishing Company, 1990, 80 pages (pp. 79-143, 211-220).
Eugene Hecht, Optics, Fourth Edition, Pearson Education, Inc., Addison Wesley, 2002, 355 pages. (uploaded in three parts).
Eugene Hecht, Optics, Second Edition, Addition-Wesley Publishing Company, 1990, 348 pages. (uploaded in two parts).
European Office Action issued in Application No. 09791157.2, dated Jun. 20, 2016.
European Office Action issued in application No. 10763901.5 on Jan. 11, 2013.
European Office Action issued in application No. 10763901.5 on Aug. 6, 2015.
European Office Action issued in application No. 10763901.5 on Aug. 27, 2014.
Excerpts of Design of Pulse Oximeters, J.G. Webster, Institution of Physics Publishing, IOP Publishing Ltd, 1997, 150 pages. [uploaded in 3 parts].
Fabio Buttussi et al., “MOPETt: A context-aware and user-adaptive wearable system for fitness training,” Artificial Intelligence in Medicine 42, 2008, pp. 153-163.
Faulkner, “Apple Watch Heart Rate Sensor: Everything You Need To Know.” TechRadar India, TechRadar, 2015.
Feather et al., “A portable reflectometer for the rapid quantification of cutaneous haemoglobin and melanin,” Phys. Med. Biol., vol. 33, No. 6, 1988, pp. 711-722.
Fontaine, et al. “Reflectance-Based Pulse Oximetry for the Chest and Wrist,” Digitalcommons.WPI.edi/mqp-all/1703.
Frank H. Netter, M.D., Atlas of Human Anatomy Third Edition—Section VI Upper Limb, ICON Learning Systems, LLC, 2003, 81 pages.
G. Comtois et al., “A Wearable Wireless Reflectance Pulse Oximeter for Remote Triage Applications,” Proceedings of the IEEE 32nd Annual Northeast Bioengineering Conference, 2006, pp. 53-54.
G. Tamannagari, “Power Efficient Design of Finder-Ring Sensor for Patient Monitoring,” Master of Science in Electrical Engineering, The University of Texas at San Antonio, College of Engineering, Department of Electrical Engineering, Dec. 2008, 74 pages.
Gibbs, et al. “Active Motion Artifact Cancellation for Wearable Health Monitoring Sensors Using Collocated MEMS Accelerometers,” Proceedings of SPIE Smart Structures and Materials: Sensors and Smart Structures Technologies for Civil, Mechanical, and Aerospace Systems, May 17, 2005, pp. 811-819.
Graaff et al., “Optical Properties of Human Dermis In Vitro and In Vivo,” Applied Optics, vol. 32, No. 4, Feb. 1, 1993, pp. 435-447.
H. Ding et al., “Refractive indices of human skin tissues at eight wavelengths and estimated dispersion relations between 300 and 1600 nm”, Physics in Medicine & Biology, vol. 51, 2006, pp. 1479-1489.
H. DiSpirito et al., “A Neural Stimulation System Model to Enhance Neural Integrated Circuit Design,” 29th Southern Biomedical Engineering Conference, 2013, pp. 9-10.
H. Kisch-Wedel et al., “Does the Estimation of Light Attenuation in Tissue Increase the Accuracy of Reflectance Pulse Oximetry at Low Oxygem Saturations In Vivo?” IEEE Transactions on Biomedical Engineering., vol. 56, No. 9, Sep. 2009, pp. 2271-2279.
Hall, et al., Jeffrey W.; Near-Infrared Spectrophotometry: A New Dimension in Clinical Chemistry; vol. 38; No. 9; 1992.
Harsanyi, Sensors in Biomedical Applications, Fundamentals, Technology and Applications, CRC Press LLC, 2000, 368 pages. [uploaded in 2 parts].
Hayes, “How the Sensors inside Fitness Tracker Work.” Digital Trends, 2014.
Heerlein, et al. “LED-Based Sensor For Wearable Fitness Tracking Products”, EDN, 2014.
Home Use Guide: Nellcor Symphony N-3000 Pulse Oximeter, Nellcor Puritan Bennett, Inc., Copyright 1996, 50 pages.
http://amivital.ugr.es/blog/?tag+spo2; Monitorizacion de la hemoglobina ... y mucho mas, printed on Aug. 20, 2009.
http://blogderoliveira.blogspot.com/2008_02_01_archive.html; Ricardo Oliveira, printed on Aug. 20, 2009.
http://www.masimo.com/generalFloor/system.htm; Masimo Patient SafetyNet System at a Glance, printed on Aug. 20, 2009.
http://www.masimo.com/partners/Graseby.htm; Graseby Medical Limited, printed on Aug. 20, 2009.
http://www.masimo.com/partners/welchallyn.htm; Welch Allyn Expands Patient Monitor Capabilities with Masimo Pulse Oximetry Technology, printed on Aug. 20, 2009.
http://www.masimo.com/pulseOximeter/ppo.htm; Masimo Personal Pulse Oximeter, printed on Aug. 20, 2009.
http://www.masimo.com/pulseOximeter/Rad5.htm; Signal Extraction Pulse Oximeter, printed on Aug. 20, 2009.
http://www.masimo.com/rad-57/; Noninvasive Measurement of Methemoglobin, Carboxyhemoglobin and Oxyhemoglobin in the blood. Printed on Aug. 20, 2009.
http://www.masimo.com/rainbow/pronto.htm Noninvasive & Immediate Hemoglobin Testing, printed on Aug. 20, 2009.
http://www.masimo.com/spco/; Carboxyhemoglobin Noninvasive > Continuous > Immediate, printed on Aug. 20, 2009.
Humphreys, An Investigation of Remote Non-Contact Photoplethysmography and Pulse Oximetry, National University of Ireland: Department of Electronic Engineering, Aug. 2007.
Interim Procedure for Discretionary Denials in AIA Post-Grant Proceedings with Parallel District Court Litigation, issued Jun. 21, 2022 (“Interim Guidance”).
J Kraitl et al., “An optical device to measure blood components by a photoplethysmographic method,” Journal of Optics A: Pure and Applied Optics. 7, 2005, pp. S318-S324.
J. A. Pologe, “Pulse Oximetry: Technical Aspects of Machine Design,” International Anesthesiology Clinics, vol. 25, No. 3, 1987, pp. 137-153.
J. A. Tamada et al., “Noninvasive Glucose Monitoring: Comprehensive Clinical Results,” JAMA, Nov. 17, 1999, vol. 282, No. 19, pp. 1839-1844.
J. Bronzino et al., Medical Devices and Systems, The Biomedical Engineering Handbook, Third Edition, Taylor & Francis Group, LLC, Apr. 2006, 20 pages.
J. Bronzino et al., The Biomedical Engineering Handbook, Second Edition, CRC Press LLC, 2000, 21 pages.
J. C. D. Conway et al., “Wearable computer as a multi-parametric monitor for physiological signals,” Proceedings IEEE International Symposium on Bio-Informatics and Biomedical Engineering, Arlington, A, USA, 2000, pp. 236-242.
J. Chong et al., “Photoplethysmograph Signal Reconstruction Based on a Novel Hybrid Motion Artifact Detection-Reduction Approach. Part I: Motion and Noise Artifact Detection,” Annals of Biomedical Engineering, vol. 42, No. 11, Nov. 2014, pp. 2238-2250.
J. Fiala et al., “Implantable optical sensor for continuous monitoring of various hemoglobin derivatives and tissue perfusion,” IEEE Sensors Conference, 2009, pp. 1971-1974.
J. Harvey et al., “A Portable Sensor for Skin Bioimpedance Measurements,” International Journal of Sensors and Sensor Networks, vol. 7, No. 1, Aug. 2019, pp. 1-8.
J. Harvey et al., “Correlation of bioimpedance changes after compressive loading of murine tissues in vivo,” Physiological Measurement, vol. 40, No. 10, Oct. 2019, pp. 1-13.
J. Harvey et al., “OxiMA: A Frequency-Domain Approach to Address Motion Artifacts in Photoplethysmograms for Improved Estimation of Arterial Oxygen Saturation and Pulse Rate,” IEEE Transactions on Biomedical Engineering, vol. 66, No. 2, Feb. 2019, pp. 311-318.
J. Hayano et al., “Assessment of pulse rate variability by the method of pulse frequency demodulation.” BioMedical Engineering OnLine vol. 4, No. 62, Nov. 1, 2005, doi: 10.1186/1475-925X-4-62, pp. 1-12.
J. Hodby, “A ratio-measuring detection system for use in pulsed spectroscopic measurements,” Journal of Physics E: Scientific Instruments, vol. 3, 1970, pp. 229-233.
J. McNeill et al., “Flexible Sensor for Measurement of Skin Pressure and Temperature in a Clinical Setting,” 2016 IEEE Sensors, Nov. 2016, pp. 1-3.
J. McNeill et al., “Wearable Wireless Sensor Patch for Continuous Monitoring of Skin Temperature,Pressure, and Relative Humidity,” IEEE International Symposium on Circuits and Systems (ISCAS), 2017, pp. 1-4.
J. Schmitt et al., “An Integrated Circuit-Based Optical Sensor for In Vivo Measurement of Blood Oxygenation,” IEEE Transactions on Biomedical Engineering, vol. BME-33, No. 2, Feb. 1986, pp. 98-107.
J. Webster et al., Nanoparticles—Radiotherapy Accessories, Encyclopedia of Medical Devices and Instrumentation, Second Edition, vol. 5, Wiley-Interscience, 2006, 42 pages.
J. Yao, et al., “Stimulating Student Learning with a Novel 'In-House' Pulse Oximeter Design”, Proceedings of the 2005 American Society for Engineering Education Annual Conference & Exposition, 2005, 14 pages.
Japanese Notice of Allowance, re JP Application No. 2011-516895, issued on May 12, 2015, no translation.
Japanese Office Action, re JP Application No. 2011-516895, mailed Sep. 2, 2014, with translation.
Johnston, et al. “Extracting Breathing Rate Information from a Wearable Reflectance Pulse Oximeter Sensor,” Proceedings of the 26th Annual International Conference of the IEEE EMBS, Sep. 1-5, 2004, pp. 5388-5391.
Johnston, et al. “Extracting Heart Rate Variability from a Wearable Reflectance Pulse Oximeter,” IEEE, 2005, pp. 1-2.
K. Chon et al., “Wearable Wireless Sensor for Multi-Scale Physiological Monitoring,” Worcester Polytechnic Institute, Oct. 2014, 82 pages.
K. Chon et al., “Wearable Wireless Sensor for Multi-Scale Physiological Monitoring,” Worcester Polytechnic Institute, Oct. 2015, 142 pages. (Uploaded in 2 parts).
K. Faisst et al., “Reflectance pulse oximetry in neonates,” European Journal of Obstetrics & Gynecology and Reproductive Biology, vol. 61, No. 2, Aug. 1995, pp. 117-122.
K. Hickle et al., “Wireless Pressure Ulcer Sensor,” Annals of Plastic Surgery, vol. 82, Supplement 3, Apr. 2019, pp. S215-S221.
K. Kilbane, “Design Considerations for Wrist-Wearable Heart Rate Monitors,” GSA, Copyright 2021, 5 pages.
K. Kuboyama, “Motion Artifact Cancellation for Wearable Photoplethysmographic Sensor,” Massachusetts Institute of Technology, 2010, 66 pages.
K. Li et al., “A High-Performance Wireless Reflectance Pulse Oximeter for Photo-Plethysmogram Acquisition and Analysis in the Classroom,” American Society for Engineering Education, 2010, 12 pages.
K. Li et al., “A Wireless Reflectance Pulse Oximeter with Digital Baseline Control for UnfilteredPhotoplethysmograms,” IEEE Transactions on Biomedical Circuits and Systems, Nov. 2011, pp. 1-11.
K. M. Warren et al., “Improving Pulse Rate Measurements during Random Motion Using a Wearable Multichannel Reflectance Photoplethysmograph,” Sensors (Basel), vol. 16, No. 3, Mar. 2016, p. 1-18.
K. Nakajima et al., “Monitoring of heart and respiratory rates by photoplethysmography using digital filtering technique,” Med. Eng. Phy. Vol. 18, No. 5, pp. 365-372, 1996.
K. Ono et al., “Fiber optic reflectance spectrophotometry system for in vivo tissue diagnosis,” Applied Optics, vol. 30, No. 1, Jan. 1991, pp. 98-105.
K. Self, Application Note 78—Using Power Management with High-Speed Microcontrollers, Maxim Integrated Products, Inc., Mar. 29, 2001, 25 pages.
K. Shin et al., “A Novel Headset with a Transmissive PPG Sensor for Heart Rate Measurement,” ICBME 2008 Proceedings vol. 23, 2009, 519-522 Pages.
Kanukurthy et al., “Data Acquisition Unit for an Implantable Multi-Channel Optical Glucose Sensor”, Electro/Information Technology Conference, Chicago, IL, USA, May 17-20, 2007, pp. 1-6.
Keikhosravi, et al. “Effect of deep breath on the correlation between the wrist and finger photoplethysmograms”, pp. 135-138, 2012.
Konig et al., “Reflectance Pulse Oximetry - Principles and Obstetric Application in the Zurich System”, Journal of Clinical Monitoring and Computing, vol. 14, No. 6, Aug. 1998, pp. 403-412.
Certified English Translation of Korean Pat. Appl. No. 10-2018-0038206 (“Chung-KR-Application”), as filed Apr. 2, 2018, p. 64.
Kuenstner, et al., J. Todd; Measurement of Hemoglobin in Unlysed Blood by Near-Infrared Spectroscopy; vol. 48; No. 4, 1994.
Kviesis-Kipge, et al., “Miniature Wireless Photoplethysmography Devices: Integration in Garments and Test Measurements”, SPIE vol. 8427 84273H-6, 2012.
L. Grajales et al., “Wearable multisensor heart rate monitor,” International Workshop on Wearable and Implantable Body Sensor Networks (BSN'06), Cambridge, MA, 2006, pp. 4-157.
L. Xu et al., “An integrated wrist-worn routine monitoring system for the elderly using BSN,” 2008 5th International Summer School and Symposium on Medical Devices and Biosensors, Hong Kong, 2008, pp. 45-48.
Lam et al., “A Smartphone-Centric Platform for Personal Health Monitoring using Wireless Wearable Biosensors”, IEEE, ICICS 2009, 7 pages.
Laukkanen RM et al., “Heart Rate Monitors: State of the Art,” Journal of Sports Science, Jan. 1998, pp. S3-S7.
Lee, et al. “Development of a Wristwatch-Type PPG Array Sensor Module”, IEEE, 2011.
Lee, et al. “Reflectance pulse oximetry: Practical issues and limitations,” ICT Express 2 (2016) 195- 198.
Lin, et al. “RTWPMS: A Real-Time Wireless Physiological Monitoring System”, IEEE Transactions On Information Technology in Biomedicine, vol. 10, No. 4, 2006.
Lingaiah, et al. “Measurement of Pulse rate and SPo2 using Pulse Oximeter developed using LabView”, IOSR Journal of Electrical and Electronics Engineering (IOSR-JEEE), e-ISSN: 2278-1676,p. ISSN: 2320-3331, vol. 8, Issue 1, pp. 22-26, 2013.
Love et al., Personal Status Monitor, Sandia National Laboratories, Feb. 1997, 211 pages. [uploaded in 2 parts].
Lukowicz, et al. “Amon: A Wearable Medical Computer for High-Risk Patients,” Proceedings of the 6th International Symposium on Wearable Computers (ISWC'02), 2002, pp. 1-2.
Lukowicz, et al. “The WearARM Modular, Low-Power Computing Core,” IEEE Micro, May-Jun. 2001, pp. 16-28.
M. Barr, “Introduction to Pulse Width Modulation (PWM),” Barr Group, Embedded Systems Programming, Sep. 2001, pp. 1-3.
M. Corcoran et al., “A Humidifier for Olfaction Studies During Functional Magnetic Resonance Imaging,” Proceedings of the IEEE 31st Annual Northeast Bioengineering Conference, 2005, pp. 1-2.
M. J. Hayes, “Artefact Reduction in Photoplethysmography,” Doctoral thesis, Department of Electronic and Electrical Engineering, Loughborough University, Nov. 1998, 195 pages. (uploaded in 2 parts).
M. Last et al., Chapter 14: Early Warning from Car Warranty Data using a Fuzzy Logic Technique,Scalable Fuzzy Algorithms for Data Management and Analysis: Methods and Design, 2010, pp. 347-364.
M. Nogawa et al., “A Novel Hybrid Reflectance Pulse Oximeter Sensor with Improved Linearity and General Applicability to Various Portions of the Body,” Proceedings of the 20th Annual International Conference of the IEEE Engineering in Medicine and Biology Society, vol. 20, No. 4, 1998, pp. 1858-1861.
M. Poh et al., “Motion-Tolerant Magnetic Earring Sensor and Wireless Earpiece for WearablePhotoplethysmography,” IEEE Transactions on Information Technology in Biomedicine, vol. 14, No. 3, May 2010, pp. 786-794.
M. Savage et al., “Optimizing Power Consumption in the Design of a Wearable Wireless Telesensor: Comparison of Pulse Oximeter Modes,” Proceedings of IEEE 29th Annual Nonheust Bioengineering Conference, 2003, pp. 150-151.
M. Yamashita et al., “Development of a Ring-Type Vital Sign Telemeter,” Biotelemetry XIII, Mar. 26- 31, 1995, pp. 145-150.
Manzke, et al., B., Multi Wavelength Pulse Oximetry in the Measurement of Hemoglobin Fractions; SPIE, vol. 2676, Apr. 24, 1996.
Matthes, K. & W. Hauss, Lichtelektrische Plethysomgramme Klinische Wochenschrift, No. 17 (5):1211- 1213, 1938.
McGraw-Hill Dictionary of Scientific and Technical Terms, Sixth Edition, 2003. p. 2133.
McPherson, “How to Do Everything with Windows Mobile”, McGraw Hill, 2006, 431 pages (uploaded in three parts).
Mendelson et al. “Noninvasive Pulse Oximetry Utilizing Skin Reflectance Photoplethysmography”, IEEE Biomedical Engineering, vol. 35 No. 10, 1988.
Mendelson et al., “A Mobile PDA-Based Wireless Pulse Oximeter,” Proceedings of the IASTED International Conference Telehealth, Jul. 19-21, 2005, pp. 1-6.
Mendelson et al., “A Wearable Reflectance Pulse Oximeter for Remote Physiological Monitoring,” Proceedings of the 28th IEEE Embs Annual International Conference, August 30-Sep. 3, 2006, pp. 912-915.
Mendelson et al., “Accelerometery-Based Adaptive Noise Cancellation for Remote Physiological Monitoring by a Wearable Pulse Oximeter,” Proceedings of the 3rd IASTED International Conference TeleHealth, May 31-Jun. 1, 2007, pp. 28-33.
Mendelson et al., “Measurement Site and Photodetector Size Considerations in Optimizing Power Consumption of a Wearable Reflectance Pulse Oximeter,” Proceedings of the 25th Annual International Conference of the IEEE EMBS, Sep. 17-21, 2003, pp. 3016-3019.
Mendelson et al., “Minimization of LED Power Consumption in the Design of a Wearable Pulse Oximeter, ”Proceedings of the IASTED International Conference Biomedical Engineering, Jun. 25-27, 2003, 6 pages.
Mendelson et al., Skin Reflectance Pulse Oximetry: In Vivo Measurements from the Forearm and Calf, Journal of Clinical Monitoring vol. 7 No. 1, pp. 7-12, dated Jan. 1991.
Mendelson, “Invasive and Noninvasive Blood Gas Monitoring,” Bioinstrumentation and biosensors, 1991, pp. 249-279.
Mendelson, et al., “Design and Evaluation of a New Reflectance Pulse Oximeter Sensor”, Worcester Polytechnic Institute, Biomedical Engineering Program, Worcester, MA 01609, Association for the Advancement of Medical Instrumentation, vol. 22, No. 4, 1988, pp. 167-173, Abstract, 1 page.
Mendelson, Theory and Development of a Transcutaneous Reflectance Oximeter System for Noninvasive Measurements of Arterial Oxygen Saturation, Thesis for Case Western Reserve University Department of Biomedical Engineering, May 25, 1983, 284 pages. [uploaded in 2 parts].
Mendelson et al., “The Feasibility of Measuring SpO2 from the Head Using a Reflectance Pulse Oximeter: Effect of Motion Artifacts,” Proceeding of the 3rd European Medical & Biological Engineering Conference, 2005, 5 pages.
Mendelson et al., “Wireless Reflectance Pulse Oximetery for Remote Triage Application,” Worcester Polytechnic Institute, 1 page. Undated.
Mendelson et al., “A Multiwavelength VIS-NIR Spectrometer for Pulsatile Measurement of Hemoglobin Derivatives in Whole Blood,” 18th Annual International Conference of the IEEE Engineering in Medicine and Biology Society, 1996, pp. 134-135.
Mendelson et al., “An In Vitro Tissue Model for Evaluating the Effect of Carboxyhemoglobin Concentration on Pulse Oximetry,” IEEE Transactions on Biomedical Engineering, vol. 36, No. 6, Jun. 1989, pp. 625-627.
Mendelson et al., “Blood Glucose Measurement by Multiple Attenuated Total Reflection and Infrared Absorption Spectroscopy,” IEEE Transactions on Biomedical Engineering, vol. 37, No. 5, May 1990, pp. 458-465.
Mendelson et al., “Carbon dioxide laser based multiple ATR technique for measuring glucose in aqueous solutions,” Applied Optics, vol. 27, No. 24, Dec. 1988, pp. 5077-5081.
Mendelson et al., “Evaluation of the Datascope ACCUSAT Pulse Oximeter in Healthy Adults,” Journal of Clinical Monitoring, vol. 4, No. 1, Jan. 1988, pp. 59-63.
Mendelson et al., “Multi-channel pulse oximetry for wearable physiological monitoring,” IEEE International Conference on Body Sensor Networks, 2013, pp. 1-6.
Mendelson et al., “Noninvasive Transcutaneous Monitoring of Arterial Blood Gases,” IEEE Transactions on Biomedical Engineering, vol. BME-31, No. 12, Dec. 1984, pp. 792-800.
Mendelson et al., Pulse Oximetry: Theory and Applications for Noninvasive Monitoring, Clinical Chemistry, vol. 38, No. 9, 1992, pp. 1601-1607.
Mendelson et al., “Variations in Optical Absorption Spectra of Adult and Fetal Hemoglobins and Its Effect on Pulse Oximetry,” IEEE Transactions on Biomedical Engineering, vol. 36, No. 8, Aug. 1989, pp. 844-848.
Mendelson et al., “Wearable Wireless Pulse Oximetry for Physiological Monitoring,” Worcester Polytechnic Institute, Precise Personnel Location Workshop, Aug. 4, 2008, p. 34.
Mendelson et al., A Wireless Wearable Reflectance-Based Forehead Pulse Oximeter, PowerPoint, The Bioengineering Institute, Worcester Polytechnic Institute, 8 pages. Undated.
Mendelson et al., Chapter 9: Biomedical Sensors, Introduction to Biomedical Engineering, Second Edition, Apr. 2005, pp. 505-548.
Mendelson, “Wearable, Wireless, Noninvasive Physiological Sensing,” The Bioengineering Institute, Worcester Polytechnic Institute, 2005, 2 pages.
Mendelson, Pulse Oximetry, PowerPoint, UMass Center for Clinical and Translational Science Research Retreat, 2017, 22 pages.
Mio ALPHA Complete User Guide, Physical Enterprises, https://www.medisana.com/out/pictures/media/manual/mio_alpha_user_guide_en.pdf (2014).
N. Reljin et al., “Automatic Detection of Dehydration using Support Vector Machines,” 14th Symposium on Neural Networks and Applications (NEUREL), Nov. 2018, pp. 1-6.
N. Reljin et al., “Detection of Blood Loss in Trauma Patients using Time-Frequency Analysis of Photoplethysmographic Signal,” IEEE-EMBS International Conference on Biomedical and Health Informatics (BHI), 2016, pp. 118-121.
N. Reljin et al., “Using support vector machines on photoplethysmographic signals to discriminate between hypovolemia and euvolemia,” PLoS One, vol. 13, No. 3, Mar. 2018, pp. 1-14.
N. Selvaraj et al., “A Novel Approach Using Time-Frequency Analysis of Pulse-Oximeter Data to Detect Progressive Hypovolemia in Spontaneously Breathing Healthy Subjects,” IEEE Transactions on Biomedical Engineering, vol. 58, No. 8, Aug. 2011, pp. 2272-2279.
N. Selvaraj et al., “Statistical Approach for the Detection of Motion/Noise Artifacts in Photoplethysmogram,” 33rd Annual International Conference of the IEEE EMBS, Sep. 2011, pp. 4972-4975.
N. Stuban et al., “Optimal filter bandwidth for pulse oximetry,” Review of Scientific Instruments vol. 83, 2012, 6 pages.
National Instruments LabVIEW User Manual, National Instruments Corporation, Nov. 2001 Edition, Part No. 320999D-01, 293 pages.
Naumenko, E. K.; Choice of Wavelengths for Stable Determination of Concentrations of Hemoglobin Derivatives from Absorption Spectra of Erythrocytes; vol. 63; No. 1; pp. 60-66 Jan.-Feb. 1996; Original article submitted Nov. 3, 1994.
Netter, Frank H., “Atlas of Human Anatomy”, Third Edition, 2003.
Nixon et al., “Novel Spectroscopy-Based Technology for Biometric and Liveness Verification,” Proceedings of SPIE vol. 5404, Biometric Technology for Human Identification, Aug. 25, 2004, pp. 287-295.
Nonin Medical, Inc., “Operator's Manual—Models 8600F0 and 8600FOM Pulse Oximeters,” 2005, 25 pages.
Oliver et al., “HealthGear: A Real-time Wearable System for Monitoring and Analyzing Physiological Signals,” Proceedings of the International Workshop on Wearable and Implantable Body Sensor Networks, IEEE Computer Society, 2006, pp. 1-4.
Operator's Manual: Nellcor N-200 Pulse Oximeter, Nellcor Incorporated, Copyright 2003, 96 pages.
Optoelectronics, Data Book 1990, Siemens Components, Inc., 770 pages. (uploaded in 7 parts).
OxiplexTS Near Infrared, Non-Invasive, Tissue Spectrometer Brochure, ISS, Inc., Copyright 2001, 6 pages.
P. Bhandare et al. “Glucose Determination in Simulated Plasma Solutions Using Infrared Spectrophotometry,” 14th Annual International Conference of the IEEE Engineering in Medicine and Biology Society, Nov. 1992, pp. 163-164.
P. Bhandare et al., “Glucose determination in simulated blood serum solutions by Fourier transforms infrared spectroscopy: investigation of spectral interferences,” Vibrational Spectroscopy, vol. 6, No. 3, Mar. 1994, pp. 363-378.
P. Bhandare et al., “IR Spectrophotometric Measurement of Glucose in Phosphate Buffered Saline Solutions: Effects of Temperature and pH,” Proceedings of the 18th IEEE Annual Northeast Bioengineering Conference, 1992, pp. 103-104.
P. Bhandare et al., “Multivariate Determination of Glucose in Whole Blood Using Partial Least-Squares and Artificial Neural Networks Based on Mid- Infrared Spectroscopy,” Society for Applied Spectroscopy, vol. 47, No. 8, 1993, pp. 1214-1221.
P. Bhandare et al., “Neural Network Based Spectral Analysis of Multicomponent Mixtures for Glucose Determination,” Proceedings of the IEEE, 17th Annual Northeast Bioengineering Conference, 1991, pp. 249-250.
P. Branche et al., “Signal Quality and Power Consumption of a New Prototype Reflectance Pulse Oximeter Sensor,” Proceeding of the 31th Annual Northeast Bioengineering Conference, Hoboken, NJ, IEEE, 2005, pp. 1-2.
P. C. Branche et al., “A Wearable Wireless Reflectance Pulse Oximeter with Automatic and Remote On-Demand Activation,” Annual Fall Meeting of the BMES, 2004, p. 1.
P. C. Branche et al., “Measurement Reproducibility and Sensor Placement Considerations in Designing a Wearable Pulse Oximeter for Military Applications,” IEEE, 2004, pp. 216-217.
P. Celka et al., “Motion Resistant Earphone Located Infrared Based Hearth Rate Measurement Device,” In Proceeding of the 2nd International Conference on Biomedical Engineering, Innsbruck, Austria, Feb. 16-18, 2004, pp. 582-585.
P. Muller et al., “A Preliminary In-Vitro Evaluation and Comparative Study of Various Tissue pH Sensors,” Proceedings of the 18th IEEE Annual Northeast Bioengineering Conference, 1992, pp. 158-159.
P. P. Vaidyanathan, “Multirate Digital Filters, Filter Banks, Polyphase Networks, and Applications: A Tutorial,” Proceedings of the IEEE, vol. 78, No. 1, Jan. 1990, pp. 56-93.
P. Shaltis et al., “Novel Design for a Wearable, Rapidly Depolyable, Wireless Noninvasive Triage Sensor,” Proceedings of the 2005 IEEE, Engineering in Medicine and Biology 27th Annual Conference, Sep. 1-4, 2005, pp. 3567-3570.
P. Shyamkumar et al., “Wearable Wireless Cardiovascular Monitoring Using Textile-Based Nanosensor and Nanomaterial Systems,” Electronics vol. 3, 2014, pp. 504-520.
Pandian et al., “Smart Vest: Wearable Multi-Parameter Remote Physiological Monitoring System,” Medical Engineering & Physics 30, 2008. pp. 466-477.
Perform Tek Precision Biometrics White Paper, ValenCell, Jan. 4, 2013, 13 pages.
Perry, T., “Should You Trust Apple's New Blood Oxygen Sensor?” View From the Valley - IEEE Spectrum, Sep. 21, 2020, retrieved from https://spectrum.IEEE.org/view-from-the-valley/biomedical/devices/should-you-trust-apples-new-blood-oxygen-sensor, 4 pages.
Phattraprayoon, et al. “Accuracy Of Pulse Oximeter Readings From Probe Placementon Newborn Wrist And Ankle”, Journal of Perinatology, vol. 32, pp. 276-280, 2012.
Physical Enterprises Inc., Mio Alpha Complete User Guide, Copyright 2012, 15 pages.
Poh et al. “Motion-Tolerant Magnetic Earring Sensor and Wireless Earpiece for Wearable Photoplethysmography”, IEEE Transactions On Information Technology in Biomedicine, vol. 14, No. 3, 2010.
QuickSpecs; HP iPAQ Pocket PC h4150 Series, dated Nov. 20, 2003, in 8 pages.
R. Fensli et al., “A Wireless ECG System for Continuous Event Recording and Communication to a Clinical Alarm Station,” Conf Proc IEEE Eng Med Biol Soc, 2004, pp. 1-4.
R. Gupta et al., “Design and Development of Pulse Oximeter,” Proceedings Rc IEEE-EMBS & 14th BMESI, 1995, p. 1.13-1.16.
R. J. Duckworth et al., Field Testing of a Wireless Wearable Reflectance Pulse Oximeter Printout, Department of Electrical and Computer Engineering and Department of Biomedical Engineering, Worcester Polytechnic Institute, 1 page. Undated.
R. Kasbekar et al., “Evaluation of key design parameters for mitigating motion artefact in the mobile reflectance PPG signal to improve estimation of arterial oxygenation,” Physiological Measurement, vol. 39, No. 7, Jul. 2018, pp. 1-12.
R. Paradiso, “Wearable Health Care System for Vital Signs Monitoring,” In Proceedings of IEEE International Conference on Information Technology Applications in Biomedicine, May 2003, pp. 283-286.
R. Peura et al., “Biotechnology for Biomedical Engineers,” IEEE Engineering in Medicine and Biology, vol. 14, No. 2, Apr. 1995, pp. 199-200.
R. Yotter et al., “A Review of Photodetectors for Sensing Light-Emitting Reporters in Biological Systems”, IEEE Sensors Journal, vol. 3, No. 3, Jun. 2003, pp. 288-303.
Renevey et al., “Wrist-Located Pulse Detection Using IR Signals, Activity and Nonlinear Artifact Cancellation,” Proceedings of the 23rd Annual EMBS International Conference, Oct. 25-28, 2001, pp. 3030-3033.
RF Cafe, Electronic Warfare and Radar Systems Engineering Handbook, Duty Cycle, available athttps://www.rfcafe.com/references/electrical/ew-radar-handbook/duty-cycle.htm, retrieved Jul. 11, 2020, 3 pages.
Rhee et al. “Artifact-Resistant Power-Efficient Design of Finger-Ring Plethysmographic Sensors,” IEEE Transactions on Biomedical Engineering, vol. 48, No. 7, Jul. 2001, pp. 795-805.
Rhee et al. “Artifact-Resistant, Power Efficient Design of Finger-Ring Plethysmographic Sensors, Part I: Design and Analysis,” 22nd Annual International Conference IEEE Engineering in Medicine and Biology Society, Jul. 23-28, 2000, pp. 2792-2795.
Rhee et al., “Design of a Artifact-Free Wearable Plethysmographic Sensor,” 21st Annual International Conferemce IEEE Engineering in Medicine and Biology Society, Oct. 13-16, 1999, p. 786.
Rhee et al., “The Ring Sensor: a New Ambulatory Wearable Sensor for Twenty-Four Hour Patient Monitoring,” Proceedings of the 20th Annual International Conference of the IEEE Engineering in Medicine and Biology Society, Oct. 29-Nov. 1, 1998, 4 pages.
Dresher, “Wearable Forehead Pulse Oximetry: Minimization of Motion and Pressure Artifacts,” May 3, 2006, 93 pages.
S. DeMeulenaere, “Pulse Oximetry: Uses and Limitations,” The Journal for Nurse Practitioners—JNP, May 2007, pp. 312-317.
S. Djamasbi et al., “Affect Feedback during Crisis and Its Role in Improving IS Utilization,” Proceedings of the 7th International Conference on Information Systems for Crisis Response and Management (ISCRAM), 2010, pp. 1-4.
S. Duun et al., “A Novel Ring Shaped Photodiode for Reflectance Pulse Oximetry in Wireless Applications,” IEEE Sensors Conference, 2007, pp. 596-599.
S. Kastle et al., “A New Family of Sensors for Pulse Oximetry,” Hewlett-Packard Journal, Article 7, Feb. 1997, pp. 1-17.
S. LeGare et al., “A Device to Assess the Severity of Peripheral Edema,” IEEE 33rd Annual Northeast Bioengineering Conference, 2007, pp. 257-258.
S. Salehizadeh et al., “A Novel Time-Varying Spectral Filtering Algorithm for Reconstruction of Motion Artifact Corrupted Heart Rate Signals During Intense Physical Activities Using a Wearable Photoplethysmogram Sensor,” Sensors 2016, vol. 16, No. 1, Dec. 2015, pp. 1-20.
S. Salehizadeh et al., “Photoplethysmograph Signal Reconstruction based on a Novel Motion Artifact Detection-Reduction Approach. Part II: Motion and Noise Artifact Removal,” Annals of Biomedical Engineering, vol. 42, May 2014, pp. 2251-2263.
S. Mace, “The Fifth Vital Sign: Pulse Oximetetry in Noninvasive Respiratory Monitoring,” Relias Media, May 1, 2005, retrieved from https://www.reliasmedia.com/articles/85751-the-fifth-vital-sign-pulse-oximetry-in-noninvasive-respiratory-monitoring, 21 pages.
S. N. Kasarova et al., “Analysis of the dispersion of optical plastic materials”, Optical Materials vol. 29, 2007, pp. 1481-1490.
S. Oshima et al., “Optical Measurement of Blood Hematocrit on Medical Tubing with Dual Wavelength and Detector Model,” 31st Annual International Conference of the IEEE EMBS, Sep. 2009, pp. 5891-5896.
S. Patrick et al., “An Electromyogram Simulator for Myoelectric Prosthesis Testing,” Proceedings of the IEEE 36th Annual Northeast Bioengineering Conference (NEBEC), 2010, pp. 1-2.
S. Pentland, “Healthwear: Medical Technology Becomes Wearable,” IEEE Computer Society, vol. 37, Issue 5, May 2004, pp. 34-41.
S. Xie et al., “A Predictive Model for Force-Sensing Resistor Nonlinearity for Pressure Measurement in a Wearable Wireless Sensor Patch,” IEEE 61st International Midwest Symposium on Circuits and Systems, 2018, pp. 476-479,.
Savage et al., “Optimizing Power Consumption in the Design of a Wearable Wireless Telesensor: Comparison of Pulse Oximeter Modes,” Proceedings of IEEE 29th Annual Nonheust Bioengineering Conference, 2003, pp. 150-151.
Scarlett, The Multilayer Printed Circuit Board Handbook, Electrochemical Publications Limited, 1985, 130 pages.
Schmitt, et al., Joseph M .; Measurement of Blood Hematocrit by Dual-Wavelength near-IR Photoplethysmography; vol. 1641; 1992.
Schmitt, Joseph M.; Simple Photon Diffusion Anaylsis of the Effects of Multiple Scattering on Pulse Oximetry; Mar. 14, 1991; revised Aug. 30, 1991.
Schnapp, et al., L.M.; Pulse Oximetry. Uses and Abuses.; Chest 1990; 98; 1244-1250 DOI 10.1378/Chest.98.5.1244.
Service Manual: Nellcor Symphony N-3000 Pulse Oximeter, Nellcor Puritan Bennett, Inc., Copyright 1996, 110 pages.
Service Manual: NPB-40 Handheld Pulse Oximeter, Nellcor Puritan Bennett, Inc., Copyright 2001, 55 pages.
Severinghaus, “Pulse Oximetry,” Computing and Monitoring in Anesthesia and Intensive Care, 1992, pp. 391-403.
Silicon Planar Epitaxial Phototransistor, pp. 5-5-5-6, 1972.
Small et al., “Data Handling Issues for Near-Infrared Glucose Measurements”, http://www.IEEE.org/organizations/pubs/newsletters/leos/apr98/datahandling.htm, accessed Nov. 27, 2007.
Smith, “The Pursuit of Noninvasive Glucose: 'Hunting the Deceitful Turkey”, 2006.
Sonnia Maria Lopez Silva et al., “Near-infrared transmittance pulse oximetry with laser diodes,” Journal of Biomedical Optics vol. 8 No. 3, Jul. 2003, pp. 525-533.
Stephen A. Mascaro et al., “Measurement of Finger Posture and Three-Axis Fingertip Touch Force Using Fingernail Sensors,” IEEE International Conference on Robotics and Automation, 2002, pp. 1-11.
Stephen A. Mascaro et al., “Photoplethysmograph Fingernail Sensors for Measuring Finger Forces Without Haptic Obstruction,” IEEE Transactions on Robotics and Automation, vol. 17, No. 5, Oct. 2001, pp. 698-708.
Stojanovic, et al. “Design of an Oximeter Based on LED-LED Configuration and FPGA Technology”, Sensors, 13, 574-586, 2013.
T. Hayes, 'What's inside a fitness tracker, anyway?' published Nov. 29, 2014, retrieved from https://www.digitaltrends.com/wearables/whats-inside-fitness-tracker-anyway/, 24 Pages.
T. Kiyokura et al., “Wearable Laser Blood Flowmeter for Ubiquitous Healthcare Service,” 2007 IEEE/LEOS International Conference on Optical MEMS and Nanophotonics, Hualien, 2007, pp. 4-5.
T. Martin et al., “Issues in Wearable Computing for Medical Montioring Applications: A Case Study of a Wearable ECG Monitoring Device,” In Proceedings of International Symposium of Wearable Computers (ISWC'00), Feb. 2000, pp. 43-49.
T. Torfs et al., “Body-Heat Powered Autonomous Pulse Oximeter,” IEEE Sensors 2006, EXCO, Oct. 22-25, 2006, pp. 427-430.
Takatani et al., “Experimental and Clinical Evaluation of a Noninvasive Reflectance Pulse Oximeter Sensor,” Journal of Clinical Monitoring, vol. 8, No. 4, Oct. 1992, pp. 257-266.
Takatani et al., “Optical Oximetry Sensors for Whole Blood and Tissue,” IEEE Engineering in Medicine and Biology, 1994, pp. 347-357.
Takumi Morita et al., “Integrated Blood Flowmeter Using Micromachining Technology,” Dec. 2004, pp. 77-80.
Tamura et al. “Wearable Photoplethysmographic Sensors-Past and Present”, Electronics, 3, 282-302, 2014.
Team SO-SIG, Final Report, Aug. 22, 2007, 4 pages.
Townsend, et al. “Pulse Oximetry,” Medical Electronics, 2001, pp. 32-42.
Tura, et al., “A Medical Wearable Device with Wireless Bluetooth-based Data Transmission”, Measurement Science Review, vol. 3, Section 2, 2003.
V. Floroff, “PDA Interface for the WPI Wireless Physiological Monitor,” Directed research, Department of Biomedical Engineering, Worcester Polytechnic Institute, Mar. 2006, 42 pages.
V. Floroff, “Remote Pulse Oximetry: The wireless side of the TATRC project.” Thesis, Worcester Polytechnic Institute, Feb. 2005, pp. 1-20.
V. Konig et al., “Reflexions-Pulsoximetrie—Untersuchungen mit eigenem Mess-System,” Biomedical Engineering, Biomedizinische Technik, vol. 37. No. s2, 1992, pp. 39-40.
Vashist et al., “Commercial Smartphone-Based Devices and Smart Applications for Personalized Healthcare Monitoring and Management”, Diagnostics, 2014, vol. 4, pp. 104-128.
Vogel et al., “In-Ear Vital Signs Monitoring Using a Novel Microoptic Reflective Sensor,” IEEE Transactions on Information Technology in Biomedicine, vol. 13, No. 6, Nov. 2009, pp. 882-889.
W. Johnston et al., “Effects of Motion Artifacts on Helmet-Mounted Pulse Oximeter Sensors,” Proceedings of the IEEE 30th Annual Northeast Bioengineering Conference, 2014, pp. 214-215.
W. S. Johnston et al., “Investigation of Signal Processing Algorithms for an Embedded Microcontroller-Based Wearable Pulse Oximeter,” Proceedings of the 28th IEEE EMBS Annual International Conference, Aug. 30-Sep. 3, 2006, pp. 5888-5891.
Wang et al., “Multichannel Reflective PPG Earpiece Sensor with Passive Motion Cancelation,” IEEE Transactions on Biomedical Circuits and Systems, vol. 1, No. 4, Dec. 2007, pp. 235-241.
Wareing, Optimization of Reflectance-Mode Pulse Oximeter Sensors, National Science Foundation Research Experiences, 1 page. Undated.
Wareing, Previous Research Experience, 2 pages. Undated.
Warren et al., “Wearable Sensors and Component-Based Design for Home Health Care,” Proceedings of the Second Joint EMBS/BMES Conference, Oct. 23-26, 2002, pp. 1871-1872.
Warren et al., “Wearable Telemonitoring Systems Designed with Interoperability in Mind,” Proceedings of the 25th Annual International Conference of the IEEE Engineering in Medicine and Biology Society, vol. 4, 2003, 4 pages.
Warren et al., “Designing Smart Health Care Technology into the Home of the Future, ” Workshops on Future Medical Devices: Home Care Technologies for the 21st Century, Apr. 1999, 19 pages.
Warren, Pulse Oximetry Laboratory, 8 pages. Undated.
Wireless Wearable Reflectance Pulse Oximeter, PowerPoint, The Bioengineering Institute, Worcester Polytechnic Institute, TATRC, 10 pages. Undated.
Withings, Withings Pulse: Activity Tracker—Sleep Analyzer Heart Rate Analyzer—Installation and Operating Instructions (iOS users), Apr. 2015, 43 pages.
Written Opinion received in International Application No. PCT/US2016/040190, dated Jan. 2, 2018.
Y. Shimada et al., “Evaluation of a new reflectance pulse oximeter for clinical applications,” Medical & Biological Engineering & Computing, vol. 29, No. 5, Sep. 1991, pp. 557-561.
Y. Xu et al., “Drowsiness Control Center by Photoplethysmogram,” 38th Annual Northeast Bioengineering Conference (NECBEC), IEEE, 2012, pp. 430-431.
Yan, et al. “ An Efficient Motion-Resistant Method for Wearable Pulse Oximeter,” IEEE Transactions on Information Technology in Biomedicine, vol. 12, No. 3, May 2008, pp. 399-405.
Yao et al., “A Novel Algorithm to Separate Motion Artifacts from Photoplethysmographic Signals Obtained with a Reflectance Pulse Oximeter”, Conf Proc IEEE Eng Med Biol Soc., 2004, 4 pages.
Yao et al., “A Wearable Point-of-Care System for Home Use That Incorporates Plug-and-Play and Wireless Standards”, IEEE Transactions on Information Technology in Biomedicine, vol. 9, No. 3, Sep. 2005, pp. 363-371.
Yao et al., “A Wearable Standards-Based Point-of-Care System for Home Use,” Proceedings of the 25th Annual International Conference of the IEEE, vol. 4, 2003, 4 pages.
Yao et al., “Applying the ISO/IEEE 11073 Standards to Wearable Home Health Monitoring Systems,” Journal of Clinical Monitoring and Computing, vol. 19, No. 6, 2005, pp. 427-436.
Yao et al., “Design of a Plug-and-Play Pulse Oximeter,” Proceedings of the Second Joint EMBS/BMES Conference, Oct. 23-26, 2002, pp. 1752-1753.
Yao, Design of Standards-Based Medical Components and a Plug-and-Play Home Health Monitoring System, A Dissertation for Kansas State University Department of Electrical & Computer Engineering, 2005, 155 pages. [uploaded in 2 parts].
Yuan-Hsiang Lin et al., “A wireless PDA-based physiological monitoring system for patient transport,” IEEE Transactions on Information Technology in Biomedicine, vol. 8, No. 4, pp. 439-447, Dec. 2004.
Zhai, et al. “A Wireless Sensor Network For Hospital Patient Monitoring,” Thesis for University of Calgary Department of Electrical and Computer Engineering, Apr. 2007, 134 pages.

Related Publications (1)

	Number	Date	Country
	20210290120 A1	Sep 2021	US

Provisional Applications (3)

Number	Date	Country
63023156	May 2020	US
62984243	Mar 2020	US
62960610	Jan 2020	US

Wearable device with physiological parameters monitoring

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