ELECTRICAL COUPLING OF PULSE TRANSIT TIME (PTT) MEASUREMENT SYSTEM TO HEART FOR BLOOD PRESSURE MEASURMENT

Abstract

Wrist-worn devices and related methods measure a pulse transit time non-invasively and calculate a blood pressure value using the pulse transit time. A wrist-worn device include a wrist-worn elongate band, at least four EKG or ICG electrodes coupled to the wrist-worn device for detecting a ventricular ejection of a heart, a photo-plethysmogram (PPG) sensor coupled to the wrist-worn device for detecting arrival of a blood pressure pulse at the user's wrist, and a controller configured to calculate a pulse transit time (PTT) for the blood pressure pulse. The controller calculates one or more blood pressure values for the user based on the PTT.

Claims

1. A wrist-worn device for determining a pressure of blood within a cardiovascular system of a user, the cardiovascular system including a heart and the user having a wrist covered by skin, the device comprising: a first pair of electrodes that non-invasively engage the skin over the wrist of the user when the device is worn on the wrist, the first pair of electrodes including a first drive current electrode and a first sense electrode, the first drive current electrode being configured to transfer a drive current between the first drive current electrode and the wrist, the first sense electrode being configured for sensing a first voltage level of the user; a second pair of electrodes that are externally located on the wrist-worn device so as to be interfaceable with the user, the second pair of electrodes including a second drive current electrode and a second sense electrode, the second drive current electrode being configured to transfer drive current between the second drive current electrode and the user, the second sense electrode being configured for sensing a second voltage level of the user, wherein the first and second voltage levels are indicative of an impedance of a thorax of the user; a photo-plethysmogram (PPG) or a pulse pressure sensor coupled to the wrist-worn device for detecting the arrival of a blood pressure pulse at the user's wrist; and a controller configured to: process a signal indicative of the sensed voltage levels to generate an impedance cardiogram (ICG) for the user; process the ICG to detect when blood is ejected from the left ventricle of the user's heart; process a signal from the PPG or the pulse pressure sensor to detect when a blood pressure pulse corresponding to the ejected blood arrives at the user's wrist; calculate a pulse transit time (PTT) for the blood pressure pulse from the ejection of the blood from the left ventricle to arrival of the blood pressure pulse at the wrist; and generate one or more blood pressure values for the user based on the PTT.

2. The wrist-worn device of claim 1, wherein: the second drive current electrode is sized and positioned for contact by a first finger of an arm of the user opposite to the arm on which the device is worn; and the second sense current electrode is sized and positioned to be contacted by a second finger of the opposite arm.

3. The wrist-worn device of claim 2, wherein each of the first drive current electrode and the first sense electrode is disposed so that contact pressure between the first and second fingers and the second pair of electrodes increases contact pressure between the wrist and each of the first drive current electrode and the first sense electrode.

4. The wrist-worn device of claim 1, wherein: the wrist-worn device comprises a wrist-worn elongate band; the first and second pairs of electrodes are disposed on the wrist band; and contact pressure on each of the second pair of electrodes causes: (a) increased contact pressure between the wrist band and a respective one of the first pair of electrodes, and (b) increased contact pressure with the respective one of the first pair of electrodes and the user's wrist.

5. The wrist-worn device of claim 1, wherein the each of the first pair of electrodes is disposed directly between a respective one of the second pair of electrodes and the skin engaged by first electrode.

6. The wrist-worn device of claim 1, wherein each of the second pair of electrodes is configured to be engaged with a skin surface of a thorax of the user while the device is worn on the wrist so that a portion of the drive current propagates through the user's thorax.

7. The wrist-worn device of claim 1, wherein the controller is configured to generate an electrocardiogram (EKG) for the user from one or more signals from the first and second pair of electrodes.

8. The wrist-worn device of claim 1, wherein each of the first and second pair of electrodes is a dry electrode.

9. (canceled)

10. The wrist-worn device of claim 1, wherein the PPG sensor comprises a light source and a plurality of light detectors, at least two of the light detectors being disposed at different distances from the light source so to enable detection of different mean penetration depths of light emitted by the light source.

11. The wrist-worn device of claim 1, wherein the controller is configured to determine the amount of light returned from a deeper penetration depth relative to the detected mean penetration depths.

12. The wrist-worn device of claim 10, wherein at least two of the light detectors are disposed in a range of 2 mm to 10 mm from the light source.

13. The wrist-worn device of claim 10, wherein the controller is configured to process signals from the light detectors to detect when the blood pressure pulse corresponding to the ejected blood arrives at the deep blood plexus (DBP) layer at the user's wrist.

14. The wrist-worn device of claim 10, wherein: the PPG sensor is positioned over a radial artery and configured to detect when the blood pressure pulse corresponding to the ejected blood arrives at the user's wrist within the user's radial artery; and the controller is configured to process signals from the light detectors to detect when the blood pressure pulse corresponding to the ejected blood arrives at the user's wrist within the user's radial artery.

15. The wrist-worn device of claim 10, wherein the controller is configured to process one or more signals from the light detectors to determine a tone of the user's blood vessels, and wherein the one or more blood pressure values generated for the user is further based on the determined tone of the user's blood vessels.

16. The wrist-worn device of claim 10, wherein the controller is configured to determine the amount of light returned from a deeper penetration depth relative to the detected mean penetration depths.

17. The wrist-worn device of claim 1, wherein the PPG sensor comprises at least two light sources configured to emit different wavelengths of light so as to enable detection of a plurality of mean penetration depths for light emitted by the light sources.

18. The wrist-worn device of claim 17, wherein the at least two light sources include at least two of an infra-red light source, a red light source, or a green light source.

19. The wrist-worn device of claim 17, wherein the different wavelengths of light emitted include a first wavelength of about 525 nm and a second wavelength of about 940 nm.

20. The wrist-worn device of claim 17, wherein the controller is configured to process one or more signals from the PPG sensor to detect when the blood pressure pulse corresponding to the ejected blood arrives at the deep blood plexus (DBP) layer at the user's wrist.

21. The wrist-worn device of claim 17, wherein: the PPG sensor is positioned over a radial artery and configured to detect when the blood pressure pulse corresponding to the ejected blood arrives at the user's wrist within the user's radial artery; and the controller is configured to process one or more signals from the PPG sensor to detect when the blood pressure pulse corresponding to the ejected blood arrives at the user's wrist within the user's radial artery.

22. The wrist-worn device of claim 17, wherein the controller is configured to process one or more signals from the PPG sensor to determine a tone of the user's blood vessels, and wherein the one or more blood pressure values generated for the user is further based on the determined tone of the user's blood vessels.

23. The wrist-worn device of claim 17, wherein the PPG sensor comprises a plurality of light detectors, at least two of the light detectors being disposed at different distances from each of the at least two light sources so to detect different mean penetration depths of light emitted by each the at least two light sources.

24. The wrist-worn device of claim 1, wherein the pulse pressure sensor being configured to detect the arrival of the blood pressure pulse at the user's wrist comprises at least one pressure transducer, accelerometer, or strain gauge positioned over a radial artery of the wrist of the user.

25. The wrist-worn device of claim 1, wherein the controller is further configured to calculate trending data for a time period based on the one or more blood pressure values.

26. The wrist-worn device of claim 25, wherein the time period comprises one or more days, one or more weeks, one or more months, or one or more years.

27.-43. (canceled)

Description

BRIEF DESCRIPTION OF THE DRAWINGS

[0034] FIG. 1 illustrates a propagation path of a blood pressure pulse from ejection from the left ventricle to a wrist on which a wrist-worn blood pressure measurement device is worn, in accordance with many embodiments.

[0035] FIG. 2 illustrates EKG, ICG, and PPG signals relative to a pulse transit time (PTT) for a blood pressure pulse propagating from the left ventricle to a wrist on which a wrist-worn blood pressure measurement device is worn, in accordance with many embodiments.

[0036] FIG. 3 schematically illustrates a four-electrode configuration used to measure impedance of a subject, in accordance with many embodiments.

[0037] FIG. 4 is a schematic side view of a wrist-worn blood-pressure measurement device, in accordance with many embodiments.

[0038] FIG. 5 is a cross-sectional view of another wrist-worn blood-pressure measurement device, in accordance with many embodiments.

[0039] FIG. 6 schematically illustrates electrode locations and related body impedances in an approach for measuring chest-cavity impedance variations, in accordance with many embodiments.

[0040] FIG. 6A is a cross-sectional view of another wrist-worn blood-pressure measurement device having exterior electrodes shown engaged with skin of a user's thorax, in accordance with many embodiments.

[0041] FIG. 7 is a schematic diagram of a wrist-worn blood-pressure measurement device main unit, in accordance with many embodiments.

[0042] FIG. 8 shows typical EKG and ICG data traces, in accordance with many embodiments.

[0043] FIG. 9 illustrates subsurface layers of a subject.

[0044] FIGS. 10 through 12 illustrate detection of different mean penetration depths of light emitted by a PPG sensor having returning light detectors disposed at different distances from each of two light sources of the PPG sensor, in accordance with many embodiments.

[0045] FIGS. 13 and 14 show relative contribution by subsurface layer to returning light detected by the light detectors disposed at different distances for two different light source wavelengths, in accordance with many embodiments.

[0046] FIG. 15 illustrates variation of mean penetration depth as a function of source-detector separation for two different source light wavelengths, in accordance with many embodiments.

[0047] FIG. 16 illustrates variation of the ratio of photons from the deep blood plexus (DBP) layer as a function of source-detector separation for two different source light wavelengths, in accordance with many embodiments.

[0048] FIG. 17 illustrates a propagation path of a blood pressure pulse from ejection from the left ventricle past an auxiliary PPG sensor to a wrist on which a wrist-worn blood-pressure measurement device is worn, in accordance with many embodiments.

[0049] FIG. 18 is a schematic side view of an arm-worn auxiliary PPG sensor for a wrist-worn blood-pressure measurement device, in accordance with many embodiments.

[0050] FIG. 19 is a cross-sectional view of another wrist-worn blood-pressure measurement device that can be used with the auxiliary PPG sensor of FIG. 18, in accordance with many embodiments.

DETAILED DESCRIPTION

[0051] In the following description, various embodiments of the present invention will be described. For purposes of explanation, specific configurations and details are set forth in order to provide a thorough understanding of the embodiments. However, it will also be apparent to one skilled in the art that the present invention may be practiced without the specific details. Furthermore, well-known features may be omitted or simplified in order not to obscure the embodiment being described.

[0052] Referring now to the drawings, in which like reference numerals represent like parts throughout the several views, FIG. 1 illustrates a propagation path of a blood pressure pulse from ejection from the left ventricle of a subject's heart to a wrist on which a wrist-worn blood-pressure measurement device 10 is worn, in accordance with many embodiments. The wrist-worn device 10 is configured to detect when the blood corresponding to the blood pressure pulse is ejected from the left ventricle of a subjects heart and when the blood pressure pulse arrives at the wrist-worn device 10. The wrist-worn device 10 is configured to calculate a pulse transit time (PTT) for the blood pressure pulse for the transit of the blood pressure pulse from the left ventricle to the wrist-worn device 10. The determined PTT is then used to determine one or more blood-pressure values for the subject.

[0053] In general, a FIT is the time it takes for a pulse pressure wave to propagate through a length of a subject's arterial tree. PTT has a nonlinear relationship with blood pressure. Factors that can impact how fast a blood pressure pulse will travel at a given blood-pressure in a particular artery, include, for example, arterial stiffness, arterial wall thickness, and arterial inner diameter. Equation (1) provides a functional relationship between PTT and mean arterial blood pressure (MAP).

[00001]$\begin{array}{cc}\mathrm{MAP}=\frac{1}{\alpha }.Math.\ln \left[\frac{\rho .Math..Math.{D\left(\Delta .Math..Math.d\right)}^2}{{{\mathrm{hE}}_0\left(\mathrm{PTT}\right)}^2}\right]& \left(1\right)\end{array}$

[0054] where: [0055] MAP is mean arterial blood pressure; [0056] PTT is Pulse Transit Time; [0057] h is arterial wall thickness; [0058] D is artery diameter; [0059] ρ is density of blood; [0060] E.sub.0 is the Young's modulus of the artery at zero pressure; [0061] α is a subject dependent physiological constant; and [0062] Δd is the arterial distance between the subjects left ventricle and the wrist.

[0063] The pressure pulse travels through different arteries during its transit from the left ventricle to the wrist. As a result, variation in corresponding variables in equation (1), for example, arterial wall thickness (h), artery diameter (D), and Young's modulus of the artery at zero pressure (E.sub.0), will change the relationship between blood pressure and how fast the blood pressure pulse travels through the respective artery. Each blood pressure pulse, however, will travel through the same arteries during transit from the left ventricle to the wrist. Accordingly, a relationship between the overall PTT from the left ventricle to the wrist and MAP can be given by replacing arterial wall thickness (h), artery diameter (D), and Young's modulus of the artery at zero pressure (E.sub.0) with respective effective values suitable for the combination of all the arteries through which the pressure pulse travels from the left ventricle to the wrist. Therefore, equation (1) can be simplified to the relationship given below in equation (2).

[00002]$\begin{array}{cc}\mathrm{MAP}=\frac{1}{\alpha }.Math.\ln \left[\frac{K}{{\left(\mathrm{PTT}\right)}^2}\right]& \left(2\right)\end{array}$

[0064] where:

[00003]$K=\frac{\rho .Math..Math.{D\left(\Delta .Math..Math.d\right)}^2}{{\mathrm{hE}}_0}$

is suitable for the subject and the arterial tree segment over which PTT is being measured.

[0065] The values of (K) and (α) can be determined using any suitable approach. For example, an oscillometric blood pressure measurement cuff can be used to measure one or more blood pressure values for the subject at or at about the same time as when corresponding one or more PTTs are determined for the subject via the wrist-worn device 10. Suitable calibration data can then be formulated using the oscillometric blood pressure measurement cuff measured blood pressure values and the corresponding one or more PTTs for the subject using known approaches. For example, a least squares method can be used to determine suitable values or relationships for determining the values of (K) and (α).

[0066] A similar approach can be used to predict MAP, systolic blood pressure (SBP), and diastolic blood pressure (DBP) values based on a measured PTT value. For example, equations (3), (4), and (5) are example regression equations that can be used to predict MAP, SBP, and DBP, respectively, from a measured PTT.

MAP=K.sub.MAP×[log(PTT)−log(PTT.sub.0)]+MAP.sub.BASELINE  (3)

[0067] where: [0068] MAP is predicted mean arterial blood pressure; [0069] MAP.sub.BASELINE is a baseline measured MAP; [0070] K.sub.MAP is a subject dependent constant for MAP; [0071] PTT is the measured pulse transit time; and [0072] PTT.sub.0 is the measured pulse transit time for MAP.sub.BASELINE.

SBP=K.sub.SBP×[log(PTT)−log(PTT.sub.0)]+SBP.sub.BASELINE  (4)

[0073] where: [0074] SBP is predicted systolic blood pressure; [0075] SBP.sub.BASELINE is a baseline measured systolic blood pressure; [0076] K.sub.SBP is a subject dependent constant for systolic blood pressure; [0077] PTT is the measured pulse transit time; and [0078] PTT.sub.0 is the measured pulse transit time for SBP.sub.BASELINE.

DBP=K.sub.DBP×[log(PTT)−log(PTT.sub.0)]+DBP.sub.BASELINE  (5)

[0079] where: [0080] DBP is predicted diastolic blood pressure; [0081] DBP.sub.BASELINE is a baseline measured diastolic blood pressure; [0082] K.sub.DBP is a subject dependent constant for diastolic blood pressure; [0083] PTT is the measured pulse transit time; and [0084] PTT.sub.0 is the measured pulse transit time for DBP.sub.BASELINE.

[0085] FIG. 2 shows an EKG trace segment 12, an ICG trace segment 14, and a PPG signal 16 relative to a pulse transit time (FIT) 18 for a blood pressure pulse between the left ventricle of the subject to the wrist-worn device 10. In many embodiments, the wrist-worn device 10 includes electrodes used to generate an EKG trace and an ICG trace for the subject and a PPG sensor to generate a PPG signal for the subject. The EKG trace segment 12 has a segment (QRS) known as the QRS complex, which reflects the rapid depolarization of the right and left ventricles. The prominent peak (R) of the EKG trace corresponds to beginning of contraction of the left ventricle. A pulse arrival time (PAT) 20 is the time between the peak (R) of the EKG trace and arrival of the blood pressure pulse at the wrist-worn device 10. As the left ventricle contacts, pressure builds within the left ventricle to a point where the pressure exceeds pressure in the aorta thereby causing the aortic valve to open. A pre-ejection period (PEP) 22 is the time period between the peak (R) of the EKG trace and the opening of the aortic valve. The PEP 22 correlates poorly with blood pressure. The ICG trace 14 provides a better indication as to when the aortic valve opens. The ejection of blood from the left-ventricle into the aorta results in a significant temporary decrease in the thoracic impedance of the subject, which corresponds to a temporary increase in the ICG trace, which is the negative of the change of impedance with time. Accordingly, in many embodiments, the ICG trace 14 is processes to identify a start 24 of the temporary increase in the ICG trace as corresponding to the opening of the aortic valve and the start of the propagation of the blood pressure pulse. In many embodiments, the arrival of the blood pressure pulse is detected via the PPG signal 16, which includes an inflection point 26 that occurs upon arrival of the blood pressure pulse to the wrist-worn device 10.

[0086] FIG. 3 schematically illustrates a four-electrode configuration 30 used to measure impedance of a subject, in accordance with many embodiments. The four-electrode configuration 30 includes a drive current generator 32 electrically coupled with a first drive current electrode 34 and a second drive current electrode 36. In many embodiments, the drive current generator 32 imparts an alternating current to a subject 38 via the electrodes 34, 36. The four-electrode configuration 30 also includes a voltage sensor 40 electrically coupled with a first sense electrode 42 and a second sense electrode 44. The use of the sense electrodes 42, 44, which are separated from the drive current electrodes 34, 36, serves to reduce the impact of impedance and contract resistance by sensing voltage with electrodes that are transferring much lower levels of current relative to the current drive electrodes 34, 36. In many embodiments, the alternating drive current has a frequency between 20 kHz and 100 kHz. Drive currents below 20 kHz may create muscle excitation. And while drive currents at 100 kHz produces skin-electrode impedance approximately 100 times lower than at low frequencies, applied drive currents at greater than 100 kHz may result in stray capacitance. A drive current of about 85 kHz is preferred.

[0087] FIG. 4 shows a side view of a wrist-worn blood-pressure measurement device 50, in accordance with many embodiments. The wrist-worn device 50 includes a main unit 52, a wrist-worn elongate band 54, a first drive current electrode 56, a first sense electrode 58, a second drive current electrode 60, a second sense electrode 62, and a PPG sensor 64. The first drive current electrode 56, the first sense electrode 58, and the PPG sensor 64 are: 1) supported on the wrist-worn elongate band 54, 2) positioned and oriented to interface with a subject's wrist upon which the wrist-worn device 50 is worn, and 3) operatively connected with the main unit 52. The second drive current electrode 60 and the second sense electrode 62 are: 1) supported on the wrist-worn elongate band, 2) positioned and oriented to be interfaceable with the subject so that the drive current travels through the thoracic cavity of the subject (e.g., with separate fingers on the arm opposite to the arm on which the wrist-worn device 50 is worn), and 3) operatively connected with the main unit 52. The main unit 52 includes circuitry and/or software for imparting drive current through the subject via the first and second drive current electrodes 56, 60 and for processing signals from the PPG sensor 64 and the first and second sense electrodes 58, 62 so as to measure a PTT and calculate one or more blood pressure values for the subject based on the PTT.

[0088] FIG. 5 shows a side view of another wrist-worn blood-pressure measurement device 70, in accordance with many embodiments. The wrist-worn device 70 includes the same components as for the wrist-worn device 50, but has the first drive current electrode 56 and the first sense electrode 58 located to enhance contact pressure with a wrist 72 of the subject. In the illustrated embodiment, the first drive current electrode 56 is disposed on a directly opposite inside surface of the wrist-worn band 54 relative to the second drive current electrode 60 such that contact pressure between, for example, a finger of the subject and the second drive current electrode 60 transfers compression through the wrist-worn band 54 to the first drive current electrode 56, thereby increasing contact pressure between the first drive current electrode 56 and the wrist 72. In a similar fashion, the first sense electrode 58 is disposed on a directly opposite inside surface of the wrist-worn band 54 relative to the second sense electrode 62 such that contact pressure between, for example, a finger of the subject and the second sense electrode 62 transfers compression through the wrist-worn band 54 to the first sense electrode 58, thereby increasing contact pressure between the first sense electrode 58 and the wrist 72. Any suitable variation can be used. For example, the locations of the first drive current electrode 56 and the first sense electrode 58 can be exchanged. As another example, the electrodes 56, 58, 60, 62 can be located at any other suitable locations on the wrist-worn band 54. As another example, any suitable number of the electrodes 56, 58, 60, 62 can be disposed on the main unit 52.

[0089] In the illustrated embodiment, the PPG sensor 64 is located on the wrist-worn band 54 so as to be disposed to sense the arrival of the blood-pressure pulse within a radial artery 74 of the subject. Cross sections of the ulna bone 76 and the radius bone 78 of the subject are shown for reference.

[0090] FIG. 6 schematically illustrates electrode locations and related body impedances in an approach for measuring chest cavity impedances, in accordance with many embodiments. In the illustrated approach, the first drive current electrode 56 and the first sense electrode 58 are held in contact with the left wrist of the subject. The second drive current electrode 60 is contacted by the right index finger of the subject. The second sense electrode 62 is contacted by the right thumb of the subject. The first and second drive current electrodes 56, 60 impart a cross-body alternating drive current 80 between the drive current electrodes 56, 60. The cross-body drive current 80 propagates through the left wrist, through the left arm, through the thoracic cavity, through the right arm, and through the right index finger. The combined impedance of the left wrist local to the first drive current electrode 56 and the contact impedance of the first drive current electrode 56 and the left wrist is schematically represented as an impedance (Z1). The combined impedance of the right index finger in contact with the second drive current electrode 60 and the contact impedance of the second drive current electrode 60 and the right index finger is schematically represented as an impedance (Z3). The net cross-body impedance between the impedances (Z1 and Z3) is schematically represented as an impedance (Z5). The combined impedance of the left wrist local to the first sense electrode 58 and the contact impedance of the first sense electrode 58 and the left wrist is schematically represented as an impedance (Z2). The combined impedance of the right thumb in contact with the second sense electrode 62 and the contact impedance of the second sense electrode 62 and the right thumb is schematically represented as an impedance (Z4). In many embodiments, because the first and second sense electrodes 58, 62 are configured to measure a voltage difference without transferring any significant amount of current, the resulting voltage drops across the impedances (Z2 and Z4) are small so that the voltage difference sensed by the first and second sense electrodes 58, 62 matches the voltage difference across the impedance (Z5).

[0091] FIG. 6A shows a side view of another wrist-worn blood-pressure measurement device 71, in accordance with many embodiments. The wrist-worn device 71 includes the same components as for the wrist-worn device 70, but has the second drive current electrode 60 and the second sense electrode 62 located so that they can be engaged with another portion of the user via the user positioning the arm on which the wrist-worn device 71 is worn so as to press the electrodes 60, 62 into contact with any suitable skin portion of the user. For example, FIG. 6A illustrates the electrodes 60, 62 being pressed against a skin location on the user's thorax 73 (e.g., lower breast skin opposite to the arm on which the device 71 is worn). As another example, the electrodes 60, 62 can be pressed against skin on the user's arm opposite to the arm on which the device 71 is worn.

[0092] FIG. 7 schematically represents an embodiment of a wrist-worn device for measuring blood pressure. In the illustrated embodiment, the wrist-worn device includes one or more processors 82, memory 84, a display 86, one or more input/output devices 88, a data bus 90, an ICG/EKG unit 92, the PPG sensor 64, and a PPG sensor control unit 94. In many embodiments, the memory 84 includes read only memory (ROM) 96, and random access memory (RAM) 98. The one or more processors 82 can be implemented in any suitable form, including one or more field-programmable gate arrays (FPGA).

[0093] The ICG/EKG unit 92 includes an ICG/EKG signal processing unit 100, an ICG/EKG digital to analog unit 102, an ICG/EKG analog front end unit 104, and an ICG/EKG analog to digital unit 106. The signal processing unit 100 generates a digital alternating drive signal (e.g., a digital drive signal corresponding to an 85 kHz sinusoidal drive current) and supplies the digital alternating drive signal to the digital to analog unit 102. The digital to analog unit 102 generates a sinusoidal drive current matching the digital alternating drive signal and supplies the sinusoidal drive current to the analog front end unit 104. The analog front end 100 supplies the sinusoidal drive current to the first and second drive current electrodes 56, 60 for propagation through the subject (e.g., as the cross-body alternating drive current 80 illustrated in FIG. 6). Resulting voltage levels are sensed via the first and second sense electrodes 58, 62. Signals from the sense electrodes 58, 62 are processed by the analog front end 104 to generate an analog voltage signal supplied to the analog to digital unit 106. The analog to digital unit 106 converts analog voltage signal to a corresponding digital signal that is supplied to the signal processing unit 100. The signal processing unit 100 then generates corresponding ICG/EKG digital data that can be processed by the one or more processors 82 to determine the opening of the aortic valve and therefore the corresponding start of the propagation of a blood pressure pulse from the left ventricle to the wrist-worn device.

[0094] The PPG sensor unit 64 includes a PPG illumination unit 108 and detector line array 110. The PPG illumination unit 108 includes two light sources 112, 114 which transmit light having different wavelengths onto the wrist. While any suitable wavelengths can be used, the first light source 112 generates a beam of light having a wavelength of 525 nm. The second light source 114 generates a beam of light having a wavelength of 940 nm. Any suitable number of light sources and corresponding wavelengths can be used and selected to provide desired variation in tissue penetrating characteristics of the light. The detector line array 110 can include any suitable number of light detectors. In many embodiments, the light detectors are disposed at a plurality of different distances from the light sources 112, 114 so that the detected light is associated with different mean penetration depths so as to enable detection of the arrival of the blood pressure pulse at different layers and/or within a layer of the wrist deeper than a layer sensed by a single light source and single detector PPG sensor. In the illustrated embodiment, the detector line array 110 includes four light detectors 116, 118, 120, 122, with each of the light detectors 116, 118, 120, 122 being disposed at a different distance from the light sources 112, 114. For example, the light detectors 116, 118, 120, 122 can be disposed at 2 mm, 3 mm, 4 mm, and 6 mm, respectively, from each of the light sources 112, 114. Signals generated by the light detectors 116, 118, 120, 122 are supplied to the PPG control unit 94, which includes an analog to digital converter to generate PPG sensor digital data that can be processed by the one or more processors 82 to determine the arrival of the blood pressure pulse to the wrist-worn device. The PPG control unit 94 controls activation of the light sources 112, 114, and can alternately illuminate the light sources 112, 114 at a frequency sufficiently high to enable combined assessment of the PPG sensor digital data generated by illumination of the wrist with the different wavelengths provided by the light sources 112, 114.

[0095] The generated ICG/EKG digital data and the PPG sensor digital data can be transferred to, and stored in, the RAM 98 for any suitable subsequent use. For example, the data can be: 1) processed by the one or more processors 82 to determine PTTs and corresponding blood pressure values for the subject, 2) displayed on the display 86, and/or 3) output via the input/output devices 88 for any suitable purpose such as to a health care professional and/or a monitoring service. In many embodiments, the one or more processors 82 processes the ICG/EKG and PPG sensor digital data to generate trending data for a time period based on the one or more relative blood pressure values. Such trending data can be generated for any suitable time period, for example, for one or more days, one or more weeks, one or more months, and/or one or more years. One or more blood pressure values and/or associated trending data can be: 1) stored in the RAM 98, 2) displayed on the display 86, and/or 3) output via the input/output devices 88 for any suitable purpose such as to a health care professional and/or a monitoring service.

[0096] FIG. 8 shows typical EKG and ICG data traces, in accordance with many embodiments. AC body impedance Z(t) is calculated using the applied drive current I(t) and the measured resulting voltage difference signal V(t) per equation (6).

Z(t)=V(t)/I(t)  (6)

[0097] The ICG signal is then generated by calculating the negative time differential of Z(t) as shown in equation (7).

ICG Signal=−dZ/dt  (7)

[0098] The EKG signal is generated by voltages generated within the body having variations at a much lower frequency (e.g., 0.05-100 Hz) in comparison to the relatively higher frequency of the impedance drive current (e.g., 85 kHz). Accordingly, signals from the first and second sense electrodes 58, 62 can be processed to generate both the ICG and the EKG traces. When both the EKG and the ICG traces are generated, the pre-ejection period (PEP) can be determined. While the PEP time period does not correlate well with blood pressure, it may correlate with an extent of vasomotion (vasodilation and vasoconstriction) and thereby serve as an additional factor that can be used to correlate blood pressure with measured PTT. For example, a relationship can be developed where predicted blood pressure is a correlated function of both PTT and PEP.

[0099] FIG. 9 illustrates subsurface layers of a subject. The illustrated layers include: 1) the stratum corneum (about 20 μm thick), 2) the living epidermis (80 to 100 μm thick), 3) the papillary dermis (150 to 200 μm thick), 4) the superficial plexus (80 to 100 μm thick with a blood volume fraction of about 1.1%), 5) the reticular dermis (1400 to 1600 μm thick with a blood volume faction of about 0.83%), and 6) the deep blood net plexus (80 to 120 μm thick with a blood volume fraction of about 4.1%). Upon arrival to the wrist, the blood pressure pulse arrives at the deep blood net plexus layer before propagating to the overlying layers. As vasomotion (vasodilation and vasoconstriction) plays an important role in regulating blood flow in arterioles and capillaries further downstream in the arterial tree, using the PPG sensor to detect the arrival of the blood pressure pulse in the deep blood net plexus layer may increase the strength of the correlation between blood pressure and PTT by reducing vasomotion induced variability of PTT in shallower layers more subject to vasomotion induced variation in pulse wave velocity of the blood pressure pulse.

[0100] FIGS. 10 through 12 illustrate detection of different mean penetration depths of light emitted by a PPG sensor having returning light detectors disposed at different distances from each of two light sources of the PPG sensor, in accordance with many embodiments. FIG. 10 illustrates distribution of sensing depths for a combination of a 525 nm light source and a point detector disposed 2 mm from the 525 nm light source. FIG. 11 illustrates distributions of sensing depths for the combination of a 525 nm light source and point detectors disposed at 2 mm, 3 mm, 4 mm, and 6 mm from the 525 nm light source, as well as corresponding graphs of mean penetration depth and ratio of photons from the deep blood net plexus layer to the total detected returned light as a function of source-detector separation. FIG. 12 illustrates distributions of sensing depths for the combination of a 940 nm light source and point detectors disposed at 2 mm, 3 mm, 4 mm, and 6 mm from the 940 nm light source, as well as corresponding graphs of mean penetration depth and ratio of photons from the deep blood net plexus layer to the total detected returned light as a function of source-detector separation. FIGS. 13 and 14 show contribution of the total detected returned light for each layer for each wavelength and source-detector separation. FIGS. 15 and 16 show combined graphs corresponding to the graphs of FIGS. 11 and 12.

[0101] Using the data illustrated in FIGS. 10 through 16, the signals from the detectors 116, 118, 120, 122 generated for each of the light wavelengths generated by the light sources 112, 114 can be processed to detect arrival of the blood pressure pulse within a selected layer (e.g., with the deep blood net plexus layer). For example, arrival of the blood pressure pulse within the reticular dermis layer can be detected first due to the large percentage of the returning light incident on the detectors 116, 118, 120, 122 that returns from the reticular dermis layer. Once the arrival time to the reticular dermis layer is determined, the signals during a suitable time interval prior to the arrival time to the reticular dermis layer can be combined and/or processed to focus attention on detecting the earlier arrival of the blood pressure pulse to the deep blood plexus layer. Typically, infrared (e.g., 940 nm wavelength) light penetrates deeper into the skin compared to visible light such as green (e.g., 525 nm wavelength) or red (e.g., 660 nm wavelength). Hence, a PPG waveform recorded from infrared light corresponds to light reflected from deeper blood vessels, while a PPG waveform recorded from green light corresponds to light reflected from capillaries near the skin surface. Since the blood pulse arrives at deeper blood vessels earlier than capillaries near the skin surface, the blood pulse appears in the infrared PPG before the green PPG at the same location (e.g., on the wrist). A cross correlation of infrared and green PPG signals can be used to determine the relative delay between the arrival of the blood pulse at deeper blood vessels and the arrival of the blood pulse at capillaries near the skin surface.

[0102] The PPG signal can first be filtered in one of several ways, for example with a low-pass filter or with a regression filter. The pulse arrival can be detected as the peak of the amplitude of the PPG signal, or the “zero crossing point”. Alternatively, the PPG signal can be differentiated with respect to time and the differentiated signal used to determine a pulse arrival time. This signal processing can be performed on single pulses, leading to PTs for each heartbeat. Or, the processing can be performed on signals that are an average from more than one pulse. One multi-beat averaging method is to first transform the signals (ICG or ECG, and also PPG) into the frequency domain using a Fourier Transform. Then a cross-correlation between the two transformed signals will give a PTT value.

[0103] FIG. 17 illustrates another approach for measuring a PTT that can be used to generate one or more blood pressure values for a subject. The PTT measured in this approach is for the propagation of a blood pressure pulse from an arm-worn auxiliary device 130 to arrival at a wrist-worn device 132. The auxiliary device 130 and the wrist-worn device 132 can use any suitable approach for detecting the arrival of the blood-pressure pulse, such as via a PPG sensor as described herein.

[0104] FIGS. 18 and 19 show side views of the auxiliary device 130 and the wrist-worn device 132. The auxiliary device 130 includes an arm-worn elongate band 134 and an auxiliary PPG sensor 136 coupled to the band 134. The auxiliary device 130 can include one or more reference features or marks to as to enable reliable positioning and/or orientation of the auxiliary PPG sensor 136 relative to a selected underlying artery so as to detect arrival of the blood pressure pulse within the selected underlying artery. The wrist-worn device 132 can be configured similar to the wrist-worn devices 50, 70 with respect to the PPG sensor 64 and can have a main unit 138 that is configured similar to the main unit 52 with respect to all relevant functionality thereof.

[0105] It will be appreciated that personal information data may be utilized in a number of ways to provide benefits to a user of a device. For example, personal information such as health or biometric data may be utilized for convenient authentication and/or access to the device without the need of a user having to enter a password. Still further, collection of user health or biometric data (e.g., blood pressure measurements) may be used to provide feedback about the user's health and/or fitness levels. It will further be appreciated that entities responsible for collecting, analyzing, storing, transferring, disclosing, and/or otherwise utilizing personal information data are in compliance with established privacy and security policies and/or practices that meet or exceed industry and/or government standards, such as data encryption. For example, personal information data should be collected only after receiving user informed consent and for legitimate and reasonable uses of the entity and not shared or sold outside those legitimate and reasonable uses. Still further, such entities would take the necessary measures for safeguarding and securing access to collected personal information data and for ensuring that those with access to personal information data adhere to established privacy and security policies and/or practices. In addition, such entities may be audited by a third party to certify adherence to established privacy and security policies and/or practices. It is also contemplated that a user may selectively prevent or block the use of or access to personal information data. Hardware and/or software elements or features may be configured to block use or access. For instance, a user may select to remove, disable, or restrict access to certain health related applications that collect personal information, such as health or fitness data. Alternatively, a user may optionally bypass biometric authentication methods by providing other secure information such as passwords, personal identification numbers, touch gestures, or other authentication methods known to those skilled in the art.

[0106] Other variations are within the spirit of the present invention. Thus, while the invention is susceptible to various modifications and alternative constructions, certain illustrated embodiments thereof are shown in the drawings and have been described above in detail. It should be understood, however, that there is no intention to limit the invention to the specific form or forms disclosed, but on the contrary, the intention is to cover all modifications, alternative constructions, and equivalents falling within the spirit and scope of the invention, as defined in the appended claims.

[0107] The use of the terms “a” and “an” and “the” and similar referents in the context of describing the invention (especially in the context of the following claims) are to be construed to cover both the singular and the plural, unless otherwise indicated herein or clearly contradicted by context. The terms “comprising,” “having,” “including,” and “containing” are to be construed as open-ended terms (i.e., meaning “including, but not limited to,”) unless otherwise noted. The term “connected” is to be construed as partly or wholly contained within, attached to, or joined together, even if there is something intervening. Recitation of ranges of values herein are merely intended to serve as a shorthand method of referring individually to each separate value falling within the range, unless otherwise indicated herein, and each separate value is incorporated into the specification as if it were individually recited herein. All methods described herein can be performed in any suitable order unless otherwise indicated herein or otherwise clearly contradicted by context. The use of any and all examples, or exemplary language (e.g., “such as”) provided herein, is intended merely to better illuminate embodiments of the invention and does not pose a limitation on the scope of the invention unless otherwise claimed. No language in the specification should be construed as indicating any non-claimed element as essential to the practice of the invention.

[0108] Preferred embodiments of this invention are described herein, including the best mode known to the inventors for carrying out the invention. Variations of those preferred embodiments may become apparent to those of ordinary skill in the art upon reading the foregoing description. The inventors expect skilled artisans to employ such variations as appropriate, and the inventors intend for the invention to be practiced otherwise than as specifically described herein. Accordingly, this invention includes all modifications and equivalents of the subject matter recited in the claims appended hereto as permitted by applicable law. Moreover, any combination of the above-described elements in all possible variations thereof is encompassed by the invention unless otherwise indicated herein or otherwise clearly contradicted by context.

[0109] All references, including publications, patent applications, and patents, cited herein are hereby incorporated by reference to the same extent as if each reference were individually and specifically indicated to be incorporated by reference and were set forth in its entirety herein.