WO2006113900A2 - Procedes et dispositifs de soulagement du stress - Google Patents

Procedes et dispositifs de soulagement du stress Download PDF

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Publication number
WO2006113900A2
WO2006113900A2 PCT/US2006/015013 US2006015013W WO2006113900A2 WO 2006113900 A2 WO2006113900 A2 WO 2006113900A2 US 2006015013 W US2006015013 W US 2006015013W WO 2006113900 A2 WO2006113900 A2 WO 2006113900A2
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WO
WIPO (PCT)
Prior art keywords
wave
flow continues
point
exemplary
waves
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PCT/US2006/015013
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English (en)
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WO2006113900A3 (fr
WO2006113900A8 (fr
Inventor
Michael Wood
Adam Forbes
Kirstin Rhys
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Helicor, Inc.
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Publication date
Application filed by Helicor, Inc. filed Critical Helicor, Inc.
Priority to MX2007013110A priority Critical patent/MX2007013110A/es
Priority to JP2008507896A priority patent/JP2008536648A/ja
Priority to KR1020077026989A priority patent/KR101303354B1/ko
Priority to AU2006236216A priority patent/AU2006236216A1/en
Priority to CA2604741A priority patent/CA2604741C/fr
Priority to CN200680022173.7A priority patent/CN101203175B/zh
Priority to BRPI0610848-2A priority patent/BRPI0610848A2/pt
Priority to EP06750906.7A priority patent/EP1874186A4/fr
Publication of WO2006113900A2 publication Critical patent/WO2006113900A2/fr
Publication of WO2006113900A3 publication Critical patent/WO2006113900A3/fr
Publication of WO2006113900A8 publication Critical patent/WO2006113900A8/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A62—LIFE-SAVING; FIRE-FIGHTING
    • A62B—DEVICES, APPARATUS OR METHODS FOR LIFE-SAVING
    • A62B7/00—Respiratory apparatus
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/48—Other medical applications
    • A61B5/486—Bio-feedback
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/024—Detecting, measuring or recording pulse rate or heart rate
    • A61B5/02405—Determining heart rate variability
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/024—Detecting, measuring or recording pulse rate or heart rate
    • A61B5/02416—Detecting, measuring or recording pulse rate or heart rate using photoplethysmograph signals, e.g. generated by infrared radiation
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/08—Detecting, measuring or recording devices for evaluating the respiratory organs
    • A61B5/0816—Measuring devices for examining respiratory frequency
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/40—Detecting, measuring or recording for evaluating the nervous system
    • A61B5/4029—Detecting, measuring or recording for evaluating the nervous system for evaluating the peripheral nervous systems
    • A61B5/4035—Evaluating the autonomic nervous system

Definitions

  • the present invention relates to methods and devices for evaluating and treating stress and stress-related disorders. More particularly the present invention relates to biofeedback devices and methods for increasing parasympathetic nerve activity by providing information on respiratory sinus arrhythmia patterns. Background Information
  • KL3:2S 13465.1 relationship between stress and respiratory infections Moreover, those suffering from an illness take longer to recover if suffering from stress as well.
  • ANS ANS
  • Impairment of the ANS results in degenerative disease and premature death.
  • a clinical study examined a single two minute measurement of the ANS from 14,025 healthy men and women between the ages of 45 and 64. After eight years, those with a lower parasympathetic measurement had a much greater incidence of disease and death.
  • Three other studies (US, Denmark, and Finland) have also examined ANS function as it relates to "all cause mortality". In each study, low parasympathetic ANS function preceded and predicted illness and death. Literally hundreds of other studies have examined ANS function as it relates to individual illnesses such as heart disease, diabetes, and stroke.
  • the stress response involves two basic systems: the autonomic nervous system and the endocrine system.
  • the ANS generally innervates smooth muscles of internal organs and consists of sympathetic and parasympathetic divisions.
  • the sympathetic division is responsible for mobilizing energy to respond to emergencies ("fight or flight"), express emotions or perform strenuous activities, while the parasympathetic division acts to exert a calming influence and thereby balance the sympathetic system.
  • sympathetic nerves become increasingly active, they increase heart rate, blood pressure, breathing rates, mental activity (thereby agitating the brain) and other bodily functions. Thus, stress is maintained by high activity of the sympathetic nerves.
  • the endocrine system is also involved in stress-related processes.
  • the hypothalamic-pituitary adrenal (HPA) axis plays a major role in the endocrine system's stress response.
  • the hypothalamus secretes peptide hormones to stimulate the pituitary glands which in turn secrete its own hormones to stimulate other endocrine glands.
  • the adrenal glands secrete Cortisol which regulates metabolism and the production of energy and regulates responses in the sympathetic and parasympathetic branches of the autonomic nervous system. Cortisol levels are directly related to the degree of an individual's stress response.
  • parasympathetic and parasympathetic can be characterized by examining the small changes in the time occurring between each consecutive heart beat.
  • variation in the beat to beat time is caused by the parasympathetic branch. This variation will increase and decrease according to an individual's respiratory pattern.
  • inspiration the parasympathetic branch is inhibited, and the heart rate will begin to rise.
  • expiration the parasympathetic branch engages and lowers the heart rate. This relationship between the
  • RSA respiratory sinus arrhythmia
  • the present invention provides easy to use, cost-effective methods and devices for evaluating and treating stress and thereby disorders caused or exacerbated by stress.
  • the present invention provides methods and devices for identifying individual RSA waves and providing a subject with RSA wave information.
  • This information can be used, for example, in biofeedback settings to assist subjects in reducing levels of stress and achieving rhythmic breathing.
  • the present invention also provides methods and devices which allow for the immediate cessation of the physiological stress response which prevents the stress response from harming the body and mind. Regular use of methods and devices according to the present invention allows for the reversal of physiological damage caused by prior exposures to stress, including the accumulated effects of chronic stress.
  • one exemplary embodiment of the present invention provides portable, handheld biofeedback devices for preventing, reducing or eliminating stress in human subjects.
  • Another exemplary embodiment of the present invention provides methods and devices for maintaining a substantially continual state of high parasympathetic activity for a sustained period of time.
  • Another exemplary embodiment of the present invention provides portable, handheld biofeedback devices which contain a photoplethysmograph ("PPG") sensor and a display screen to provide subjects with information on their RSA waves.
  • PPG photoplethysmograph
  • a further exemplary embodiment of the present invention provides methods and devices for training subjects to reduce levels of stress by achieving a respiration frequency of close to 6 breaths per minute.
  • Another exemplary embodiment of the present invention provides methods and devices which promote the reduction of stress by providing high levels of uninterrupted parasympathetic activity along with real-time feedback on such activity.
  • a further exemplary embodiment of the present invention provides methods and devices which give the user information about the transition in RSA waves from ascending points to descending points wherein such information can be used to guide the respiration of the user.
  • Yet another exemplary embodiment of the present invention provides methods for detecting and correcting erroneous data relating to RSA waves and devices which utilize such methods.
  • Another exemplary embodiment of the present invention provides methods for adjusting scaling on a display screen of portable biofeedback devices and devices which utilize such methods.
  • Still another embodiment of the present invention identifies respiration patterns including depth, rate and volume by analyzing RSA waves and provides a display of same.
  • FIG 1 illustrates a typical heart rate variability (HRV) pattern caused by respiratory sinus arrhythmia (RSA).
  • HRV heart rate variability
  • RSA respiratory sinus arrhythmia
  • Figure 2 illustrates an exemplary series of RSA waves and identifies several pulse peaks.
  • Figure 3 illustrates an exemplary series of RSA waves and calculates the interbeat interval times (IBI) between successive pulse peaks.
  • Figures 4a-d identify, respectively, a representative top point, bottom point, ascending transition point and descending transition point.
  • Figure 5 illustrates representative consecutive ascending and descending transition points.
  • Figure 6 illustrates an exemplary method for identifying a top point.
  • Figure 7 illustrates an exemplary method for identifying a bottom point.
  • Figures 8(a)-(b) depict an exemplary process flow for an exemplary procedure for finding RSA waves within a data set according to an exemplary embodiment of the present invention
  • Figure 9 illustrates an exemplary procedure for identifying RSA waves within a data set.
  • Figure 10 illustrates an exemplary double top wave.
  • Figure 11 illustrates an exemplary method for correcting data from a representative double top wave.
  • Figure 12 illustrates an exemplary display of a stress meter.
  • Figure 13 illustrates an exemplary method for determining long term direction of RSA waves.
  • Figure 14 illustrates an exemplary process flow for an exemplary procedure for determining wave phase.
  • Figure 15 illustrates an exemplary process flow for an exemplary procedure for determining wave side.
  • Figures 16(a)-(b) illustrate exemplary methods for determining wave completion.
  • Figure 17 illustrates an exemplary method for delineating wave boundaries.
  • Figure 18 illustrates an exemplary method for assessing continuity parasympathetic activity
  • Figure 19 illustrates an exemplary method for assessing continuity of parasympathetic activity.
  • Figure 20 illustrates an exemplary embodiment of a device in accordance with the present invention and identifies a potential location for a power switch.
  • Figure 21 illustrates a representative location for a PPG sensor which can collect data from a subject's finger.
  • Figures 22(a)-(b) illustrate alternate methods for a subject to hold an exemplary device while the subject's finger is in the PPG sensor.
  • Figure 23 illustrates an exemplary display of a countdown meter.
  • Figure 24 illustrates an exemplary display of a representative average pulse rate as well as a pulse rate over time.
  • Figure 25 illustrates an exemplary display of an error message.
  • Figure 26 illustrates an exemplary embodiment of a countdown timer.
  • Figure 27 provides a representative illustration of RSA waves of a subject whose breathing has slowed over time.
  • Figure 28 provides a representative illustration of RSA waves of a subject who has taken deeper breaths over time.
  • Figure 29 illustrates a representative RSA pattern consistent with rhythmic breathing.
  • Figure 30 provides a representative display of a subject with a wave frequency of six.
  • Figure 31 provides another representative display of a subject with a wave frequency of six.
  • Figure 32 illustrates an exemplary display of a subject's RSA wave history.
  • Figure 33 illustrates an exemplary display of a subject whose depth of breathing has increased and is generated relatively large waves with a duration of about 10 seconds each.
  • Figure 34 illustrates a representative location for a guided breathing switch for activating a guided breathing function in exemplary devices of the present invention.
  • Figures 35(a)-(b) illustrate an exemplary display for guided breathing with a breathing bar that increases to guide inhalation and decreases to guide exhalation.
  • Figure 36 illustrates an exemplary display of a session summary screen.
  • Figure 37 illustrates an exemplary display of various types of RSA information which may be shown by representative devices according to the present invention.
  • Figure 38 illustrates an alternate form factor for exemplary devices of the present invention.
  • Figure 39(a)-(b) illustrate, respectively, a display having sufficient size to show both accurate data and erroneous data and a display of a small, portable device in which only the erroneous data is discernible.
  • Figure 40 illustrates a series of representative pulse peaks.
  • Figure 41(a)-(b) illustrate, respectively, a representative false positive pulse peak and a representative false negative pulse peak.
  • Figure 42 depicts an exemplary process flow for an exemplary error correction method employed during a representative error correction mode.
  • Figure 43 illustrates representative wave features which may be used to determine when a subject has achieved rhythmic breathing.
  • Figure 44 depicts an exemplary system in which a software process can be implemented according to an exemplary embodiment of the present invention .
  • Figures 45-46 depict an exemplary process flow for an exemplary top level procedure for interacting with a user according to an exemplary embodiment of the present invention.
  • Figures 47-51 depict an exemplary process flow for an exemplary procedure for processing a detected pulse according to an exemplary embodiment of the present invention.
  • Figures 52-54 depict an exemplary process flow for an exemplary procedure for error correction for a sequence of detected pulses according to an exemplary embodiment of the present invention.
  • Figures 55-56 depict an exemplary process flow for an exemplary procedure for error detection for a sequence of detected pulses according to an exemplary embodiment of the present invention.
  • Figures 57 depicts an exemplary process flow for an exemplary procedure for initializing a range for detected pulses according to an exemplary embodiment of the present invention.
  • Figures 58-59 depict an exemplary process flow for an exemplary procedure for processing RSA waves within a sequence of detected pulses according to an exemplary embodiment of the present invention.
  • Figures 60-62 depict an exemplary process flow for an exemplary procedure for processing RSA wavelengths within a sequence of detected pulses to determine a stress level for a user according to an exemplary embodiment of the present invention.
  • Figure 63 depicts an exemplary process flow for an exemplary procedure for assigning wavelengths to RSA waves according to an exemplary embodiment of the present invention.
  • Figures 64-74 depict an exemplary flow process for an exemplary procedure for determining the phase of RSA waves in real-time, using the phase changes to detect the drop point, using the phase changes to detect the completion of a wave, and determining parasympathetic intensity of the newly formed wave.
  • Figs. 75-83 depict another exemplary flow process for an exemplary procedure for determining wave phase and delineating waves on a pulse-by-pulse basis.
  • Figures 84-87 depict an exemplary flow process for an exemplary procedure for determining both the drop point and the completion of a wave in real time.
  • biofeedback methods and devices involve training processes which allow subjects to facilitate changes in behavior or activity in order to improve or maintain one or more physiological functions. Over time, a subject can be trained with biofeedback methods and devices to exercise greater control over these functions. In contrast to other forms of therapy in which treatment is imposed upon the subject, biofeedback methods and devices allow the subject to gradually integrate the training processes into almost automatic responses.
  • the present invention relates to methods and devices which can provide biofeedback information and training for subjects suffering from stress and stress-related disorders.
  • biofeedback information and training may be based on an analysis of respiratory sinus arrhythmia patterns and breathing that can affect such patterns.
  • KL3:2513465.1 There are no known methods for identifying individual RSA waves during spontaneous breathing using only the RSA data set. In order to correlate RSA waves with respiration, usually heart rate and respiration rate information is collected and mapped separately.
  • One aspect of the present invention includes the identification of the individual waves within a RSA data set. Further aspects of the present invention include the use of RSA wave patterns to provide subjects with real-time respiratory feedback information based on heart rate data. Means for decreasing or adequately controlling stress levels are also provided based on wave pattern analysis and respiratory feedback.
  • identification and analysis of respiratory sinus arrhythmia wave patterns begins by measuring a subject's pulse rate on a beat to beat basis. It is well established in medical literature that human heart rates, and therefore pulse rates, continually fluctuate up and down in a wave like manner (Fig. 1). These waves are known as heart rate variability (HRV) waves. When a person is physically still and resting, the HRV waves are related to a person's respiration. These resting HRV waves are medically known as respiratory sinus arrhythmia or RSA waves, as the size and shape of these waves is related to the rate, rhythm, and depth of a person's breathing.
  • HRV heart rate variability
  • the frequency of the waves will essentially match the frequency of respiration. Most individuals breathe within this range, but even when a person is breathing outside this range, the wave frequency still provides a close approximation to the respiration frequency.
  • KL3:251346S.l While the correlation between waves and breathing has been well established in the medical literature by visual analysis, no automated method exists to identify individual waves within a heart beat data set.
  • An exemplary embodiment of the present invention includes a novel method of identifying each individual wave for a heart beat data set.
  • the amount of time (in milliseconds) between two consecutive pulse peaks is called the pp interval (pp) (Fig. 2).
  • a device records successive pp intervals.
  • pp interval points also applies to rr intervals (the interval between consecutive R waves in an electrocardiograph or ECG), any derivative of pp intervals such as the pulse rate points, and any derivative of rr intervals such as heart rate. Collectively, these intervals may be referred to as "heart rate-related intervals.” Furthermore, the same method of extracting RSA waves from pp intervals can be directly applied to these other points as well. Certain preferred embodiments of the present invention, however, parse waves within pp interval data sets.
  • the pulse rate of each recorded pp interval (60,000 / pp) may be displayed on the screen each time a new pulse peak is encountered.
  • the absolute time difference between successive pp intervals (absolute (pp[n] - pp[n-l])) is called the interbeat interval time (IBI) (Fig. 3).
  • IBI interbeat interval time
  • An aspect of the present invention uses the pp interval times to identify individual RSA waves. The methods described herein may be used for both spontaneous and guided breathing.
  • Each p-p may be categorized by examining its relationship to the p-p immediately before it (the previous pp) and the p-p immediately after it (the next p-p).
  • a p-p may be considered a top point (tp) if the previous p-p is equal to or less than it and the next p- p is equal to or less than it as well (Fig. 4a).
  • a p-p may be considered a bottom point (bp) if the previous p-p is equal to or greater then it and the next p-p is equal to or greater than it as
  • a p-p may be considered an ascending transition point (at) if the previous p-p is less than it and the next p-p is greater than it (Fig. 4c).
  • a p-p may be considered a descending transition point (dt) if the previous p-p is greater than it and the next p-p is less than it (Fig. 4d).
  • a p-p may be categorized as either a top point (tp), bottom point (bp), ascending transition point (at), or descending transition point (dt).
  • transition point can be used to refer to both ascending and descending transition points when it is not qualified with the words "ascending” or “descending”.
  • Consecutive transition points refers to a series of consecutive ascending transition points or descending transition points (Fig. 5).
  • top level may be used to refer to the relative height of the top point.
  • R the number of consecutive points immediately to the right of the top point that are less than or equal to the top point. If L ⁇ R, then the top level is equal to L, otherwise the level of the top is equal to R.
  • Fig. 6 illustrates, using three examples, how the top point level may be categorized.
  • bottom level may be used to refer to the relative height of the bottom point.
  • Fig. 7 illustrates, using three examples, how the bottom point level may be categorized.
  • Figs. 8(a)-(b) provide an exemplary flowchart which illustrates an exemplary procedure for finding the RSA waves within a data set while Fig. 9 illustrates how this procedure may be applied.
  • KL3:2513465.1 step is to locate the highest number of consecutive transition points (ctp) in the data set.
  • the highest number of consecutive transition points begins at point 1.
  • the wave depth is equal to the number of these transition points.
  • the wave depth in this example is 2.
  • the wave depth value is adjusted down to 4.
  • the next step is to locate the bottom point to the right of the consecutive transition points where the bottom level is equal to or greater than the wave depth. This is the right valley point (v2) of the RSA wave.
  • bottom point no. 8 has a level of 3, which is greater than the wave depth.
  • the next step is to locate the bottom point to the right of the consecutive transition points where the bottom level is equal to or greater than the wave depth. This is the left valley point (vl) of the RSA wave.
  • bottom point no. 0 has a level 4, which is greater than the wave length.
  • the next step is to find the highest point between the left valley point and the right valley point. This is the peak (p) of the RSA wave.
  • point 6 is the highest point between the two valley points. All data from the left valley point (vl) to the right valley point (v2) is considered processed data. The same procedure is repeated on the remaining unprocessed data until all possible waves have been identified.
  • the wave parsing method discussed above is used each time a new bottom level 4 point is identified.
  • devices according to exemplary embodiments of the present invention "look" for RSA waves between bottom level 4 points.
  • devices may be configured to "look" for RSA waves after each point, or after a certain period of time elapses (every 30 seconds for example), etc.
  • Exemplary embodiments use bottom level 4 points because they have a very high probability of delineating RSA waves. That is, they have a high probability of being valley points (vl, v2) of RS A waves.
  • Double top waves may be formed when a person waits a long time to inhale after he or she has already exhaled. Another may occur when double bottom waves are formed. Double bottom waves may be formed when a person holds his breath for a long time after inhaling. Double tops are easily identified by examining the ratios of lengths of the two waves (Fig. 10).
  • double tops may be defined as situations where: ((pi - v2) / (pi — v2)) ⁇ 0.50 and ((p2 - v2) / (p2 - v3)) ⁇ 0.50 and ((pi - vl) / (p2 - v3)) > 0.75.
  • Double bottoms may be defined as the inverse of double tops.
  • the two waves forming the pattern may be merged together into one wave.
  • Point vl is the vl of the new wave.
  • Point v3 becomes the v2 of the new wave.
  • the highest value between vl and v3 is the peak point of the new wave. This is illustrated by Fig. 1.1.
  • Exemplary embodiments of the present invention can use the RSA wave information described above to assess the user's level of mental stress. This mental stress
  • KL3:25I3465.1 measurement may be presented in devices as a stress meter (Fig. 12(5)).
  • a stress meter Fig. 12(5)
  • Methods and devices according to the present invention can be used to determine the user's stress level by determining how far the user's average wavelengths deviate from a level that represents a relaxed state. Such methods and devices also may compute how irregular (arrhythmic) the user's waves are. These two assessments may be used individually or combined into a single value to indicate the overall stress level.
  • exemplary embodiments of the present invention use wavelengths of 10 seconds as the relaxation threshold when assessing the user's stress level.
  • exemplary embodiments also include methods and devices which compute the average wavelength of the last five waves to determine how far the average is, proportionally, from 10 seconds. This is one example of a "wavelength score".
  • Arrhythmic waves may be quantified using a number of standard variance formulas.
  • Exemplary embodiments of the present invention use the sum of the differences of each consecutive wavelength in the last five waves to compute a "variance score".
  • Exemplary embodiments also can use the sum of the differences between successive wavelengths and may use a rank order weighted averaging so that the variance of the most recent waves count more.
  • KL3:2513465.1 uses 70% of the "wavelength score" + 30% of the "variance score”.
  • the user's stress level can be recalculated each time a new RSA wave is identified.
  • Stress can cause a variety of RSA wave behaviors: decreased peak to peak times, increased peak to peak frequency, decreased wavelength, increased wave frequency, decreased amplitude, irregular wavelengths, irregular wave frequencies, irregular amplitudes, irregular peak to peak times, irregular peak to peak frequencies, irregular peak placements or decreased variation. Any one of the preceding variables, or any combinations thereof, can be applied to RSA waves and used as an indicator of the level of stress. Identifying individual RSA waves and using any of the preceding variables alone, in combination with each other, and/or in combination with other variables, to evaluate stress is within the scope of the present invention and has not been described in the prior art.
  • devices and methods according to exemplary embodiments of the present invention can also use RSA wave information to determine and display both average heart rate and wave frequency.
  • the average of all the pulse rates in the last wave may be used to assess average heart rate. For example, each time a new RSA wave is identified, the average of the pulse rates may be computed and the heart rate may be updated.
  • the wave frequency display also may be updated every time that a new RSA wave is identified.
  • Exemplary embodiments can express frequency relative to waves (breaths) per minute. In exemplary embodiments the wave frequency and heart rate may be rounded to the nearest integer.
  • the present invention provides also provides methods of real-time RSA wave pattern identification. In certain embodiments such methods involve two primary interrupt driven processes.
  • the first process may be triggered each time a new pulse is detected by a PPG sensor. This process may provide for (1) converting received pulses into a pulse rate values (prv); (2) updating the wave display with the new prv; (3) confirming whether a new prv marks the beginning of a new wave (indicating that the previous wave has just been completed); (4) delineating the boundaries of the last wave (identifying the valley-peak- valley points); (5) assessing parasympathetic activity of the wave; (6) displaying an appropriate symbol under the wave; (7) updating the wave history; and (8) updating the score.
  • a pulse rate values prv
  • a second process may be responsible for detecting and marking drop points in real-time. This process may be driven by a clock interrupt. In preferred embodiments, this process may occur, for example, every 250 milliseconds. When the process detects the occurrence of a drop point, it may be marked with a drop point indicator, such as a triangle, for example.
  • the second process may occur each time a pulse is detected.
  • Exemplary embodiments use clock interrupts so that the drop point is detected more quickly. Reasonable results may be provided, however, by marking the drop point based on received pulse beats.
  • Preferred embodiments of the present invention also provide various methods for the precise characterization of RSA wave patterns in real time. Such methods include those that may be conveniently referred to as “wave phase” methods and “wave side” methods.
  • the present invention also provides methods of determining wave phase and devices which utilize such methods.
  • methods of determining wave phase and devices which utilize such methods.
  • a long term wave direction can be assessed. This process is illustrated in Fig. 13.
  • the slope of the last six (6) pulse rate points can be used.
  • the resulting value can, for example, be termed the "long slope”.
  • the slope of a time based sliding window of points for example, can be used (such as, for example, the last 12 seconds, the last 5 seconds, etc.), or, for example, another general indicator of direction could be used.
  • the absolute amount of long term change can then be computed. This provides a degree of change value.
  • the absolute value of the long slope can be used, which can be termed, for example, the "absolute long slope”.
  • the absolute value or similar conversion of any of the long term wave assessments can be used.
  • the short term direction of the wave can be determined.
  • the slope of the last three (3) pulse rate points can, for example, be used. This can be termed, for example, the "short slope".
  • any directional indicator on a smaller subset of points than the points chosen for the long term direction assessment can be used.
  • the short term direction indicator and the absolute long term indicator can be used to assess the actual direction of the wave itself.
  • the short slope can be compared to the absolute long slope, for example. If the short slope is greater than, for example, 30% of the absolute long slope, then the wave direction can, for example, be considered as UP. If the short slope is less than (-1) * 30% of the absolute long slope, then, for example, the direction can be considered as DOWN. If it fails both tests, then the direction can, for example, be considered to be FLAT.
  • Percentages may be based on the degree of desired parasympathetic sensitivity. Higher percentages may be less sensitive to parasympathetic interruption, while lower percentages may be more sensitive. Around 30% is generally sensitive enough to detect major interruptions, yet forgiving enough to put the behavior within the control of the user.
  • the percentage for determining an UP direction can be different from the percentage determining a DOWN direction.
  • other mathematical comparisons of the short slope to absolute long slope can be used, for example, to determine the relative relationship between the two and thereby determine wave direction.
  • other mathematical functions may be used in place of short slope and absolute long slope to assess, for example, the short term direction and the long term degree of change.
  • the wave direction and the long term direction can be used, for example, to determine the phase of the wave.
  • the wave direction and the long slope can be examined in order to make this assessment, as is illustrated, for example, in the exemplary process flow diagram of Fig. 14.
  • Process flow begins at 301, where the query "Long Slope is Positive?" is evaluated. If, for example, at 301 the long slope is positive, process flow moves to 310, where the query "Direction is Up?" is evaluated. If at 310 the direction is UP, then process flow proceeds to 311 and the phase is determined to be RISING.
  • process flow proceeds to 312 and the phase is determined as CRESTING. If, for example, at 301 the long slope is negative (i.e., a "No" is returned at 301 to the query "Long Slope is Positive?") which moves process flow to 320, and then at 320 a "Yes" is returned to the query "Direction is Up?”, then process flow proceeds to 330. If at 301 the long slope is negative (i.e., a "No" is returned at 301 to the query "Long Slope is Positive?") which moves process flow to 320, and then at 320 a "Yes" is returned to the query "Direction is Up?", then process flow proceeds to 330. If at 301 the long slope is positive, but at 310 the direction is not UP, then process flow proceeds to 312 and the phase is determined as CRESTING. If, for example, at 301 the long slope is negative (i.e., a "No" is returned at 301 to the query "Long Slope is Positive?") which moves process
  • KL3:2S1346S.l 330 the direction is DOWN, then process flow moves to 331 and the phase is determined to be FALLING.
  • process flow moves to 332 and the phase is determined to be TROUGHING.
  • the result is passed to 350, where the phase as determined can be returned to another process for further processing or output.
  • the present invention also provides methods of determining wave side and devices which utilize such methods.
  • an alternative to determining all four phases of the wave can be implemented.
  • This alternative method can, for example, just detect the RISING and FALLING phases of a wave using a combination of range and direction.
  • An exemplary process flow for this method is illustrated in Fig. 15. Process flow begins at 401, where "High" - highest prv in a given interval , "Low” - lowest prv in a given interval, and "Range" - High - Low, values can, for example, be obtained.
  • “High”, “Low” and “Range” refer to assessing prv values in a sliding window (such as, for example, the last 12 points, the last 12 seconds, etc.). In exemplary embodiments of the present invention the prv range of the last 12 seconds can be used. At 410 Direction can be assessed, as described above.
  • Phase can be assessed. This can be done by looking at wave direction and current prv in relation to the range. If wave direction is up at the bottom of the range then wave phase has shifted to rising. Alternatively, if wave direction is down at the top of the range then wave phase has shifted to falling. Whether a wave is in the top or bottom of its range can be determined, for example, by choosing a fraction or percentage of total range, as shown in Fig. 15, where being within 25% of the top of the range is considered as near the top, and being no more than 25% above the bottom of
  • KL3:2513465.1 the range is considered as near the bottom.
  • other thresholding values can be used.
  • the current prv can be tested for being in the top 25% of the Range. If at 420 the last point is near the top of the range, i.e., "Yes" at 420, then process flow can proceed to 430 where wave direction is analyzed. If at 430 wave direction is DOWN, then process flow moves to 431 and the wave phase is determined to have shifted to FALLING, and the process is exited at 460. [00116] However, if at 420 the current prv is not in the upper 25% of the range, then process flow moves to 440. At 440 the wave is tested for being in the bottom 25% of the range. If Yes, process flow moves to 450, where, for example, wave direction can be assessed.
  • process flow moves to 451 where wave phase is determined to have shifted to RISING, and the process is exited at 460.
  • process flow moves to 460 and the process is exited. The process is also exited if at 450 the wave direction is not UP or if at 430 the wave direction is not DOWN.
  • Wave Phase (Fig. 15) or Wave Side (Fig. 14), can be used to determine current phase.
  • Wave Side for example, can be used inasmuch as the use of the range adds a degree of precision.
  • Wave Phase for example, may be used inasmuch as it also identifies TROUGHING and CRESTING.
  • the present invention also provides methods of determining wave completion and devices which utilize such methods.
  • the present invention also provides methods of determining wave completion and devices which utilize such methods.
  • the current phase can be tracked on a beat-to-beat basis, using, for example, the phase determination method as described above.
  • the current phase shifts to RISING, it is known that a wave has recently finished, as shown, for example, in Fig. 16a.
  • the wave side can be tracked on a beat-to-beat basis.
  • the wave side shifts to LEFT, then it is known that a new wave has been completed, as shown, for example, in Fig. 16b.
  • the present invention also provides methods of delineating wave boundaries and devices utilizing such methods.
  • the points between the beginning of the previous wave trough and the point where the new wave is rising may be obtained, as shown, for example, in Fig. 17.
  • the lowest point in the previous wave trough may be referred to as the left-valley point.
  • the lowest point between the left-valley and the new rising point may be referred to as the right-valley point.
  • the highest point between the left-valley point and the right-valley point may be referred to as the peak.
  • a wave side analysis could be performed using, for example, the points from the previous wave's right side up to the end of the newly formed wave's right side.
  • the lowest point in the previous wave's right side may be referred to as the left-valley point.
  • the lowest point between the left-valley point and the new waves right side may be referred to as the right-valley point.
  • the highest point between the left-valley point and the right-valley point may be referred to as the peak.
  • the present invention also provides methods of assessing parasympathetic activity and devices which utilize such methods.
  • wave boundaries may be used in the assessment of parasympathetic activity.
  • two parasympathetic parameters may be measured for the resulting wave: the intensity of the parasympathetic response and the continuity of parasympathetic activity.
  • the intensity of parasympathetic response may be determined, for example, by the wavelength (timestamp of the right-valley point minus the timestamp of the left-valley point). If the wavelength is less than, for example, 6 seconds, the intensity may be considered LOW. If the wavelength is greater than, for example, 6 seconds and less than, for example, 9.5 seconds, the intensity may be considered MEDIUM. If the wavelength is greater than or equal to, for example, 9.5 seconds, the wavelength may be considered HIGH.
  • the parasympathetic activity level also may be assessed using traditional RSA measurements such as, for example, consecutive heart period, standard deviation, mean deviation and the like.
  • the slope of every three consecutive points may be computed, for example, by starting from the left-valley point to the peak. If any of the slopes approach zero or become negative, for example, then the parasympathetic outflow was interrupted during the rising of the wave (Fig. 18). Likewise, the slope of every three consecutive points may be computed, for example, by starting from the peak to the right-valley point. If any of the slopes approach zero or become positive, for example, then the parasympathetic outflow was interrupted during the falling of the wave. If the short term slope on the left side of the wave remains high and positive, for example, and the short term slope on the right side of the wave remains high and negative, for example, then parasympathetic outflow is deemed to have been continuous, without interruption (Fig. 19).
  • the threshold for the short term slopes may be variable.
  • Exemplary devices may keep track of the highest positive slope over the last 5 seconds, for example.
  • Such devices may keep track of the absolute value of the highest negative slope of the last 5 seconds, for example. If the absolute value of the highest negative slope is greater than the highest positive slope, for example, that value may be used to represent the "fastest change”. Otherwise, the highest positive slope may be used to represent the "fastest change”.
  • any of the three point slopes are less than 30%, for example, of the fastest change, then parasympathetic interruption is presumed.
  • any of the three point slopes is greater than 30% of (-1) x (fastest change), for example, then parasympathetic interruption is presumed.
  • the present invention also provides methods of detecting drop points and devices which utilize such methods.
  • the drop point detection routine may run, for example, every 250 ms. Each time the, for example, 250 ms clock interrupt triggers, the device may insert a phantom value into a set of received pulse beats. In exemplary devices, phantom values are perceived, for example, as a newly received pulse the moment the interrupt was triggered. The routine then may apply a phase determination method with this phantom value in the data set. If such phase determination method assesses that the phase shifts to FALLING with this phantom value, then the drop point has been detected, because the next actual pulse will occur after the drop point. When the drop point is
  • KL3:2513465.1 detected a symbol such as a triangle, may be displayed immediately by the interrupt routine. If the test is false, no symbol is displayed. Methods utilizing such interrupt routines allow the detection and marking of drop points in real-time.
  • RSA waves may be identified and characterized in any of the ways described above and may be used to provide biofeedback to a user.
  • Such exemplary devices include those that provide information to users in real-time to promote the production of uninterrupted high parasympathetic output over a substantial period of time.
  • other methods and devices are intended to be within the scope of the present invention.
  • alternative embodiments are not explicitly described, it is not the intention of applicants to limit the present invention to the exact description provided in this section.
  • various combinations of features described below may be incorporated into a single device and that such device will fall within the scope of the invention disclosed herein. Naturally, the full scope of the invention is based on the disclosure in the specification as a whole.
  • the present invention provides, for example, battery powered handheld portable devices which may include a PPG sensor, a display screen, control buttons, and a power button (Fig. 20).
  • the user may turn on such devices by pressing a power button. If the devices are used in a dark room, the user may turn on backlighting by pressing the power button a second time and keeping it pressed for a few seconds. Soon after the device is powered on, it may prompt the user to insert a finger into the finger sensor (Fig. 21). The user then may gently hold the device with a finger resting on top of the sensor throughout the
  • the device may be comfortably held vertically, resting on the thumb (Fig. 22a) or at an angle, resting on the curled fingers of the hand holding it (Fig. 22b).
  • the device may then begin to calibrate the PPG sensor.
  • a countdown meter may mark the amount of time required for the calibration (Fig. 23).
  • the device may use the PPG sensor to detect each pulse of blood in the finger.
  • the resulting pulse rate (60,000 / number of milliseconds between two consecutive pulse peaks) then may be plotted on the screen on a pulse by pulse basis (Fig. 24(2)).
  • the display also shows the user his average pulse rate (Fig. 24(1)).
  • PPG sensors can be very sensitive to finger pressure. That is, if the user squeezes the device, the resulting finger pressure may prevent the device from gathering accurate pulse rate information. Whenever the user applies too much pressure, the device may display an error message alerting the user to stop squeezing the device and start to relax his or her finger (Fig. 25). As soon as the user has successfully relaxed his finger, he or she then may return attention to the pulse rate display screen.
  • the device may use the wave information to determine and display one or more of the following: the frequency of the last wave, the average pulse rate of all the pulse points in the wave, the session score, the remaining session time and the stress index - how much mental stress the user is currently experiencing.
  • the device may update the session countdown clock after every RSA wave has been identified.
  • Devices may include a session countdown clock that decrements on a regular basis (e.g., once per second, once every fifteen seconds, etc.). In such embodiments, the device may update after each RSA wave to avoid unconscious associations being made between the clock and the desired behavior. In other words, if the clock counts down on a per second basis, the user could consciously or unconsciously use the seconds as a guide to
  • KL33513465.1 breathing at the rate of 6 breaths per minute Such an association may prevent the user from unconsciously learning how to breathe at 6 breaths per minute whenever becoming stressed. If the user consciously (or even unconsciously) uses the clock, he or she may always be dependent on the device. However, by updating the clock based upon every wave, such a potential situation is not only avoided, but the clock can reinforce the learning. The user will see the exact number of seconds of each breath by the amount that the clock decrements. If the clock were to decrement more slowly (e.g., once every 30 seconds), the potential for unconscious associations between time and desired behavior would be avoided. However, in such an alternative implementation, the clock would not be reinforcing the learning.
  • the session countdown timer may begin to decrement once the first wave is identified and data is displayed (Fig. 26). However, other embodiments may begin decrementing the counter when the user begins to breathe rhythmically, or only when good waves are achieved (e.g., waves with a frequency less than six), or only while the user is practicing rhythmic breathing. Another alternative is to not decrement the counter when the breathe button is being used and guidance is being provided.
  • Users may alter the behavior of the waves, and therefore their calculated stress level, by changing their breathing pattern. As the user slows down his or her rate of breathing, the wavelengths increase and the amplitude of the waves increases as well (Fig. 27). When a person breathes more deeply, the amplitude of the waves becomes even larger (Fig. 28). When a person breathes rhythmically at a steady rate, the wavelengths entrain on the breathing rate (Fig. 29).
  • the user may begin by inhaling deeply and then slowly, letting the air out and extending exhalation. This will cause the wave lengths to become longer and therefore the frequency of the waves to decrease. The user may continue to inhale deeply and to slow exhalation even more until the wave frequency drops to about 6 (Fig. 30).
  • the user may continue breathing at the same rate and rhythm that produced a frequency of about 6. If the user's breathing rate increases, the frequency will increase, indicating that the next breath should have a longer exhalation. If the user's breathing rate becomes too slow, the frequency will drop below about 6, indicating that the exhalation of the next breath should be a little faster.
  • a user may quickly fill the screen with rhythmic waves that are about 10 seconds in length (Fig. 31) corresponding to a frequency of about 6 respiration cycles per minute.
  • the session score may be calculated and displayed after each RSA wave is identified.
  • the score may be based upon how close the user is to achieving the desired behavior.
  • the user may accumulate score points and various methods for scoring the session may be used. In certain embodiments, the user may receive, for example, 3 points if the waves have a frequency of 6 or less. The user may receive two points for wave frequencies of 7 or 8, one point for wave frequencies of 9 or 10 and no points for frequencies greater than 10.
  • the accumulated session score may be displayed numerically. Alternatively, each individual score may be displayed. Yet another alternative is to show the current score along side a set of the previous scores (either numerically or graphically). Certain preferred embodiments may display graphically the current score and a set of the previous scores (Fig. 32). In this way, the user can tell when he or she is breathing rhythmically. When the score display is uniform, the user is breathing rhythmically.
  • KL3:251346S.l gently increases the depth of his or her breathing, the size of the waves will increase (Fig. 33).
  • the user may continue to fill the screen with large waves having wavelengths of about 10 seconds each until the session timer runs out. The user then may find that he or she has achieved a very deep and profound state of relaxation.
  • a breathing guide function may appear on the display.
  • the user may be instructed to inhale as the breathing bar rises (Fig. 35a) and to exhale as the breathing bar descends (Fig. 35b).
  • the breathing guide paces the user's breathing to about 6 breaths per minute with, for example, a 1 :2 inhale to exhale ration.
  • the breathing guide may be programmed to provide other ratios (e.g., 1:3) at a rate of about 6 breaths per minute (e.g., 4-8/minute).
  • the breathing guide may remain active, for example, for about one minute and then, automatically shut off thereafter.
  • the user is encouraged to use the biofeedback protocol to achieve a respiration pattern of about 6 breaths per minute. If the user were to rely solely on the breathing guide, it may be more difficult to learn how to achieve the pattern on his or her own.
  • Alternative embodiments prompt the user to turn off the breathing pattern after a period of time has occurred. Other breathing rates and rhythms may be used as well.
  • Devices according to the present invention may return the user to the regular display after the breathing guide has been completed. The user then may adjust his or her breathing in the manner previously described to reduce the wave frequency to about 6, maintain rhythmic breathing, and increase the size of the waves by breathing more deeply.
  • the user may continue this process until the session timer reaches 0:00, at which time the session summary screen may be displayed (Fig. 36).
  • Exemplary embodiments also include devices which allow the user to use up/down arrows to select the number of large waves he or she wishes to produce during a session. For example, a user may choose to generate 10 large waves during a session. The credit area may increase or decrease to accommodate the number of selected session waves.
  • Devices according to the present invention may continually identify individual
  • RSA waves one at a time.
  • a user may be given one credit, for example, in the credit area each time a large wave is identified, and half a credit, for example, in the credit area each time a medium sized wave is identified.
  • a sound beep may indicate the size of the previous waves. If the previous wave was small, a high pitch beep may be generated, for example. If the previous wave was of medium size, then a mid-level pitch tone may be generated, for example. Otherwise, a low pitch tone may be generated, for example.
  • the sound may be controlled by a switch such as an "(o)" button. Such a button may toggle the sound from, for example, low volume, high volume and off.
  • a breathe feature may temporarily activate a breathing metronome to show the user one way in which he or he may breathe to generate large waves.
  • biofeedback credit is based upon achieving two equally important objectives: a high level of parasympathetic intensity and a sustained parasympathetic outflow.
  • the present invention may detect each wave of parasympathetic activity in real-time. When a new wave is complete, the device may assess both the intensity and continuity of the parasympathetic output that produced that wave. As shown in Fig.
  • a two-dot symbol (Fig. 37a), for example, may be placed underneath the wave. If the wave was produced by a continual, very strong level of parasympathetic activity, then a three-dot symbol (Fig. 37b), for example, may be placed underneath the wave. If the wave was either interrupted and/or weak, a one-dot symbol (Fig. 37c), for example, may be placed underneath the wave. Two squares side-by-side may represent, for example, a broken wave (Fig. 37d).
  • These symbols may reflect the activity of the person's parasympathetic nervous system (the stress recovery system) at the time the wave was made: very active (long wave), active (medium wave), not active (short wave) and interrupted (broken wave).
  • These representations may be displayed in real time and provide information on the last several preceding waves (Fig. 37e). For example, the display may show representations of the last twenty waves or a number much greater or significantly less. Exemplary embodiments also may recall and display representations of waves from much earlier in the breathing session or from previous sessions.
  • the display also may show a cumulative total score for a specific amount of time (e.g., 24 hours) (Fig. 37f).
  • a cumulative total score may be generated, for example, by
  • KL3:2513465.1 assigning a single point for a long wave, a half point for a medium wave and no points for a short wave.
  • the display may continue to update the cumulative total until, for example, a predetermined goal is reached, a preset time period elapses or the cumulative total score is reset.
  • a subject may try to achieve a goal of reaching, for example, 100 points per day.
  • Particularly preferred embodiments of the present invention also provide novel forms of biofeedback information that can be used to induce the desired physiological state through unique breathing exercises. Such embodiments avoid drawbacks of techniques which create one or more interruptions of the parasympathetic branch on a per breath basis. For example, such breathing techniques involve extending exhalation for a very long time.
  • a longer exhale is beneficial; but when it is extended for a long period of time, long exhalations can interrupt the parasympathetic response immediately after the trough of the wave. Waiting to inhale for too long may cause an interruption right before the crest of the wave. Likewise, holding the breath for too long or inhalation that is either too long or too short, for example, can each strain the parasympathetic nervous system, causing a temporary inhibition of parasympathetic outflow.
  • Embodiments of the present invention overcome the above-described shortcomings by, for example, guiding the user in finding a breathing rate and rhythm that produces an intense level of sustained parasympathetic outflow.
  • Feedback provided by methods and devices according to the present invention allows a user to maintain a substantially continual state of parasympathetic outflow, thereby suppressing sympathetic activity.
  • Preferred embodiments of the present invention also may indicate to the user the point at which an RSA wave transitions from cresting to descending.
  • Such drop points may be identified, for example, by marking such point with a marker that is easily visible by a user.
  • Such visible indicators may be in the form of a triangle, for example (Fig. 37g).
  • KL3:2S13465.1 Visible indicators also may be other shapes.
  • the drop point is an ideal time to begin an extended exhale. Indicators alternatively may be audible.
  • a user may quickly learn to extend the exhale to an appropriate length to create, the highest scoring waves (e.g. a three dot wave).
  • the user may also receive guidance to indicate when exhalation has extended too long, as the wave will break resulting in a low scoring wave (e.g., a one dot wave).
  • methods and devices according to certain embodiments of the invention enable users to find their unique window of exhale lengths which produce a sustained outflow of intense parasympathetic activity.
  • the display may provide Exhale Numbers corresponding to a number that the user may count to while exhaling. Once a breathing session begins, the subject may inhale until, for example, a drop point is indicated and then exhale while counting (preferably calmly and silently) to the Exhale Number.
  • a timer bar may descend in an Exhale Number column for a fixed amount of time (e.g., 30 seconds, 60 seconds, etc.).
  • the Exhale Number column may display a score from, for example, 1 to 9 corresponding to the effectiveness of the subject's breathing at that Exhale Number for the fixed length of time.
  • a longer wave indicates more effective breathing than a shorter wave and thus may receive a higher score.
  • the score may be based on a single wave, from all waves, or a subset of the waves.
  • the display also may allow for the selection of alternate Exhale Numbers allowing the subject to experiment with different Exhale Numbers to find
  • KL3:251346S.l one or more which provides the best scores.
  • the best scores are produced by the longest waves.
  • handheld, portable devices may be used as follows: a subject turns a device on by pressing a power button; when prompted a subject inserts, for example, his or her left index finger into a pulse detection portion of the device; while the subject gets comfortable (e.g., subject sits upright with feet flat on floor), the sensor adjusts to the pulse rate of the user; the subject selects a target number of large waves (e.g., 5 to 100 depending on the level of stress perceived by the subject); the subject observes the pulse rate wave on the device's display as he or she breathes at a pace that is natural and effortless; while breathing slowly and deeply, preferably through the nose, the subject may observe the affect of respiration depth and frequency on the wave patterns; the subject creates long waves by exhaling slowly and for a duration approximately twice that of inhalation; long waves are tallied on the device's display, while waves that are not long are not tallied; beginners may press a breathe button on the device to help pace the subject to
  • the device can feature a meter that could be used as an amplitude feedback meter rather than a stress meter.
  • the meter could further have a target bar.
  • the device could graphically display how deeply a person is breathing so he could learn to take deeper breaths. If a target bar is used, users
  • KL3:2S1346S.l could try to breathe deeply enough with each breath to cause the meter to rise above the target bar. Any numerical or graphical feedback (visual or otherwise) of amplitude would be within the scope of this alternative embodiment.
  • wave information e.g., wavelength, amplitude, and peak placement
  • a prescribed breathing protocol e.g., 6 breaths per minute with an inhale:exhale ratio of 1 :3
  • the user could be given a breathing guide while being provided simultaneous auditory or visual feedback on how closely they are conforming to the guided breathing pattern.
  • a target level could be displayed such that a user would be considered compliant if he were above the target level and non-compliant with the breathing protocol if he or she were below the level.
  • Alternative embodiments also may use the variance of one or more wave parameters to detect rhythmic breathing. Then, the degree of rhythmic breathing may be visually displayed numerically, graphically, or in some other manner.
  • audible feedback may be provided. For example, in an exemplary embodiment a tone can increase as the breathing becomes more arrhythmic and decrease as it became more rhythmic.
  • a single beep can indicate rhythmic breathing
  • a double beep can indicate near rhythmic breathing
  • a triple beep could indicate arrhythmic breathing.
  • any of the previously mentioned feedback techniques or derivatives of these techniques could be used independently, in combination with each other, in combination with other techniques, or in combination with both each other and other techniques.
  • Such an implementation may be used, for example, to practice yoga style rhythmic breathing patterns. For example, if the yoga student were practicing rhythmic breathing at an inhale:hold:exhale ratio of 1 : 1 : 1, he or she could use the device to ensure that rhythmic breathing was being maintained.
  • a pre-programmed breathmg guide can be provided on the device so the user could follow the breathing guide while receiving visual and/or auditory feedback on the rhythmicity of his breathing.
  • the breathing guide could be programmable.
  • feedback can be provided not only on the rhythm of the breathing, but rate as well. For example, if the user wanted to practice breathing at a 1:1:1 ratio at 5 breaths per second, visual and/or auditory feedback can indicate the degree to which a user is breathing rhythmically at five breaths per minute. Breathing at another frequency and/or arrhythmically would reduce the score.
  • Another exemplary embodiment provides feedback on the depth of breathing.
  • exemplary embodiments of the present invention can provide auditory and/or visual feedback for the following: rate of breathing, rhythmicity of breathing, depth of breathing, breathing conformance to a prescribed rate/rhythm, transition points from cresting to descending (e.g., drop points) and the like. An assessment can be made of each of these, alone or in any combination. Feedback can be provided on one or more of such assessments. Any implementation that identifies two or more RSA waves and derives rate, rhythm, depth, and/or conformance is within the scope of the present invention.
  • Exemplary embodiments of the present invention incorporate a number of features in addition to those described above.
  • One such feature is the design of the device
  • biofeedback programs used finger PPG sensors, ear PPG sensors, and/or heart rate ECG sensors that attached to a computer via a wire.
  • PPG sensors are sensitive to movement and finger pressure
  • prior devices did not have to deal with the many artifacts created by movement or excessive pressure because they used finger PPG sensors which were often placed on tables or desks. In this situation, users could rest their hands and fingers on the desk which stabilized the hand and finger, thereby preventing excessive movement and finger pressure.
  • exemplary embodiments of the present invention integrate a PPG sensor directly into portable devices and eliminates external wires.
  • devices according to exemplary embodiments of the present invention may be used comfortably in a public setting. Integrating a PPG sensor into a portable device, however, requires innovative form factors. For example, since session times may range from 5 - 15 minutes or may, users of the device will be holding the device, without a stabilizing structure like a desk, for an extended period of time. Accordingly, the present invention provides devices which may be gripped comfortably, while simultaneously allowing the user to gently rest his finger on the finger sensor.
  • the present invention also provides form factors that provide comfort while minimizing artifacts caused by movement and pressure over extended periods of time (e.g., 10 - 15 minutes).
  • Two exemplary form factors accomplish these objectives.
  • the finger sensor may be on the top of the device near one of the edges. Ergonomically, the height from the bottom of the device to the top may be between about 1.5 inches and about 3.5 inches and is preferably around 2.5 inches. This allows the device to be supported either by the thumb when held vertically (Fig. 22a), or supported by the curled fingers when tilted (Fig. 22b).
  • the finger sensor is located on the rounded back of the device with
  • KL3:2513465.1 the display on the front, allowing the device to rest, for example, in the palm of the hand during use (Fig. 38).
  • the particularly preferred form factor is the first-described above which allows for the design of products with a scientific and medical look and feel.
  • the present invention also provides methods for detecting and correcting errors in devices described above and devices which utilize such methods. While either of the above-described form factors minimizes artifacts, the hardware form factor may not eliminate every possible artifact. Because there is no supporting structure such as a table or desk, the hand and finger will move at different times throughout the session. Remaining artifacts may be addressed by software in exemplary embodiments of the present invention which may not only detect when an error has occurred, but may correct it as well. [00166] In general, displays on small portable devices are much more sensitive to errors because such displays are very small compared to that of a desktop computer, for example. When an error occurs on a desktop computer, the display has enough resolution to show both the accurate data and the error (Fig. 39a). On a small, portable device, however, one error can cause all the correct data to become indiscernible due to its low resolution (Fig. 39b).
  • PPG sensors detect the amount of blood pressure in the finger on a continual basis. Each time the heart beats, the corresponding pulse of blood results in a rapid increase in blood pressure in the finger, which then quickly subsides. The PPG sensor continually seeks to identify the time when the blood pressure peaks (Fig. 40). This is the pulse peak. As discussed previously, the amount of time (in milliseconds) between two consecutive pulse peaks is called the pp interval (pp). Devices according to the present invention can record each successive pp interval.
  • the pulse rate of each recorded pp interval (60,000 / pp) can be displayed on the screen each time a new pulse peak is encountered.
  • the absolute time difference between successive pp intervals (absolute (pp[n] - pp[n-l])) is called the interbeat interval time or IBI.
  • Fig. 41 Two types of errors occur when the PPG sensor is attempting to correctly identify the next pulse peak.
  • One type of error can occur when the PPG sensor incorrectly identifies an artifact as a pulse peak. That is, the PPG sensor determines that a pulse peak occurs where one does not actually exist (Fig. 41a). This type of error is called a false positive error.
  • the second type of error occurs when the PPG sensor does not identify a pulse peak that does exist (Fig. 41b). This is called a false negative error. Both false negatives and false positives result in large IBIs. Error free data may or may not result in large IBIs. However, erroneous data always produces a large IBI.
  • the first step in the error detection strategy is to wait for a certain number of heart rate related
  • KL3:2513465.1 intervals (e.g., 10 pp intervals) where every IBI time is less than 200ms. These data points are considered to be error free;
  • the number of consecutive intervals can be less than 10 but needs to be at least 2, preferably at least 3 and even more preferably at least 5.
  • Another alternative is to wait for a set of consecutive data points where every IBI time is less than 1/3 of the lowest heart rate related interval, such as a pp interval, in the consecutive data set (e.g., 5 consecutive pp intervals).
  • range of these data points can be computed.
  • range can refer to the absolute range (i.e., min pp to max pp), a derivation of the range (e.g.
  • each new p-p is tested to determine if it is "in range".
  • a new pp value is considered “in range” if it is greater than the bottom value and less than the top value.
  • "in range” also can refer to any mathematical determination of close proximity of the current p-p to the range as determined by the selected range calculation. For example, if the range was calculated using the standard deviation, "in range” could refer to the statistical determination that the current p-p has an 80% or higher probability of being within the computed variation.
  • the new IBI also may be computed (absolute new pp - previous pp).
  • the new EBI may be tested to determine if it is "large”. In preferred embodiments, the device tests whether the IBI is greater than one half the bottom value of the range. If it is greater, the IBI is considered to be large. In other exemplary embodiments, the JBI time of the new pp interval minus the previous interval can be computed. Other IBI times
  • KL3:2S1346S,1 could be used instead, such as the EBI of the new p-p compared to the average p-p of the last n number of pp intervals.
  • different implementations can use a different threshold for distinguishing large IBIs from non-large EBIs.
  • any implementation can be used that uses the difference of pp intervals or the difference of a derivative of pp intervals (such as the average) in order to detect an error.
  • the device can calculate the range of these pp intervals and initiates an error detection mode.
  • the device can test each new pp to determine if it is "in range” and the device tests each new D3I to determine if it is "large”. Any other suitable method of determining either or both of these two properties for use in error detection also is within the scope of the present invention.
  • the new p-p can be considered to be error-free. If the p-p is not “in range” and the IBI is not “large”, the new p-p can be considered to be error-free and the range is recalculated to include the newly found pp value. If the new p-p is "in range” but the IBI is "large”, the new p-p can be considered to be error-free. However, when the new p-p is "out of range” and the IBI is "large”, then the new p-p can be considered to be the result of an error. Once an error has been detected, it should be corrected. Therefore, each time that an error is detected in error detection mode, the device changes to error correction mode. The device can remain in error correction mode until erroneous condition has been resolved.
  • Fig. 42 provides a flowchart showing an exemplary error correction methodology employed during an error correction mode. Error correction includes summing together each successive pp interval as it is identified until either the sum of the pp intervals
  • KL3:25134G5.1 is "in range” or the sum can be divided by an integer such that the result of the division is "in range”.
  • the sum itself is “in range”
  • all the pp intervals forming the sum can be combined together into a single value equal to the sum.
  • devices according to the present invention will be able to generate corrected values within one or two additional pp intervals.
  • the present invention can include a safety mechanism to resolve this situation if it should occur. For example, if the device remains in error correction mode for too long, then the device recalculates the range by applying a statistical method to all original data points encountered.
  • KL3:2S13465.1 That is, every unprocessed pp interval received from the PPG sensor is used.
  • the range is then computed with a statistical based range calculation, for example, a standard deviation formula.
  • the median pp interval is determined from all unprocessed pp intervals encountered (whether authentic or erroneous).
  • the range is defined as 15 beats per minute below the median up to 15 beats per minute above the median.
  • the pp intervals in the error queue are reprocessed according to the new range. Note that the range could also be computed with a subset of the unprocessed data points (e.g., the last 50 data points).
  • the present invention also can include any method of recalculating the range to resolve an extended error condition.
  • PPG sensors are sensitive to movement and finger pressure. They are also sensitive to bright light and cold fingers. Therefore, there are a number of factors that can cause multiple errors.
  • the device may cycle a display of error messages (such as that shown in Fig 18) until the device exits from error correction mode. Thus, the user will be provided information on changes can be made to assist the device in gathering accurate pulse information.
  • the present invention also provides alternative methods for detecting and correcting errors in a heart rate interval data set. For example, there are a number of implementations that would permit the range and/or IBI thresholds to dynamically change as new heart rate interval values were detected. Such implementations may provide a marginal increase in accuracy in certain circumstances.
  • the range may be continually assessed using a rolling window.
  • the range may be initialized after receiving the first 10 seconds of pp intervals such that each consecutive IBI is less than 200ms. After this point, the range could be continually reassessed using a rolling window of the last 10 seconds of reliable data. The last 10 seconds
  • KL3:25134S5.1 of reliable data may or may not be consecutive.
  • the top of the range CO 0 P) could be the highest p-p in the last 10 seconds of reliable data and the bottom of the range (r__bottom) could be the lowest p-p in the last 10 seconds of reliable data.
  • Another alternative is to dampen the rate in which the range can dynamically expand and contract. For example, each time a new pp value is detected, the range could be updated in three steps. First the data set top (ds_top) and the data set bottom (ds_bottom) are identified from the last 10 seconds of reliable data.
  • the ds_top and ds_bottom are adjusted in a manner such that they do not change significantly from the previous ds__top (p_ds_top) and the previous ds_bottom (p_ds_bottom). For example, if the p_ds_top is greater than ds_top, then ds_top could be reset to p_ds_top - ((p_ds_top - ds_top)/25+l). If p_ds__top less than ds_top then ds_top could be reset to p_ds_top + ((ds_top - p_ds_top)/4 + 1).
  • ds_bottom could be reset to p_ds_bottom - ((p_ds_bottom - ds_bottom)/2 + 1). If p_ds__bottom is less than ds_bottom then ds_bottom can be reset to ((ds_bottom - p_ds_bottom)/25+l). Thus, r_top would be equal to the adjusted ds_top and r_bottom would be equal to the adjusted ds_bottom. A p-p would be considered "in range” if it is between r_bottom and r_top.
  • the above-described methodology can accomplish three objectives. First, it allows the range to dynamically increase and decrease. Secondly, the range can expand faster than it contracts. Third, the bottom of the range can expand faster than the top of the range. There are a number of ways to implement these methods and any implementation that accomplishes any of these three objectives is intended to be within the scope of the present invention.
  • Yet another alternative includes converting the computed pp range to a range of pulse rate values (prv) and comparing each newly detected prv (60,000/pp) to the pulse rate range. "In range” could be determined by whether or not the new prv was less than the
  • prv range calculations can also be dynamic. That is, as new prv' s arrive, the range could be recalculated if the new prv is considered to be reliable (e.g., IBI is not too large).
  • Another method for increasing error detection capabilities is to use two threshold values for determining how close a new IBI is from the previous IBI. For example, if the new IBI is less than the low threshold, it can be considered a "small jump”. If the new IBI is between the two thresholds, it can be considered a "significant jump”. And if the new IBI is higher then the second threshold, it can be considered a "large jump”. Thus, as new values come in, they could be assessed as to whether the new value is "in range” or "out of range”, and whether the new EBI is a small jump, significant jump, or large jump. Decisions on whether to display the value, use the value for updating the range, and/or whether to correct the value may be based upon such assessments.
  • Any heart rate related interval may be used for determining the significance of
  • IBI levels For example, the inter-beat interval difference of two prv's (the prv IBI) could be used when assessing the proximity of the new pulse value to the previous pulse values.
  • IBI's can be computed and assessed for pp intervals, prv values, rr intervals, hr values and the like.
  • Still another alternative includes using the direction of the IBI change to determine whether the jump is small, significant, or large. When a person is physically still, pulse rates can rise or fall at different rates. Thus, different thresholds could be used
  • a prv IBI that's greater than the previous prv IBI could be considered to be a small jump up if it is less than 8 bpm, a significant jump up if it is between 8 - 15 bpm, and a large jump up if it is greater than 15 bpm.
  • a prv IBI that's smaller than the previous prv IBI could be considered a small jump if it is less than 8 bpm, a significant jump if it is between 8 - 12 bpm, and a large jump if it is greater than 12 bpm.
  • Yet another exemplary embodiment includes basing the prv IBI thresholds on the location of the previous prv in the range. If the previous prv is already toward the top of the range, the threshold could be set smaller, since in theory, one would not want the next prv to jump too far outside the range. Likewise, if the previous prv is already toward the bottom of the range, the prv thresholds for jumping down could be decreased.
  • examples of prv IBI thresholds based on the location of the previous prv in the range could include: ((r_top - prev_prv)(l/3))+10 for a small jump up, ((r_top - prev_pr)(2/3))+15 for a large jump up, ((prev_prv - r_bottom)(l/2))+10 for a small jump down, and ((prev_prv - r_bottom) x (2/3))+15 for a large jump down.
  • Yet another exemplary embodiment is to add a third test such as direction when determining if a new heart rate interval point needs to be corrected. For example, if the point fails the IBI and the range tests, but is closer to the range then the previous heart rate interval point, then it could still be considered acceptable.
  • a marginal improvement may be obtainable by combining the dynamic range method, the double IBI threshold method with different thresholds based upon direction, and the heart rate interval direction method.
  • An example of such a combination is as follows. As each new prv is calculated (60,000/pp), it can first be assessed whether or not it is 'immediately displayable'. If the prv is a small jump up or small jump down (using appropriate thresholds) it is 'immediately displayable' and therefore is immediately displayed. If it is a significant jump but is 'in range' then it is 'immediately displayable' and therefore is immediately displayed. Otherwise, it could be reevaluated by direction to see if it is displayable. If the current prv is closer to the range than the previous prv, then it is still displayed. Otherwise, it is not displayed and must be corrected.
  • Combinations of the above-described methods also may be used to determine when a value was 'reliable' or not. That is, these methods may be used to determine whether a new prv should be used in recalculating the dynamic range. For example, if the new prv is a small jump, it could be considered 'reliable'. If the new prv is a significant jump, but is 'in range' then it could be considered 'reliable'. And if the new prv is a significant jump and 'out of range' but is closer to the range than the previous prv, then it can be considered 'reliable'.
  • Methods and devices described above also may use RSA wave information to innovatively scale the area of the display where the waves are shown.
  • the amplitude of RSA waves can vary significantly from person to person.
  • RSA amplitude depends on the individual's age, sex, fitness level, breathing pattern, and more. While large display screens can accommodate large waves or small waves, small display screens on portable devices require sophisticated scaling. Thus, if the scale on a small display is too small, then large waves will not fit on the display. If the scale is too large, then the shape and size of small waves will become indiscernible. And if the scale is too dynamic and adjusts too frequently, then large waves and small waves will appear to be the same size, and the user will not be able to discern whether or when his breathing pattern has changed.
  • Devices according to the exemplary embodiments of the present invention can solve the scaling issue by adjusting the display scaling differently during two stages.
  • the first stage lasts from the time the device is powered on until the user begins to breathe rhythmically.
  • the second stage lasts from the time the device detects rhythmic breathing until the device is turned off.
  • stage 1 a very basic scaling technique can be implemented.
  • stage 2 an innovative approach can be employed so the user can accurately assess when his breathing has become more shallow (less deep).
  • the scaling is preferably zoomed in to a small, preset value. Then, the device zooms out whenever a pulse rate point is encountered that is greater than highest value or lesser than the lowest value that can be plotted using the current zoom level.
  • the scale is zoomed out such that the new pulse point is plotted at the edge of the device display area.
  • the device only zooms out, not in, at the beginning.
  • the display also zooms back in after large waves have exited the screen, so that the full height of the display is used from top to bottom.
  • the display continually zooms in and out such that the data points being shown consume the full range of the display at all times until the user begins rhythmic breathing. [00198] Once the user begins to breathe rhythmically, the device seeks to encourage him to breathe deeply. If the device continued to automatically zoom in when small waves
  • KL3:251346S.l appear, then the small waves produced by shallow breathing will appear the same size as the large waves produced by deep breathing. This will not allow a user to visually discern his depth of breathing from the size of the waves.
  • Devices use the wave information to detect rhythmic breathing.
  • Rhythmic breaths produce waves with uniform wavelengths, frequencies, amplitudes, peak to peak times, and peak placement times (Fig. 43). By measuring the variance of one or more of these wave feature parameters, rhythmic breathing can be identified.
  • Exemplary embodiments calculate the variation of the wavelengths and amplitudes of the last three waves. When both of these variations are low, then rhythmic breathing is considered to have begun.
  • One method of determining variance, and thus establishing when a variance is small, can be based on the percent relative deviation. This method is useful when comparing the variation of two or more values (e.g., peak-to-peak times, wavelengths, frequencies, etc.). This may be done as described below. First the mean (average) of the values can be determined. Then the sum of the difference (sun ⁇ _dif) of each value from the average can be computed. The sum can be divided by the average x number of values. For example, consider four wavelengths: 10, 8, 10, 8 seconds. The average is 9. The sum of the differences from the mean is 4 (10 is 1 away, plus 8 is 1 away, plus 10 is 1 away, plus 8 is 1 away).
  • K13:2SI346S.l relative mean deviation The greater the resulting percentage, the greater the variance.
  • a variance threshold could be set to determine if rhythmic breathing has commenced. For example, if three or more waves have a variation in a wave feature less than 20%, one may conclude that rhythmic breathing has commenced. In a preferred embodiment, rhythmic breathing is considered to have commenced when the variation of the wavelength and amplitude of the last three waves is less than 10% each.
  • rhythmic breathing the can keep track of the largest amplitude (maximum amplitude) formed by the resulting rhythmic waves.
  • the device continues to determine if the user is still breathing rhythmically with, for example, each and every wave. As long as the user continues to breathe rhythmically, the device will continue to look for the largest amplitude (maximum amplitude). If a newly formed rhythmic wave has a higher amplitude than the current maximum amplitude, then the maximum amplitude can be readjusted to be equal to the new amplitude.
  • the display does not zoom in more than the maximum amplitude. That is, the display scale can be set such that a wave with an amplitude equal to the max amplitude would fully consume the screen from top to bottom.
  • the zoom level can be set to not exceed this set point.
  • the device can zoom out, but it may not zoom in beyond the set point determined by the maximum amplitude. In this way, users will notice when they are breathing shallowly, because they will see the relatively smaller waves (relative to the maximum amplitude) on the screen.
  • an erroneous wave (a wave with corrected errors that is incorrectly reconstructed) can have the largest amplitude. This large amplitude may be erroneously high. Also, a person's largest possible amplitude can degrade with time until their lungs become used to rhythmic breathing. That is, as their lungs become tired, they will not be able to reproduce waves with amplitudes equal to the maximum amplitude. Since the device should not frustrate the user, but rather encourage him to produce the largest waves that he
  • the device can decrease the maximum amplitude value over time if a successive series of waves do not come sufficiently close to the maximum amplitude.
  • the maximum amplitude may be readjusted using the following formula: (largest amplitude of the last three waves) x (100 / 85).
  • Another alternative is to continually decrease the maximum amplitude until the waves are sufficiently close to occupying the display from top to bottom.
  • the maximum amplitude could be decremented by 5% every time a newly formed rhythmic wave has an amplitude less than 80% of the current max amplitude.
  • Another way to use amplitudes would be to take the highest average amplitude. For example, the average amplitude of the last three waves could be calculated every time a new wave is encountered. The highest average amplitude can be used as the minimum set point.
  • Methods and devices described above may be implemented, for example, as a process stored in a memory of a data processing device, such as, for example, a computer.
  • a process can, for example, be in the form of software, and can, for example, be executed by a data processor or CPU and the results displayed on a display, such as, for example
  • KL3:251346S.I example, a CRT, plasma or other computer display as is known in the art.
  • such software can be implemented on a system comprising a CPU, a memory, and a display, all connected by one or more busses or data pathways.
  • Fig. 44 depicts such an exemplary system.
  • an I/O or input/output interface 5501 a CPU 5505 and a memory 5510.
  • the three components of the exemplary system are communicably connected via a system bus 5520.
  • system bus 5520 is a logical component, and in any given embodiment, can comprise a plurality of interconnections between system elements.
  • a software process can be loaded in memory 5510 and executed in CPU 5505.
  • a user can provide input to the process via the I/O 5501, and output to user by way of visual, auditory, tactile, or other means can be provided to a user also using the I/O.
  • Such I/O can comprise a physical interface device, comprising one or more sensors, or can, for example, comprise one or more of a microphone and one or more speakers, a keyboard, mouse and visual display, and a tactile input and output mechanism .
  • such a software process can, for example, be expressed using any appropriate computer language or combination of languages using known techniques, and can be, for example, implemented as an embedded system or a conventionally stored program of instructions using known techniques.
  • Such a software process can be implemented, for example, on a device which can be used to evaluate stress in humans, as described above.
  • Such an exemplary software process can have, for example, a top level process that interacts with a user by displaying messages to a user and by, for example, continually looking for and responding to various user actions, such as, for example, a user pressing a breathing guidance button or a pulse emanating from a user's finger.
  • a top level process that interacts with a user by displaying messages to a user and by, for example, continually looking for and responding to various user actions, such as, for example, a user pressing a breathing guidance button or a pulse emanating from a user's finger.
  • KL3:25U465.1 software process is depicted in Figs. 45-63, as next described. It is noted that Figs. 8(a)-(b), described above, integrate with this exemplary software process, and thus the "process_waves" subroutine, described below in connection with Fig. 58, calls the subroutine "get_waves” depicted in Figs 8(a)-(b).
  • Figs. 45-46 depict an exemplary top level process, which can control what is displayed to a user and can, for example, respond to user actions.
  • This top level process essentially initializes variables and then waits for interrupts to which it responds.
  • variables can be initialized. This initialization can include, for example, setting the device mode to "Spontaneous" and setting the values for the following variables to zero: number of raw timesteps, number of timesteps, number of pp intervals, number of interbeat intervals, error_sum, number of waves, number of pp intervals and number of pp interval timesteps, as well as setting the variable state to RAW.
  • an "Insert Finger” message can be displayed to a user.
  • the process waits for an interrupt, taking no further action until one occurs.
  • the display message is updated and the interrupt cleared, returning to 3602.
  • Process flow then moves to 3720, for example, where the device mode is set to "Guided", the variable Start set to be the current time and the interrupt cleared. Process flow can then move to 3721, where a clock interrupt
  • KL3:2513465.1 can be, for example, set to 100 milliseconds.
  • Process flow can then move to 3730, where the Guided Mode display can be presented to the user.
  • Process flow then returns through breakpoint 2 in Fig. 37 back to 3603 of Fig. 45, where the top level process again waits for another interrupt to occur.
  • process flow can move to 3702, the Mode variable is reset to "Spontaneous", and process flow moves to 3701 where, for example, the Spontaneous Mode display is restored.
  • Process Pulse calls the subroutines error_correction (Figs. 52-54), error_detection (Figs. 55-56), initialize_range (Fig. 57) and process_waves (Figs. 58-59).
  • process_waves calls subroutines get_waves (Figs. 8(a)-(b)) and determine_stress (Figs. 60-62).
  • the raw timestep rt[n_rt], which is rt[O], given the initialization at 3601 of Fig. 45, is set to the current time in milliseconds, and n_rt, or the number of raw timesteps, is pre-incremented.
  • state DETECTION
  • the data path beginning at 3804 will be taken, ultimately calling an error_detection subroutine at 3910 of Fig. 48.
  • state RAW
  • process flow can continue directly to 3901 of Fig. 48 where timing variables are initialized, including pre-incrementing n_ts, a variable that tracks the number of timesteps, and through 3902 where n_ts is verified to be greater than one. If that is the case, at 3903, for example, n_val, the number of pp intervals to be assigned, can, for example, be set equal to 1, and process flow can continue, through breakpoint 9, to 4010 of Fig. 49, and through to 4011.
  • each pp value is assigned a value and if there are more than one pp values (i.e., n_val >1) then the actual time steps can be generated, and the instantaneous pulse rate is displayed, which is the frequency of the current pp interval determined by (60000/pp[n_pp-l]).
  • IBFs interbeat intervals
  • process flow moves to 4201 to test how many pp values there are. If there are more than 8, i.e., at least 9, then there is sufficient data to identify a level 4 valley. Once there is are at least two level 4 valley points, i.e., num_val4 > 1 at 4212 the exemplary process can look for RSA waves, as described above. Thus, a yes at 4212 can, for example, cause the process flow to call a process_waves subroutine at 4213.
  • Figs. 52-54 depict an exemplary process flow for an error correction subroutine. As described above in connection with the exemplary Process Pulse routine, at
  • an error correction subroutine is called.
  • process flow begins at 4301, where the subroutine begins.
  • a variable err_sum which accumulates current pp interval times, has the most recent pp interval added to it.
  • n__val is set to 0.
  • Process flow continues at 4303, where the new value for err_ sum is tested as to whether it is in range.
  • process flow can move, for example, to 4310, where the variable n_val is set to 1, representing a correct pp interval being identified, and the value of that pp interval is set equal to the number of milliseconds in err_sum, and process flow returns at 4320 to Process Pulse.
  • process flow can move to 4304, where, for example, the subroutine tests whether the current pp interval time is below the range. If yes, process flow returns to 4302 and an additional pp interval time is added to the variable errjsum.
  • test_integer 2 is set as a test divisor and process flow can move, for example, to 4402 where a temporary variable tmp_val is set up to hold the quotient of err_sum/test_integer, representing a possible actual corrected pp interval. Process flow can then move to 4403, where, for example, tmp_val is tested for being above the range. If yes, then at 4410, for example, the test_integer variable is incremented and the proposed division occurs one more time at 4402.
  • a count variable can be set to 1, and at 4502, for example, the subroutine can query whether count is less than the current value of test_ integer. If no, then process flow can move, for example, to 4510, and the variable n_val can be set equal to
  • KL3:2S1346S.l test_integer and at 4520 for example, return to Process Pulse, at breakpoint 6 of Fig. 47.
  • process flow can, for example, loop through 4503, 4504 and 4502, incrementing the value of count each loop (at 4504) until count equals test_integer, at which time process flow can return to Process Pulse.
  • Figs. 55-56 process flow begins at 4601 and continues to 4602, where a current pp interval is loaded into temporary (in the sense of tentatively correct) pp interval tmp_pp .
  • tmp_pp is tested for being within range. If yes, then n_val is set to 1 and val[0] is set equal to tmp_pp at 4610 and at 4620 process flow returns to the calling program, Process Pulse, in particular to 3911 in Fig. 48. However, if at 4603 tmp_pp is found to be out of range then, at 4604, temporary interbeat interval variable tmp_ibi is generated to use in detecting any errors as described above. Process flow can then continue (through breakpoint 22) to 4701 of Fig. 56, where tmp_ibi is tested for being greater than half the lower end of the range, which is a test for being too large, as described above.
  • err_sum is set equal to tmp_pp (err_sum is an input to the error correction subroutine described above)
  • state is set to be CORRECTION
  • tmp_ibi is not greater than half of the lower end of the range, in which case it is not considered to be large and thus no error present in the pp interval data
  • process flow can continue to 4710, and, for example, test whether the tmp_pp is greater than the top of the range. Because tmp_ibi was not found to be large at 4701, and thus no error is assumed present, if at 4710 the tmp_pp interval is still larger than the existing top of the
  • KL3:2S1346S.l range the range needs to be recalculated using the new pp interval as max_pp, which holds the value for the maximum possible pp interval which is not the result of an error in the data.
  • max_pp can be set equal to tmp_pp and, using this new value, at 4712, for example, the upper and lower ends of the range are recalculated.
  • Flow can then continue, for example, to 4713 where the n_val is set equal to 1 and val[0] is set equal to the current pp interval, tmp_pp.
  • process flow can return to the calling routine Process Pulse.
  • process flow for the subroutine initializejrange is next described.
  • This subroutine can be used in exemplary embodiments of the present invention to calculate the range for pp intervals within which the data is assumed to be error free, for use in the error detection and correction routines.
  • the upper and lower ends of the range of data points used for error detection and correction as described above.
  • Figs. 58-59 depict an exemplary process flow for a wave processing subroutine.
  • a pulse acquisition processing routine such as Process Pulse, as
  • process flow can continue at 4902, where the get_waves subroutine described above can be called to input the waves identified from the pulse data.
  • process flow continues, for example, to 4903, where, given the acquired waves, a score indicative of a user's stress level reflected in the identified waves can be assigned using an exemplary determine_stress subroutine.
  • process flow can continue to 5001 on Fig. 59, where a score between 0-3 can be assigned to a user based upon the frequency of the current wave, where a higher score indicates a lower stress level.
  • the subroutine can, for example, display to the user each of his or her (i) stress level (obtained from the call to determine_stress at 4903); (ii) frequency (from 4904); and (iii) score (from 5001), at which point, for example, at 5003, process flow can return to the calling routine, Process Pulse.
  • Figs. 60-62 depict an exemplary subroutine for determining a stress score.
  • Fig. 60 At 5104 the determine_stress subroutine calls assigned_wavelengths, which assigns a wavelength between wl_lo and wl_high (which are set at 5102) to each wave. Using these wavelengths and how many waves there are (i.e., the value of n_waves), Figs. 60-61 depicts process flow for each value of njwaves between 1 and 4.
  • a scorel is determined at each of 5110, 5201, 5202 and 5203, which is a weighted sum of the differences between each wave's wavelength and w_lo, which measures how far off the baseline that particular wave is.
  • w_lo a weighted sum of the differences between each wave's wavelength
  • w_lo a weighted sum of the differences between each wave's wavelength
  • process flow can begin at 5401 with a call to the subroutine.
  • the value of wl is compared with that of wl_lo and wl_high, which can be set in the calling subroutine as seen at 5102 of Fig. 60 (where, for example, they are set as 3 and 10, respectively). If wl is less than wl_lo or higher than wl_high, a_wl[n] is truncated at either wl_lo or wl_high, as the case may be, and flow continues at 5407 where the value of n is pre-incremented.
  • wl has a value between wl_low and wl_high
  • a_wl[n] is set to wl, and process flow continues to 5407.
  • the value of n is compared with that of n_waves, to insure that each acquired wave has been assigned a wavelength. If they are equal, at 5410, for example, process flow ends for this subroutine, and returns to 5105 n Fig. 60. If they are not equal, then flow loops through 5403 for each acquired wave until all acquired waves have been assigned wavelengths.
  • Exemplary embodiments of the present invention also provide, tor example, methods and devices which can determine the phase of RSA waves in real-time, using the phase changes to detect the drop point, using the phase changes to detect the completion of a wave, and determining parasympathetic intensity of the newly formed wave.
  • Figs. 64 to 74 depict exemplary flow processes for an exemplary procedure for determining the phase of RSA waves on a pulse-by-pulse basis, using the phase changes to detect the drop point, using the phase changes to detect the completion of a wave, and determining parasympathetic intensity of the newly formed wave.
  • This exemplary embodiment describes a single, interrupt driven process that executes each time a new pulse is received.
  • This exemplary process begins at 6000 (Fig. 64).
  • the first step, 6001 in the process is to clear all counters: num_points (tracks the number of pulses received), num_valley (tracks the number of wave valleys identified), num_peaks (tracks the number of wave peaks identified), prey_phase (keeps track of the previous wave phase), prev_direction (keeps track of the previous wave direction), prey_side (keeps track of the previous wave side), and wave_size (tracks the length of the last wave).
  • Fig. 65 describes an exemplary process for processing a pulse. This process begins at 6004. The first step in the process, at 6005, is to get and record the timestamp in ms of the new pulse beat, which is stored as point[num_points].ts. Then the process flows to 6006 where it assesses whether there are at least two points within the record. If not, the process flows to 6007 where the num_points counter is incremented. The process further continues to 6012 and returns. However, if there are at least two points in the record, the process flows to 6008.
  • the peak-to-peak (pp) time of the last two points is computed and recorded as point[num_points].pp. Also, the pulse-rate-value represented by the pp time is computed and recorded as point[num__points].prv. Then the flow continues to 6010. [00230] At 6010 the process assesses whether there are at least 8 points in the record.
  • the flow continues to 6011, and the num_points counter is incremented.
  • the process further continues to 6012 and returns. However, if there are at least 8 points in the record, the
  • KL3:2513465.1 process flows to 6009, which calls the Process Wave process. After the Process Wave process returns, the process in Figure 65 flows to 6012 and returns.
  • Figure 66 describes a process for processing wave information.
  • the process begins at 6013.
  • the first step, at 6014, consists of computing and storing the long_slope, abs_long_slope, and the short_slope.
  • the flow then continues to 6015 where the direction is determined by the Get Direction process.
  • the flow continues to 6016 where the phase of the wave is determined by the Get Phase process.
  • the flow continues to 6017 where the side of the wave is determined by the Get Side process.
  • the Get Side process returns the flow continues to 6018.
  • the process determines whether or not there has been a change in sides. If the wave has not changed sides, the process flows to 6020. Otherwise, the process flows to 6019 where the peaks and valleys are assessed by the Get Peaks and Valleys process. After this process returns, the flow continues to 6020.
  • the process sets a flag indicating whether a wave has just completed or not via the Check to See if Wave has Completed process. After this process returns, the flow continues to 6021 where the Wave Completed flag is checked. If a wave has not just completed, the flow continues to 6023. Otherwise, the flow continues to 6022.
  • the Mark Parasympathetic Strength of Wave process delineates the newly formed wave, assesses its parasympathetic activity, and marks the activity under the wave using visual symbols. After this process returns, the flow continues to 6023.
  • a flag is set indicating whether the drop point has just been crossed or not.
  • the Check to See if Drop Point is Occurring process makes this determination and sets the flag accordingly. After this process has returned, the flow continues to 6024 where the flag is analyzed. If the drop point flag has not been set, the flow continues to 6026.
  • the prev__phase, prev_side, and prev_direction markers are assigned.
  • Figure 67 describes the Get Direction process.
  • the first step at 6029 checks to see if the short term slope is greater than 30% of the absolute long slope. If it is, the flow continues to 6030. Otherwise the flow continues to 6032.
  • the process checks to see if the short slope is less than 30% of -1 x absolute long slope. If it is, the flow continues to 6033. If not, the flow continues to 6031.
  • the process checks to see if the prev direction has never been set yet.
  • prev_direction gets recorded as the current direction (direction). The flow continues to 6036 where the process returns.
  • Figure 68 describes an exemplary Get Phase process.
  • the first step at 6038 checks to see if the long slope is positive. If it is, the flow continues to 6040. If it is not, the flow continues to 6044.
  • the process checks to see if the direction is UP. If it is, the flow continues to 6039. If it is not, the flow continues to 6041.
  • the process checks to the see if the prev_phase has not yet been recorded. If it has not, the flow continues to 6046. If it has, the flow continues to 6047. [00251] At 6046, the prev_phase is recorded as the current phase (phase). Then the flow continues to 6047.
  • Figure 69 describes the Get Side process. At 6049, the process checks to see if the phase is FALLING. If it is, the flow continues to 6050. If it is not, then the flow continues to 6052.
  • the process checks to see if the phase is RISING. If it is, the flow continues to 6051. Otherwise the flow continues to 6053.
  • the process checks to see if the prev_side has yet been recorded. If it has not, then the flow continues to 6054. Otherwise the flow continues to 6055. [00258] At 6054 the prev_side is recorded as the current side (side). The flow then continues to 6055. At 6055, the Get Side process returns.
  • Figure 70 describes an exemplary Get Peaks and Valleys process.
  • the process checks to see if the wave is currently forming the RIGHT side. If yes, the flow continues to 6059. If not, flow continues to 6057.
  • Figure 71 describes the Check to See if a Wave Has Completed process. In the first step at 6064, the process checks to see if the current phase is RISING. If it is, then the flow continues to 6066. Otherwise, the flow continues to 6065. [00263] At 6065 the wave completed flag is set to false. The flow then continues to
  • Figure 72 describes an exemplary Mark Parasympathetic Strength of Wave process.
  • the process checks to see if there are at least two valleys in the record. If not, the flow continues to 6077. If yes, the flow continues 6072.
  • the wave length is computed and recorded as wave_length. Then the flow continues to 6074.
  • the process checks to see if the wave length is less than 6 seconds. If it is, the flow continues to 6073. If it is not, the flow continues to 8000.
  • the wave size is determined to be SMALL. This indicates very little parasympathetic activity when the wave was formed.
  • the process can then visually mark the wave with an appropriate symbol indicating the parasympathetic activity. In the preferred embodiment, a one dot symbol is placed below the wave. The flow then continues to 6077. [00270] At 8000 the wave length is checked to see if it is less than 9 seconds in length.
  • the wave size is marked as MEDIUM. A medium level of parasympathetic activity likely formed the wave. The process can then visually mark the wave with an appropriate symbol indicating the parasympathetic activity. In the preferred embodiment, a two dot symbol is placed below the wave. The flow continues to 6077.
  • the wave size is marked as LARGE. A high amount of parasympathetic activity is represented by such waves. The process can then visually mark the wave with an appropriate symbol indicating the parasympathetic activity. In the preferred embodiment, a three dot symbol is placed below the wave. The flow continues to 6077. [00273] At 6077 the Mark Parasympathetic Strength of Wave process then returns.
  • Figure 73 describes an exemplary Check to See if Drop Point is Occurring process.
  • the process checks to see if the current phase is CRESTING. If it is, the flow continues to 6082. Otherwise, the flow continues to 6079.
  • the drop point flag is set to false. Then the flow continues to 6083.
  • Figure 74 describes an exemplary Mark Drop Point process. The first step at
  • the process checks to see if the wave size is SMALL. If yes, the flow continues to 6088. If not, the flow continues to 6090.
  • the device At 6088 the device generates a high pitch beep. This auditorily indicates that the drop point has been encountered, as well as auditorily indicating that the previous wave was formed by a low level of parasympathetic activity. The flow then continues to 6092. [00281] At 6090 the process checks to see if the wave size is MEDIUM. If it is, the flow continues to 6089. If it is not, the flow continues to 6091.
  • the device At 6089 the device generates a middle pitch beep. This auditorily indicates that the drop point has been encountered, as well as auditorily indicating that the previous wave was formed by a medium level of parasympathetic activity. The flow then continues to 6092.
  • the device At 6091 the device generates a low pitch beep. This auditorily indicates that the drop point has been encountered, as well as auditorily indicating that the previous wave was formed by a high level of parasympathetic activity. The flow then continues to 6092. At 6092 the Mark Drop Point process returns.
  • KL3:2513465.1 detect the completion of a wave, and determining parasympathetic intensity of the newly formed wave also may be implemented using the following pseudocode corresponding substantially to the flow processes depicted in Figs. 64-74.
  • Exemplary embodiments of the present invention also provide for the identification of peaks and valleys in real time without first identifying TD4 segments. Thus, values may be processed sequentially (e.g., one by one).
  • Figs. 75-83 describe exemplary flow processes for an exemplary procedure for determining wave phase and delineating waves on a pulse-by-pulse basis. This exemplary embodiment uses a global directional indicator and the position of the points in the range to provide, for example, a greater accuracy of phase determination and wave delineation. [00287]
  • the exemplary processes and process flows illustrated in Figs. 75 through 83, as well as any exemplary functions implementing such processes, including any auxilliary functions and/or processes called or utilized by such exemplary flow processes, are presented for illustrative purposes.
  • the process begins at 6093.
  • the first step is 6094.
  • the process sets the UP PERCENT to 30 and the DOWN PERCENT to 15. Then the flow continues to 6095 where the counters and markers are initialized. Then the flow continues to 6096 where the process waits for 15 seconds worth of pulse information to arrive. Then the flow continues to 6097, where the process waits for the next pulse beat. After the next pulse beat is receive, the flow continues to 6098 where the global directional indicators are determined by the Get Fast Information process.
  • the Determine Direction process determines the direction of the wave.
  • the flow continues to 6102 where the current points peak-to-peak (pp) value, pulse rate value (prv), timestamp (ts), direction, and point index are computed and recorded.
  • KL3:.513465.1 [00292] Then the flow continues to 6103 where the Get Point Position process determines what part of the range the current point is within.
  • a position of 100 means the point is at the very top or is above the range.
  • a position of 0 means the point is at the very bottom or below the range.
  • a value between 0 and 100 indicates the percent height of the point within the range.
  • the process checks to see if the direction had changed when the last prv was received. If the direction did not change, the flow continues to 6097 where the process waits for the next pulse. If the direction did change, the flow continues to 6106 where the change of direction is handled by the Process Direction Change process. When this process returns, the flow continues to 6097 where the process waits for the next pulse to arrive.
  • Figure 76 describes an exemplary Get Fast Information process.
  • the highest positive slope during the last 5 seconds is recorded as fast_rise.
  • the process checks to see if the fast_rise is greater than the absolute value of the fastjirop. If it is, then the flow continues to 6110. If it is not, then the flow continues to 6112.
  • Figure 77 describes an exemplary Determine Direction process.
  • the process checks to see if the current slope is greater then UP PERCENT% of the fastest change. If it is, then the flow continues to 6116. If it is not then the flow continues to 6117.
  • PEAK_PLATEAU also known as
  • the process checks to see if the current direction is DOWN. If it is, then the flow continues to 6122. If it is not then the flow continues to 6123. [00306] At 6122 the current direction is recorded as VALLEY_PLATEAU, also known as TROUGH. Then the flow continues to 6123. At 6123 the Determine Direction process returns.
  • Figure 78 describes an exemplary Determine Point Position process.
  • the process checks to see if the current point's prv is less than the lowest prv in the range. If it is, the flow continues to 6126. If it is not, then the flow continues to 6127. [00308] At 6126 the point position is recorded as 0. Then the flow continues to 6130.
  • Figure 79 describes an exemplary Process Direction Change process.
  • the process checks to see if the current direction is UP. If it is then the flow continues to 6135. If it is not then the flow continues to 6138.
  • Figure 80 describes an exemplary Process Regular Up Swing process.
  • the lowest prv since the previous direction began is recorded as the newest valley point. Then the flow continues to 6147.
  • the wavelength of the last wave is computed and recorded. Then the flow continues to 6149.
  • the stress index is computed, and the score is computed. Also, the stress index, wavelength, history, score, and other wave based metrics are displayed on the screen. Then the flow continues to 6150.
  • the previous direction is recorded as being UP. Then the flow continues to 6151. At 6151 the previous direction index is recorded as having occurred two points ago. Then the flow continues to 6152 where the Process Regular Up Swing process returns.
  • Figure 81 describes an exemplary Process Regular Up Swing process.
  • the highest prv since the last direction change began is recorded as the next peak point. Then the flow continues to 6155.
  • the previous direction indicator is set to DOWN. Then the flow continues to 6158 where the previous direction index is set to two points ago. Then the flow continues to 6159 where the Process Regular Up Swing Process returns.
  • Figure 82 describes an exemplary Process Null Up Swing process.
  • the previous direction indicator is set to UP.
  • the flow continues to 6162, where the previous direction index is set to two points ago.
  • the flow continues to 6163 where the Process Null Up Swing process returns.
  • Figure 83 describes an exemplary Process Null Down Swing process.
  • the previous direction indicator is set to DOWN. Then the flow continues to
  • Exemplary procedures for determining, for example, wave phase and delineating waves on a pulse-by-pulse basis also may be implemented using the following pseudocode corresponding substantially to the flow processes depicted in Figs. 75-83.
  • the present invention also provides processes for determining both the drop point and the completion of RSA waves in real time rather than on a pulse-by-pulse basis.
  • Figs. 84-87 describe two exemplary processes that run simultaneously. The first process, Realtime Process 1 (at 6168) is executed on a pulse by pulse basis. The second process, Realtime Process 2 (at 6171), is executed every 250 ms. The two processes work together to allow for the real time detection of the drop point and the real time detection of the termination of the current wave.
  • KL3:25134S5.1 continual reference to the exemplary nature of each stage or step in process flow, it being understood that in exemplary embodiments of the present invention functionally equivalent implementations can, for example, use different processes, as well as different sequences of processes and organizations of process flow, from that which is illustrated in Figs. 84 through 87, to achieve equivalent functionalities. All of such alternate embodiments and equivalent functional implementations are understood to be within the methods and techniques of the present invention.
  • Figure 84 describes the interrupt nature of the two exemplary processes.
  • Realtime process 1 begins at 6168.
  • the process waits for the next pulse to be received.
  • the flow continues to 6170, where the pulse is handled by the Handle Pulse Peak process.
  • the flow continues back to 6169, where the process waits for the next pulse.
  • Realtime Process 2 which begins at 6171, operates simultaneously.
  • the first step in this process at 6172 is to set the clock interrupt to 250 ms so that this process is called every 250 ms.
  • the flow continues to 6173 where the process sleeps until the clock interrupt occurs.
  • the clock interrupt occurs, the interrupt is handled by the Handle Clock Interrupt process.
  • the flow continues to 6172, where the clock interrupt is set again.
  • Figure 85 describes an exemplary Handle Pulse Peak process.
  • the direction is determined by the Get Direction process. (The Get Direction process and related processes have been described in detail above and are thus not repeated here.) After this process returns, the flow continues to 6177.
  • KL3:2513465.1 [00342] At 6178 the process checks to see if the direction is PEAK_PLATEAU. If it is then the flow continues to 6182. If it is not then the flow continues to 6179. [00343] At 6179 the process checks to see if the direction is DOWN. If it is then the flow continues to 6183. If it is not then the flow continues to 6180.
  • Figure 86 describes an exemplary Handle Clock Interrupt process.
  • the process checks to see if the valley plateau flag is true. If it is then the flow continues to 6191. If it is not then the flow continues to 6189.
  • a phantom prv value is computed called tmp_prv. Then the flow continues to 6194 where the current slope is computed based upon the two previous real prv's and the phantom prv. Then the flow continues to 6195.
  • Figure 87 describes an exemplary Handle VALLEY PLATEAU process.
  • the up flag is set to false. Then the flow continues to 6202.
  • the process checks to see if the timestamp of the last known valley is less than the timestamp of the last known peak. If it is, then the flow continues to 6209. If it is not, then the flow continues to 6210.
  • Exemplary procedures for determining, for example, both the drop point and the completion of RSA waves in real time also may be implemented using the following pseudocode corresponding substantially to the flow processes depicted in Figs. 84-87.

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Abstract

Cette invention concerne des procédés et des dispositifs faciles à utiliser et efficaces en terme de coûts, pour évaluer et traiter le stress et, partant, les troubles causés ou exacerbés par le stress. Cette invention concerne plus particulièrement des procédés et des dispositifs permettant d'identifier les ondes d'arythmie sinusale respiratoire (RSA) pendant la respiration, qui fournissent à un sujet des informations d'ondes RSA en temps réel. Ces procédés et ces dispositifs peuvent également servir à identifier les points de chute des ondes RSA. Ces procédés et ces dispositifs offrent aux sujets la capacité de préserver l'influx parasympathique et empêcher et/ou réduire ainsi les niveaux de stress.
PCT/US2006/015013 2005-04-20 2006-04-20 Procedes et dispositifs de soulagement du stress WO2006113900A2 (fr)

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MX2007013110A MX2007013110A (es) 2005-04-20 2006-04-20 Metodos y dispositivos para aliviar el estres.
JP2008507896A JP2008536648A (ja) 2005-04-20 2006-04-20 ストレスを緩和する方法および装置
KR1020077026989A KR101303354B1 (ko) 2005-04-20 2006-04-20 스트레스를 완화시키기 위한 방법 및 장치
AU2006236216A AU2006236216A1 (en) 2005-04-20 2006-04-20 Methods and devices for relieving stress
CA2604741A CA2604741C (fr) 2005-04-20 2006-04-20 Procedes et dispositifs de soulagement du stress
CN200680022173.7A CN101203175B (zh) 2005-04-20 2006-04-20 用于缓解压力的方法和设备
BRPI0610848-2A BRPI0610848A2 (pt) 2005-04-20 2006-04-20 métodos e dispositivos para alìvio de stress
EP06750906.7A EP1874186A4 (fr) 2005-04-20 2006-04-20 Procedes et dispositifs de soulagement du stress

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DE102008030956A1 (de) 2007-10-16 2009-04-23 Biosign Gmbh Gerät zur Messung der Herzratenvariabilität und dessen Verwendung
JP2010508128A (ja) * 2006-11-01 2010-03-18 ビアンカメッド リミテッド 心肺パラメータモニタ用システムおよび方法
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EP4085826A1 (fr) 2021-05-04 2022-11-09 Koa Health B.V. Détermination de la fréquence cardiaque et de la fréquence respiratoire sur smartphone en utilisant une pondération des mesures de précision
WO2023234840A1 (fr) * 2022-06-02 2023-12-07 Linkura Ab Procédé, produit logiciel et système de détermination de la qualité de la respiration

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JP2010508128A (ja) * 2006-11-01 2010-03-18 ビアンカメッド リミテッド 心肺パラメータモニタ用システムおよび方法
JP2015027550A (ja) * 2006-11-01 2015-02-12 レスメッド センサー テクノロジーズ リミテッド 心肺パラメータモニタ用装置、心肺パラメータモニタ用システムおよび非一時的な記録媒体
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JP2008279126A (ja) * 2007-05-11 2008-11-20 Terumo Corp 拍動ゆらぎ測定装置およびその情報処理方法
DE102008030956A1 (de) 2007-10-16 2009-04-23 Biosign Gmbh Gerät zur Messung der Herzratenvariabilität und dessen Verwendung
DE102008030956B4 (de) * 2007-10-16 2010-01-07 Biosign Gmbh Gerät zur Messung der Herzratenvariabilität
DE102008061997A1 (de) 2008-12-12 2010-06-17 Karlsruher Institut für Technologie System und Verfahren zum Stresstraining eines Benutzers
US10632279B2 (en) 2016-08-30 2020-04-28 Dentsu Inc. Meditation support device and meditation support system
EP4085826A1 (fr) 2021-05-04 2022-11-09 Koa Health B.V. Détermination de la fréquence cardiaque et de la fréquence respiratoire sur smartphone en utilisant une pondération des mesures de précision
WO2023234840A1 (fr) * 2022-06-02 2023-12-07 Linkura Ab Procédé, produit logiciel et système de détermination de la qualité de la respiration

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CA2604741C (fr) 2014-11-25
CA2604741A1 (fr) 2006-10-26
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MX2007013110A (es) 2008-02-19
BRPI0610848A2 (pt) 2010-08-03
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EP1874186A4 (fr) 2013-08-21
KR20080011294A (ko) 2008-02-01

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