WO2006134197A1 - Procede permettant de traiter des signaux photoplethysmographiques obtenus a partir d'une personne ou d'un animal et oxymetre utilisant ledit procede - Google Patents

Procede permettant de traiter des signaux photoplethysmographiques obtenus a partir d'une personne ou d'un animal et oxymetre utilisant ledit procede Download PDF

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Publication number
WO2006134197A1
WO2006134197A1 PCT/ES2006/070080 ES2006070080W WO2006134197A1 WO 2006134197 A1 WO2006134197 A1 WO 2006134197A1 ES 2006070080 W ES2006070080 W ES 2006070080W WO 2006134197 A1 WO2006134197 A1 WO 2006134197A1
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WIPO (PCT)
Prior art keywords
peak
parameter
candidate
signals
peaks
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PCT/ES2006/070080
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English (en)
Spanish (es)
Inventor
Juan Pedro SILVEIRA MARTÍN
Maria Luisa Dotor Castilla
María Dolores GOLMAYO FERNÁNDEZ
Amaia Bilbao Monasterio
Romano Giannetti
Sonnia María LÓPEZ SILVA
Pilar MARTÍN ESCUDERO
Francisco Miguel Tobal
Original Assignee
Consejo Superior De Investigaciones Científicas
Universidad Pontificia Comillas De Madrid
Universidad De Las Palmas De Gran Canaria
Universidad Complutense De Madrid
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Application filed by Consejo Superior De Investigaciones Científicas, Universidad Pontificia Comillas De Madrid, Universidad De Las Palmas De Gran Canaria, Universidad Complutense De Madrid filed Critical Consejo Superior De Investigaciones Científicas
Publication of WO2006134197A1 publication Critical patent/WO2006134197A1/fr

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    • 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
    • A61B5/14551—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 for measuring blood gases
    • 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
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06F—ELECTRIC DIGITAL DATA PROCESSING
    • G06F17/00—Digital computing or data processing equipment or methods, specially adapted for specific functions

Definitions

  • the present invention generally concerns, in a first aspect, a method for obtaining physiological parameters in real time from photoplethysmographic signals (PPG) measured by optical sensors, and in particular a method for obtaining the heart rate value at from these photoplethysmographic signals, even in extreme situations such as during the continuous realization of movements during the practice of exercises.
  • PPG photoplethysmographic signals
  • the invention also concerns, in a second aspect, an oximeter suitable for processing photoplethysmographic signals according to the proposed method.
  • Pulse oximetry is based on the measurement of the light radiation at two determined wavelengths after interacting with the arterial blood, the venous blood and the rest of the tissues existing in the measurement zone. Radiation is generally used in the near red and infrared zone and in configuration by reflection or transmission. The variation of the volume of blood in the arteries by pumping the heart allows to obtain a variable light signal related to the heart rhythm and hemoglobin.
  • the pulse oximeters existing according to own experience and the data obtained in the literature offer a false heart rate value during the practice of exercise.
  • Application US-A-20040171948 concerns a method for processing photoplethysmographic signals in different domains: temporal, spectral and cepstral, and based on the results of the analysis of the signals in one or more of said domains, estimate one or more conditions physiological aspects of a patient, as well as movement artifacts in the temporal domain included in the photoplethysmographic signal.
  • the application US-A-20030163032 concerns a method to eliminate motion artifacts of electrical signals representative of attenuated light signals, such as those corresponding to photoplethysmographic signals, by transforming said signals into a spectral domain, the identification of some candidate peaks between the spectral data of said signals, their corresponding filtering, and their analysis based on a series of parameters to finally find out the peak corresponding to the heart rate of the patient whose photoplethysmographic signals are subject to analysis.
  • the present invention concerns, in a first aspect, a method for processing photoplethysmographic signals obtained by a pulse oximeter sensor, by means of the application of which it is possible to reliably obtain the heart rate even when the individual performs exercises.
  • the present invention concerns an oximeter adapted to process photoplethysmographic signals according to the method proposed by the first aspect of the present invention.
  • the proposed method according to the first aspect of the present invention has its application in the processing of photoplethysmographic signals obtained from a person or animal, in order to find out at least the heart rate thereof.
  • the proposed method comprises emitting, on an area irrigated by blood capillaries, such as a finger or other organ of said person or animal, two or more light signals to obtain said photoplethysmographic signals in response, by means of detection with at least one photodetector of said light signals, once they have crossed said area.
  • Said emitted light signals preferably come from LEDs or lasers of different wavelengths, between 630 and 980 nm, at least one of them being infrared.
  • the method is particularly applicable to the processing of photoplethysmographic signals that contain harmonics of different frequencies, some of which have been produced by artefacts representative of the movement of said person or animal, either by movement of arms, legs and / or legs of said person or animal, caused by walking or running, which generate harmonics at frequencies other than cardiac, which varies according to the intensity of the march or race.
  • Said movement caused by walking or running is generated, for example, when performing a sports activity that requires measuring heart rates in conditions of continuous and extreme effort, very different from those measured at rest.
  • the proposed method comprises performing, according to known technique, the following stages sequentially: a) receive photoplethysmographic electrical signals in a temporal domain, b) transform said temporal signals into signals with a frequency domain, or spectral signals, c) identify a series of candidate peaks to be the peak produced at said domain heart rate, between part or all of said spectral signals, d) obtain a series of parameters from said candidate peaks, and e) determine from at least one of said parameters obtained in d) what is the representative peak of said frequency cardiac, or peak sought.
  • the method proposed by the first aspect of the present invention comprises performing said step d) to obtain at least a first and a second parameter by means of calculations carried out in parallel, being:
  • said first parameter resulting from a harmonic probability function of said candidate peaks, consisting of a two-to-two comparison thereof, which results in a series of values for the first parameter
  • said second parameter resulting from a preponderance function, in energy, of said candidate peaks, consisting of a two-to-two comparison thereof, which results in a series of values for the second parameter.
  • the proposed method finally comprises assigning, at said stage e), to said peak determined as representative of said heart rate a confidence coefficient.
  • the method further comprises performing said step d) for a third parameter to be obtained based on calculations performed in parallel with those made to obtain said first and second parameters, said third parameter being resulting from an analysis function history of these candidate peaks, consisting of a comparison of at least the peak determined as representative of the heart rate in said stage e), for a previous cycle, which has a high confidence coefficient assigned, with said candidate peaks, to look for the peak of the same frequency or of the frequency closest to that of said peak determined in said previous stage e), and assign a probability coefficient that is the peak sought as a result of devaluing said high confidence coefficient in a certain percentage that is inversely proportional to the proximity of both frequencies.
  • the method according to a preferred implementation comprises carrying it out by dividing it into two sub-stages:
  • pre-selection stage consisting of analyzing the values obtained for at least said first and second parameters, and preferably also said third parameter, and selecting a single candidate peak for each parameter, depending on of said analysis, and
  • said sub-stage e.1) comprises:
  • the proposed method comprises carrying out the following actions:
  • the method comprises calculating the level of oxygen saturation based on one or more of said photoplethysmographic signals whose frequency is that of said wanted peak determined in stage e).
  • an oximeter of the type comprising at least:
  • the oximeter proposed according to the second aspect of the present invention is characterized in that said electronic system incorporating it is adapted to process said photoplethysmographic signals to implement the method proposed by the first aspect of the present invention, that is to say it incorporates specific means intended to perform the calculations and / or treatments of the acquired signals, parameter management, etc.
  • Fig. 1 is an illustrative flow chart of the main stages of the proposed method according to the first aspect of the present invention for an exemplary embodiment
  • Fig. 2 is a graph showing part of the spectral content of a photoplethysmographic signal contaminated with noise signals or motion artifacts, for an exemplary embodiment
  • Fig. 3 is a graph relative to a harmonic probability function l (x), whose result is the first parameter mentioned, for an embodiment example,
  • Fig. 4 is a graph relative to a preponderance function p (x), the result of which is said second parameter, for an exemplary embodiment
  • Fig. 5 is a flow chart of the stages of the proposed method, plus detailed than that of Fig. 1, for an exemplary embodiment. Detailed description of some embodiments
  • the method to obtain the heart rate during the performance of exercises is based on obtaining the frequency of the variable part of the photoplethysmographic signal (PPG).
  • PPG photoplethysmographic signal
  • FFT fast Fourier transform
  • the performance of individual movements, such as during the race involves the appearance of periodic signals (artifacts), which in the range of accessible heart rates can be frequencies similar to the frequency of strokes or steps. This makes a measure of the frequency of the PPG signal provide random values of frequencies related to the superposition of the signals due to the heart rate and the movements performed.
  • the method comprises generating a spectrum of amplitude of the signal over a range of data measured during the last seconds (time window) and recalculating it frequently, obtaining a diagram known as spectrogram of the measured signal.
  • each of the generated spectra is examined to extract the information from the spectral lines present, eliminating noise.
  • a novel algorithm associates each line with its fundamental; The set of lines is compared with the pattern provided for the useful signal (low harmonic content) so that it can be distinguished from the others.
  • the amplitude information of the pulsatile signal is obtained directly from the value of the selected spectral lines.
  • this block executes a fast Fourier transform, providing at its output a signal constituted by the spectral power density spectrum of the signal in a time window T 0 ;
  • This type of signal is usually called a "spectrogram.” From this spectrogram, only the M points corresponding to interesting frequencies for the type of application will be considered, including between 30 and 330 beats per minute (ppm), which are represented by Fig. 2.
  • This block corresponds to stage b ) mentioned above.
  • Peak detection deals with the identification of the spectral "lines" present in the signal provided by the previous block. Due to both the intrinsic presence of electronic noise and electromagnetic interference, as well as the artifacts introduced by the numerical elaboration of the spectrogram itself, it is necessary to identify the so-called here "significant peaks” to separate them from noise.
  • This block corresponds to the stage c) mentioned above and, as indicated, is applied to part of the spectral signals, specifically to those represented by said M points.
  • the search is "refined", locating for each section, which has been chosen in the previous step, the real maximum in the complete diagram. 4.
  • the peaks with value that is to say energy, are discarded below VMAX I KS, where K s is the expected level of noise in the measurement (typically around 2OdB).
  • Step 2 manages to reject, as separate peaks, mathematical artifacts that generate two apparent peaks very close in the spectrogram; This is due, for example, to the interaction between the FFT algorithm and the filtering window (square, Hamming, Hanning, etc.) used before said algorithm.
  • Step 3 recovers (in part) the resolution in frequency, and step 4 eliminates very low local peaks generated by noise.
  • Harmonics in this block the search of lines that probably belong to the same signal is carried out. The algorithm is based on comparing the spectral lines between them, two by two, calculating the quotient where the first frequency is the highest of the pair of peaks under examination. This fraction is used as input in a harmonic probability function l (x), whose shape is stylized in the graph of Figure 3. The output of this function has been called in the previous section, as the first parameter.
  • the output of said function indicates the probability for the frequency f A of being a harmonic of the frequency f B.
  • This method repeated for each frequency, allows identifying which of the lines identified are the most likely to be fundamental, the harmonic content of them (sum of the values of the frequencies that are likely harmonic), and a reliability index of said evaluation (product of the l (x) of said harmonics).
  • this block also analyzes peaks two to two, providing a coefficient that expresses how much each peak is more significant, in energy, than the other.
  • This coefficient is called the preponderance of the major peak over the minor peak, and is calculated with a preponderance function that has the appearance shown in Figure 4. The output of this function has been called in the previous section, as the second parameter.
  • this block analyzes the history of the value of the chosen peak, in previous moments, as a "valid" peak of the photoplethysmographic signal. If in the previous step a peak had been selected by the final block with a confidence coefficient (see following description) equal to one or very close, and in the new spectrogram a peak was found very close to it, this peak is presented to the next block as a candidate with high probability to be the new "good” peak.
  • the probability assigned is the confidence value devalued by a D coefficient (between 10 and 50%). The output of this function has been called in the previous section, as the third parameter.
  • this block makes the decision of which is the peak that represents the fundamental harmonic of the photoplethysmographic signal based on the information provided by the previous blocks. He is responsible for carrying out the aforementioned stage e).
  • the candidate is determined by harmonics: with all the frequencies that the "Harmonics" block has determined as fundamental, an ordered list is prepared with the decreasing harmonic content. An increasing probability (the higher the lower the harmonic content) is then assigned to said frequencies if the chosen frequency is. The probability is weighted with the amplitude of the fundamental, removing "merits" to very weak signals. The peak with the highest probability is the candidate peak for harmonics.
  • a candidate is determined by preponderance: it is the highest peak, with its probability, provided by the "Energy" block.
  • the candidate is chosen as a "good” peak, with a confidence coefficient given by the product of the three associated probabilities.
  • the peak with the highest probability is chosen. From these data, the heart rate (the horizontal coordinate of the fundamental peak chosen) is calculated, and the amplitude data of the photoplethysmographic signal necessary to calculate the oxygen saturation.
  • Fig. 5 a flow chart of the steps of the proposed method is shown, in detail, for another embodiment, which is explained below.
  • the exemplary embodiment illustrated in said Fig. 5 is based on a system that acquires analog phototransmittance data with high sampling rate (from 2 to 4 lasers) to allow a simple analog anti-aliasing.
  • Said acquisition Ia performs the block indicated as 2 in Fig. 5, and in particular said sampling rate is 1 kHz.
  • the sampled data has been previously filtered in block 1.
  • another filtering is performed, in this case an analog filtering of 4 or Bessel order (to maintain the information in the form of the pulses a filter with linear phase is used) and a decimation of the data up to 100 Sa / s per channel.
  • an analog filtering of 4 or Bessel order to maintain the information in the form of the pulses a filter with linear phase is used
  • decimation of the data up to 100 Sa / s per channel.
  • the determination of the data of interest which are the heart rate (indicated in Fig. 5 as PPM) and the pulsatile and continuous components of the signal of each laser.
  • a confidence factor C is calculated with each strategy, which estimates the significance of the value obtained.
  • An FFT is performed on a window of the last 10 seconds of filtered and decimated data (block 4).
  • An identification of an NP number of main peaks (from 3 to 7 peaks) is made (block 8)
  • An estimation of the pulsatile amplitude in the time domain is made, using the noise estimate as a confidence factor (block 6).
  • An estimate of the average value of the signal is made, by means of a low-pass filter at 0.1 Hz and a delay to synchronize the filters (no trust value is needed), by block 7.
  • the new PPM value for the current measurement is selected, using an empirical algorithm that chooses the measurement with better confidence as long as you have no confidence less than the previous measurement , in which case the other is maintained.
  • the latter also responsible for calculating the oxygen saturation based on the comparison of all the pulsatile values of the lasers with which it has been emitted to obtain the photoplethysmographic signals, using average method and of maximum confidence to choose the correct value.
  • a series of instructions of a computer program are included, in the C language of LabWindows / CVr, which is developed in Appendices A and B, and that implements the proposed method according to the first aspect of this invention.
  • the group of instructions included in the two appendices A and B constitute the core for calculating the heart rate of the oximeter implemented by the inventors, and proposed by the second aspect of the invention.
  • the program receives the data in time in a channel through the function add_fft_points () (called by the main program of the instrument) and accumulates them in a cyclic buffer; As soon as it obtains the necessary points (FFT_POINTS, defined in the cardfft.h file) it emits a signal to the main program that calls the routing compute_fft_hb () that performs the calculation described above.
  • APPENDIX B CARDIAC FREQUENCY CALCULATION PROGRAM - CARDFFT.C tinclude ⁇ analysis.h> tinclude ⁇ ansi_c.h> tinclude "cardfft.h"
  • double heu_good_max (double vmax, double vnextmax) ⁇ // sqrt () is for the power spectra return only_pos (1-sqrt (heu_goodmax_factor * vmax / vnextmax)); ⁇ void initialize_fft (double samplerate, double p_bpm_min, double p_bpm_max) ⁇ int i;
  • timestep l / samplerate; / * from * measure.h
  • FFT_DUE_AFTER FFT_POINTS - FFT_OVERLAP
  • Chl_data [i] is the first unused data now ...
  • points_read + NumPoints - FFT_DUE_AFTER; return FFT_READY; ⁇
  • first_n_power_spectrum (double ** x_out, double ** y_out, int * n_min, int * n_max) ⁇ // NOTE: it destroys time_chl! ! !
  • double smooth [FFT_POINTS]; // too big, but uf ... int ngroups, i_realmax; double s, realmax; double smoothed_maxs_v [4]; // one more than the interesting int smoothed_maxs_i [4]; int s_max_found 0; double real_maxs_v [3]; int real_maxs_i [3];
  • ngroups (int) ((i_bpm_max-i_bpm_min) / heu_groups) -1;
  • heu_max_win_threshold p_heu_max_win_threshold
  • heu_cutoff p_heu_cutoff
  • heu_d.00ness_factor p_heu_d.00ness_factor

Abstract

L'invention concerne un procédé permettant de traiter des signaux photopléthysmographiques obtenus à partir d'une personne ou d'un animal. Ce procédé consiste : a) à recevoir des signaux électriques photopléthysmographiques dans le domaine temporel ;b) à transformer ces signaux temporels en signaux spectraux ; c) à identifier une série de crêtes candidates pour être produites à la fréquence cardiaque ; d) à obtenir une série de paramètres à partir des crêtes candidates et e) à déterminer, à partir de ces paramètres, quel est la crête représentative de la fréquence cardiaque. L'étape d) sert à obtenir un premier, un second et un troisième paramètres au moyen de calculs exécutés en parallèle. Le premier paramètre est issu d'une fonction de probabilité d'harmoniques des crêtes candidates, le second paramètre est issu d'une fonction de prépondérance en énergie de ces crêtes candidates et le troisième paramètre est issu d'une fonction d'analyse historique de ces crêtes candidates.
PCT/ES2006/070080 2005-06-13 2006-06-12 Procede permettant de traiter des signaux photoplethysmographiques obtenus a partir d'une personne ou d'un animal et oxymetre utilisant ledit procede WO2006134197A1 (fr)

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ES200501425A ES2276594B1 (es) 2005-06-13 2005-06-13 Metodo para procesar señales fotopletismograficas obtenidas de una persona o animal, y oximetro que utiliza dicho metodo.
ESP20001425 2005-06-13

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US10986816B2 (en) 2014-03-26 2021-04-27 Scr Engineers Ltd. Livestock location system
US10986817B2 (en) 2014-09-05 2021-04-27 Intervet Inc. Method and system for tracking health in animal populations
US11071279B2 (en) 2014-09-05 2021-07-27 Intervet Inc. Method and system for tracking health in animal populations
USD990063S1 (en) 2020-06-18 2023-06-20 S.C.R. (Engineers) Limited Animal ear tag
USD990062S1 (en) 2020-06-18 2023-06-20 S.C.R. (Engineers) Limited Animal ear tag
US11832587B2 (en) 2020-06-18 2023-12-05 S.C.R. (Engineers) Limited Animal tag
US11832584B2 (en) 2018-04-22 2023-12-05 Vence, Corp. Livestock management system and method
US11864529B2 (en) 2018-10-10 2024-01-09 S.C.R. (Engineers) Limited Livestock dry off method and device
US11960957B2 (en) 2020-11-25 2024-04-16 Identigen Limited System and method for tracing members of an animal population

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Publication number Priority date Publication date Assignee Title
US10986816B2 (en) 2014-03-26 2021-04-27 Scr Engineers Ltd. Livestock location system
US11963515B2 (en) 2014-03-26 2024-04-23 S.C.R. (Engineers) Limited Livestock location system
US10986817B2 (en) 2014-09-05 2021-04-27 Intervet Inc. Method and system for tracking health in animal populations
US11071279B2 (en) 2014-09-05 2021-07-27 Intervet Inc. Method and system for tracking health in animal populations
US11832584B2 (en) 2018-04-22 2023-12-05 Vence, Corp. Livestock management system and method
US11864529B2 (en) 2018-10-10 2024-01-09 S.C.R. (Engineers) Limited Livestock dry off method and device
USD990063S1 (en) 2020-06-18 2023-06-20 S.C.R. (Engineers) Limited Animal ear tag
USD990062S1 (en) 2020-06-18 2023-06-20 S.C.R. (Engineers) Limited Animal ear tag
US11832587B2 (en) 2020-06-18 2023-12-05 S.C.R. (Engineers) Limited Animal tag
US11960957B2 (en) 2020-11-25 2024-04-16 Identigen Limited System and method for tracing members of an animal population

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