WO2000002486A1 - Stethoscope analytique - Google Patents

Stethoscope analytique Download PDF

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Publication number
WO2000002486A1
WO2000002486A1 PCT/US1999/012369 US9912369W WO0002486A1 WO 2000002486 A1 WO2000002486 A1 WO 2000002486A1 US 9912369 W US9912369 W US 9912369W WO 0002486 A1 WO0002486 A1 WO 0002486A1
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WO
WIPO (PCT)
Prior art keywords
electronic stethoscope
heart
variables
display
intensities
Prior art date
Application number
PCT/US1999/012369
Other languages
English (en)
Inventor
Ali R. Kolaini
James E. Hendrix
Original Assignee
Cirrus Systems, Llc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Cirrus Systems, Llc filed Critical Cirrus Systems, Llc
Priority to AU49532/99A priority Critical patent/AU4953299A/en
Publication of WO2000002486A1 publication Critical patent/WO2000002486A1/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B7/00—Instruments for auscultation
    • A61B7/02—Stethoscopes
    • A61B7/04—Electric stethoscopes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0002—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B7/00—Instruments for auscultation
    • A61B7/003—Detecting lung or respiration noise

Definitions

  • the present invention relates to an electronic stethoscope capable of analyzing heart and respiratory sounds in real-time and displaying the results in an improved format .
  • the invention also relates to a method of processing electronic signals relating to heart and respiratory sounds in real-time, analyzing the electronic signals, and displaying results of the analysis.
  • the stethoscope disclosed in the Bennett patent includes a pair of microphones connected to circuitry which performs a digital Fourier conversion of the sounds picked up by the microphones and displays the results on a video monitor as a three-dimensional graph of sound pressure plotted as a function of frequency and time.
  • features of the overall heart sound such as the "first" through “fourth” heart sounds and their components can easily be detected as peaks on the graph whose frequencies and location along the time axis identifies the sounds, and whose amplitudes indicate intensity.
  • a graph of this type offers a more precise analysis of certain types of heart conditions than can be provided by simply listening to heart sounds through a conventional acoustic or electronic stethoscope with no graphical display capabilities.
  • Such a display could be used by medical technicians, paramedics, or nurses who lack the training or time to analyze a three-dimensional frequency spectrum graph of heart sounds, or emergency room doctors or residents who often must make instantaneous diagnoses under extremely difficult conditions.
  • Such a display could also be utilized by lay persons such as patients with known heart conditions, family members of patients, and nursing home staff, in order to provide at least limited diagnoses and assist in determining whether hospitalization or emergency resuscitation procedures are necessary.
  • the only available heart monitoring devices that can be used by lay persons are simple devices that display pulse rate and/or blood pressure, and which are incapable of performing any sort of analysis of heart sounds.
  • an electronic stethoscope for use by medical professionals that provides both verbal descriptions of heart sounds and a graphical display of signal components showing amplitudes and timings.
  • the electronic stethoscope of this embodiment of the invention provides a more sensitive and reliable detection of subtle, but critical features in the heart sounds than is possible by mere human auscultation, but with a display that is more easily and quickly interpreted than is possible with prior such devices, including verbal characterization of the significant heart sounds detected by the device, which characterizations are important to medical professionals because they have been reported in the literature, but which cannot be determined accurately by auscultation alone .
  • the graphical display of signal components is eliminated and detailed characterizations of the data are eliminated in favor of summary messages that can be understood by the user, with the option of providing supporting details for communication to medical personnel over, for example, a telephone or via a modem.
  • the message display unit preferably includes a signal processor and at least a message display table located in random access memory during processing.
  • data is associated with text strings stored in the table for display as appropriate.
  • Successive frames of sampled signals are transformed into the frequency domain and pertinent features are stored in data structures for long- term analysis. Decisions based on stored long-term data are mapped to text strings in the table and presented on the display.
  • Fig. 1 is a schematic illustration of an analytic stethoscope constructed in accordance with the principles of the invention.
  • Fig. 2 is a functional block diagram of the principle circuit elements used in the analytic stethoscope illustrated in Fig. 1.
  • Fig. 3 is a representation of a display for the analytic stethoscope of Fig. 1, arranged according to the principles of a first preferred embodiment of the invention.
  • Fig. 4 is a flowchart of a control program for the analytic stethoscope of the first preferred embodiment of the invention.
  • Fig. 5 is a flowchart of an interrupt service routine for the control program illustrated in Fig. 4.
  • Fig. 6 is a flowchart of an adjustments routine for the control program illustrated in Fig. 4.
  • Fig. 7 illustrates a frame buffer suitable for use in connection with the control program of Fig. 4.
  • Fig. 8 illustrates a graphic display table suitable for use in connection with the control program of Fig. 4.
  • Fig. 9 illustrates a message display table suitable for use in connection with the control program of Fig. 4.
  • Fig. 1 illustrates the principal hardware components of an analytic stethoscope constructed in accordance with the principles of the invention, including a sensor 1, handheld processor/display device 2 , and headset 3.
  • sensor 1 can be made up of one or more integral or separately positionable sensors capable of picking-up heart or respiratory sounds and converting the acoustic vibrations into electrical signals, including commercially available microphones and other piezoelectric sensors, or combinations of different types of sensors.
  • Headset 3 may also be a headset of known type, including commercially available headsets, with or without some form of active or passive noise reduction or signal processing capabilities, for converting electrical signals from the sensor into acoustic signals corresponding to those that would be produced by a conventional nonelectronic stethoscope, so that the user can correlate the display with actual heart sounds. It will be appreciated that the headset is not essential to operation of the invention, and that the headset may be omitted, particularly in the case of embodiments intended to be used by the general public or non-medical personnel.
  • the processor/display device 2 includes a display panel 4 capable of displaying text and images, such as a graphical liquid crystal diode display screen, and a keypad 5 to allow the user to enter data and display control commands.
  • the keypad 5 may include power and backlight on/off key 6, left, right, up, and down cursor control keys 7-10 to facilitate data entry, an enter or "o.k.” key 11, a "NEXT" or scroll key 12, and volume up and down keys 12 and 13 for the audio output to the headset 3.
  • the processor/display device may also include a removable storage option, such as a disk or solid state memory module (not shown) , and/or a printer or printer port (also not shown) . As illustrated in Fig.
  • the processor/display device includes, in addition to display panel 4 and keypad 5, at least one sensor input 14, appropriate amplifier and filter circuitry 15,16, which may be separate or combined, an analog-to-digital converter 17, digital signal processor 18, digital-to-analog converter 19, output low pass filter 20, output filter and/or amplifier circuitry 21, read only memory 22, which may be programmable, random access memory 23, and headset output 24.
  • each of the elements illustrated in Fig. 2 are known and commercially available, including digital signal processors that can be programmed by those skilled in the art to carry out the functions described below, and integrated circuits that combine the digital signal processor with amplification, filtering, data conversion, and/or memory elements. Suitable digital signal processors are described, for example, in the U.S. patents cited above, each of which is incorporated herein by reference.
  • the digital signal processor accepts keypad inputs, controls system functions, performs the analysis functions, controls display 4, and outputs an audible signal to the headset 3.
  • the analog signal from the sensor is first amplified by pre-amplifier 15 and then, as is well-known, low pass filtered by filter 16 to prevent aliasing when the signal is digitized by analog-to-digital converter 17, i.e., sampled at regular intervals and converted into digital values that are passed on to the digital signal processor 18 through its serial port.
  • the instructions that constitute the digital signal processors program permanently reside in read only memory 22, which retains its contents even when the unit is turned off.
  • the digital signal processor retrieves its initial instructions from read only memory 22, with the random access memory being used for temporary storage of the instructions retrieved from the read only memory, and also for storage of data when carrying out processing and display operations.
  • Results of the processing are displayed on the display panel 4, and a copy of the original digitized signal input from the sensor is converted back to an analog signal by the digital-to-analog converter 19, low pass filtered by filter 20 to smooth out the digital steps, and amplified and impedance matched by amplifier 21 to provide a signal that can be output to headset 3.
  • the headset volume By driving the headset using the initially digitalized signal, rather than a signal obtained directly from the sensor, it is possible to control the headset volume through the keypad 5 instead of using a potentiometer, to signal the user with tones to verify key strokes or to prompt the user, and, optionally, to issue verbal information and instructions to the user using speech synthesis techniques.
  • the digital signal processor may vary the frequency response of the headset signal to optimize auscultation of various specific conditions .
  • a circuit of the type illustrated can be powered by a conventional voltage regulated battery power source or AC inverter circuit.
  • An input frame of 256 samples may be used for either fast Fourier transform (FFT) or wavelet analysis inputs.
  • FFT fast Fourier transform
  • Each input frame represents 32 ms of elapsed time, which corresponds to a frequency of 31.25 Hz, which is the lowest frequency for which a full cycle can be seen in the frame, and therefore roughly the lowest detection frequency.
  • the input frames preferably should overlap by 248 samples or 96.875%, yielding a time resolution of 1 ms per frame, but even conventional digital signal processors that can easily handle a resolution of 2 or 3 ms will still provide useful information.
  • Either a Fourier transform or a wavelet transform can be used to describe signal features in the frequency domain, but in the embodiments described below, an FFT algorithm is used, in which case the above parameters imply that the highest frequency detected will be 4 kHz and the frequency resolution will be 15.6 Hz. If the analysis algorithm tracks the most recent 30 frames in a continuous, cyclical buffer structure, it will be able to resolve features spanning one entire heart cycle at a minimum heart rate of 33.3 beats per minute, which is sufficiently low to ensure that any real heart beat interval can be fully analyzed.
  • an input buffer of 256 positions is sufficient for holding the input data for the transform into frequency space, the input buffer preferably being arranged as a circular buffer with 32 imaginary boundaries, one every eight samples, corresponding to intervals of 1 ms each.
  • the main control loop polls the input pointer, which is updated by the interrupt service routine, to determine when it hits one of the boundaries.
  • a new frame is ready for analysis.
  • the new frame is transformed into the frequency domain, and essential parameters are determined and sorted for analysis, after which the recent set of frame parameters is examined to determine the time trends in the data, features unique to each possible finding are identified, and messages are tagged for display. Finally, adjustments to the graphical and message displays are effected, and the control program then returns to the point where the input pointer is polled for the next frame and the process repeats.
  • Fig. 3 illustrates the display of a professional level electronic stethoscope arranged according to the principles of a first preferred embodiment of the invention.
  • the display 4 of Fig. 1 includes a graphical display section 25 and a verbal message section 26.
  • the word "continued" at the bottom of the screen indicates that additional messages follow, but will not fit on the screen.
  • the continuation messages will replace the previous ones. After the last message, the display cycles back to the first messages again.
  • the graphical display section 25 shows the principal heart sound components as vertical bars 27 representing both intensity and timing relationships.
  • Intensity which is used here and below in the sense found in medical literature, i . e . , as referring generally to loudness, rather than in the strictly technical sense of power per unit area, is represented by the height of the bars, and timing is represented by their spacing.
  • Murmur sounds are represented in a similar manner by vertical dashed lines 28 in the areas where they are detected.
  • the intensity profile of the murmur lines reveals the murmur intensity versus time, i.e., the murmur envelope.
  • the vertical axis has tick marks at five points representing the mid-points of five intensity categories: very soft, soft, moderate, loud, and booming.
  • the display is updated on a real-time basis so that the diagnostician can view changes as he or she hears them with the headset.
  • heart sounds which will also be described below are heart sounds that are well-known to those with appropriate medical training, and that the invention lies not in the discovery of any new types of heart sounds or any relationships between features present in the graphical display and particular heart conditions, but rather in the manner in which useful parameters of the heart sounds are displayed.
  • the terminology used to describe the heart sounds, such as the terms “first,” “second,” “third,” and “fourth” heart sounds are standard terms of art with specific meanings in the context of the invention which are well-known to those skilled in the art of auscultation.
  • the first heart sound (SI) has four sequential components, including small usually inaudible low frequency vibrations, audible low frequency vibrations, large high frequency mitral closure sounds (Ml) , and large high frequency tricuspid closure sounds (TI) , with the high frequency tricuspid closure sounds (TI) usually following the high frequency mitral closure sounds (Ml) by 20 or 30 milliseconds.
  • the intensity variation is noted as the difference between the maximum and minimum measured intensities expressed as a percentage of the minimum measured intensity (example: varies 25% over minimum) .
  • the display indicates whether after-vibrations exist (example: "1st heart sound (SI) after-vibrations exist”) , and whether the first heart sound is widely split (example: "1st heart sound (SI) is widely split by 50 ms”) .
  • the second heart sound (S2) has two components, the aortic valve closing sound (A2 ) and the pulmonary valve closing sound (P2) .
  • the verbal message display provides messages indicating the intensity of the second heart sound if its aortic and pulmonary components cannot be separated, or messages indicating the intensity of the individual aortic and pulmonary components if the components can be separated, according to one of the five sound intensity categories, whether the components of S2 are widely split (defined as a separation of more than 30 ms) , the corresponding time difference of the split, if applicable, whether the components are reversed split with any detectible amount of separation, and the corresponding time difference of the reverse split, if applicable.
  • the verbal message display indicates whether the second heart sound (S2) is narrowly split, defined as the occurrence of a loud high frequency heart sound (P2) and a detectable separation between the aortic and pulmonary sounds of between 10 and 30 ms, the magnitude of the narrow split, and whether the second heart sound (S2) is a single heart sound characterized by a 10 ms or less separation, as well as the intensities, according to the five intensity categories .
  • the verbal message display may also include a number of messages concerning murmurs, which are abnormal relatively prolonged sounds resulting from obstructions or regurgitation at the valves that have varying intensity, frequency, quality, configuration, and duration.
  • Murmur intensities are categorized as either level 1 murmurs, which require a special effort to hear, level 2 murmurs, which are faint, but easily heard, level 3 murmurs, which are moderately loud, and level 4 murmurs, which are very loud, level 5 murmurs, which are extremely loud and can be heard if the stethoscope is just touching skin, and level 6 murmurs, which are exceptionally loud and can be heard with the stethoscope just above the skin.
  • Timing of the murmurs is categorized as early, mid, or late systolic murmurs, and as early, mid, or late diastolic murmurs, with further categories for systolic murmurs that overlap the second heart sound (S2) , diastolic murmurs that overlap the first heart sound (SI) , and continuous murmurs, which usually peak around the second heart sound.
  • S2 second heart sound
  • SI first heart sound
  • continuous murmurs which usually peak around the second heart sound.
  • the verbal message display may indicate whether the murmur is an ejection murmur, which begins after the first heart sound (SI) or a regurgitation murmur, whether the intensity of the murmur changes from beat-to-beat, the category of the intensity variation envelope, e . g. , rounded, diamond, kite (early or late) , crescendo, etc. , whether the murmur is an innocent murmur, defined as a murmur that is totally systolic and less than grade 3, or a significant murmur, defined as a murmur with at least a grade 3 intensity or diastolic timing, or a "bruit," which is a supraclavicular arterial murmur.
  • SI first heart sound
  • a regurgitation murmur the category of the intensity variation envelope
  • the murmur is an innocent murmur, defined as a murmur that is totally systolic and less than grade 3
  • a significant murmur defined as a murmur with at least a grade 3 intensity or diastolic timing,
  • the verbal message display of the invention may display the intensity, according to the scale described above, of ejection sounds or clicks, and whether the ejection sounds are aortic valvular or pulmonary valvular ejection sounds, and the intensity of pericardial knocks.
  • the verbal message display also may indicate the intensity of the third heart sound (S3) , whether the third heart sound is intermittent, and the intensity of the left and right ventricular components of the third heart sound, as well as the timing and intensity of the fourth heart sound (S4) , its timing in relation to the first heart sound (SI), i.e., whether the fourth heart sound (S4) is, relative to the first heart sound (SI) , overlapping, an isolated diastolic event, or has random timing, and whether the fourth heart sound (S4) is loudest during expiration (left fourth heart sound) or inspiration (right fourth heart sound) .
  • SI first heart sound
  • the verbal message display may indicate whether the third and fourth heart sounds are fused, which is also known as a summation gallop, the intensity of any pericardial friction rub, and whether the pericardial friction rub occurs during atrial systole, ventricular contraction, or rapid early diastolic filling.
  • the main control program for processing the signal from sensor 1 to provide the above-described display functions is illustrated in Fig. 4.
  • a reset signal is applied to the digital signal processor 18 so as to start the processor in a known state and enable it to perform a boot sequence (step 100) , after which the digital signal processor memory interface is optimally configured to ensure that the minimum number of required wait states will be used for future memory references, and to ensure that proper account is taken of the physical memory width and the logical data width (step 110) .
  • step 120 the digital signal processor memory interface is optimally configured to ensure that the minimum number of required wait states will be used for future memory references, and to ensure that proper account is taken of the physical memory width and the logical data width
  • step 200 to initiate a new processing sequence
  • all analysis variables are reset to appropriate initial values and the display initialized, so that the display starts from a known state (step 120)
  • the digital signal processor serial port input and output sides which are connected respectively to analog-to-digital converter 17 and digital- to-analog converter 19, is configured to the mode of operation (asynchronous or synchronous)
  • the proper word size is then set to match the data converters and a programmable timer is set up and started (step 130) .
  • the programmable timer generates a bit-clock signal used by the data converters for shifting the data into and out of the digital signal processor 18.
  • the general purpose timer of the digital signal processor 18 is configured for the desired sample rate and type of output signal (pulse or clock) and started (step 140) , the input pointer used by the interrupt service routine to indicate where in the input buffer the last input sample was placed is initialized to some address within the buffer (step 150) , and the interrupt system, described in more detail below in connection with Fig. 5, is started (step 160) .
  • the interrupt service routine 300 stores incoming data and supplies corresponding signals to the analog-to-digital converter for playback.
  • the main control program is copied from the read only memory 22 to the random access memory 23 for further execution (step 170) , and an adjustment subroutine described in detail below in connection with Fig. 6 is called (step 180) to enable operator input of the volume, which increases or decreases the processor gain variable, and scrolling of the display if there are any continuation messages.
  • the main control program checks whether an o.k. command has been entered via the o.k. key 11 (step 190) . If the o.k. command has not been detected, the adjustment subroutine is re-entered. Once the o.k.
  • the main control program resets program variables and initializes the display (step 200) , and polls the input pointer to determine if new input data has reached a buffer boundary, i.e., whether the next complete frame of data has been sampled (step 210) , at which point a frame pointer to the next entry in a circular frame buffer (not shown) is advanced (step 220) .
  • the frame pointer establishes the location in the frame buffer that will characterize the frame consisting of the most recently input samples.
  • the digital signal processor 18 transforms the frame into the frequency domain (step 230) by, for example, applying a Hanning or other type of window to the frame and performing a fast Fourier transform (FFT) or discrete wavelet transform (DWT) .
  • FFT fast Fourier transform
  • DWT discrete wavelet transform
  • the needed parameters are then extracted from the frequency data by calculating the total power and power spectral density (PSD) of each of a predetermined number of frequency bands corresponding to predominant frequencies of major heart sound features (step 240) , and the extracted parameters are then stored in a frame buffer 30, illustrated in Fig. 7, at locations corresponding to the frequency bands for analysis (step 250) , with each row in the table illustrated in Fig. 7 corresponding to a successive time interval indicated by an input pointer 31.
  • PSD total power and power spectral density
  • the frame buffer 30 is scanned using a separate scan pointer to identify the onset and demise of signal peaks and to update parameters describing existing conditions, and the information is stored in two display tables 32 and 33 in memory in order to update the display (step 260) .
  • the main control program checks whether the o.k. key 11 has been pushed and either returns to the operator input loop represented by steps 180 and 190 or returns to step 210 to wait for another frame of data. This permits the operator to freeze the analysis at any point and start another analysis later.
  • the random access memory thus temporarily stores the control program during execution, includes the frame buffer 30 for receiving data and storage for parameters extracted from the frames for analysis, as well as two display tables 32 and 33 used to update the display.
  • One of the two display tables is a graphics display table 32, depicted in Fig. 8, which contains as many entries as the frame buffer, one for each time interval. Each entry corresponds to a position on the horizontal axis of the graphical display 4, with data describing what is to be displayed at each position being placed into the table for the display routine to use in presenting the display.
  • the entries include "type line, " which refers to the type of heart sound depicted, and an intensity level code corresponding to the intensities described above.
  • the other of the two tables is a message display table
  • the message display table contains enough entries to describe all of the messages that might possibly be selected for display at one time. Each entry consists of a list of indexes and numbers.
  • the first field is an index to identify the message by pointing to a text string in memory.
  • Imbedded in the text string are replacement symbols that are to be replaced by words or phrases identified by corresponding indexes in the table entry.
  • Also imbedded in the text string are symbols to be replaced by numbers found in corresponding entries of the table .
  • the analysis step simply involves correlating heart sounds with the parameters of peaks, and in particular the location of the peaks, which indicates frequency and timing, and their amplitude, and storing the parameters in locations in the display tables corresponding to the heart sounds. Since each sound has a specific range of frequencies and timings, location of the peaks identifies the sounds and relationships between the sounds. Once the sounds and their intensities and timings are identified, the intensities and/or timings can then be associated with appropriate text strings stored in memory and corresponding to the identified sounds, intensities, and/or timings for display in the text message portion 26 of the display, and also used to locate the bars on the graphics display 25.
  • the processor 18 After adding one to the frame count, the processor 18 begins the analysis step 250 by looking back through the frame buffer for a combination of sounds that represent a sequence of the first and second heart sounds
  • the processor searches for a cluster of peaks in the SI frequency band ( ⁇ 400 Hz) , an appropriate time interval without significant peaks but perhaps with murmur noise (approximately 5-25 ms depending on heart rate) , and a cluster of peaks in the S2 frequency band (>200Hz) .
  • the display table is updated to indicate the missed beat graphically, and a message table entry indicating the skipped beat in relation to the number of beats between skipped beats is added or updated in the message table. If the average of total noise levels is high or if a nonsensical pattern is recognized, the message table entry for "excessive noise" is added/updated, or if the average of total noise levels is low, a message table entry for "place sensor on chest” is added/updated. If a new S1/S2 combination is found, the frame counts
  • the display specifications can of course be varied accordingly.
  • the time or frame count since the last SI is noted and the average, maximum and minimum heart rate variables are updated based on the number of beats since the last skipped beat.
  • the systole (SI to S2) and diastole (previous S2 to current SI) intervals are determined and the message table entries for heart rate, systole interval, and diastole interval are added or updated, as are message table entries for irregular heart rate minima and maxima is the deviation in heart rates is excessive, and the skipped beat message table entry.
  • SI data is removed from the graphics display table, the intensity levels of Ml and TI are noted, the minimum and maximum Ml and TI intensities are tracked, the graphics display table updated with the location and intensity of Ml and TI, and the message display table updated with the Ml and TI are updated to indicate intensities, and variations if significant .
  • the intensity levels of A2 and P2 are noted, the minimum and maximum intensities are tracked, the graphics display table is updated with the location and intensities of A2 and P2 , and entries in the message table are updated or added corresponding to the intensities and, if significant, the intensity variations.
  • A2 occurs before P2 , indications of the reversal and split time are added to the message table, if A2 precedes P2 by less than 30 ms, a message table entry for a narrowly split S2 is added or updated, and if A2 precedes P2 by more than 30 ms, a message table entry for a widely split S2 is added/updated.
  • the graphics display table is updated with locations and intensity level of murmur lines, the grade level of the murmurs are noted according to maximum intensity, the maximum and minimum grade levels are tracked, the murmur timing is noted, the envelope shapes are noted and tracked, and corresponding entries are made to the message display table.
  • the analysis step is completed when all appropriate display table entries have been added and updated, at which time the display is updated according to the display table entries (step 260) .
  • the interrupt service routine 300 handles the regular flow of digital signal samples into and out of the digital signal processor. Since control enters this routine from random points in the main program, it is necessary for this routine to save the contents of registers that it will be using and restore them to prevent the main program from being affected by the interruption before control is returned to it.
  • the save step is indicated in Fig. 5 by reference numeral 310 and the restore step by reference numeral 360, after which the interrupt service routine returns to the point in the main control loop at which it exited (step 370) .
  • Data sample processing occurs in steps 320-350, which begin by advancing the input pointer to the position where the new input sample is to be placed, or to the beginning of the buffer if the pointer would advance beyond the buffer (step 320) , followed by reading the sample from the serial port and storing the sample in the input buffer at the location indicated by the input pointer (step 330) , multiplying the sample by a gain factor (step 340) , and sending the sample to the digital-to-analog converter via the serial port output for playback over the headset 3.
  • the adjustments subroutine 400 illustrated in Fig. 6 polls, in steps 410-430, the volume adjustment and scrolling buttons, and adjusts the level of the audio output and the message display accordingly in steps 440- 460, with a corresponding adjustment of the graphical display (step 470) as necessary, before returning to the main control loop (step 480) .
  • message table entries and corresponding calculations may be added, by way of example, to indicate overall heart condition. This can be accomplished by weighting each reported finding as either normal (0) , marginal (1), abnormal (3), and emergency (10) to obtain a heart condition value, and summing the total values, with age and sex being taken into account in assigning weights as appropriate.
  • the graphical display may be eliminated, although the message capabilities included in the first embodiment of the invention would be retained. Standard messages would be simplified and the overall heart condition would be added. Detailed technical messages would be available as an option so that the user could communicate them to professional medical personnel for further analysis.

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  • Physics & Mathematics (AREA)
  • Acoustics & Sound (AREA)
  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Medical Informatics (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)

Abstract

Un stéthoscope manuel électronique comprend un affichage graphique (4) affichant des informations d'interprétation indicatives du type, de l'intensité et du rythme des sons cardiaques ou respiratoires détectés par le stéthoscope. Dans le cas d'un affichage de message textuel, lors de l'entrée d'un bloc complet de données provenant d'un capteur (14), un processeur (18) de signal, dans le stéthoscope, effectue une conversion dans le domaine fréquence du bloc, une corrélation des caractéristiques dans les blocs convertis en fréquence le plus récemment avec les sons cardiaques ou respiratoires, il dérive des variables relatives aux sons cardiaques ou respiratoires et il stocke (23) les variables dans des tables d'affichage avec des pointeurs sur des chaînes de texte préstockées (22) pour effectuer un affichage en temps réel sous forme de message textuel. On peut aussi ajouter une sortie audio (24). On peut aussi prévoir une connexion à un modem ou à un ordinateur afin d'offrir la possibilité d'archivage local ou de transmettre vers une installation médicale distante à des fins d'archivage et de contrôle.
PCT/US1999/012369 1998-07-08 1999-07-08 Stethoscope analytique WO2000002486A1 (fr)

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AU49532/99A AU4953299A (en) 1998-07-08 1999-07-08 Analytic stethoscope

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US11171198A 1998-07-08 1998-07-08
US09/111,711 1998-07-08

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Cited By (11)

* Cited by examiner, † Cited by third party
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GB2369434A (en) * 2000-08-01 2002-05-29 Michael James Reeves Graphical display for a stethoscope
WO2005041778A1 (fr) * 2003-10-22 2005-05-12 3M Innovative Properties Company Analyse de sons auscultatoires par decomposition ponctuelle
EP1615546A2 (fr) * 2003-04-23 2006-01-18 Hemchandra Shertukde Appareil et methode de diagnostic non invasif de coronaropathie
WO2006079062A1 (fr) * 2005-01-24 2006-07-27 Regents Of The University Of Minnesota Analyse de sons auscultatoires a l'aide de la reconnaissance vocale
WO2011082199A1 (fr) * 2009-12-29 2011-07-07 The Board Of Governors For Higher Education, State Of Rhode Island And Providence Plantations Systèmes pour la détection de l'apnée du sommeil à partir des sons respiratoires
CN102697520A (zh) * 2012-05-08 2012-10-03 天津沃康科技有限公司 基于智能识别功能的电子听诊器
US8870791B2 (en) 2006-03-23 2014-10-28 Michael E. Sabatino Apparatus for acquiring, processing and transmitting physiological sounds
US20160192846A1 (en) * 2015-01-07 2016-07-07 Children's National Medical Center Apparatus and method for detecting heart murmurs
WO2019048961A1 (fr) 2017-09-05 2019-03-14 Bat Call D. Adler Ltd. Diagnostic de pathologies à l'aide de signatures infrasonores
US11116478B2 (en) 2016-02-17 2021-09-14 Sanolla Ltd. Diagnosis of pathologies using infrasonic signatures
US12029606B2 (en) 2017-09-05 2024-07-09 Sanolla Ltd. Electronic stethoscope with enhanced features

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Cited By (19)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB2369434A (en) * 2000-08-01 2002-05-29 Michael James Reeves Graphical display for a stethoscope
EP1615546A2 (fr) * 2003-04-23 2006-01-18 Hemchandra Shertukde Appareil et methode de diagnostic non invasif de coronaropathie
EP1615546A4 (fr) * 2003-04-23 2010-10-06 Medscansonics Inc Appareil et methode de diagnostic non invasif de coronaropathie
WO2005041778A1 (fr) * 2003-10-22 2005-05-12 3M Innovative Properties Company Analyse de sons auscultatoires par decomposition ponctuelle
US7300405B2 (en) 2003-10-22 2007-11-27 3M Innovative Properties Company Analysis of auscultatory sounds using single value decomposition
WO2006079062A1 (fr) * 2005-01-24 2006-07-27 Regents Of The University Of Minnesota Analyse de sons auscultatoires a l'aide de la reconnaissance vocale
US8870791B2 (en) 2006-03-23 2014-10-28 Michael E. Sabatino Apparatus for acquiring, processing and transmitting physiological sounds
US8920343B2 (en) 2006-03-23 2014-12-30 Michael Edward Sabatino Apparatus for acquiring and processing of physiological auditory signals
US11357471B2 (en) 2006-03-23 2022-06-14 Michael E. Sabatino Acquiring and processing acoustic energy emitted by at least one organ in a biological system
WO2011082199A1 (fr) * 2009-12-29 2011-07-07 The Board Of Governors For Higher Education, State Of Rhode Island And Providence Plantations Systèmes pour la détection de l'apnée du sommeil à partir des sons respiratoires
US9345432B2 (en) 2009-12-29 2016-05-24 Rhode Island Board Of Education, State Of Rhode Island And Providence Plantations Systems and methods for sleep apnea detection from breathing sounds
CN102697520A (zh) * 2012-05-08 2012-10-03 天津沃康科技有限公司 基于智能识别功能的电子听诊器
US20160192846A1 (en) * 2015-01-07 2016-07-07 Children's National Medical Center Apparatus and method for detecting heart murmurs
WO2016112215A3 (fr) * 2015-01-07 2016-09-22 Children's National Medical Center Appareil et procédé de détection de souffles cardiaques
US10251562B2 (en) 2015-01-07 2019-04-09 Children's National Medical Center Apparatus and method for detecting heart murmurs
US11116478B2 (en) 2016-02-17 2021-09-14 Sanolla Ltd. Diagnosis of pathologies using infrasonic signatures
WO2019048961A1 (fr) 2017-09-05 2019-03-14 Bat Call D. Adler Ltd. Diagnostic de pathologies à l'aide de signatures infrasonores
EP3678553A4 (fr) * 2017-09-05 2021-05-26 Sanolla Ltd Diagnostic de pathologies à l'aide de signatures infrasonores
US12029606B2 (en) 2017-09-05 2024-07-09 Sanolla Ltd. Electronic stethoscope with enhanced features

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