EP2976016A1 - Analyse spectrale de flux sanguin turbulent d'artère coronaire - Google Patents

Analyse spectrale de flux sanguin turbulent d'artère coronaire

Info

Publication number
EP2976016A1
EP2976016A1 EP14770732.7A EP14770732A EP2976016A1 EP 2976016 A1 EP2976016 A1 EP 2976016A1 EP 14770732 A EP14770732 A EP 14770732A EP 2976016 A1 EP2976016 A1 EP 2976016A1
Authority
EP
European Patent Office
Prior art keywords
vibrational
frequency power
frequency
cardiac data
power spectrum
Prior art date
Legal status (The legal status 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 status listed.)
Withdrawn
Application number
EP14770732.7A
Other languages
German (de)
English (en)
Other versions
EP2976016A4 (fr
Inventor
Norman Lee OWSLEY
Roger Paul NORRIS
Ralph Walter ZAORSKI
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
PhonoFlow Medical LLC
Original Assignee
PhonoFlow Medical 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
Priority claimed from US13/815,961 external-priority patent/US8961427B2/en
Application filed by PhonoFlow Medical LLC filed Critical PhonoFlow Medical LLC
Publication of EP2976016A1 publication Critical patent/EP2976016A1/fr
Publication of EP2976016A4 publication Critical patent/EP2976016A4/fr
Withdrawn legal-status Critical Current

Links

Classifications

    • 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
    • A61B5/026—Measuring blood flow
    • 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
    • A61B5/02007—Evaluating blood vessel condition, e.g. elasticity, compliance
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7203—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7271—Specific aspects of physiological measurement analysis
    • A61B5/7275—Determining trends in physiological measurement data; Predicting development of a medical condition based on physiological measurements, e.g. determining a risk factor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/08—Detecting organic movements or changes, e.g. tumours, cysts, swellings
    • A61B8/0883—Detecting organic movements or changes, e.g. tumours, cysts, swellings for diagnosis of the heart
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/52—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/5215—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data
    • A61B8/5223—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data for extracting a diagnostic or physiological parameter from medical diagnostic data
    • G—PHYSICS
    • G16—INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR SPECIFIC APPLICATION FIELDS
    • G16H—HEALTHCARE INFORMATICS, i.e. INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR THE HANDLING OR PROCESSING OF MEDICAL OR HEALTHCARE DATA
    • G16H50/00—ICT specially adapted for medical diagnosis, medical simulation or medical data mining; ICT specially adapted for detecting, monitoring or modelling epidemics or pandemics
    • G16H50/20—ICT specially adapted for medical diagnosis, medical simulation or medical data mining; ICT specially adapted for detecting, monitoring or modelling epidemics or pandemics for computer-aided diagnosis, e.g. based on medical expert systems
    • G—PHYSICS
    • G16—INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR SPECIFIC APPLICATION FIELDS
    • G16H—HEALTHCARE INFORMATICS, i.e. INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR THE HANDLING OR PROCESSING OF MEDICAL OR HEALTHCARE DATA
    • G16H50/00—ICT specially adapted for medical diagnosis, medical simulation or medical data mining; ICT specially adapted for detecting, monitoring or modelling epidemics or pandemics
    • G16H50/30—ICT specially adapted for medical diagnosis, medical simulation or medical data mining; ICT specially adapted for detecting, monitoring or modelling epidemics or pandemics for calculating health indices; for individual health risk assessment
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2505/00—Evaluating, monitoring or diagnosing in the context of a particular type of medical care
    • A61B2505/05—Surgical care
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/02—Details of sensors specially adapted for in-vivo measurements
    • A61B2562/0204—Acoustic sensors
    • 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
    • A61B5/0803—Recording apparatus specially adapted therefor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/103—Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
    • A61B5/11—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb
    • A61B5/1102—Ballistocardiography
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/103—Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
    • A61B5/11—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb
    • A61B5/113—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb occurring during breathing
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7235—Details of waveform analysis
    • A61B5/7253—Details of waveform analysis characterised by using transforms
    • A61B5/7257—Details of waveform analysis characterised by using transforms using Fourier transforms
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7271—Specific aspects of physiological measurement analysis
    • A61B5/7282—Event detection, e.g. detecting unique waveforms indicative of a medical condition
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/44—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device
    • A61B8/4427—Device being portable or laptop-like

Definitions

  • the body is made up of structures that have very different physical properties which, are distributed as a function of space throughout the body cavity. Some of these structures are lungs, ribs, organs, blood, arteries, fat, etc. These structures present a non-homogeneous media to the propagation of vibrational energy. Such a non-homogenous media can make it difficult to characterize the media sufficiently to f m: focused listening beams while processing the vibrational energy emitted f om the areas of stenosis during a parametric analysis that assumes a known vibrational wave speed. This can present a problem.
  • FIG. 1 Figure 4 illustrates several channels of vibrational cardiac data, according to an embodiment of the invention.
  • Figure 15 illustrates an apparatus according to embodiments of the invention.
  • the cross section 1 1 2 of the human presents a non-homogeneous media through which the vibrational energy 1 10 propagates and contains various structures such as ribs, lungs, organs interfaces, muscles, fat, and skin tissue indicated generally by 1 14.
  • the vibrational energy propagates through the non-homogeneous media and is measured on ( he surface 1 1 1 by the array of N sensors 1 16, in one embodiment, it can be desirable to place the array of sensors 1 1 ( > over a person's heart and above a space between adjacent ribs to facilitate detection of the vibrational energy.
  • a nominal duration of the entire heart waveform is .from one h undred and twenty (120) to one hundred and eighty ( 1 0) seconds and is made up of six (6) twenty (20) to thirt (30) second segments.
  • FIG. 1 00531
  • the M sensor array described in Figure IA, is used to measure and process vibrational cardiac energy, which is measured at the surface 1 .1 1 during the diastolic intervals, in one embodiment, such measurement and processing of the vibrational cardiac energy is used to determine whether a plaque deposits) (coronary artery lesion(s)) 108 exists in the human due to coronary arter-' disease. In other embodiments, such processing can be used to detect vibrational energy generated within the human in genera! and not necessarily caused by coronary artery disease.
  • Figure 3 illustrates, generally a 300, a method for processing vibrational cardiac data, according to embodiments of the in vention.
  • FIG. 4 illustrates, generally at 400, several channels 402, 404, 406, and 408 of vibrational cardiac data according to an embodiment of the invention.
  • Channel 6 indicated at 404 is selected as the high quaiity channel, with signal -to-noise ratio metric indicated at 410, 10056 j
  • the vibrational cardiac data from the high quality channel is band pass filtered to suppress energy at frequencies that are above and below the frequency content of the first and second peaks of the heart cycle.
  • the band pass filter operation typically passes energy in the band from approximately 5 cycles per second (Hz) to several tens of Hz,
  • a master replica is selected from the high quality channel, which was specified at the block 304.
  • the master replica is selected by selecting a heart cycle that is highly representative of a majority of heart cycles within the segment of the heart waveform represented by the high quality channel.
  • the master replica is either a portion of or the entire heart cycle so identified.
  • Figure 4 displays vibrational cardiac data, generally at 400, collected front four (4) different transducer channels, i.e., a channel five (5) at 402 compute a channel six (6) at 404, a channel seven (7) at 406 and a channel eight (8) at 408.
  • the vibrational cardiac data collected from channel six (6) at 404 ( Figure 4) will be used for master replica selection and correlation due to favorable signal-to- noise characteristics as indicated at 410.
  • correlation coefficient c(t) is plotted at 602 as a function of time 604.
  • A. threshold is indicated at 60S.
  • the threshold 608 can be defined by an operator with graphical user interface (GUI) or it can be defined by the system.
  • Figure 9 illustrates a two- dimensional space-time frequency power spectrum (cross-channel power spectral density matrix "CSDM") of vibrational cardiac data, generally at 900, according to one embodiment of the invention.
  • CSDM cross-channel power spectral density matrix
  • spatial frequency number is plotted on an axis 902 and temporal frequency is plotted on an axis 904. Normalized amplitude is indicated by a grey scale color and a reference key is illustrated at 906.
  • an eigenvalue-eigenvector decomposition (EBD) of the CSDM in each slot and for each FFT frequency bin in the range k ⁇ k ⁇ k ⁇ is computed.
  • This decomposition of the CSDM provides estimates of the b!ood flow turbulence induced noise spectrum level and bandwidth.
  • Rectangular spectral Bandwidth, ERB Rectangular spectral Bandwidth, ERB, for spatial eigenvalue p.
  • the estimated number set C [Cup ⁇ *&>, C S ( P) . ⁇ , , ⁇ character ⁇ , for p - 1 , 2, ... , ⁇ Nf can provide a diagnostic tooi for the detection of arterial blood flow turbulence and thereby the causative pathology.
  • a simulation of such detection was performed on a phantom and is described below in conjunction with Figure II through Figure 14.
  • Eigenvalue svl4 is shown at .1206 with occluder and at 1 208 without occluder.
  • Eigenvalue sv0.1 is plotted at 1216, as a function of flow speed, with occluder in to simulate an area of stenosis.
  • Eigen value svOl. is plotted at 12.18 without occluder to simulate the healthy state, free of stenosis.
  • Figure 13 illustrates an Equivalent Rectangular ' bandwidth (ER ' B) display of vibrational energy resulting from fluid flow with occluder present (area of stenosis), generally at 300, according to one embodiment of the invention.
  • temporal frequency is plotted on an axis 1302 and eigenvalue number/inde is piotted on an axis 1304.
  • Relative amplitude 1308 of the data 1306 is displayed as a modulation of gray scale.
  • Data 1306 represents an Equi valent Rectangular Bandwidth (ER ' B) estimate for the 35 cm/see flow rate with an occluder present.
  • the vibrational cardiac data that occurs during a diastolic interval are processed to assess a condition of health of the coronary arteries.
  • Blood flow through the coronary arteries is at a maximum at the onset of diastole and then decreases as a function of time through diastole.
  • a typical time slot length can be in the range 0,125 to 0.1825 seconds in duration when four (4) rime slots are used to process the diastolic window with 50% overlap between time slots.
  • Other amounts of time slot overlap can be used and in some embodiments time slots can be configured without overlap.
  • the example of four (4) time siots with a 50% overlap is provided merely for illustration and does not present any limitation to embodiments of the invention.
  • the first heart sound interval is indicated at 1806,
  • the first heart sound interval 180 includes a closure snap 1812 of a mitral valve and a closure snap of a tricuspid valve at 1814.
  • the second heart sound interval 1808 includes an aortic valve closure 1818 and i 820.
  • 1 820 is either a pulmonary valve closure and/or an early ventricular refilling turbulence transient.
  • the diastolic interval is the region of interest.
  • the aforementioned heart sounds constitute unwanted coronary events and are eliminated from the processing by placement of the time slots.
  • valve vibrational energy propagates by means of elastic waves in the walls of the heart chamber, if (here is other energy that is time coincident with the third and fourth heart sounds, e.g., 1820 and 1.830 (Figure 18), then the corresponding spectrum is masked fay 1 820 and 1 30 ( Figure 18). Power line artifacts of 60 Hz are indicated at 1918.
  • Time slot 2 captures the trailing edge of ventricle refilling (S3), the leading edge of S4 and a uiet area which permits measurement of energy due to blood flow turbulence in the left coronary artery.
  • a moderate strength spread spectrum energy swath is indicated at 21 14. This swath has a center frequency of 350 Hz, a bandwidth of approximately 60 Hz, and a signal-to-noise ratio (SN ) of approximately 8-10 dB. This
  • Time slot 2 shown at 2124 reckon also indicates a low level of spectrum ripple.
  • the ripple has a period of approximately 30 to 40 Hz and a peak-to- alley amplitude differential of 2 to 3 dB as indicated at 2126.
  • Tin ' s effect is consistent with an interference pattern produced by energy propagating from a vibration source to a vi bration transducer (measurement location) along more than a single path.
  • Phase coherent energy arrivals on different paths can periodically suppress or support each other and a frequency spectrum ripple period of 30 to 40 Hz is consistent with elastic wave propagation speeds in tissue with multiple path length differences on the order of centimeters.
  • time is plotted on an axis 2202 and amplitude is plotted on an axis 2204.
  • a systolic interval is indicated at 2206 and a diastolic interval is indicated at 2208.
  • the diastolic interval 2208 has been partitioned into four (4) overlapping time slots 2210, 2212, 214, and 2216.
  • Figure 24 illustrates, generally at 2400, an overlay of vibrational frequency power spectra estimates from -multiple slots corresponding to the human's data shown in Figure 22, according to embodiments of the invention.
  • time and channel averaged vibrational frequency power spectrum estimates for each time slot (22.1 , 2212, 2214, and 2216 from Figure 22) are plotted o a graph with frequency on an axis 2402 and spectrum level on an axis 2404,
  • Time slot I , time slot 2, and time slot 3 contain features, the types of which were described above, which are associated with coronary artery blood flow turbulence and a state of health of a coronary artery.
  • Time slot 4 (22.16 in Figure 22) contains valve snap energ and has been placed to capture part of the valve snap to illustrate die fact that the first three time slots (2210, 2212, and 2214 from Figure 22) are measuring blood flow turbulence.
  • Another example of a feature changing between time slots is medium spread spectrum energy swath 2412 in time slot 2 (2212) transforming into a frequency band limited whistle 2414 in time slot 3 (2214).
  • the estimated center frequency of the swath 2412 and the whistle 2414 is 390 Hz as indicated at 2422.
  • FIG. 25 illustrates, generally at 2500, a method for identifying a feature related to coronary artery blood flow turbulence using a single human, according to embodiments of the .invention.
  • a process starts at a block 2502
  • a di astolic interval of a heart cycle is partitioned into at least two time slots.
  • a time to frequency transformation i performed on vibrational cardiac data collected from the time slots created in the block 2504.
  • FIG. 26 illustrates, generally at 2600, a comparison of vibrational cardiac data from multiple humans, according to embodiments of the in vention.
  • frequency is plotted on an axis at 2602 and spectrum level is plotted on an axis at 2604.
  • the vibrational cardiac data plotted in Figure 26 are the time and channel averaged vibrational frequenc power spectrum estimates for time slot 1 (for the symptom free person at 2630) data previously shown in Figure 21 and the person whose coronary arteries indicate coronary artery turbulence at 2620, which are data previously shown in Figure 23 and Figure 24 (2210) for the clinically diagnosed individual.
  • the roll-off of the low frequency plateau differs between the symptom free person's measurement 2620 and the clinically diagnosed person's measurement 2630.
  • the roll-off is 24 dB indicated at 2612.
  • the roil-off is 1 ? dB indicated at 2614.
  • Figure 27 illustrates, generally at 2700, a method for identifying a feature related to coronary artery blood, flow turbulence using multiple humans, according to embodiments of the invention.
  • a process starts at a block 2702.
  • a time to frequency transformation is performed on vibrational cardiac data collected during a diastohc interval of a heart cycle, thereby resulting in a vibrational frequency power spectrum estimate.
  • a feature(s) is extracted from the vibrational frequency power spectrum estimate with the aid of previously identified and clinically verified features that are related to blood flow turbulence in a coronary artery and the related condition of health of the coronary artery.
  • propagated signals e.g., carrier waves, infrared signals, digital signals, etc.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Medical Informatics (AREA)
  • Public Health (AREA)
  • Biomedical Technology (AREA)
  • General Health & Medical Sciences (AREA)
  • Pathology (AREA)
  • Surgery (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Veterinary Medicine (AREA)
  • Animal Behavior & Ethology (AREA)
  • Physics & Mathematics (AREA)
  • Molecular Biology (AREA)
  • Biophysics (AREA)
  • Physiology (AREA)
  • Cardiology (AREA)
  • Computer Vision & Pattern Recognition (AREA)
  • Signal Processing (AREA)
  • Psychiatry (AREA)
  • Databases & Information Systems (AREA)
  • Data Mining & Analysis (AREA)
  • Epidemiology (AREA)
  • Artificial Intelligence (AREA)
  • Primary Health Care (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Radiology & Medical Imaging (AREA)
  • Vascular Medicine (AREA)
  • Hematology (AREA)
  • Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)

Abstract

L'invention concerne des procédés et des appareils pour obtenir des données cardiaques, qui incluent l'acquisition de données de champ vibratoire cardiaque à partir d'un transducteur où le transducteur mesure la vibration sur une surface d'un corps humain. Un événement coronaire indésirable est séparé des données cardiaques vibratoires. Un événement transitoire est extrait des données cardiaques vibratoires du cycle cardiaque. L'événement transitoire apparaît durant un intervalle diastolique dans un cycle cardiaque. L'événement transitoire est évalué pour un état de turbulence de flux sanguin d'artère coronaire et un état de santé d'une artère coronaire est évalué à partir d'une caractéristique dans une estimation du spectre de puissance fréquentiel vibratoire.
EP14770732.7A 2013-03-18 2014-03-14 Analyse spectrale de flux sanguin turbulent d'artère coronaire Withdrawn EP2976016A4 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US13/815,961 US8961427B2 (en) 2008-08-09 2013-03-18 Spectrum analysis of coronary artery turbulent blood flow
PCT/US2014/029833 WO2014153265A1 (fr) 2013-03-18 2014-03-14 Analyse spectrale de flux sanguin turbulent d'artère coronaire

Publications (2)

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EP2976016A1 true EP2976016A1 (fr) 2016-01-27
EP2976016A4 EP2976016A4 (fr) 2016-12-07

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CA (1) CA2907400A1 (fr)
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Publication number Priority date Publication date Assignee Title
US11240579B2 (en) 2020-05-08 2022-02-01 Level 42 Ai Sensor systems and methods for characterizing health conditions

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EP1808122A3 (fr) * 1997-11-10 2007-08-08 Harris Corporation Système d'imagerie de flux sanguin turbulent non invasif
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JP2010187928A (ja) * 2009-02-18 2010-09-02 Gifu Univ 測定対象血管の力学的機能の評価方法、測定対象血管の力学的機能評価装置、測定対象血管の力学的機能の評価プログラム及び記憶媒体
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Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US11240579B2 (en) 2020-05-08 2022-02-01 Level 42 Ai Sensor systems and methods for characterizing health conditions

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WO2014153265A1 (fr) 2014-09-25
CA2907400A1 (fr) 2014-09-25
EP2976016A4 (fr) 2016-12-07

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