• 专利附录
  • 专利说明
  • 权利要求
  • 类似技术
  • 同族专利
  • 引用文献
  • 法律状态
  • 优先权
    • 专利摘要:
    Methodology for determining the bounds of a patient's acoustic window is described. Medical application acoustic array designs with apertures accommodated by patient acoustic windows and merged acoustic windows are exemplified.
    公开号:US20010001808A1
    申请号:US09/734,448
    申请日:2000-12-11
    公开日:2001-05-24
    发明作者:Charles Chassaing；Hung Nguyen
    申请人:Chassaing Charles E.；Hung Nguyen；
    IPC主号:A61B7-00
    专利说明:
    [0001] This application is related to concurrently filed and co-assigned U.S. patent application entitled “Non-Invasive Turbulent Blood Flow Imaging System” identified by Attorney Docket No. 9023-11 which corresponds to PCT/US97/20186 filed Nov. 10, 1997 (“the 20186 application”). This application is also related to co-pending and co-assigned patent application Ser. No. 09/136,933, entitled “Thin Film Piezoelectric Polymer Sensor,” and concurrently filed and co-assigned Provisional Patent Application identified by Attorney Docket No. 9023-16 entitled “Acoustic Window Identification.” The contents of the above-identified applications are hereby incorporated by reference as if recited in full herein. [0001] FIELD OF THE INVENTION
    [0002] This invention relates to arrays of acoustic sensors that facilitate the non-invasive detection of coronary artery disease (CAD). [0002] BACKGROUND OF THE INVENTION
    [0003] The 20186 application describes an invention for the non-invasive in vivo detection and localization of abnormal blood flow. Embodiments of that invention display the spatial distribution of phase coherence in the shear eave component of blood flow signals generated by an acoustic sensor array. An essentially uniform display indicates normal blood flow. A non-uniform display may indicate the presence of an occlusion and the presence or extent of abnormal, turbulent blood flow. Poor correlation of signals from the array sensors may adversely affect the display uniformity. [0003]
    [0004] Acoustic sensor arrays are conventionally positioned above a measurement area defined as the hairless human chest skin located vertically between the sternum and a parallel line passing through the left nipple and horizontally 10 cm above and 6 cm below the left and right nipples. [0004]
    [0005] A prior art acoustic sensor array comprising eight equally spaced sensors in two concentric circles having prime numbers of sensors in each circle and a ninth sensor at the common center of the concentric circle is illustrated by FIG. 6 of the 20186 application. [0005]
    [0006] To reach sensors in a conventionally positioned prior art array as described in the 20186 application, sound waves must travel either directly through lung tissue or first to the body surface and then laterally with consequent attenuation of correlation. A study of the correlation by that array of patient data signals generated by the quiet interval revealed that only four or five of the nine sensors are well correlated. [0006]
    [0007] It is known that a notch (“cardiac notch”) in the human left lung allows the heart to be in contact with the chest wall. Well correlated blood flow signals may be generated by acoustic sensors positioned on a human chest in a small area (“acoustic window”) located above the cardiac notch. The bounds of the acoustic window have been approximated by ultrasonic probe means as described in this application and by locating the portions of sensor corresponding to channels achieve the highest apparent signal to noise ratio (SNR) as described in the Stearns application. [0007] DEFINITIONS
    [0008] Acoustic Window—An area above the notch in the human left lung which allows the heart to be in contact with the chest wall. Well correlated acoustic blood flow signals of good quality may be generated by a sensor array positioned on a patient's chest within or substantially within the perimeter of an acoustic window. [0008]
    [0009] Sensor or Accelerometer—Any current or voltage mode device which generates an electric signal from displacement or a derivative thereof upon detection of a sound wave. [0009]
    [0010] Sensor Array—A pattern or spaced arrangement of a plurality of sensors on or to be placed on the body surface of a patient. [0010]
    [0011] Sensor Array Aperture—The space or area within the perimeter of an array. [0011]
    [0012] Sensor Array Geometry—The shape of the perimeter of a sensor array. [0012]
    [0013] Channel—The path to a receiver followed by a signal from the sensor by which the signal is generated. [0013] SUMMARY OF THE INVENTION
    [0014] Pursuant to one embodiment of the invention, an acoustic window may be defined by ultrasonic probe means. The invention includes sensor arrays having an aperture locatable within or substantially within the bounds of an acoustic window when the array is positioned on the chest of a person. [0014]
    [0015] An important aspect of the invention includes the identification of an acoustic window comprising the merged acoustic window sub-areas corresponding to two or more intercostal spaces (ICS's), and array designs to accommodate such acoustic windows. [0015] BRIEF DESCRIPTION OF THE FIGURES
    [0016] FIG. 1 illustrates an ultrasonic probe acoustic window characterization method that provides a template for the positioning of sensors on a person's chest. All acoustic window data illustrated by FIGS. 2 through 8 and [0016] 10 through 12 was obtained by the FIG. 1 method.
    [0017] FIG. 2 is a plot in polar format of the acoustic window size data obtained from 22 male and 7 female subjects (29 subjects). [0017]
    [0018] FIG. 3 is a histogram of the window areas of the same 29 subjects from which the FIG. 2 data was obtained. [0018]
    [0019] FIG. 4 shows acoustic window size in polar format. Maximum, minimum and average window size for all of the same 29 subjects is depicted. [0019]
    [0020] FIG. 5 illustrates in Cartesian coordinates variations of the ICS ultrasonic probe data points from the left (□) and right (⋄) ICS. The statistical averages for ICS's [0020] 1 to 5 are shown in solid lines. A perimeter connecting the ends of the solid lines is a visualization of the average geometry of the six intercostal spaces.
    [0021] FIG. 6 is a histogram that indicates ICS nearest to the centroids of the average window area (see FIG. 4). [0021]
    [0022] FIG. 7 is a histogram indicating the distribution of the perpendicular distances from the centroid of the average window area (see FIG. 4) to the nearest ICS. [0022]
    [0023] FIG. 8 is a histogram illustrating the distribution of the distance from the left side of the nearest ICS to the projection of the centroid of the average window area (see FIG. 4). [0023]
    [0024] FIG. 9 depicts a prior art nine sensor array based on seismic accelerometers commercially available from Wilcoxon Research, 21 Firstfield Road, Gaithersburg, Md. 20878. The array comprises eight equally spaced sensors in two concentric circles having prime numbers of sensors in each circle and a ninth sensor in the common center of the concentric circles. [0024]
    [0025] FIG. 10 depicts a 13 element array positioned over an acoustic window of average size (solid line, see FIG. 4). An acoustic window of maximum area is also shown (broken line). [0025]
    [0026] FIG. 11 illustrates a 57 element small PVDF sensor array based on averaging of ICS data points. The array comprises five linear subarrays positioned above intercostal spaces [0026] 2 to 6.
    [0027] FIG. 12 illustrates a 32 element array of large PVDF sensors based on averaging of ICS data points. The array comprises five linear subarrays positioned above intercostal spaces [0027] 2 to 6.
    [0028] FIG. 13 illustrates a beam pattern in x for delay-and-sum (DS) (higher in value) and MVDR (lower in value) beamformers using prior art (HA) (dashed lines), bowling pin (BO) (dashed dotted lines), small PDVF (SP) (solid lines) and large PDVF (LP) (dotted lines) arrays. [0028]
    [0029] FIG. 14 illustrates a beam pattern in y (dB) for delay-and-sum (DS) (broken lines) and MVDR (solid lines) beamformers using prior art (HA), bowling pin (BO), small PDVF (SP) and large PDVF (LP) arrays. [0029]
    [0030] FIG. 15 illustrates a beam pattern in z (dB) for delay-and-sum (DS) (broken lines) and MVDR (solid lines) beamformers using Harris (HA), bowling pin (BO), small PDVF (SP) and large PDVF (LP) arrays. [0030]
    [0031] FIG. 16 is a proposed array based on the medical Wilcoxon accelerometer. Only 12 elements are used due to the limitation of the data collection system. The broken line indicates the perimeter of an acoustic window. [0031]
    [0032] FIG. 17 illustrates a 45-element PVDF sensor array comprising five nine element linear subarrays positioned above intercostal spaces [0032] 2 to 6. Large and small acoustic window perimeters with centroids near the fourth and fifth ICS's are shown. DETAILED DESCRIPTION OF THE INVENTION
    [0033] The invention generally comprises the identification of an acoustic window and the design of arrays having geometry sized to fit within or substantially within and thus accommodate the perimeter of the window. The invention may include an average acoustic window and consolidated or merged window subareas and array geometry sized accordingly. [0033] Ultrasonic Probe Determination of The Size and Location of The Acoustic Window—Design of Template for Sensor Positioning
    [0034] The acoustic window may include one or a combination of the small areas (intercostal space window areas) of the patient's chest surface directly above the intercostal spaces one through six. Determination of the size of an acoustic window may be accomplished by steps (i) to (v). [0034]
    [0035] (i) With the patient supine, i.e., lying on his back or side, draw a series of dots along the left sternal border at the beginning of each intercostal space (ICS) for spaces one through six. [0035]
    [0036] (ii) Place an ultrasound probe at the left sternal border of the first intercostal space (ICS). Then move the probe along the intercostal space until the lung tissue is encountered. Place a dot on the chest to mark where the lung tissue begins. [0036]
    [0037] (iii) Repeat step (ii) for intercostal spaces two through six. [0037]
    [0038] (iv) Wipe the ultrasound gel off the chest, and draw a line following each intercostal space, connecting the two previously drawn dots. The lines should be similar to FIG. 1. [0038]
    [0039] (v) After the chest has been marked as above, place a sheet of tracing paper on the chest, and transfer the markings onto the paper to provide a template for positioning of sensors. [0039]
    [0040] Average or “generic” templates may be prepared from average data determined in the same way from a plurality of persons. [0040]
    [0041] A like procedure may be used to determine an acoustic window of a person lying slanted on a bed. [0041]
    [0042] Table 1 lists the window areas in cm-squared for the three window sizes in two bed positions. For the maximum and average window cases, lying slanted on the bed produces a slightly larger (5% and 16%, respectively) window size than lying flat on the bed. In the case of the minimum window, lying flat does produce a significant 37% larger window area than lying slanted on the bed. [0042] TABLE 1 Differences in the Flat and Slanted Bed Positions Areas in cm Average Area Maximum Area Minimum Area Slant 58.08 134.46 6.73 Position Flat Position 48.82 127.37 9.22 % Difference 15.94 5.26 −36.87
    [0043] Based on these results, the flat position is more advantageous since it does not significantly reduce the acoustics window for subjects with large to medium window sizes and at the same time significantly opens up the smaller acoustic window sizes. [0043]
    [0044] Another method for identifying an acoustic window entails examination of which sensor channels receive the highest signal to noise ratio (SNR) as measured by the optimal weights for summing channels. See copending, commonly assigned Stearns U.S. application. [0044] Statistical Analysis of Acoustic Window Data
    [0045] Acoustic window size data, collected pursuant to the described ultrasonic probe methodology, was obtained from 22 male and 7 female subjects. There are two types of data. [0045]
    [0046] 1. Measurements based on a Cartesian coordinate with X axis on the 6[0046] th intercostal space (ICS) and Y axis along the left end of the ICS.
    [0047] 2. Data estimate in polar coordinate centered at the centroid of the acoustic window mass. This data is derived from measuring the distance from the centroid to the edge of the window at 30 degree angle increments. There is a total of twelve data points per subject. [0047] The Distribution of Polar Data
    [0048] The distribution of the window size data in polar format was tested for normality using the normal probability plot from the MATLAB Statistics Toolbox. The purpose of a normal probability plot is to graphically assess whether the data could come from a normal distribution. If the data are normal, the plot will be linear. Other distribution types will introduce curvature in the plot. As shown in FIG. 2, the data points are virtually in a straight line, indicating that the polar coordinate data is Gaussian. [0048]
    [0049] When the area for each of the 22 male windows was computed using AutoCad software, the ratio of the maximum to the minimum area was found to be 15. FIG. 3 illustrates the histogram of the window areas. [0049]
    [0050] FIG. 4 shows the acoustics window size in polar format. In this figure, the outside perimeter is for maximum, the inside perimeter is for the minimum and the intermediate perimeter is for the average across all subjects. [0050] Correlation Coefficients Between Acoustics Window Areas and Demographic Data
    [0051] Computed correlation coefficients between the window area and the subject demographics data are shown in Table 2. This analysis was carried out based on data broken down by male (22 subjects), female (7 subjects) and a combination of both sexes. In general, there exists no strong correlation between the window area and demographics data, with the exception of strong negative correlation of −0.84 between the acoustics window area and the anterior/posterior (AP) diameter of the female subjects and a strong negative correlation between the acoustics window area and the sternum length in both male and female subjects. [0051] TABLE 2 Correlation w/ Correlation w/ Correlation w/ Acoustics Acoustics Acoustics Demographic Window Window Window Feature Area (M&F) Area (Male) Area (Female)Age 0.0043 0.0152 −0.0095 Height −0.1846 −0.4345 0.2794 Weight −0.3503 −0.3579 −0.6678 Chest −0.3578 −0.3800 −0.3623 Circumference AP Diameter −0.5904 −0.5027 −0.8690 Aortic Valve Depth 0.1868 −0.0043 0.5311 ICS of Aortic −0.0774 −0.2081 0.1810 Valve Sternum Length −0.6446 −0.6959 −0.6587 Body Type −0.0874 −0.1637 0.0604 Variations of the ICS End Points in Cartesian Coordinate
    [0052] Examination of the data in Cartesian coordinate reveals the absence of common single reference point such as the centroid in the polar data case. The X-Y data was collected relative to the six intercostal spaces and was measured as left and right ICS. The only single common reference was made when the six ICS's were aligned on the x-axis so that the other spaces can be seen relative to this reference space. [0052]
    [0053] As seen from FIG. 5, the XY coordinates of the left in (□) and right in (⋄) ICS are quite different across the subjects. The statistical averages of the left and right ICS are also shown. When connected, a visualization of the average geometry of the six intercostal spaces is provided. [0053] The Distribution of Window Centroids Over ICS
    [0054] The x-y coordinates of the acoustics window centroids were measured and correlated with the lines defined by the left and right ICS. The purpose of this correlation is to determine which of the six spaces the window centroid is near to and then to ascertain the best space(s) for location of the array. [0054]
    [0055] A histogram of the ICS to which the centroids of the window areas are nearest is plotted in FIG. 6. The result indicates that the fourth and fifth ICS are good candidates for positioning the array center, with the fourth ICS being more frequent than the fifth ICS. In practice, it is appropriate to consider these two ICS equally and pick one based on the best knowledge of which ICS has the best heartbeat sound. [0055]
    [0056] The distribution of (a) the perpendicular distances from the centroid to the nearest ICS and (b) the distances from the left side of the nearest ICS to the projection of the centroid are histogrammed in FIGS. 7 and 8. These results provide guidelines as to the approximate location of the array center relative to the nearest intercostal space. [0056] Array Design Based on Acoustics Window Data Factors and Constraints in Array Geometry Design
    [0057] Constraints imposed on array geometry include: [0057]
    [0058] 1. Limitation on the array aperture by the size of the acoustics window which varies from person to person. [0058]
    [0059] 2. Sensor size which limits the number of elements that can be put in the array aperture. For example, the medical Wilcoxon sensor diameter is about one cm. In the case of PVDF sensor, the prefabricated thin film strip size dictates how many sensors could be placed in the array aperture. [0059]
    [0060] 3. The anti-aliasing requirement of the array design at different operating frequencies. In principle, the inter-element spacing of the sensors is required to be less than half a wavelength at the highest operating frequency to avoid spatial aliasing in the plane wave case. This requirement is relaxed in the near field where source location is the objective. The use of irregularity in array geometry may also alleviate the aliasing problem when there is an inter-element spacing of more than half wavelength. [0060] Array Geometries
    [0061] Use of the acoustics window in array design based on the medical Wilcoxon accelerometer and the large and small PVDF sensors resulted in the three arrays depicted by FIGS. 10, 11 and [0061] 12.
    [0062] The 13-element array of FIG. 10 was based on the average window size described with reference to FIG. 4. Using the actual dimensions of the medical Wilcoxon accelerometer on graph paper, each accelerometer was placed on straight lines starting from the center and populating the perimeter until space is occupied. A total of 13 elements that were fitted into this average window size. Clinical data indicates that 13 elements may not give optimum array gain especially when element signal-to-noise ratio of turbulent flow is low. [0062]
    [0063] More elements per unit area are possible with PVDF technology. Because PVDF film is available in linear strips of 9 and 16 elements per unit, each strip can be put on the intercostal space to maximize signal reception. These factors motivate the array geometries illustrated in FIGS. 11 and 12. [0063]
    [0064] In these two arrangements, five lines of PVDF film strip are placed along ICSs [0064] 2 to 6 at approximately the length of the average ICS as described with reference to FIG. 5. The placement of these PVDF film strips as shown in FIGS. 11 and 12 are for illustration only and not necessarily the exact position and direction of the film strips. Also, because of the inherent variations in human anatomy, the actual placement of the PVDF sensor strips is expected to be different from person to person, in view of the effect of the ribs as a factor in signal reception.
    [0065] At the end, 57 elements for the small PVDF and 32 elements for the large PVDF sensors were used in this array design. [0065] Array Performance
    [0066] The performance of the four sensor arrays depicted by FIGS. 9, 10, [0066] 11 and 12 is presented in terms of beam width and array gain by FIGS. 13, 14 and 15. The beam pattern plots are for frequency at 250 Hz using Verberg propagation model and 10 dB element SNR. These figures show the beam patterns in x, y and z direction for a source 3 cm directly below the array center. The beam pattern for the conventional delay and sum (DS) beamformer is shown in dashed line, and the beam pattern for the MVDR beamformer is in solid line.
    [0067] The figures show that for a conventional beamformer, the array gain is proportional to the number of elements. The effect of the number of elements on the array beamwidth is much more visible for the MVDR beamformer than for the DS beamformer. Also notable is the lack of array aperture in the z direction, as illustrated by the large beam width shown in FIG. 15. [0067]
    [0068] It is known that the MVDR beamformer provides an estimate of the signal power at the signal direction as can clearly be seen from FIGS. 13, 14 and [0068] 15. At the source location, the output of the MVDR beamformer is 10 dB regardless of the number of element in the array. The effect of an increase in the number of elements is a narrower beam width, which is consistent with data showing that the beam width of an MVDR beamformer is inversely proportional to the number of elements (and the element SNR). Array Geometries
    [0069] Increasing the number of elements in constrained by acoustics window size and the physical dimensions of the individual sensor. [0069]
    [0070] It became apparent from the performance of the array designs of FIGS. [0070] 10 to 14 that the use of the 4th and 5th intercostal spaces for centering purpose has merit in the array design process. For both designs, the acoustics window is the union of the two window areas for the 4th and 5th ICSs. These two windows are the average of the XY data obtained from the acoustics window study. The merging of the two windows increases the area available for the array aperture which is an advantage to array performance. A Proposed Wilcoxon Accelerometer Array Based on the Dominant ICS Areas
    [0071] A design for a Wilcoxon commercial accelerometer array is shown in FIG. 16. In this design, there are a total of 16 elements that will fit the composite window area. The composite window area consists of the two averaged windows with centroids near the 4[0071] th and 5th ICSs. In the current data collection system, only 12 elements are used. The missing elements are chosen such that the resulting array is as irregular as possible with at least one sensor pair very close to each other to prevent spatial aliasing. A PVDF Sensor Array
    [0072] For the same composite acoustics window, a 45-element PVDF array is shown in FIG. 17. This array essentially consists of 5 rows of 9-element large PVDF linear array arranged in such a way that conforms to the human chest curvature and, if possible, lies within the lower ICS to adapt to the patient anatomy. One reason for a 5 by 9 linear PVDF array is in the manufacturing and logistics of the thin film technology. [0072]
    [0073] It may not be possible to use all 45 elements for beamforming, since some of the array elements may fall out the acoustics window and thus will not be able to receive the heart sound. An acceptable data collection scheme includes estimation of the signal-to-noise ratio at each element, and weighting or eliminating the sensors that receive the noisiest signal. The use of this weighting technique enables the array to adapt to the differences in acoustic window size that are embodied in human anatomy. [0073]
    权利要求:
    Claims (21)
    [1" id="US-20010001808-A1-CLM-00001] 1. An acoustic sensor array for the detection of blood flow sounds wherein a plurality of sensors is located within the array aperture and wherein said aperture is positionable above an acoustic window when said array is positioned on the chest of a patient.
    [2" id="US-20010001808-A1-CLM-00002] 2. The
    claim 1 sensor array wherein the aperture of said array is sized to accommodate said acoustic window.
    [3" id="US-20010001808-A1-CLM-00003] 3. A
    claim 1 array wherein said acoustic sensors in said array are piezoelectric film sensors.
    [4" id="US-20010001808-A1-CLM-00004] 4. A
    claim 2 array wherein said acoustic sensors in said array are piezoelectric film sensors.
    [5" id="US-20010001808-A1-CLM-00005] 5. A
    claim 1 array wherein said array comprises at least one linear multisensor sequence.
    [6" id="US-20010001808-A1-CLM-00006] 6. A
    claim 2 array wherein said array comprises at least one linear multisensor sequence.
    [7" id="US-20010001808-A1-CLM-00007] 7. A
    claim 1 array wherein said array comprises a plurality of spaced apart generally linear sensor sequences and wherein at least one of said spaced apart generally linear sensor sequences may be located above an intercostal space when said array is positioned on the chest of a patient.
    [8" id="US-20010001808-A1-CLM-00008] 8. A
    claim 2 array wherein said array comprises a plurality of spaced apart generally linear sensor sequences and wherein at least one of said spaced apart generally linear sensor sequences may be located above an intercostal space when said array is positioned on the chest of a patient.
    [9" id="US-20010001808-A1-CLM-00009] 9. A
    claim 5 array wherein said sensors in said array are piezoelectric film sensors.
    [10" id="US-20010001808-A1-CLM-00010] 10. A
    claim 5 array wherein said sensors in said array are polyvinylidene difluoride film sensors.
    [11" id="US-20010001808-A1-CLM-00011] 11. The
    claim 1 array in which said sensors are accelerometers.
    [12" id="US-20010001808-A1-CLM-00012] 12. The
    claim 2 array in which said sensors are accelerometers.
    [13" id="US-20010001808-A1-CLM-00013] 13. A method which comprises the steps of:
    (i) visualizing the perimeters of an acoustic window of an individual; and
    (ii) providing an acoustic sensor array having an aperture sized to accommodate said acoustic window perimeter.
    [14" id="US-20010001808-A1-CLM-00014] 14. The
    claim 13 method further comprising the step of:
    (iii) positioning within said aperture of said array a number of sensors as determined by sensor size and by the quality of the combined signal from all sensors.
    [15" id="US-20010001808-A1-CLM-00015] 15. A method which comprises the steps of:
    (i) determining the perimeter of a proximate acoustic window area separately for a plurality of adjacent intercostal spaces; and
    (ii) merging two or more of said proximate intercostal space window areas,
    wherein a merged acoustic window is defined.
    [16" id="US-20010001808-A1-CLM-00016] 16. The
    claim 15 method further comprising the step of:
    (iii) providing a sensor array wherein said array comprises an aperture sized to accommodate said merged acoustic window of step (ii).
    [17" id="US-20010001808-A1-CLM-00017] 17. The
    claim 15 method wherein said merged window areas are the fourth and fifth intercostal space window areas.
    [18" id="US-20010001808-A1-CLM-00018] 18. The method which comprises the steps of:
    (i) determining the average size of the acoustic window of a plurality of patients; and
    (ii) providing an acoustic array geometry which accommodates a predetermined number of sensors within said average acoustic window size as determined in step (i)
    wherein said number of sensors is predetermined by sensor size and by the quality of a combined signal from all sensors in said array.
    [19" id="US-20010001808-A1-CLM-00019] 19. A template for determining appropriate locations on the chest of a patient, wherein said template includes a perimeter corresponding to the average size of the acoustic window of a plurality of individuals, and
    wherein said template includes indicia to indicate an appropriate position of said template on a person's chest.
    [20" id="US-20010001808-A1-CLM-00020] 20. A method for visualizing the acoustic window of a person which comprises the steps of:
    (i) causing said person to assume a supine position;
    (ii) drawing a series of indicia along the left sternal border at the beginning of each intercostal space for each of intercostal spaces 1 to 6 of said person;
    (iii) placing an ultrasound probe at the left sternal border of each of said intercostal spaces and moving said probe along each said intercostal space until lung tissue is encountered;
    (iv) placing an indicator on the chest of said person to identify as to each intercostal space where lung tissue is encountered;
    (v) drawing a series of lines connecting said lung indicator indicia to said left sternal border wherein said lines indicate the bounds of the acoustic window perimeter of one corresponding intercostal space; and
    wherein a perimeter enclosing all of said lines defines said perimeters of said total acoustic window area of said person.
    [21" id="US-20010001808-A1-CLM-00021] 21. A method which comprises the step of:
    (i) separately determining acoustic window areas proximate to a plurality of adjacent intercostal spaces, wherein each of said proximate acoustic window areas comprises an area of an intercostal space extending from the left sternal border to a point above lung tissue.
    类似技术:
    公开号 | 公开日 | 专利标题
    US6478746B2|2002-11-12|Acoustic sensor array for non-invasive detection of coronary artery disease
    US6699201B2|2004-03-02|Acoustic window identification
    US10758146B2|2020-09-01|System and method for fetal heartbeat sound monitoring and recording by propagation and spacial location analysis by a sensor matrix
    US7409243B2|2008-08-05|Breast cancer detection
    EP1876958B1|2014-08-27|Method and dual-array transducer probe for real time mechanical imaging of prostate
    EP2386250B1|2013-09-11|Cardiac parameter measurement
    US7857763B2|2010-12-28|Automatic signal-optimizing transducer assembly for blood flow measurement
    US20130178742A1|2013-07-11|Method and an apparatus for recording bladder volume
    US20050020921A1|2005-01-27|Ultrasonic sensor garment for breast tumor
    US7922674B2|2011-04-12|Method and device for real time mechanical imaging of prostate
    US20080167566A1|2008-07-10|Systems and methods for determining systolic time intervals
    US20080039733A1|2008-02-14|Systems and methods for calibration of heart sounds
    CN102440806B|2016-08-10|The ultrasonic method eliminated for electromagnetic noise and probe
    CN109498054B|2020-12-25|Heart sound monitoring device, method for acquiring heart sound signal and configuration method
    KR101649074B1|2016-08-17|Method for sensing intercellular potential difference and breastcancer diagnosis system thereof
    WO2000027287A1|2000-05-18|Non-invasive acoustic detection of coronary artery disease
    Karlsson et al.2000|The DopFet system: a new ultrasonic Doppler system for monitoring and characterization of fetal movement
    KR20190057344A|2019-05-28|Fetal monitoring electronic system
    EP3701876A1|2020-09-02|Acoustic sensing apparatus and method
    US20200289089A1|2020-09-17|Ultrasound device including a detachable acoustic coupling pad
    Azad et al.2021|Spatial Distribution of Seismocardiographic Signals
    CN112869776A|2021-06-01|Bladder urine volume monitoring method based on multi-array-element ultrasonic probe
    WO2020223085A1|2020-11-05|Systems and methods for locating and monitoring a subcutaneous target site
    RU16444U1|2001-01-10|DEVICE FOR ULTRASONIC BRAIN STUDY
    WO2021198340A1|2021-10-07|Medical sensing system and positioning method
    同族专利:
    公开号 | 公开日
    US6939308B2|2005-09-06|
    US6478746B2|2002-11-12|
    US20030069506A1|2003-04-10|
    US6193668B1|2001-02-27|
    引用文献:
    公开号 | 申请日 | 公开日 | 申请人 | 专利标题
    US20060055599A1|2004-08-31|2006-03-16|Raytheon Company|Transmitting and receiving radio frequency signals using an active electronically scanned array|
    US20070249945A1|2006-04-19|2007-10-25|Dan Li|Probabilistic fusion in arrhythmia diagnosis and therapy|
    US20130116578A1|2006-12-27|2013-05-09|Qi An|Risk stratification based heart failure detection algorithm|US32180A||1861-04-30||Halter-king |
    US390733A||1888-10-09||Velocipede |
    US3442264A|1964-06-04|1969-05-06|Joseph R Levitt|Data processing method and means|
    US3573394A|1967-09-14|1971-04-06|Ind Scient Research Corp|Piezoelectric microphone with biasing means|
    US3799147A|1972-03-23|1974-03-26|Directors University Cincinnat|Method and apparatus for diagnosing myocardial infarction in human heart|
    JPS4975182A|1972-11-20|1974-07-19|||
    JPS5215972B2|1974-02-28|1977-05-06|||
    US4054808A|1974-08-19|1977-10-18|Matsushita Electric Industrial Co., Ltd.|Vibration detecting device having a piezoelectric ceramic plate and a method for adapting the same for use in musical instruments|
    US4183249A|1975-03-07|1980-01-15|Varian Associates, Inc.|Lens system for acoustical imaging|
    US4413630B1|1976-04-05|1994-04-05|Diasonics Delaware Inc|Sector scanner display and recording system for ultrasonic diagnosis|
    US4094308A|1976-08-19|1978-06-13|Cormier Cardiac Systems, Inc.|Method and system for rapid non-invasive determination of the systolic time intervals|
    US4146955A|1977-08-15|1979-04-03|Harris Corporation|Method of fabricating a stepped-array acousto-optic beam deflector|
    JPS5840805B2|1978-04-10|1983-09-08|Toray Industries||
    US4376302A|1978-04-13|1983-03-08|The United States Of America As Represented By The Secretary Of The Navy|Piezoelectric polymer hydrophone|
    US4268912A|1978-06-06|1981-05-19|Magnavox Government And Industrial Electronics Co.|Directional hydrophone suitable for flush mounting|
    US4387378A|1978-06-28|1983-06-07|Harris Corporation|Antenna having electrically positionable phase center|
    US4226248A|1978-10-26|1980-10-07|Manoli Samir H|Phonocephalographic device|
    US4255791A|1978-12-04|1981-03-10|Harris Corporation|Signal processing system|
    DE3069001D1|1979-05-16|1984-09-27|Toray Industries|Piezoelectric vibration transducer|
    US4385255A|1979-11-02|1983-05-24|Yokogawa Electric Works, Ltd.|Linear array ultrasonic transducer|
    FR2475804B1|1980-02-12|1985-05-24|Lewiner Jacques||
    US4491051A|1980-02-22|1985-01-01|Barcus Lester M|String instrument pickup system|
    US4308870A|1980-06-04|1982-01-05|The Kendall Company|Vital signs monitor|
    JPS5741100A|1980-08-23|1982-03-06|Kureha Chem Ind Co Ltd|Ultrasonic probe|
    US4428380A|1980-09-11|1984-01-31|Hughes Aircraft Company|Method and improved apparatus for analyzing activity|
    US4546777A|1981-03-06|1985-10-15|Siemens Gammasonics, Inc.|Heart sound detector and synchronization for diagnostics|
    US4458693A|1981-03-13|1984-07-10|Medtronic, Inc.|Monitoring system|
    FR2507424B1|1981-06-05|1984-09-14|Cgr||
    IL67815A|1982-02-12|1988-01-31|Sanz Ernst|Method and apparatus for cardiogonometry|
    US4628321A|1982-04-14|1986-12-09|Harris Corporation|Aperture transformation sidelobe canceller|
    DE3234584A1|1982-09-17|1984-03-22|Reinhard 8206 Bruckmühl Fuchs|Structure-borne sound pick-up of piezo-electric flexion pick-ups|
    CA1198806A|1982-11-24|1985-12-31|Her Majesty The Queen, In Right Of Canada, As Represented By The Ministe R Of National Defence|Heart rate detector|
    US4509527A|1983-04-08|1985-04-09|Timex Medical Products Corporation|Cardio-respiration transducer|
    US4812976A|1983-07-22|1989-03-14|Lundy Research Laboratories, Inc.|Method and apparatus for characterizing the unknown state of a physical system|
    US4586514A|1983-08-10|1986-05-06|Biotronics Instruments|Phonoangiographic spectral analysing apparatus|
    US4630203A|1983-12-27|1986-12-16|Thomas Szirtes|Contour radiography: a system for determining 3-dimensional contours of an object from its 2-dimensional images|
    JPS60169927U|1984-04-17|1985-11-11|||
    GB2166871A|1984-09-03|1986-05-14|Vickers Plc|Respiration monitor|
    US4617935A|1985-03-12|1986-10-21|Ndm Corporation|Medical electrode|
    FR2581496B1|1985-05-02|1987-06-26|Silec Liaisons Elec|MICROPHONE CONTACT SENSOR WITH PIEZO POLYMER MEMBRANE|
    US4862361A|1985-06-05|1989-08-29|Massachusetts Institute Of Technology|Methods and apparatus for monitoring cardiovascular regulation using heart rate power spectral analysis|
    EP0212528A3|1985-08-30|1988-11-30|Studer Revox Ag|Method of determining the beginning and the end of a three-dimensional signal displayed as a closed loop|
    US4781200A|1985-10-04|1988-11-01|Baker Donald A|Ambulatory non-invasive automatic fetal monitoring system|
    US4777961A|1985-10-15|1988-10-18|Bruce Saltzman|High sensitivity stethoscopic system and method|
    US4742458A|1985-10-29|1988-05-03|Software Plus, Inc.|Method and apparatus for performing pattern recognition analysis|
    US4862897A|1985-11-05|1989-09-05|Sound Enhancement Systems, Inc.|Electrocardiogram enhancement system and method|
    US4792145A|1985-11-05|1988-12-20|Sound Enhancement Systems, Inc.|Electronic stethoscope system and method|
    US4842411A|1986-02-06|1989-06-27|Vectron, Inc.|Method of automatically measuring the shape of a continuous surface|
    GB2188732B|1986-04-07|1990-04-04|Micro Medical Ltd|Portable computer apparatus for the display of a phonocardiogram and an electrocardiogram of a person|
    US5002058A|1986-04-25|1991-03-26|Intra-Sonix, Inc.|Ultrasonic transducer|
    US4712565A|1986-10-27|1987-12-15|International Acoustics Incorporated|Method and apparatus for evaluating of artificial heart valves|
    US4784154A|1986-11-13|1988-11-15|Colin Electronics Co., Ltd.|Interference resistant biomedical transducer|
    JPH033289Y2|1987-01-26|1991-01-29|||
    US4862144A|1987-04-21|1989-08-29|Tao Billy S K|Movement monitor|
    US4803986A|1987-04-24|1989-02-14|Minnesota Mining And Manufacturing Company|Ergonometric transcutaneous electrical nerve stimulator|
    US4840183A|1987-08-13|1989-06-20|Tdk Corporation|Electrocardiograph|
    US4803996A|1987-09-28|1989-02-14|Nippon Colin Co., Ltd.|Cardiovascular monitor|
    US4924875A|1987-10-09|1990-05-15|Biometrak Corporation|Cardiac biopotential analysis system and method|
    US4928705A|1987-12-08|1990-05-29|University Of Pittsburgh Of The Commonwealth System Of Higher Education|Acoustic aneurysm detector and associated method|
    CN1035213A|1987-12-29|1989-08-30|精工电子工业株式会社|Travelling wave motor|
    DE3744605C1|1987-12-31|1989-04-27|Jochen Dipl-Ing Heimann|Sensor|
    US5010889A|1988-02-04|1991-04-30|Bloodline Technology|Intelligent stethoscope|
    US5218969A|1988-02-04|1993-06-15|Blood Line Technology, Inc.|Intelligent stethoscope|
    US5213108A|1988-02-04|1993-05-25|Blood Line Technology, Inc.|Visual display stethoscope|
    US4991581A|1988-03-04|1991-02-12|Andries Tek R&D Limited Partnership|Acoustic processing apparatus|
    US4821584A|1988-03-15|1989-04-18|The United States Of America As Represented By The United States Department Of Energy|Piezoelectric film load cell robot collision detector|
    US5129403A|1988-04-14|1992-07-14|The United States Of America As Represented By The Secretary Of The Navy|Method and apparatus for detecting and transducing intersaccular acoustic signals|
    US4905706A|1988-04-20|1990-03-06|Nippon Colin Co., Ltd.|Method an apparatus for detection of heart disease|
    IL86759A|1988-06-16|1992-09-06|Dror Nedivi|Medical monitoring system|
    US5164627A|1988-07-26|1992-11-17|Harris Corporation|Phased array acoustic signal processor|
    US4957369A|1989-01-23|1990-09-18|California Institute Of Technology|Apparatus for measuring three-dimensional surface geometries|
    US4947859A|1989-01-25|1990-08-14|Cherne Medical, Inc.|Bio-acoustic signal sensing device|
    US4967760A|1989-02-02|1990-11-06|Bennett Jr William R|Dynamic spectral phonocardiograph|
    US5012815A|1989-02-02|1991-05-07|Yale University|Dynamic spectral phonocardiograph|
    US5003605A|1989-08-14|1991-03-26|Cardiodyne, Inc.|Electronically augmented stethoscope with timing sound|
    US5315512A|1989-09-01|1994-05-24|Montefiore Medical Center|Apparatus and method for generating image representations of a body utilizing an ultrasonic imaging subsystem and a three-dimensional digitizer subsystem|
    US5036857A|1989-10-26|1991-08-06|Rutgers, The State University Of New Jersey|Noninvasive diagnostic system for coronary artery disease|
    US5109863A|1989-10-26|1992-05-05|Rutgers, The State University Of New Jersey|Noninvasive diagnostic system for coronary artery disease|
    US5025809A|1989-11-28|1991-06-25|Cardionics, Inc.|Recording, digital stethoscope for identifying PCG signatures|
    US5086776A|1990-03-06|1992-02-11|Precision Diagnostics, Inc.|Apparatus and method for sensing cardiac performance|
    US5140992A|1990-07-16|1992-08-25|The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration|Passive fetal monitoring sensor|
    US5176153A|1990-11-02|1993-01-05|Eberhardt Allen C|Heart chamber simulator with electronic accelerated heart valve wear and fatigue test apparatus and method|
    US5301679A|1991-05-31|1994-04-12|Taylor Microtechnology, Inc.|Method and system for analysis of body sounds|
    US5288551A|1991-08-09|1994-02-22|Kureha Kagaku Kogyo Kabushiki Kaisha|Flexible piezoelectric device|
    US5337752A|1992-05-21|1994-08-16|Mcg International, Inc.|System for simultaneously producing and synchronizing spectral patterns of heart sounds and an ECG signal|
    US5365937A|1992-09-09|1994-11-22|Mcg International, Inc.|Disposable sensing device with contaneous conformance|
    US5368041A|1992-10-15|1994-11-29|Aspect Medical Systems, Inc.|Monitor and method for acquiring and processing electrical signals relating to bodily functions|
    WO1994013207A1|1992-12-05|1994-06-23|Avl Medical Instruments Ag|Sensor, device and process for measuring blood pressure|
    US5363401A|1993-02-25|1994-11-08|Harris Corporation|Mechanism for extracting hybrid spread spectrum signals within multi-signal type environment|
    US5455385A|1993-06-28|1995-10-03|Harris Corporation|Multilayer LTCC tub architecture for hermetically sealing semiconductor die, external electrical access for which is provided by way of sidewall recesses|
    US5724968A|1993-12-29|1998-03-10|First Opinion Corporation|Computerized medical diagnostic system including meta function|
    HRP940025A2|1994-01-14|1996-06-30|Branko Breyer|A blood flow velocity measurement system perpendicular to a single probing beam|
    US5713367A|1994-01-26|1998-02-03|Cambridge Heart, Inc.|Measuring and assessing cardiac electrical stability|
    US5673702A|1994-06-10|1997-10-07|Cambridge Heart, Inc.|Method and apparatus for the improved electronic display of physiologic waveforms|
    US5394876A|1994-06-30|1995-03-07|Spacelabs Medical, Inc.|Method and apparatus for aiming a doppler flow sensing device|
    US5724983A|1994-08-01|1998-03-10|New England Center Hospitals, Inc.|Continuous monitoring using a predictive instrument|
    US5501229A|1994-08-01|1996-03-26|New England Medical Center Hospital|Continuous monitoring using a predictive instrument|
    US5680513A|1994-08-19|1997-10-21|Hyland; David C.|Series parallel approach to identification of dynamic systems|
    US5796920A|1994-08-19|1998-08-18|Harris Corporation|Multiprocessor system and method for identification and adaptive control of dynamic systems|
    US5553113A|1994-11-18|1996-09-03|Analogic Corporation|Auxiliary data acquisition in a medical imaging system|
    US5686917A|1995-04-19|1997-11-11|National Instruments Corporation|System and method for demultiplexing data in an instrumentation system|
    US5617869A|1995-06-16|1997-04-08|The United States Of America As Represented By The Secretary Of The Navy|Device and method for locating flow blockage in a three-dimensional object|
    US5687738A|1995-07-03|1997-11-18|The Regents Of The University Of Colorado|Apparatus and methods for analyzing heart sounds|
    US5595188A|1995-07-26|1997-01-21|Flowscan, Inc.|Assembly process for polymer-based acoustic differential-output sensor|
    US5638823A|1995-08-28|1997-06-17|Rutgers University|System and method for noninvasive detection of arterial stenosis|
    US5598845A|1995-11-16|1997-02-04|Stellartech Research Corporation|Ultrasound transducer device for continuous imaging of the heart and other body parts|
    US5724967A|1995-11-21|1998-03-10|Nellcor Puritan Bennett Incorporated|Noise reduction apparatus for low level analog signals|
    US5727561A|1996-04-23|1998-03-17|The United States Of America As Represented By The Department Of The Navy|Method and apparatus for non-invasive detection and analysis of turbulent flow in a patient's blood vessels|
    US5853005A|1996-05-02|1998-12-29|The United States Of America As Represented By The Secretary Of The Army|Acoustic monitoring system|US6371924B1|1998-11-09|2002-04-16|Medacoustics, Inc.|Acoustic window identification|
    AU2004201785B2|1999-03-01|2007-10-25|Harris Corporation|Low Profile Acoustic sensor array and sensors with pleated transmission lines and related methods|
    US7037268B1|1999-03-01|2006-05-02|Medacoustics, Inc.|Low profile acoustic sensor arry and sensors with pleated transmission lines and related methods|
    US7113825B2|2002-05-03|2006-09-26|Cardiac Pacemakers, Inc.|Method and apparatus for detecting acoustic oscillations in cardiac rhythm|
    US7123962B2|2002-12-02|2006-10-17|Cardiac Pacemakers, Inc.|Phonocardiographic image-based atrioventricular delay optimization|
    US7260429B2|2002-12-02|2007-08-21|Cardiac Pacemakers, Inc.|Method and apparatus for phonocardiographic image acquisition and presentation|
    US7930019B2|2002-12-02|2011-04-19|Cardiac Pacemakers, Inc.|Method and apparatus for phonocardiographic image acquisition and presentation|
    US7101339B2|2002-12-13|2006-09-05|Cardiac Pacemakers, Inc.|Respiration signal measurement apparatus, systems, and methods|
    US8391989B2|2002-12-18|2013-03-05|Cardiac Pacemakers, Inc.|Advanced patient management for defining, identifying and using predetermined health-related events|
    US7972275B2|2002-12-30|2011-07-05|Cardiac Pacemakers, Inc.|Method and apparatus for monitoring of diastolic hemodynamics|
    US8951205B2|2002-12-30|2015-02-10|Cardiac Pacemakers, Inc.|Method and apparatus for detecting atrial filling pressure|
    EP1615546A4|2003-04-23|2010-10-06|Medscansonics Inc|Apparatus and method for non-invasive diagnosing of coronary artery disease|
    US7186220B2|2003-07-02|2007-03-06|Cardiac Pacemakers, Inc.|Implantable devices and methods using frequency-domain analysis of thoracic signal|
    US7200440B2|2003-07-02|2007-04-03|Cardiac Pacemakers, Inc.|Cardiac cycle synchronized sampling of impedance signal|
    US7559894B2|2003-09-18|2009-07-14|New Paradigm Concepts, LLC|Multiparameter whole blood monitor and method|
    US20060287590A1|2003-09-18|2006-12-21|Mceowen Edwin L|Noninvasive vital sign measurement device|
    US7248923B2|2003-11-06|2007-07-24|Cardiac Pacemakers, Inc.|Dual-use sensor for rate responsive pacing and heart sound monitoring|
    US7115096B2|2003-12-24|2006-10-03|Cardiac Pacemakers, Inc.|Third heart sound activity index for heart failure monitoring|
    US7431699B2|2003-12-24|2008-10-07|Cardiac Pacemakers, Inc.|Method and apparatus for third heart sound detection|
    EP1722686A4|2004-02-10|2009-07-22|Cardiovascular Resonances Llc|Methods, systems, and computer program products for analyzing cardiovascular sounds using eigen functions|
    US7209786B2|2004-06-10|2007-04-24|Cardiac Pacemakers, Inc.|Method and apparatus for optimization of cardiac resynchronization therapy using heart sounds|
    US7480528B2|2004-07-23|2009-01-20|Cardiac Pacemakers, Inc.|Method and apparatus for monitoring heart failure patients with cardiopulmonary comorbidities|
    US7559901B2|2004-07-28|2009-07-14|Cardiac Pacemakers, Inc.|Determining a patient's posture from mechanical vibrations of the heart|
    US7044922B1|2004-12-29|2006-05-16|Leon Michael Dondysh|Non-invasive diagnostic apparatus and method comprising a cerebral stethoscope for detecting cerebrovascular disease|
    US7662104B2|2005-01-18|2010-02-16|Cardiac Pacemakers, Inc.|Method for correction of posture dependence on heart sounds|
    US20070055151A1|2005-01-20|2007-03-08|Shertukde Hemchandra M|Apparatus and methods for acoustic diagnosis|
    KR100752333B1|2005-01-24|2007-08-28|주식회사 메디슨|Method for improving the quality of a three-dimensional ultrasound doppler image|
    US7520860B2|2005-04-13|2009-04-21|Marie G. Johnson|Detection of coronary artery disease using an electronic stethoscope|
    US7907997B2|2005-05-11|2011-03-15|Cardiac Pacemakers, Inc.|Enhancements to the detection of pulmonary edema when using transthoracic impedance|
    US7424321B2|2005-05-24|2008-09-09|Cardiac Pacemakers, Inc.|Systems and methods for multi-axis cardiac vibration measurements|
    US7922669B2|2005-06-08|2011-04-12|Cardiac Pacemakers, Inc.|Ischemia detection using a heart sound sensor|
    US7711164B2|2005-08-02|2010-05-04|Siemens Medical Solutiions Usa, Inc.|System and method for automatic segmentation of vessels in breast MR sequences|
    US8108034B2|2005-11-28|2012-01-31|Cardiac Pacemakers, Inc.|Systems and methods for valvular regurgitation detection|
    US7567836B2|2006-01-30|2009-07-28|Cardiac Pacemakers, Inc.|ECG signal power vector detection of ischemia or infarction|
    US8920343B2|2006-03-23|2014-12-30|Michael Edward Sabatino|Apparatus for acquiring and processing of physiological auditory signals|
    US7780606B2|2006-03-29|2010-08-24|Cardiac Pacemakers, Inc.|Hemodynamic stability assessment based on heart sounds|
    US8000780B2|2006-06-27|2011-08-16|Cardiac Pacemakers, Inc.|Detection of myocardial ischemia from the time sequence of implanted sensor measurements|
    US20080119749A1|2006-11-20|2008-05-22|Cardiac Pacemakers, Inc.|Respiration-synchronized heart sound trending|
    US8096954B2|2006-11-29|2012-01-17|Cardiac Pacemakers, Inc.|Adaptive sampling of heart sounds|
    US7736319B2|2007-01-19|2010-06-15|Cardiac Pacemakers, Inc.|Ischemia detection using heart sound timing|
    US7853327B2|2007-04-17|2010-12-14|Cardiac Pacemakers, Inc.|Heart sound tracking system and method|
    WO2011071989A2|2009-12-08|2011-06-16|Aum Cardiovascular, Llc|Systems and methods for detecting cardiovascular disease|
    EP2585227A1|2010-06-24|2013-05-01|CVR Global, Inc.|Sensor, sensor pad and sensor array for detecting infrasonic acoustic signals|
    US9226726B1|2014-11-25|2016-01-05|John L Semmlow|Method and system for detection of cardiac sounds|
    KR20180008914A|2015-06-15|2018-01-24|씨브이알 글로발, 인크.|Non-Invasive Method for Measuring Acoustic Frequency Generated by Eddy Current in the Carotid Artery|
    CA2989412A1|2015-06-15|2016-12-22|Cvr Global, Inc.|Yoke for sensing carotid stenosis|
    EP3701876A1|2019-02-27|2020-09-02|Koninklijke Philips N.V.|Acoustic sensing apparatus and method|
    法律状态:
    2002-10-24| STCF| Information on status: patent grant|Free format text: PATENTED CASE |
    2006-02-14| AS| Assignment|Owner name: HARRIS CORPORATION, FLORIDA Free format text: ASSIGNMENT OF PATENTS;ASSIGNOR:MEDACOUSTICS, INC.;REEL/FRAME:017251/0857 Effective date: 20051110 |
    2006-04-14| FPAY| Fee payment|Year of fee payment: 4 |
    2010-06-02| FPAY| Fee payment|Year of fee payment: 8 |
    2010-06-02| SULP| Surcharge for late payment|Year of fee payment: 7 |
    2011-08-29| AS| Assignment|Owner name: MCG INTERNATIONAL INC., CONNECTICUT Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:HARRIS CORPORATION;REEL/FRAME:026825/0176 Effective date: 20110601 |
    2014-06-20| REMI| Maintenance fee reminder mailed|
    优先权:
    申请号 | 申请日 | 专利标题
    US09/188,434|US6193668B1|1997-11-10|1998-11-09|Acoustic sensor array for non-invasive detection of coronary artery disease|
    US09/734,448|US6478746B2|1998-11-09|2000-12-11|Acoustic sensor array for non-invasive detection of coronary artery disease|US09/734,448| US6478746B2|1998-11-09|2000-12-11|Acoustic sensor array for non-invasive detection of coronary artery disease|
    US10/291,129| US6939308B2|1998-11-09|2002-11-08|Acoustic sensor array for non-invasive detection of coronary artery disease|
    [返回顶部]