TW202245693A - Myocardial ischemia detection device and myocardial ischemia detection method detect the position of myocardial ischemia of human body by calculating feature values during QT interval - Google Patents
Myocardial ischemia detection device and myocardial ischemia detection method detect the position of myocardial ischemia of human body by calculating feature values during QT interval Download PDFInfo
- Publication number
- TW202245693A TW202245693A TW110119295A TW110119295A TW202245693A TW 202245693 A TW202245693 A TW 202245693A TW 110119295 A TW110119295 A TW 110119295A TW 110119295 A TW110119295 A TW 110119295A TW 202245693 A TW202245693 A TW 202245693A
- Authority
- TW
- Taiwan
- Prior art keywords
- myocardial ischemia
- human body
- chest
- intervals
- points
- Prior art date
Links
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/316—Modalities, i.e. specific diagnostic methods
- A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/25—Bioelectric electrodes therefor
- A61B5/251—Means for maintaining electrode contact with the body
- A61B5/256—Wearable electrodes, e.g. having straps or bands
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/25—Bioelectric electrodes therefor
- A61B5/279—Bioelectric electrodes therefor specially adapted for particular uses
- A61B5/28—Bioelectric electrodes therefor specially adapted for particular uses for electrocardiography [ECG]
- A61B5/282—Holders for multiple electrodes
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/316—Modalities, i.e. specific diagnostic methods
- A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
- A61B5/346—Analysis of electrocardiograms
- A61B5/349—Detecting specific parameters of the electrocardiograph cycle
- A61B5/352—Detecting R peaks, e.g. for synchronising diagnostic apparatus; Estimating R-R interval
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/316—Modalities, i.e. specific diagnostic methods
- A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
- A61B5/346—Analysis of electrocardiograms
- A61B5/349—Detecting specific parameters of the electrocardiograph cycle
- A61B5/353—Detecting P-waves
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/316—Modalities, i.e. specific diagnostic methods
- A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
- A61B5/346—Analysis of electrocardiograms
- A61B5/349—Detecting specific parameters of the electrocardiograph cycle
- A61B5/355—Detecting T-waves
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/316—Modalities, i.e. specific diagnostic methods
- A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
- A61B5/346—Analysis of electrocardiograms
- A61B5/349—Detecting specific parameters of the electrocardiograph cycle
- A61B5/358—Detecting ST segments
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/316—Modalities, i.e. specific diagnostic methods
- A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
- A61B5/346—Analysis of electrocardiograms
- A61B5/349—Detecting specific parameters of the electrocardiograph cycle
- A61B5/36—Detecting PQ interval, PR interval or QT interval
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/316—Modalities, i.e. specific diagnostic methods
- A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
- A61B5/346—Analysis of electrocardiograms
- A61B5/349—Detecting specific parameters of the electrocardiograph cycle
- A61B5/366—Detecting abnormal QRS complex, e.g. widening
Landscapes
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Cardiology (AREA)
- Heart & Thoracic Surgery (AREA)
- Molecular Biology (AREA)
- Pathology (AREA)
- Engineering & Computer Science (AREA)
- Biomedical Technology (AREA)
- Physics & Mathematics (AREA)
- Medical Informatics (AREA)
- Biophysics (AREA)
- Surgery (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Measurement And Recording Of Electrical Phenomena And Electrical Characteristics Of The Living Body (AREA)
- Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)
- Medicines Containing Antibodies Or Antigens For Use As Internal Diagnostic Agents (AREA)
Abstract
Description
本發明是有關於一種心電訊號的分析,特別是指一種心肌缺血檢測裝置及心肌缺血檢測方法。The invention relates to an analysis of electrocardiographic signals, in particular to a myocardial ischemia detection device and a myocardial ischemia detection method.
維持心臟血液供給的三條冠狀動脈分別為冠狀動脈右支(RCA)、冠狀動脈左前下降支(LAD),及冠狀動脈左迴返支(LCX)。因應不同的動脈血管阻塞,所進行的醫療處置均有所不同。美國心臟學會律定心肌梗塞患者在到院後的90分鐘內應接受心導管治療,以減少病人心肌缺血的時間及死亡率,因此如何在最短的時間內評估是否有心肌缺血及心肌缺血位置是相當重要的 。The three coronary arteries that maintain blood supply to the heart are the right coronary artery (RCA), the left anterior descending coronary artery (LAD), and the left recurrent coronary artery (LCX). According to different arterial blockages, the medical treatments are different. The American Heart Association stipulates that patients with myocardial infarction should receive cardiac catheterization within 90 minutes after arriving at the hospital to reduce the time and mortality of myocardial ischemia. Therefore, how to evaluate whether there is myocardial ischemia and myocardial ischemia in the shortest time Location is quite important.
一般評估急性心肌缺血位置時,是透過十二導程心電圖進行評估。在評估時,醫療人員需要依據前胸導程(V1-V6)、下壁導程(II、III、aVF),及側壁/心尖導程(I、aVL、V5、V6)等不同組群導程的ST段的上升或下降波形變化情形綜合評估,由於在心肌缺血的早期往往ST段的變化並不明顯,因此在實務上要縮短評估時間實有一定的困難度。Generally, when evaluating the location of acute myocardial ischemia, a twelve-lead electrocardiogram is used for evaluation. During the evaluation, medical personnel need to base the lead of different groups such as anterior chest lead (V1-V6), inferior wall lead (II, III, aVF), and lateral wall/apical lead (I, aVL, V5, V6). In the early stage of myocardial ischemia, the change of ST segment is often not obvious, so it is difficult to shorten the evaluation time in practice.
此外,心電圖的ST段的波形變化很容易受到胸壁阻抗、噪訊與基線偏移的影響,因此也容易產生評估誤差。In addition, the waveform changes of the ST segment of the electrocardiogram are easily affected by chest wall impedance, noise, and baseline shift, and thus are prone to evaluation errors.
因此,本發明的目的,即在提供一種能克服至少一個先前技術缺點的的心肌缺血檢測裝置。Therefore, the object of the present invention is to provide a myocardial ischemia detection device that can overcome at least one of the disadvantages of the prior art.
本發明的另一目的,即在提供一種能克服至少一個先前技術缺點的的心肌缺血檢測方法。Another object of the present invention is to provide a method for detecting myocardial ischemia that can overcome at least one disadvantage of the prior art.
於是,本發明心肌缺血檢測裝置,適用於一人體。該心肌缺血檢測裝置包含一量測單元,及一處理單元。Therefore, the myocardial ischemia detection device of the present invention is applicable to a human body. The myocardial ischemia detection device includes a measurement unit and a processing unit.
該量測單元包括四個肢導電極,及數個胸前電極。該等肢導電極及該等胸前電極適用於取得該人體的數個心電訊號。至少部分的該等胸前電極的量測位置對應該人體的左胸口。The measurement unit includes four limb electrodes and several chest electrodes. The limb electrodes and the chest electrodes are suitable for obtaining several electrocardiographic signals of the human body. The measurement positions of at least part of the chest electrodes correspond to the left chest of the human body.
該處理單元訊號連接該量測單元並能接收該等心電訊號。該處理單元能擷取該等心電訊號的QT間期,並藉由該等QT間期計算數個分別對應於該人體左胸口的數個點位的特徵值,再依據該等特徵值中最低的至少一者所對應的心電訊號量測位置,以檢測出該人體的心肌缺血位置。The processing unit is connected to the measurement unit and can receive the ECG signals. The processing unit can extract the QT intervals of the ECG signals, and use the QT intervals to calculate several eigenvalues corresponding to several points on the left chest of the human body, and then according to the eigenvalues The ECG signal measurement position corresponding to at least one of the lowest ones is used to detect the myocardial ischemia position of the human body.
本發明心肌缺血檢測方法,包含一量測步驟、一擷取特徵步驟,及一第一分析步驟。The myocardial ischemia detection method of the present invention includes a measurement step, a feature extraction step, and a first analysis step.
該量測步驟是取得一人體的數個心電訊號。至少部分的該等心電訊號的量測位置對應該人體的左胸口。The measurement step is to obtain several ECG signals of a human body. The measuring positions of at least part of the ECG signals correspond to the left chest of the human body.
該擷取特徵步驟藉由一處理單元擷取每一心電訊號的QT間期,並依據該等QT間期計算數個分別對應該人體的左胸口的數個點位的特徵值。In the feature extraction step, a processing unit extracts the QT interval of each ECG signal, and calculates several feature values respectively corresponding to several points of the left chest of the human body according to the QT interval.
該第一分析步驟是比對該等特徵值中最低的至少一者所對應的點位對應於該人體的左胸口的位置,以檢測出心肌缺血位置。The first analyzing step is to compare the point corresponding to at least one of the lowest characteristic values to the position of the left chest of the human body, so as to detect the myocardial ischemia position.
本發明的功效在於:藉由以該等QT間期計算該等特徵值以檢測出該人體的心肌缺血位置,由於相對於現有以ST段的波形變化的分析方式,該等QT間期較不會受到胸壁阻抗、噪訊與基線偏移的影響,因此能避免產生評估誤差。The efficacy of the present invention lies in: by calculating the characteristic values with the QT intervals to detect the myocardial ischemia position of the human body, since the QT intervals are shorter than the existing analysis method based on the waveform change of the ST segment Unaffected by chest wall impedance, noise, and baseline offset, evaluation errors can be avoided.
參閱圖1至圖4,本發明心肌缺血檢測裝置的一實施例,適用於一人體1。該人體包括一對應左胸口的參考面100。該參考面100是由該人體1的一右胸骨緣11、一第一肋間對應於該右胸骨緣11高度的水平線12、一左腋下中線13,及一第八肋骨對應於該右胸骨緣11高度的水平線14所界定出。Referring to FIG. 1 to FIG. 4 , an embodiment of the myocardial ischemia detection device of the present invention is applicable to a
該心肌缺血檢測裝置包含一量測單元2、一處理單元3、一資料庫單元4、一輸入單元5、一輸出單元6,及一穿戴單元7。該處理單元3訊號連接該量測單元2、該處理單元3、資料庫單元4、該輸入單元5,及該輸出單元6。The myocardial ischemia detection device includes a
該輸入單元5能被輸入一操作指令、一模式選擇指令,及一輸出指令。The
該量測單元2包括四個肢導電極26,及數個適用於設置並佈設於該參考面100且彼此間隔設置的胸前電極21。該量測單元2能依據該操作指令,使該等肢導電極26及該等胸前電極21取得該人體1的數個心電訊號。至少部分的該等胸前電極21的量測位置對應該人體1的左胸口。每一心電訊號形成有P波、Q波、R波、S波與T波。The
其中,要特別說明的是,為了清楚揭露該等胸前電極21及該穿戴單元7對應於該人體1的設置位置,在圖3及後續的圖10、圖15與圖16中,該等胸前電極21是以假想線繪製,而圖2的該穿戴單元7則以虛線繪製。Among them, it should be particularly noted that, in order to clearly disclose the installation positions of the
該等胸前電極21的數量可以為16個以上,並且透過該等胸前電極21取得該人體1的該參考面100的相對應數量的心電訊號,且該等心電訊號對應量測位置佈設於該參考面100。The number of the
以該等胸前電極21的對應該人體1的橫向位置而言,該等胸前電極21中的至少2個胸前電極21對應該右胸骨緣11、至少3個胸前電極21對應該左胸骨緣111、至少3個胸前電極21對應介於該左胸骨緣111及一左鎖骨正中線112間之中線113、至少4個胸前電極21對應該左鎖骨正中線112、至少2個胸前電極21對應一左腋下前緣線114,並至少2個胸前電極21對應該左腋下中線13。In terms of the lateral positions of the
以該等胸前電極21的對應該人體1的縱向位置而言,該等胸前電極21中至少3個胸前電極21對應一第三肋間對應於該右胸骨緣11高度、至少5個胸前電極21對應一第四肋間對應於該右胸骨緣11高度、至少4個胸前電極21對應一第五肋間對應於該右胸骨緣11高度、至少1個胸前電極21對應一第六肋間對應於該右胸骨緣11高度、並對應介於該左胸骨緣111及該左鎖骨正中線間112之中線113的至少3個該等胸前電極21的高度是介於該第三肋間至該第六肋骨之間。In terms of the longitudinal positions of the
在本實施例中,該等胸前電極21的數量為16個,以該等胸前電極21的對應該人體1的橫向位置而言,該等胸前電極21中的2個胸前電極21對應該右胸骨緣11、3個胸前電極21對應該左胸骨緣111、3個胸前電極21對應介於該左胸骨緣111及該左鎖骨正中線112間之中線113、4個胸前電極21對應該左鎖骨正中線112、2個胸前電極21對應該左腋下前緣線114、2個胸前電極21對應該左腋下中線13;以該等胸前電極21的對應該人體1的縱向位置而言,該等胸前電極21中的3個胸前電極21對應該第三肋間對應於該右胸骨緣11高度、5個胸前電極21對應該第四肋間對應於該右胸骨緣11高度、4個胸前電極21對應該第五肋間對應於該右胸骨緣11高度、4個胸前電極21對應該第六肋間對應於該右胸骨緣11高度,並對應介於該左胸骨緣111及該左鎖骨正中線112間之中線113的3個該等胸前電極21分別對應於一第四肋骨、一第五肋骨及一第六肋骨的高度。In this embodiment, the number of the
在本實施例中,該量測單元2還包括一電連接該等胸前電極21的訊號緩衝器22、一電連接該訊號緩衝器22的訊號放大器23、一電連接該訊號放大器23的濾波器24,及一電連接該濾波器24的訊號轉換器25。該訊號緩衝器22能提供一足夠大的輸入抗阻以耦合該等心電訊號至該訊號放大器23,該訊號放大器23進一步放大該等心電訊號並輸入該濾波器24,該濾波器24能去除該等心電訊號的雜訊及電源訊號的干擾,而該訊號轉換器25則能將該心電訊號轉換為類比訊號,以供後續該處理單元3分析使用。In this embodiment, the
該資料庫單元4儲存一比對資訊41。該比對資訊41由右上至左下區分為三個比對區域411,該等比對區域411由右上至左下依序代表冠狀動脈左迴返支(LCX)、冠狀動脈左前下降支(LAD),及冠狀動脈右支(RCA)。The
該處理單元3訊號連接該量測單元2並能接收該等心電訊號。該處理單元3能擷取該等心電訊號的QT間期及RR間期,並藉由該等QT間期及該等RR間期計算數個分別對應於該人體1的左胸口該參考面100的數個點位的特徵值。該等特徵值為依據該等心電訊號計算對應該等點位的QTc間期。The
該等特徵值的計算方式是藉由該等QT間期與該等RR間期計算該等心電訊號的QTc間期,再視該等胸前電極21的數量及需求決定是否以二維的內插計算擴充計算更多點位的QTc間期,並以該等心電訊號計算出的QTc間期,及擴充計算出的QTc間期分別作為該等特徵值。The calculation method of these characteristic values is to calculate the QTc interval of the ECG signal by the QT interval and the RR interval, and then decide whether to use two-dimensional The interpolation calculation expands and calculates the QTc interval of more points, and uses the QTc interval calculated from the ECG signals and the QTc interval calculated by the expansion as the feature values respectively.
在本實施例中,該處理單元3擷取上述16個心電訊號的QT間期及RR間期,並藉由該等QT間期及該等RR間期分別計算16個QTc間期,接著透過二維的內插計算擴充為24個點位的QTc間期。其中,以該等QT間期及該等RR間期計算該等心電訊號的QTc間期的計算公式為:In this embodiment, the
其中,QTc為QTc間期,QT為QT間期(單位為毫秒),RR為RR間期(單位為秒)。Among them, QTc is the QTc interval, QT is the QT interval (in milliseconds), and RR is the RR interval (in seconds).
該處理單元3能依據該等特徵值中最低的至少一者所對應的心電訊號量測位置,以檢測出該人體1的心肌缺血位置,並能依據該等特徵值的高低分布狀態與該比對資訊41進行比對,以檢測出心肌缺血的範圍,且能依據該輸出指令將心肌缺血位置及心肌缺血的範圍的檢測結果輸出於該輸出單元6。The
該處理單元3還能依據該輸出指令,將該等特徵值顯示於該輸出單元6,並且還能以不同的色階將該等特徵值的數值差異與對應的分佈位置成像於該輸出單元6。其中,該處理單元3以不同色階將該等特徵值的數值差異與對應的分佈位置成像的方式,是類似於製圖學中所使用的分層設色法及地貌彩色暈渲法,也就是以不同的顏色或陰影表示不同的特徵值高低,以供一使用者簡易且便捷地瞭解該等特徵值的高低分佈情形,以利於評估心肌缺血位置及心肌缺血的範圍。The
此外,該處理單元3能依據該輸入單元5的該模式選擇指令,以一第一評估模式及一第二評估模式的至少其中一者計算並評估整體心肌缺血的嚴重程度,且依據該輸出指令將該評估結果輸出於該輸出單元6。In addition, the
該第一種評估模式是以一評估參數演算法計算一離散參數(
),並依據該離散參數評估該人體1的整體心肌缺血的嚴重程度。該評估參數演算法為:
The first evaluation mode is an evaluation parameter algorithm to calculate a discrete parameter ( ), and evaluate the severity of the overall myocardial ischemia of the
其中,
為該離散參數,S為該等點位的總數量,
為一特定點位的QTc間期,n為最接近該特定點位對應於該人體1位置的點位數目,
為其中一個最接近該特定點位對應於該人體1位置的點位的QTc間期。當
值越大,代表該人體1的整體心肌缺血的嚴重程度越嚴重。
in, is the discrete parameter, S is the total number of such points, is the QTc interval of a specific point, n is the number of points closest to the specific point corresponding to the position of the
該第二種評估模式為計算該等點位的該等QTc間期的最大值與最小值的差距值QTcD,並且依據該等QTc間期的最大值與最小值的差距值QTcD評估該人體1的整體心肌缺血的嚴重程度。當該等QTc間期的最大值與最小值的差距值QTcD越大,代表該人體1的整體心肌缺血的嚴重程度越嚴重。The second evaluation mode is to calculate the difference QTcD between the maximum value and the minimum value of the QTc interval at the points, and evaluate the human body according to the difference QTcD between the maximum value and the minimum value of the
該穿戴單元7能供該人體1穿戴,且該量測單元2的該等胸前電極21設置於該穿戴單元7。該人體1穿戴該穿戴單元7時,該等胸前電極21分別對應於該參考面100的預定位置。在本實施例中,該穿戴單元7是一背心式的外衣。The wearing
參閱圖1至圖4,實際應用時,可搭配一種心肌缺血檢測方法進行檢測,該心肌缺血檢測方法包含下列步驟S1至步驟S5。Referring to FIG. 1 to FIG. 4 , in actual application, it can be detected with a myocardial ischemia detection method, which includes the following steps S1 to S5.
步驟S1、輸入指令步驟:於該輸入單元5輸入該操作指令、該模式選擇指令,及該輸出指令。Step S1 , input command step: input the operation command, the mode selection command, and the output command into the
步驟S2、量測步驟:取得該人體1的該等心電訊號。Step S2, measuring step: obtaining the ECG signals of the
其中,至少部分的該等心電訊號的量測位置對應該人體1的左胸口。Wherein, at least part of the measurement positions of the ECG signals correspond to the left chest of the
其中,該量測步驟是取得該人體1的一參考面100的該等心電訊號。該參考面100是由該人體1的該右胸骨緣11、該第一肋間對應於該右胸骨緣11高度的水平線12、該左腋下中線13,及該第八肋骨對應於該右胸骨緣11高度的水平線14所界定出。Wherein, the measuring step is to obtain the ECG signals of a
步驟S3、擷取特徵步驟:藉由該處理單元3擷取每一心電訊號的QT間期及RR間期,並依據該等QT間期與該等RR間期計算數個分別對應該人體1的左胸口的數個點位的該等特徵值。Step S3, feature extraction step: the
在本實施例中,擷取特徵步驟所計算的該等特徵值為依據該等心電訊號計算對應該等點位的QTc間期。In this embodiment, the feature values calculated in the feature extraction step are calculated based on the ECG signals to calculate the QTc interval corresponding to the corresponding points.
步驟S4、第一分析步驟:比對該等特徵值中最低的至少一者所對應的點位對應於該人體的左胸口的位置,以檢測出心肌缺血位置,並將該等特徵值的高低分布狀態與該比對資訊41進行比對,以檢測出心肌缺血的範圍。Step S4, the first analysis step: comparing the point corresponding to at least one of the lowest eigenvalues to the position of the left chest of the human body to detect the location of myocardial ischemia, and comparing the points corresponding to the lowest one of the eigenvalues The high-low distribution state is compared with the comparison information 41 to detect the range of myocardial ischemia.
其中,該第一分析步驟可以由該處理單元3自動處理以檢測該人體1的心肌缺血位置及心肌缺血的範圍,再依據該輸出指令將檢測結果輸出於該輸出單元6。該第一分析步驟也可以由該處理單元3先依據該輸出指令,將該等特徵值依照對應於該人體1的左胸口的位置並以不同的色階代表該等特徵值的高低而於該輸出單元6產生對應的影像後,再由該使用者目視評估該等特徵值的高低分佈情形,並由該使用者透過比對該影像與該比對資訊41檢測出心肌缺血位置及心肌缺血的範圍。Wherein, the first analysis step can be automatically processed by the
步驟S5、第二分析步驟:該處理單元3依據該輸入單元5的該模式選擇指令,以該第一評估模式及該第二評估模式的至少其中一者計算並評估該人體1的整體心肌缺血的嚴重程度,且依據該輸出指令將該評估結果輸出於該輸出單元6。Step S5, second analysis step: the
藉由上述步驟S1至步驟S5,就能評估出該人體1的心肌缺血位置、心肌缺血範圍,及整體心肌缺血的嚴重程度。Through the above steps S1 to S5, the location of myocardial ischemia, the extent of myocardial ischemia, and the severity of the overall myocardial ischemia of the
參閱下表1及圖4、圖6,舉例而言,表1是一張QTc間期分佈表,其是利用該心肌缺血檢測裝置及該心肌缺血檢測方法,以16個該等胸前電極21對一冠狀動脈左迴返支(LCX)狹窄的病患的左胸前取得的16個心電訊號,經過計算該等心電訊號的QTc間期後,再透過二維的內插計算求得共計24個點位的QTc間期分佈表(包含前述16個由心電訊號計算得的QTc間期),表中的數值代表每一點位的QTc間期,並且依據所對應的心電訊號量測位置及二維內插對應的點位位置進行排列,而圖6則是以不同的色階代表該等特徵值的高低而輸出於該輸出單元6的影像。Referring to the following Table 1 and Fig. 4 and Fig. 6, for example, Table 1 is a QTc interval distribution table, which uses the myocardial ischemia detection device and the myocardial ischemia detection method to take 16
由表1及圖6可以得知該等QTc間期中最低的一者是對應於圖中的右上方,再配合參閱圖4的該比對資訊41即可評估出該病患的心肌缺血位置是位於冠狀動脈左迴返支(LCX)的供血區域。It can be seen from Table 1 and Figure 6 that the lowest one of the QTc intervals corresponds to the upper right in the figure, and then refer to the comparison information 41 in Figure 4 to evaluate the myocardial ischemia location of the patient It is located in the blood supply area of the left recurrent coronary artery (LCX).
要特別說明的是,上述24個點位的QTc間期也可以透過17、18或者其他數量的該等胸前電極21取得心電訊號後,再透過二維內插的計算程序取得24個點位的QTc間期,或者也可以直接透過24個該等胸前電極21所取得的心電訊號進行計算,而不需要經過二維的內插的計算程序,而且該QTc間期分佈表的點位也可以是其他數量,例如可以透過24個該等胸前電極21所取得心電訊號後,以二維的內插計算而擴充為36個點位的QTc間期分佈表。It should be noted that the QTc interval of the above-mentioned 24 points can also obtain the ECG signal through 17, 18 or other numbers of the
表1冠狀動脈左迴返支(LCX)狹窄病患的QTc間期範例
參閱下表2及圖4、圖7,表2是利用該心肌缺血檢測裝置及該心肌缺血檢測方法,以16個該等胸前電極21對一冠狀動脈右支(RCA)狹窄的病患的左胸前取得的16個心電訊號,經過計算該等心電訊號的QTc間期後,再透過二維的內插計算求得共計24個點位的QTc間期分佈表(包含前述16個由心電訊號計算得的QTc間期),而圖7則是顯示於該輸出單元6的對應的影像。Refer to Table 2, Figure 4, and Figure 7 below. Table 2 uses the myocardial ischemia detection device and the myocardial ischemia detection method to detect a right coronary artery (RCA) stenosis with 16 such
由表2及圖7可以得知該等QTc間期中最低的一者是對應於圖中的左側,再配合參閱圖4的該比對資訊41即可評估出該病患的心肌缺血位置是位於冠狀動脈右支(RCA)的供血區域。From Table 2 and Figure 7, it can be known that the lowest one of the QTc intervals corresponds to the left side of the figure, and with reference to the comparison information 41 in Figure 4, it can be estimated that the patient's myocardial ischemia location is Located in the territory supplied by the right coronary artery (RCA).
表2冠狀動脈右支(RCA)狹窄病患的QTc間期範例
參閱下表3及圖4、圖8,表3是利用該心肌缺血檢測裝置及該心肌缺血檢測方法,以16個該等胸前電極21對一冠狀動脈左前下降支(LAD)狹窄的病患的左胸前取得的16個心電訊號,經過計算該等心電訊號的QTc間期後,再透過二維的內插計算求得共計24個點位的QTc間期分佈表(包含前述16個由心電訊號計算得的QTc間期),而圖8則是顯示於該輸出單元6的對應的影像。Refer to Table 3, Figure 4, and Figure 8 below. Table 3 uses the myocardial ischemia detection device and the myocardial ischemia detection method to measure the stenosis of a left anterior descending coronary artery (LAD) with 16
由表3及圖8可以得知該等QTc間期中最低的一者是對應於圖中的中間偏上方的區域,再配合參閱圖4的該比對資訊41即可評估出該病患的心肌缺血位置是位於LAD冠狀動脈左前下降支(LAD)的供血區域。It can be known from Table 3 and Figure 8 that the lowest one of the QTc intervals corresponds to the upper middle area in the figure, and then refer to the comparison information 41 in Figure 4 to evaluate the patient's myocardial The ischemic site is located in the blood supply area of the left anterior descending coronary artery (LAD).
表3冠狀動脈左前下降支(LAD)狹窄病患的QTc間期範例
參閱下表4及圖4、圖9,表4是利用該心肌缺血檢測裝置及該心肌缺血檢測方法,以16個該等胸前電極21對一三條冠狀動脈均狹窄(3VD)的病患的左胸前取得的16個心電訊號,經過計算該等心電訊號的QTc間期後,再透過二維的內插計算求得共計24個點位的QTc間期分佈表(包含前述16個由心電訊號計算得的QTc間期),而圖9則是顯示於該輸出單元6的對應的影像。Refer to the following Table 4 and Fig. 4 and Fig. 9, Table 4 is the use of the myocardial ischemia detection device and the myocardial ischemia detection method, with 16
由表4及圖9可以得知該等QTc間期中最低的一者是對應於圖中的左上方的區域,但依據圖9顯示QTc間期偏低的區域包括圖中的左上方及圖中的右上方,再配合參閱圖4的該比對資訊41,QTc間期偏低的區域涵蓋了該比對資訊41的三個比對區域411,因此可評估出該病患的心肌缺血範圍涵蓋三條冠狀動脈(3VD)的供血區域。It can be known from Table 4 and Figure 9 that the lowest one of the QTc intervals corresponds to the upper left area in the figure, but according to Figure 9, the area with a low QTc interval includes the upper left and the upper left area in the figure. In conjunction with the comparison information 41 in Figure 4, the area with a low QTc interval covers the three comparison areas 411 of the comparison information 41, so the extent of myocardial ischemia in this patient can be evaluated Covers the territory supplied by the three coronary arteries (3VD).
表4三條冠狀動脈均狹窄(3VD)病患的QTc間期範例
上述的表1至表4及圖6至圖9是以16個心電訊號進行心肌缺血檢測,但不限於此,該心肌缺血檢測裝置及該心肌缺血檢測方法也可以應用在不同數量的該等胸前電極21與不同數量的心電訊號,而且也可以用不同點位數量的QTc間期分佈表進行評估,例如以下的表5至表8及圖11至圖14是依序分別對上述表1至表4及上述圖6至圖9的病患以圖10所示的24個該等胸前電極21取得24個心電訊號,經過計算該等心電訊號的QTc間期後,再透過二維的內插計算求得共計36個點位的QTc間期分佈表(包含前述24個由心電訊號計算得的QTc間期)及顯示於該輸出單元6的對應的影像。The above-mentioned Tables 1 to 4 and Figures 6 to 9 detect myocardial ischemia with 16 ECG signals, but are not limited thereto. The myocardial ischemia detection device and the myocardial ischemia detection method can also be applied to different numbers of The
其中,以該等胸前電極21的對應該人體1的橫向位置而言,該等胸前電極21中的4個胸前電極21對應該右胸骨緣11、5個胸前電極21對應該左胸骨緣111、4個胸前電極21對應介於該左胸骨緣111及該左鎖骨正中線112間之中線113、4個胸前電極21對應該左鎖骨正中線112、4個胸前電極21對應該左腋下前緣線114、3個胸前電極21對應該左腋下中線13;以該等胸前電極21的對應該人體1的縱向位置而言,該等胸前電極21中的2個胸前電極21對應該第一肋間對應於該右胸骨緣11高度、3個胸前電極21對應一第二肋間對應於該右胸骨緣11高度、5個胸前電極21對應該第三肋間對應於該右胸骨緣11高度、6個胸前電極21對應該第四肋間對應於該右胸骨緣11高度、5個胸前電極21對應該第五肋間對應於該右胸骨緣11高度、3個胸前電極21對應該第六肋間對應於該右胸骨緣11高度。Wherein, in terms of the lateral positions of the
經比對上述表1至表4及上述圖6至圖9,與以下的表5至表8及圖11至圖14,可以發現對於相同的患者無論以16個心電訊號(見圖3;24個點位的QTc間期分佈表)或24個心電訊號(見圖10;36個點位的QTc間期分佈表)進行計算與分析,在分析心肌缺血位置與範圍時都能夠得到一致的分析結果,而且在部分的案例中,以24個心電訊號(36個點位的QTc間期分佈表)進行分析還能更加明顯地看出QTc間期偏低的區域(例如:圖14相較於圖9較能明顯看出QTc間期偏低的區域涵蓋該比對資訊41的三個比對區域411)。在以24個心電訊號(再透過二維的內插計算求得共計36個點位的QTc間期分佈表)進行分析的本實施例中,若 大於9.4毫秒(msec)或 QTcD大於66毫秒(msec)時,即代表有顯著的心肌缺血,可能需要進行較積極的治療。 After comparing the above Tables 1 to 4 and the above Figures 6 to 9, and the following Tables 5 to 8 and Figures 11 to 14, it can be found that for the same patient no matter whether the 16 ECG signals (see Figure 3; QTc interval distribution table of 24 points) or 24 ECG signals (see Figure 10; QTc interval distribution table of 36 points) can be calculated and analyzed, and can be obtained when analyzing the location and range of myocardial ischemia Consistent analysis results, and in some cases, the analysis of 24 ECG signals (QTc interval distribution table with 36 points) can more clearly show the area with low QTc interval (for example: Fig. 14 Compared with Fig. 9, it can be clearly seen that the area with low QTc interval covers the three comparison areas 411 of the comparison information 41). In the present embodiment where 24 ECG signals are analyzed (the QTc interval distribution table with a total of 36 points is obtained through two-dimensional interpolation calculation), if When it is greater than 9.4 milliseconds (msec) or QTcD is greater than 66 milliseconds (msec), it means that there is significant myocardial ischemia, and more aggressive treatment may be required.
表5冠狀動脈左迴返支(LCX)狹窄病患的QTc間期範例
表6冠狀動脈右支(RCA)狹窄病患的QTc間期範例
表7冠狀動脈左前下降支(LAD)狹窄病患的QTc間期範例
表8三條冠狀動脈均狹窄(3VD)病患的QTc間期範例
而在評估整體心肌缺血的嚴重程度時,無論是採用該第一種評估模式或該第二評估模式,其主要原理都是計算該等QTc間期的離散程度,當
值或該等QTc間期的最大值與最小值的差距值QTcD越大,代表該人體1的整體心肌缺血的嚴重程度越嚴重。
When assessing the severity of the overall myocardial ischemia, whether the first evaluation mode or the second evaluation mode is used, the main principle is to calculate the dispersion of the QTc intervals, when The larger the QTcD value or the difference QTcD between the maximum value and the minimum value of the QTc interval, the more severe the overall myocardial ischemia of the
舉例而言,以16個心電訊號的分析結果為例,表1的 值為17.96,該等QTc間期的最大值與最小值的差距值QTcD為93,而表3的 值為7.58,而該等QTc間期的最大值與最小值的差距值QTcD為41,因此無論是採用該第一種評估模式或該第二評估模式,都能推估出表1的病患整體心肌缺血的嚴重程度都較表3的病患嚴重,而且表1的 值與QTcD都顯示出表1的患者可能需要進行較積極的治療,因此具有一致的評估結果。 For example, taking the analysis results of 16 ECG signals as an example, Table 1 value is 17.96, and the gap value QTcD between the maximum value and minimum value of these QTc intervals is 93, while those in Table 3 is 7.58, and the difference QTcD between the maximum value and the minimum value of these QTc intervals is 41, so whether the first evaluation mode or the second evaluation mode is used, the patients in Table 1 can be estimated The severity of overall myocardial ischemia is more serious than that of the patients in Table 3, and the patients in Table 1 Both values and QTcD show that the patients in Table 1 may need more aggressive treatment, so they have consistent assessment results.
另外,再以24個心電訊號的分析結果為例,以分別與該表1及表3相同患者的表5及表7而言,表5的 值為13.35,該等QTc間期的最大值與最小值的差距值QTcD為93,而表7的 值為9.11,該等QTc間期的最大值與最小值的差距值QTcD為79,因此同樣能推估出表5的病患(即表1的病患)整體心肌缺血的嚴重程度較表7的病患(即表3的病患)嚴重,也就是說無論以16個心電訊號或是24個心電訊號進行分析都能達到一致的分析結果。 In addition, taking the analysis results of 24 ECG signals as an example, taking Table 5 and Table 7 of the same patient as Table 1 and Table 3 respectively, Table 5 The value is 13.35, and the gap value QTcD between the maximum value and the minimum value of these QTc intervals is 93, while the values in Table 7 value is 9.11, and the gap value QTcD between the maximum value and minimum value of these QTc intervals is 79, so it can also be estimated that the severity of the overall myocardial ischemia in the patients in Table 5 (i.e. the patients in Table 1) is higher than that in Table 1. The patients in 7 (namely the patients in Table 3) are serious, that is to say, whether the analysis is performed with 16 ECG signals or 24 ECG signals, the same analysis results can be achieved.
除此之外,該等胸前電極21的排列方式也可以不限於圖3及圖10的排列方式,以圖15為例,圖15為另一種24個胸前電極21的排列方式,以該等胸前電極21的對應該人體1的橫向位置而言,該等胸前電極21中的3個胸前電極21對應該右胸骨緣11、5個胸前電極21對應該左胸骨緣111、5個胸前電極21對應介於該左胸骨緣111及該左鎖骨正中線112間之中線113、4個胸前電極21對應該左鎖骨正中線112、4個胸前電極21對應該左腋下前緣線114、3個胸前電極21對應該左腋下中線13;以該等胸前電極21的對應該人體1的縱向位置而言,該等胸前電極21中的1個胸前電極21對應一第二肋間對應於該右胸骨緣11高度、4個胸前電極21對應該第三肋間對應於該右胸骨緣11高度、5個胸前電極21對應該第四肋間對應於該右胸骨緣11高度、5個胸前電極21對應該第五肋間對應於該右胸骨緣11高度、4個胸前電極21對應該第六肋間對應於該右胸骨緣11高度,並對應介於該左胸骨緣111及該左鎖骨正中線112間之中線113的5個該等胸前電極21分別對應於一第三肋骨、該第四肋骨、該第五肋骨、該第六肋骨及一第七肋骨的高度。In addition, the arrangement of the
經過實測與分析,依據圖15所揭示的該等胸前電極21的排列方式,在分析心肌缺血位置與範圍,以及病患整體心肌缺血的嚴重程度時能夠得到與以圖3及圖10的胸前電極21的排列方式一致的分析結果。After actual measurement and analysis, according to the arrangement of the
另外,參閱圖16,該等胸前電極21的數量也可以為36個,以該等胸前電極21的對應該人體1的橫向位置而言,該等胸前電極21中的7個胸前電極21對應該右胸骨緣11、7個胸前電極21對應該左胸骨緣111、7個胸前電極21對應介於該左胸骨緣111及該左鎖骨正中線112間之中線113、6個胸前電極21對應該左鎖骨正中線112、5個胸前電極21對應該左腋下前緣線114、4個胸前電極21對應該左腋下中線13;以該等胸前電極21的對應該人體1的縱向位置而言,該等胸前電極21中的2個胸前電極21對應該第一肋間對應於該右胸骨緣11高度,3個胸前電極21對應該第二肋間對應於該右胸骨緣11高度、4個胸前電極21對應該第三肋間對應於該右胸骨緣11高度、5個胸前電極21對應該第四肋間對應於該右胸骨緣11高度、5個胸前電極21對應該第五肋間對應於該右胸骨緣11高度、5個胸前電極21對應該第六肋間對應於該右胸骨緣11高度、5個胸前電極21對應一第七肋間對應於該右胸骨緣11高度,並對應介於該左胸骨緣111及該左鎖骨正中線112間之中線113的7個該等胸前電極21分別對應於一第二肋骨、該第三肋骨、該第四肋骨、該第五肋骨、該第六肋骨、該第七肋骨及該第八肋骨的高度。In addition, referring to FIG. 16 , the number of the
經過實測與分析,依據圖16所揭示的該等胸前電極21的排列方式,在分析心肌缺血位置與範圍,以及病患整體心肌缺血的嚴重程度時也能夠得到與以圖3、圖10及圖15的胸前電極21的排列方式一致的分析結果。After actual measurement and analysis, according to the arrangement of the
根據上述的說明,本發明心肌缺血檢測裝置及心肌缺血檢測方法的優點包含:According to the above description, the advantages of the myocardial ischemia detection device and the myocardial ischemia detection method of the present invention include:
一、本發明是以該等QT間期與該等RR間期計算該等特徵值以檢測出該人體1的心肌缺血位置,相對於現有以ST段的波形變化的分析方式,該等QT間期與該等RR間期較不會受到胸壁阻抗、噪訊與基線偏移的影響,因此能避免產生評估誤差。1. The present invention calculates the eigenvalues of the QT intervals and the RR intervals to detect the myocardial ischemia position of the
二、本發明是利用該等特徵值中最低的至少一者所對應的心電訊號量測位置,檢測出心肌缺血位置,相對於現有以同組群的多數導程之ST段的上升或下降波形變化作為評估依據的方式,本發明的檢測方式相對容易而能有效提高其靈敏度。2. The present invention uses the ECG signal measurement position corresponding to at least one of the lowest eigenvalues to detect the position of myocardial ischemia. The falling waveform change is used as the evaluation basis, and the detection method of the present invention is relatively easy and can effectively improve its sensitivity.
三、以不同的色階將該等特徵值的數值差異與對應的分佈位置成像於該輸出單元6,使該使用者能簡易且便捷地瞭解該等特徵值的高低分佈情形,以利於評估心肌缺血位置及心肌缺血的範圍,能有效縮短評估時間。3. Image the numerical differences and corresponding distribution positions of these characteristic values on the
四、以單一的指標(即 值或該等QTc間期的最大值與最小值的差距值QTcD)評估整體心肌缺血的嚴重程度,十分地簡易。 Fourth, with a single indicator (i.e. Value or the difference between the maximum value and the minimum value of the QTc interval (QTcD) evaluates the severity of the overall myocardial ischemia, which is very simple.
五、藉由設置至少16個該等胸前電極21,透過該等胸前電極21佈設於該參考面100的特殊佈設位置,並藉由該處理單元3依據該等心電訊號所計算的該等特徵值,能完整提供該參考面100的心電訊號的特徵,因此即使是應用於未經催迫的人體1也能夠推估該人體1慢性與急性心肌缺血的位置與範圍,而且由於該等胸前電極21的數量僅至少16個,所以不需要增加太多的製造成本且使用上也十分便利。5. By arranging at least 16 of the
六、由於該等胸前電極21是佈設於該參考面100,因此能藉由二維的內插計算,將16個該等胸前電極21所量測的心電訊號所計算而得的特徵值,擴充至24個點位的特徵值,相較於傳統的十二導程心電圖能提高判斷的精確度,而相較於現有以超過一百個電極取得心電圖的方式則能減少該等胸前電極21的數量而降低成本並簡化將該等電極黏貼至該人體1時的定位步驟。6. Since the
七、藉由設置該穿戴單元7,當該人體1穿戴該穿戴單元7時,該等胸前電極21分別對應於該參考面100的預定位置,因此能簡化將該等胸前電極21設置該人體1時的定位與操作步驟,能加快作業流程並確保該等胸前電極21放置位置的正確性。7. By setting the wearing
另外,要特別說明的是,在本實施例中,每一特徵值為各自的心電訊號的QTc間期,然而,在其他的實施態樣中,每一特徵值也可以為各自的心電訊號的QT間期(也就是未以RR間期進行校正,因此不需要擷取每一心電訊號的RR間期),依據上述的檢測步驟也能夠達到相同的功效。In addition, it should be noted that in this embodiment, each feature value is the QTc interval of the respective ECG signal, however, in other implementations, each feature value can also be the QTc interval of the respective ECG signal The same effect can also be achieved according to the above-mentioned detection steps for the QT interval of the signal (that is, the RR interval is not corrected, so there is no need to capture the RR interval of each ECG signal).
綜上所述,本發明心肌缺血檢測裝置及心肌缺血檢測方法,藉由以該等QT間期及該等RR間期計算該等特徵值以檢測出該人體1的心肌缺血位置,由於相對於現有以ST段的波形變化的分析方式,該等QT間期及該等RR間期較不會受到胸壁阻抗、噪訊與基線偏移的影響,因此能避免產生評估誤差,故確實能達成本發明的目的。In summary, the myocardial ischemia detection device and the myocardial ischemia detection method of the present invention detect the myocardial ischemia location of the
惟以上所述者,僅為本發明的實施例而已,當不能以此限定本發明實施的範圍,凡是依本發明申請專利範圍及專利說明書內容所作的簡單的等效變化與修飾,皆仍屬本發明專利涵蓋的範圍內。But the above-mentioned ones are only embodiments of the present invention, and should not limit the scope of the present invention. All simple equivalent changes and modifications made according to the patent scope of the present invention and the content of the patent specification are still within the scope of the present invention. Within the scope covered by the patent of the present invention.
1:人體 100:參考面 11:右胸骨緣 111:左胸骨緣 112:左鎖骨正中線 113:中線 114:左腋下前緣線 12:水平線 13:左腋下中線 14:水平線 2:量測單元 21:胸前電極 22:訊號緩衝器 23:訊號放大器 24:濾波器 25:訊號轉換器 26:肢導電極 3:處理單元 4:資料庫單元 41:比對資訊 411:比對區域 5:輸入單元 6:輸出單元 7:穿戴單元 1: human body 100: Reference surface 11: Right sternal border 111: Left sternal border 112: Midline of the left clavicle 113: center line 114: Front edge line of left armpit 12: Horizontal line 13: Left axillary midline 14: Horizontal line 2: Measuring unit 21: chest electrodes 22: Signal buffer 23: Signal amplifier 24: filter 25: Signal converter 26: limb conduction electrode 3: Processing unit 4: Database unit 41: Compare information 411: compare area 5: Input unit 6: Output unit 7: Wearing unit
本發明的其他的特徵及功效,將於參照圖式的實施方式中清楚地呈現,其中: 圖1是本發明心肌缺血檢測裝置的一實施例的一系統方塊圖; 圖2是一示意圖,說明該實施例所取得的數個心電訊號所對應的一人體的一參考面是由該人體的一右胸骨緣、一第一肋間對應於該右胸骨緣高度的水平線、一左腋下中線,及一第八肋骨對應於該右胸骨緣高度的水平線所界定出; 圖3是一示意圖,說明該實施例的16個胸前電極的設置位置; 圖4是該實施例的一資料庫單元所儲存的一比對資訊的示意圖; 圖5是一流程圖,說明利用該實施例的一種心肌缺血檢測方法的流程; 圖6是一示意圖,說明從一冠狀動脈左迴返支(LCX)狹窄的病患的左胸前取得16個心電訊號,且以二維的內插計算取得24個點位的特徵值後,以不同的色階代表該等心電訊號的特徵值的高低而輸出於一輸出單元的影像; 圖7是另一示意圖,說明從一冠狀動脈右支(RCA)狹窄的病患的左胸前取得16個心電訊號,且以二維的內插計算取得24個點位的特徵值後,以不同的色階代表該等心電訊號的特徵值的高低而輸出於該輸出單元的影像; 圖8是又另一示意圖,說明從一冠狀動脈左前下降支(LAD)狹窄的病患的左胸前取得16個心電訊號,且以二維的內插計算取得24個點位的特徵值後,以不同的色階代表該等心電訊號的特徵值的高低而輸出於該輸出單元的影像; 圖9是再另一示意圖,說明從一個三條冠狀動脈均狹窄(3VD)的病患的左胸前取得16個心電訊號,且以二維的內插計算取得24個點位的特徵值後,以不同的色階代表該等心電訊號的特徵值的高低而輸出於該輸出單元的影像; 圖10是一類似圖3的示意圖,說明該實施例的胸前電極數量改為24個的一種變化的設置方式; 圖11是一類似圖6的圖,說明從該冠狀動脈左迴返支(LCX)狹窄的病患的左胸前取得24個心電訊號,且以二維的內插計算取得36個點位的特徵值後,以不同的色階代表該等心電訊號的特徵值的高低而輸出於該輸出單元的影像; 圖12是一類似圖7的圖,說明從該冠狀動脈右支(RCA)狹窄的病患的左胸前取得24個心電訊號,且以二維的內插計算取得36個點位的特徵值後,以不同的色階代表該等心電訊號的特徵值的高低而輸出於該輸出單元的影像; 圖13是一類似圖8的圖,說明從該冠狀動脈左前下降支(LAD)狹窄的病患的左胸前取得24個心電訊號,且以二維的內插計算取得36個點位的特徵值後,以不同的色階代表該等心電訊號的特徵值的高低而輸出於該輸出單元的影像; 圖14是一類似圖9的圖,說明從該三條冠狀動脈均狹窄(3VD)的病患的左胸前取得24個心電訊號,且以二維的內插計算取得36個點位的特徵值後,以不同的色階代表該等心電訊號的特徵值的高低而輸出於該輸出單元的影像; 圖15是另一類似圖3的示意圖,說明該實施例的胸前電極數量改為24個的另一種變化的設置方式;及 圖16是又另一類似圖3的示意圖,說明該實施例的胸前電極數量改為36個的一種變化的設置方式。 Other features and effects of the present invention will be clearly presented in the implementation manner with reference to the drawings, wherein: Fig. 1 is a system block diagram of an embodiment of the myocardial ischemia detection device of the present invention; Fig. 2 is a schematic diagram illustrating that a reference plane of a human body corresponding to several ECG signals obtained in this embodiment is a horizontal line corresponding to the height of the right sternal border of the human body and a first intercostal space , a left axillary midline, and a horizontal line of the eighth rib corresponding to the height of the right sternal border; Fig. 3 is a schematic diagram illustrating the setting positions of 16 chest electrodes of this embodiment; FIG. 4 is a schematic diagram of a comparison information stored in a database unit of the embodiment; Fig. 5 is a flow chart illustrating the flow process of a method for detecting myocardial ischemia utilizing this embodiment; Fig. 6 is a schematic diagram illustrating that 16 ECG signals were obtained from the left chest of a patient with left recurrent coronary artery (LCX) stenosis, and after two-dimensional interpolation was used to obtain the eigenvalues of 24 points, An image output to an output unit representing the level of the characteristic values of the electrocardiographic signals with different color scales; Fig. 7 is another schematic diagram illustrating that 16 ECG signals were obtained from the left chest of a patient with right coronary artery (RCA) stenosis, and the eigenvalues of 24 points were obtained by two-dimensional interpolation. Representing the level of the characteristic values of the ECG signals with different color levels and outputting the image on the output unit; Fig. 8 is yet another schematic diagram illustrating that 16 ECG signals were obtained from the left chest of a patient with left anterior descending coronary artery (LAD) stenosis, and the eigenvalues of 24 points were obtained by two-dimensional interpolation calculation After that, use different color scales to represent the level of the characteristic values of the ECG signals and output the image on the output unit; Fig. 9 is another schematic diagram illustrating that 16 ECG signals were obtained from the left chest of a patient with three coronary artery stenosis (3VD), and the eigenvalues of 24 points were obtained by two-dimensional interpolation calculation , using different color scales to represent the level of the characteristic values of the ECG signals and output the image on the output unit; Fig. 10 is a schematic diagram similar to Fig. 3, illustrating a change in the arrangement of the number of electrodes in front of the chest of this embodiment to 24; Fig. 11 is a diagram similar to Fig. 6, illustrating that 24 ECG signals were obtained from the left chest of a patient with left recurrent coronary artery (LCX) stenosis, and 36 points were obtained by two-dimensional interpolation calculation After the eigenvalues, the images output on the output unit are represented by different color levels of the eigenvalues of the ECG signals; Fig. 12 is a diagram similar to Fig. 7, illustrating that 24 ECG signals were obtained from the left chest of the patient with right coronary artery (RCA) stenosis, and the characteristics of 36 points were obtained by two-dimensional interpolation calculation After the value, use different color scales to represent the level of the characteristic values of the ECG signals and output the image on the output unit; Fig. 13 is a diagram similar to Fig. 8, illustrating that 24 ECG signals were obtained from the left chest of a patient with left anterior descending coronary artery (LAD) stenosis, and 36 points were obtained by two-dimensional interpolation calculation After the eigenvalues, the images output on the output unit are represented by different color levels of the eigenvalues of the ECG signals; Fig. 14 is a diagram similar to Fig. 9, illustrating that 24 ECG signals were obtained from the left chest of the patient with three coronary artery stenosis (3VD), and the characteristics of 36 points were obtained by two-dimensional interpolation calculation After the value, use different color scales to represent the level of the characteristic values of the ECG signals and output the image on the output unit; Fig. 15 is another schematic diagram similar to Fig. 3, illustrating another variation setting mode in which the number of electrodes in front of the chest of this embodiment is changed to 24; and Fig. 16 is yet another schematic diagram similar to Fig. 3, illustrating a variation arrangement in which the number of chest electrodes in this embodiment is changed to 36.
2:量測單元 2: Measuring unit
21:胸前電極 21: chest electrodes
22:訊號緩衝器 22: Signal buffer
23:訊號放大器 23: Signal amplifier
24:濾波器 24: filter
25:訊號轉換器 25: Signal converter
26:肢導電極 26: limb conduction electrode
3:處理單元 3: Processing unit
4:資料庫單元 4: Database unit
5:輸入單元 5: Input unit
6:輸出單元 6: Output unit
Claims (14)
Priority Applications (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
TW110119295A TWI818264B (en) | 2021-05-27 | 2021-05-27 | Myocardial ischemia detection device and myocardial ischemia detection method |
PCT/US2022/029576 WO2022251003A1 (en) | 2021-05-27 | 2022-05-17 | Device and method for detecting myocardial ischemia |
CN202210543461.8A CN115399778A (en) | 2021-05-27 | 2022-05-19 | Myocardial ischemia detection device and myocardial ischemia detection method |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
TW110119295A TWI818264B (en) | 2021-05-27 | 2021-05-27 | Myocardial ischemia detection device and myocardial ischemia detection method |
Publications (2)
Publication Number | Publication Date |
---|---|
TW202245693A true TW202245693A (en) | 2022-12-01 |
TWI818264B TWI818264B (en) | 2023-10-11 |
Family
ID=84157785
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
TW110119295A TWI818264B (en) | 2021-05-27 | 2021-05-27 | Myocardial ischemia detection device and myocardial ischemia detection method |
Country Status (3)
Country | Link |
---|---|
CN (1) | CN115399778A (en) |
TW (1) | TWI818264B (en) |
WO (1) | WO2022251003A1 (en) |
Family Cites Families (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8014852B2 (en) * | 2004-10-25 | 2011-09-06 | Alfred Tai Chuan Kwek | System, method and apparatus for detecting a cardiac event |
WO2008003828A1 (en) * | 2006-07-05 | 2008-01-10 | Licentia Oy | Method and arrangement for detection of acute myocardial ischemia |
TWI446895B (en) * | 2011-12-20 | 2014-08-01 | Univ Nat Taiwan | System and method for evaluating cardiovascular performance in real time and characterized by conversion of surface potential into multi-channels |
US10433744B2 (en) * | 2015-04-09 | 2019-10-08 | Heartbeam, Inc. | Mobile three-lead cardiac monitoring device and method for automated diagnostics |
WO2016168181A1 (en) * | 2015-04-13 | 2016-10-20 | University Of Pittsburgh-Of The Commonwealth System Of Higher Education | Electrocardiographic identification of non-st elevation ischemic events |
CN111281373A (en) * | 2020-03-06 | 2020-06-16 | 何乐 | Method and device for quantitatively evaluating cardiac function based on electrocardiogram U wave and T wave |
-
2021
- 2021-05-27 TW TW110119295A patent/TWI818264B/en active
-
2022
- 2022-05-17 WO PCT/US2022/029576 patent/WO2022251003A1/en unknown
- 2022-05-19 CN CN202210543461.8A patent/CN115399778A/en active Pending
Also Published As
Publication number | Publication date |
---|---|
CN115399778A (en) | 2022-11-29 |
WO2022251003A1 (en) | 2022-12-01 |
TWI818264B (en) | 2023-10-11 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
Kania et al. | The effect of precordial lead displacement on ECG morphology | |
JP3242981B2 (en) | Method and apparatus for performing mapping analysis with a limited number of electrodes | |
EP2869759B1 (en) | Apparatus for detecting myocardial ischemia using analysis of high frequency components of an electrocardiogram | |
US7519416B2 (en) | Diagnostic method utilizing standard lead ECG signals | |
JP2007517633A (en) | Visual 3D representation of ECG data | |
Correa et al. | Novel set of vectorcardiographic parameters for the identification of ischemic patients | |
TWI667011B (en) | Heart rate detection method and heart rate detection device | |
JP2013517083A (en) | Identification of the causal coronary artery using anatomically oriented ECG data from the expanded lead set | |
JP2018528812A (en) | ECG lead signal high / low frequency signal quality evaluation | |
US10925516B2 (en) | Method and apparatus for estimating the aortic pulse transit time from time intervals measured between fiducial points of the ballistocardiogram | |
RU2598049C2 (en) | Automated identification of location of occlusion in infarct-related coronary artery | |
Benouar et al. | Systematic variability in ICG recordings results in ICG complex subtypes–steps towards the enhancement of ICG characterization | |
Sheppard et al. | Does modifying electrode placement of the 12 lead ECG matter in healthy subjects? | |
Correa et al. | Acute myocardial ischemia monitoring before and during angioplasty by a novel vectorcardiographic parameter set | |
Sejersten et al. | Detection of acute ischemia from the EASI-derived 12-lead electrocardiogram and from the 12-lead electrocardiogram acquired in clinical practice | |
US20130035604A1 (en) | Frequency Analysis of 12-Lead Cardiac Electrical Signals to Detect and Identify Cardiac Abnormalities | |
JP3137900B2 (en) | Apparatus for collecting and processing electrocardiogram signals | |
TWI802888B (en) | Cardiovascular Function Assessment System | |
Madias | Comparability of the standing and supine standard electrocardiograms and standing sitting and supine stress electrocardiograms | |
TW202245693A (en) | Myocardial ischemia detection device and myocardial ischemia detection method detect the position of myocardial ischemia of human body by calculating feature values during QT interval | |
Sakajiri et al. | Non-contact capacitive ballistocardiogram measurements using in-bed fabric-sheet electrode for blood pressure estimation | |
Abboud et al. | High-frequency QRS electrocardiogram for diagnosing and monitoring ischemic heart disease | |
Horáček et al. | Heart-surface potentials estimated from 12-lead electrocardiograms | |
KR101498581B1 (en) | Noninvasive atrial activity estimation system and method | |
Kania et al. | The effect of precordial lead displacement on P-wave morphology in body surface potential mapping |