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    • 专利摘要:
    An ECG device is described, comprising at least extremity leads and chest wall leads, which is also suitable for the derivation of the cardiac hemodynamic activity and function of the vessels or for the assessment of the fluid balance. This is achieved by the fact that the ECG electrodes are also designed as mechanical (9), acoustic (9a) and / or optical (7,8) and / or temperature sensors (35) and thereby the conventional ECG electrodes for other purposes, how the impedance measurement can be interconnected. Thus, by measuring the impedance and impedance change with the heartbeat in multiple segments, such as the thorax and the legs, along with intracellular and extracellular water measurements, cardiac output and body composition can be analyzed and delivered simultaneously with the routine ECG. Simultaneous measurement of cardiac sounds will also provide other important cardiac parameters (Figure 1).
    公开号:AT514017A1
    申请号:T135/2013
    申请日:2013-02-22
    公开日:2014-09-15
    发明作者:Falko Dr Skrabal
    申请人:Falko Dr Skrabal；
    IPC主号:
    专利说明:

    Introduction:
    There are numerous attempts with external customers to record the mechanical activity of the heart or the function of the vessels. One of the main reasons that these methods have not gained widespread acceptance is that they are not reimbursed by insurance carriers, and that doctors have little time to introduce additional non-funded research into their practice or hospital. In the present patent application, the drawbacks described above are offset by the fact that all the mentioned examinations are performed unnoticed by the executing person and unnoticed by the patient, simultaneously with a multichannel ECG. The patent document "Function and Spaces ECG", patent number AT 502921, has already set a first step in this direction.
    In the current application, the above application is further improved. The aim is, if possible, only the conventional ECG electrodes for numerous other goals such as for the multi-frequency impedance analysis, for the measurement of impedance and its sub-components, Resistance, Reactance and phase angle at different frequencies, or change the impedance with the heart activity (eg zO, dZ , dZ / dtmax) and further for mechanical, acoustic, optical and temperature measurements and to get along with as few additional electrodes. These additional transducers attached to the electrodes are used eg for the phonocardiogram, for the apexocardiogram, for the pulse wave transit time, for the pulse wave analysis, for the measurement of the oxygen saturation, the circulation times, such as PEP, LVET, A20, for the exact detection of the body compartments segmental impedance analysis, etc. used.
    The improvements are shown in the illustrations from Fig. 1 to Fig. 3.
    Figure 1 shows the derivatives of a conventional multichannel ECG consisting of limb electrodes, here e.g. as a double electrode -1-e.g. as double clamping electrodes -1-and on the other hand, as known, from the chest wall leads (V1-V6, possibly supplemented by V4r-V6r), wherein for the examination of the liquid balance the individual electrodes are cut by means of an electric or electronic switch -2-, e.g. a multiplexer -2- are interconnected or can be pronounced as a current input electrodes and / or Impedanzmesselektroden. The possible details of the arm electrodes -6-, proximal leg electrodes -4- and distal leg electrodes -5- of one half of the body are, as shown in detail in Fig. 1 left, as indicated by the arrows executed. Multiple electrical lines -31- of the electrodes are everywhere drawn for clarity's sake in the figures only as individual lines. By means of only one additional single or double neck electrode -3-, and by possible interconnection eg of V 4 to V 6 on the one hand and V 4r to V6r on the other hand, eg by the multiplexer -2-, the thorax can be measured by means of impedance measurement with respect to its 2/33 • ······ ·························································
    Impedance (zO) and the liquid content and * the% change, * the content of the skin with the heartbeat (eg dZ, dZ / dt dZ / dt max) are examined closely. As can be seen, the electrodes are not, for example, as in impedance measurements usual on the hands and feet, but attached to the distal forearm and distal lower leg, preferably where a considerable muscle mass is already available as an electrical conductor. This is approx. At the transition from the distal to the middle third of the forearm or lower leg. This has the advantage that it does not measure an unnecessary resistance of the hands and feet, which only contributes considerably to the total resistance of the segment but not to the compartments of interest of the body segment, namely fat, muscle, body water, extracellular water and intracellular water. Dual electrodes are particularly favorable for the four-point measurement of the impedance, with external feed electrodes and internal measuring electrodes. The accommodation on a common support -37-, -37a- facilitates handling, but is not essential. For this purpose, the power supply can be used, for example, between the neck electrode (neck or head or shoulders would also be suitable for the placement of the neck electrode) or the arm electrode (s) on the one hand and the proximal leg electrode (s) on the other hand. 4- and / or distal leg electrode / n -5- on the other hand, Through the measuring section between the double-neck electrode -3- one hand and eg V4 to V6, on the other hand, the electrical impedance or resistance and the reaction of the left thorax can be examined, by interconnecting eg V 4 r to V6 r, a measuring distance between the neck electrode -3- and the right thoracic half can be achieved.
    Thus, fluid collections in the left thoracic half and in the right thoracic half, e.g. by pleural effusion or fluid accumulation in the region of the lung, e.g. pneumonia, atelectasis or pulmonary edema or the change in impedance caused by the heartbeat. Also, each of the chest wall electrodes alone can also be used to measure the impedance between the neck electrode -3-one hand and one of the chest wall electrodes on the other hand, but then the reproducibility of the measurement is no longer so good. By additional interconnection, for example, from V 4 to V 6 on the one hand and V 4 r to V 6 r on the other hand in the multiplexer -2- then also the entire thorax with respect to its Fjüssigkeitshaushaltes or with respect to the change of impedance with the heartbeat (eg dZ, dZ / dt) can also be mathematically calculated without interconnecting the impedance of the entire thorax. Instead of V4 to V6, some or all of the electrodes VI to V3 could also be used and / or interconnected at least partially, and the impedance against the half electrode are measured, but these electrodes are not so ideal at the thorax. Alternatively, one or more of the leads V1-V3 could be used instead of the neck electrode to measure the impedance between 3/33 2 of these leads and the leads V4 through * V & However, the measurement distance is very short and the signal-to-noise ratio is not so favorable.
    As already mentioned, the introduction of the current for the impedance measurement advantageously takes place via one or both arm electrodes -6- and / or via the neck electrode -3-on the one hand and either via the one or both proximal leg electrodes -4-, and / or else via the one or two distal leg electrodes -5- (either suction, adhesive tape or clamp electrodes), on the left and right leg, on the other hand, where they are also used for the ECG leads. For the separate examination of the fluid or the fluid displacement in the two legs, the legs can be examined separately or together by connecting or disconnecting in the multiplexer -2- or here without interconnecting the total impedance of the left and right leg are calculated. The Armelektroden -6- are advantageous manner, for example, as a double electrode -1-, -3-, executed in the special case as Doppelklemmelektroden -1-. However, the electrically conductive electrodes -23- need not be seated on the same branch of the double clamping electrode -1- as shown in Fig. 1, but one of the two electrically conductive electrodes -23 could also be mounted on the opposite branch of the double clamping electrode-1 ,
    The additional measurement of the impedance change with the heartbeat in the extremities, arms or legs also allows a very good assessment of the power of the heartbeat, especially when used in conjunction with the change in impedance at the thorax. Also, the fluid balance of the patient can be excellently recognized with the above arrangement, since the body is replaced by the additional neck electrode -3-, the arm electrodes -6- and by the proximal leg electrodes -4- and the distal leg electrodes -5-, and the chest wall electrodes V3- V6 and / or V3r-V6r, in 6 sections, namely the two arms, the thorax and the abdomen or the two legs is divided. In each of these individual segments at several frequencies ev. Also a complete frequency sweep the AC resistance or resistance and reactance of the individual body sections analyzed and from the extracellular water (ECW), the whole body water, "total body water" (TBW), thus the intracellular Water (ICW) especially the ratio E.CW/TBW or ECW / TBW analyzed. The analysis of the segments at at least two frequencies, for example, on the one hand between 1 Hz and 10 Hz, for example 4 Hz and on the other hand at higher frequencies than 100 Hz, for example also 400 or 800 Hz or also by a frequency sweep, because so that ratio of extra- to intracellular fluid can be determined, which is independent of the dimensions of the examined segment. For the measurement of the ImpedanZähderuhg with the heartbeat (dZ, dZ / dtmax) is usually a frequency of about 40 kHz used. This or a similar frequency should also be supplied by the hemodynamic ECG device. The current supply for the individual segments takes place, for example, in each case by lying outside of the examined segment electrodes, z..B. for the measurement * cles * thorax * iwisdhen * the outer of the double neck electrode -3- or head electrode or arm electrodes / n -6- on the one hand and one of the electrodes lying distally of the chest wall electrodes, eg the proximal -4- or distal leg electrodes On the other hand, the measurement of the abdomen segment by feeding to the arm electrodes -6 and / or neck electrodes -3- on the one hand and the distal leg electrodes -5- on the other hand, the measurement of the arms, by feeding to the distal Doppelarmelektroden -6- and the Neck electrode -3-. The measured thorax segment lies between the proximal neck electrode on the one hand and one or more chest wall electrodes V4-V6 or V4r to V6r on the other hand. For the measurement of the impedance change with the heartbeat at the thorax, the proximal leg electrodes -4- can also be used because the abdomen does not contribute to the dZ / dt. It is also intended to further simplifications, such as the execution of the proximal leg electrode -4 as a single electrode.
    It is also intended to further simplifications, for example to a particular simplification of the measurement, in which case the two electrodes can be omitted on the thighs and still the body can only with the electrodes of the extremities and the chest wall in 6 segments, namely in the thorax, abdomen and each 2 legs and arms are analyzed. In many cases, it is then sufficient to use single electrodes at the measuring points, for which the ECG electrodes can be used, for example, when the current is fed in elsewhere.
    In Fig. 2, the respective localizations of the power supply are drawn with AC power source, also very schematically the thus constituting electric fields as dotted areas, the measuring sections are also marked with the usual symbols, here for example with V. The respective subfigures indicate whether the minimum requirement in the respective image is a double electrode, symbolized by D, or a single electrode or symbolized by S. Parts of the human body in which no current field is built up, are used only as an electrical conductor, since the electrolyte content of the body with its high extracellular and intracellular Jonenkonzentration represents a good conductor, especially for the alternating current. It may prove useful, even for the measurement of the impedance and its change with the heartbeat to use higher than the often used 40 kHz to ensure a line of the alternating current through the intracellular water safely. Fig. 2 shows further possible Stromeinspeislokalisationen and localizations for the tapping of the impedance, preferably with the preferred use of ECG electrodes. For example, the earthing electrode (usually a black electrode on the right leg) on the one hand and one of the arms or both arms on the other hand can be used to supply the current (Fig. 2a). The grounding electrode can be easily used for this purpose, whereas a double electrode proves itself in the arms, since the "··················· ECG lead electrodes on the arms are not suitable for * ifie« Occasional. "Cl0s". Stroms should be used (Figure 2a). In contrast, the ECG electrodes can be used to measure the impedance or its subcomponents Resistance / Reactance. Here, it is always spoken of impedance, even if the sub-components and the change of impedance with the heartbeat (dZ, dZ / dt max and other characteristics) may be meant. For example, the impedance between the neck electrode -3- and the electrodes, as they are not for the interconnection as a central terminal according to Wilson, namely one of the electrodes V1 to V6, for example, V4 to V6 for the measurement of impedance and / or the change with The heartbeat, for example, is fed via both arms and both legs (Fig. 2b), whereby one leg and one arm could suffice. It is also possible to measure the impedance between the individual chest wall electrodes, which are the ones that can not be connected together for the Wilson central terminal. For example, this could be between V1 and V6 (possibly also V4 or V5) or also connected between V1, V2 on the one hand and V6; V6r (possibly also V4 or V5 with V4r and V5r)) on the other hand (Fig. 2a). Right ventricular outgrowths are just an additional option, and even without these, a complete analysis of the heart's activity and fluid distribution in the body can be performed. The right ventricular leads have the advantage that the left and right thorax can be compared in terms of impedance, and that at the same time the diagnosis of a posterior wall infarct in the ECG is facilitated. Additional derivatives such as Nehb derivations or Franksche Abeleitungen are possible.
    These are just examples, also the combination of other electrodes, as they are not interconnected in the central terminal Wilson, is provided. Using only a single further electrode located between two of the electrodes provided for the central terminal Wilson, namely between left and right arm electrode -6-, Einthoven lead I (the electrodes red and yellow of the conventional ECG), the impedance and its Change with the heartbeat be measured particularly accurately, because the measurement distance longer and thus the signal to noise ratio is better. This electrode would come to rest on the neck, neck, upper thoracic aperture, or skull. By using a double electrode -3- at this localization not only the current can be fed in, but also the impedance can be tapped (Fig. 2c). For the measurement of the thorax segment, the supply could be on the one hand on the outer neck electrode and / or on the Armelektroden -6- and on the other hand, if present, on the proximal leg electrodes -4- or distal leg electrodes -5-, the voltage measurement between the inner shark electrode and chest wall electrodes, in which the left and right thorax should be measured overall by interconnecting eg V5, V6, V5r and V6r and / or also only right and left eg via V4-V6 on the one hand or on the other hand via V4r-V6r (Figure 2c). For 6/33 5 the measurement of the thorax segment it is not * essential · only via the grounding electrode (black, on the right leg) or over both legs namely the grounding electrode and that of the 3 electrodes which are connected together for the central terminal Wilson and which are not for derivation I to Einthoven is fed. This is because the current field in the fuselage is already extremely homogeneous even when only one leg is fed in (Fig. 2c). The measurement of the thorax could also be done by feeding on one arm on the one hand and one or both legs on the other hand, measuring the tension between the respective contralateral arm and the chest wall electrodes (Fig. 2i) or, if present, on the proximal leg electrode (s). on the other hand. The contralateral arm in Fig. 2i would only act as a conductor in this case. The measurement of the dz / dt at the thorax, however, is not favorable between the neck electrode -3- and the / the distal leg electrodes -5-, since then can not be distinguished between the volume change with the heartbeat at the thorax and in the extremities. The measurement of the volume change, eg dZ / dtmax at the thorax and at one extremity, is, however, particularly favorable for the evaluation of the cardiac output, especially if additionally the ratio of extra to intracellular fluid is considered. From these three combined parameters, a limitation or improvement of the cardiac output can be recognized particularly well. For the measurement of the abdomen, for example, the current feed between one or both arm electrodes on the one hand (alternatively the neck electrodes on the one hand), and one of the distal leg electrodes on the other hand, the impedance measurement between, for example between one or more interconnected chest wall electrodes on the one hand and, if present, the respective contralateral proximal leg electrode -4- or distal leg electrode -5-, which is not intended for current injection, on the other hand possible (z, B, Fig. 2d). For the measurement of the abdomen, the current is supplied, for example, between one of the legs and one or both arms and the voltage measurement between each of the contralateral leg and the chest wall electrodes. For the measurement of a leg segment, for example, the power supply between each of the outer of the two distal leg electrodes -5- and the impedance measurement between each of the inner distal leg electrode -5- of the examined leg on the one hand and the chest wall and / or neck and / or arm electrodes - 6- on the other hand. (eg Fig. 2g). Thus, for the measurement of the arms, the current between the outer arm electrode -6 and the outer neck electrode-3 can also be fed in and the voltage between the inner neck electrode and the inner arm electrode -6- can be dissipated (FIG. 2e). For the measurement of the left arm mirror image and in an analogous manner, which naturally also other feed points are possible. Another measurement of the arm and thorax is shown in Fig. 2j. A further simplification is given by a possible omission of the neck electrode: For the measurement of the arm segments would have to be between 7/33 6 ·· · · · · · · · · · · · · · ······························································. "······································································································································································································································································································· Leg electrode / n -5- the voltage can be measured. It is obvious that a combination of the various figures 2a to 2} is possible. A particularly practicable and preferred expression succeeds from a combination of the Eirispeisungen from Fig 2g and 2h, if you want to renounce proximal leg electrodes -4. Alternatively, the neck electrode or one or more chest wall electrodes may be used to measure the legs, as shown in Figure 2g. The arms could also be used together with the legs for measuring the impedance of the legs in Fig. 2g (not shown in Fig. 3). On the other hand, it would also be possible to supply the alternating current between a distal leg electrode -5- and one of the upper half of the body and to measure the impedance between the distal leg electrodes -5-, in which case only one leg flows through alternating current and the other leg used as an electrical conductor (not shown in Fig. 2). Thus, it is possible to analyze each of the six segments exclusively with the help of the extremity electrodes and the chest wall electrodes with or without neck electrode. However, the precision of the measurements is further improved by the additional use of the neck electrodes -3- and additional proximal leg electrodes -4-.
    In the illustrations described, for example, the principle of four-point measurement, with external current and internal voltage electrodes is realized, whereby a two-point measurement is also considered. It should also be understood that the examples given may be further modified and that whenever the derivative of the impedance occurs away from the impressing of the current, it will be understood that single electrodes suffice at the respective embossing or discharging positions. Also a combination of different feeding places eg neck and arms would make the current fields even at the thorax even more homogeneous. It is also obvious that the current fields can not be as homogeneous as drawn.
    As shown in Fig. 1 and Fig 3, it may be thought that on all electrode bodies -11- also additional sensors, such as temperature sensors -35- or light sources -7-eg LEDs and light sensors -8- at the electrode body -11- the Clamping electrodes -1-, the elastic suction pads -15- or the adhesive electrodes accommodate. The LEDs -7-could e.g. relative to the light sensors -8- be mounted on the opposite branches of the clamping electrode (Fig. 1), for example, the light sources -7 and the light sensors -8- could be next to each other and measured the reflection of the light by the arterialized blood and its pulsation become. Again, it could be on the one hand to suction electrodes, on the other hand could also be used in a known manner clamping electrodes or elastic straps for fixing the electrodes to 8/33. This concerns the electrodes I, ···· ···· * ··· • ·· ··· ··· ···; ·· · i, · ···. and III, "how" they can be connected together in the central terminal Wilson, or the earthing electrode. Here, too, mechanical transducers, such as the accelerometer -9b-, can prove themselves, for example the shockwave of the blood, the blood circulation and the volume change with the heartbeat outside the thorax, as well as the pulse wave simultaneously recording the change in the zO , dZ and dZ / dt max register. Thus, for example, circulatory disorders can be easily recognized, or the pulse wave velocity between the individual electrodes can be measured. If the mass of the electrode body -11- is small, as for example in the chest wall electrodes, the accelerometer can, for example, in a fixed connection with the electrode body -11- is the electrode body -11- large, such as in the clamping electrodes -1- it can be advantageous to store the mechanical sensor -9- movable, for example via a membrane -13- at the electrode. Understandably, this problem does not arise with adhesive electrodes, for example on a spot adhesive electrode or on a ribbon adhesive electrode or on an electrode held down with an elastic band, since the mass of the electrode body -11- is small from the outset. With temperature sensors -35-, for example, temperature differences between the different electrode positions, such as may arise, for example, from circulatory disturbances, could be detected automatically. With position sensors -36-, for example, based on electromagnetic or transit time, or radio interferometry, or triangulation, so could also be the bistance between the individual sensors or their position detected in space. The distance would be interesting, for example, from the neck electrode -3- or the chest wall electrodes V1-V6 or V1-V6r to the proximal leg electrode -4- or distal leg electrode -5-, the more automatically the pulse wave transit time of the mechanical transducer -9- or volume wave transit time by means of the impedance measurement or to detect perfusion through the light sensors -8-.
    By additionally attached inflatable cuffs -10-, in which the pressure can be changed, it is thus possible to detect particularly constrictions or closures of the bloodstream in which e.g. in the case of an existing constriction of the bloodstream, the pulse wave or the volume wave, appears only at low cuff pressures, than in the healthy state. All of these registrations occur during the performance of a normal ECG, even within the same time, e.g. During the recording of the rhythm strip, an additional large amount of information about the mechanical heart activity or the function of the vessels are obtained. All listed electrodes could be designed as adhesive electrodes, suction electrodes or clamping electrodes or be fixed by an elastic band on the body. For example, the neck electrode in Fig. 1 is a double-pole electrode -3- on a common carrier -37-, e.g. a common adhesive film -37a- executed. When the neck electrode -3- is placed over the jugular vein, a venous pulse curve can also be recorded, e.g. proven in heart failure and pericarditis. Also several interconnected Spotelektroden would be left 9/33 8 • »· t« «·« «:. ·· *: ··· ········. and easy to attach to the right neck. If * metfreffc. If the electrodes were to be attached to the electrodes, it would also be necessary to require a plurality of electrical supply lines, possibly also shielded supply lines, to the electrodes, which could restrict the mobility of the cables. To prevent this, the signals obtained could also be transmitted via radio to ELMIT (27) and the CPU (27) for further evaluation. It is also thought that additional sensors can be mounted outside the ECG electrodes. Thus, it is contemplated to include a light emitter and light sensor, e.g. in the form of a pulse oximeter -38- attached to at least one of the acres and thus to analyze the oxygen saturation and the pulse wave, for example, the shape of the pulse wave. In combination with the at least one inflatable cuff -10- placed on the arm, thigh or lower leg, so that the blood circulation or their disorder in the various extremities can be anlysiert, for example, in a known manner in the form of ankle brachial index.
    A further improvement of the conventional ECG is achieved in that one or more electrodes on the chest wall, that is, the electrodes which are not connected to the central terminal Wilson, are also suitable for recording a phono-cardiogram or mechanical excitations. For an optimal signal a 30 degree link side position proves itself, which can be facilitated eg by a wedge cushion.
    In Fig. 3 it is shown how these electrodes must be designed in order to also record the mechanical activity of the heart in addition to the ECG: an electrode body -11-, e.g. approximately circular or oval, in its interior e.g. symmetrical or asymmetrical, a mechanical transducer -9- e.g. Acceleration sensor -9b- is housed. For example, with this niche transducer -9-it could be e.g. by an accelerometer -9b, which could be completely covered by the continuous, electrically conductive electrode -23-, as shown in the upper part and lower part of Fig. 3. The accelerometer -9b- could also be on the other hand on a flexible, as little as possible damping membrane -13- be mounted, for example, within the opening -24- of the electrically conductive electrode -23-, to experience no attenuation by the mass of the electrode body -11- , as shown in the right center of Fig.3. This accelerometer -9b- can reduce the pulsation of the heart, e.g. register the apex of the heart, the apexogram, or even the sound vibrations emanating from the heart, such as the heart sounds and heart noises. If multiple mechanical transducers -9- are mounted within the various chest wall electrodes V1 to V6, delays in the movement of the heart from one section of the heart to the other can also be recorded, such as by non-functioning areas of the heart; eg after myocardial infarction, can arise. In order to use the mechanical transducer -9-, for example, the accelerometer -9b- for phonocardiogram and for the registration of the movement of the heart *, at least one electronic filter should be present for the processing of the signal. For the recording of the phonocardiogram for a high bass filter is favorable, which frequencies between about 50 to 70 Hz, preferably about 70 Hz on the one hand and about 1000 Hz on the other hand passes, for use eg in the Apexogramm a low-pass filter, which frequencies between about 0.1 on the one hand and about 20 to 70 Hz, preferably about 30 Hz on the other hand lets through. Particularly advantageous is the parallel execution of at least two electronic measuring sections so that both frequency components can be reworked in parallel and possibly different. Thus, the systolic and diastolic time intervals, such as PEP, LVET as a measure of the systolic function, eg A20 as a measure of the diastolic function, and third heart sound as seen in heart failure, or characteristic heart noises, such as from the apex cardiogram and the phonocardiogram they are found in vitia occurrence.
    Instead of the accelerometer -9b- it can also be a microphone. It is, for example, in the middle right of Fig. 3 stated that inside the electrode body -11- a dome -12- is mounted, which serves to bundle the sound and at the rear end of the microphone -9a- as a mechanical 9a - - is placed. With -13-a membrane -13- is located, which could sit at the beginning of the dome -12- near the skin of the patient and this protects against the ingress of moisture. Maybe a microphone diaphragm -9c- could also be located in front of the microphone-9- at the rear
    End of the dome -12- to protect the microphone -9a- from moisture. By -14- is a soft ring -14- to be attached, e.g. O-ring, which protects the dome -12-from the ingress of noise from the outside or at the most from an existing vacuum in the area demarcated .. When using an accelerometer -9b- the opening -24- in the electric conductive electrode -23- omitted because the acceleration is also passed through the electrically conductive electrode -23- to the mechanical transducer, eg Accelerometer -9b-. It is contemplated to attach this electrode body -11- either by means of an adhesive film (not shown, there standard) or possibly in a known manner by means of suction electrode on the body, with -15- an elastic suction cup -15- is shown, the around forms a dense lip -16- on the body being examined so that a vacuum can be generated within the suction electrode.
    In order to obtain the best possible signals, a completely vibration-free vacuum is very advantageous. The elastic suction cups -15- are connected via suction lines -17- to the vacuum source -18-, for example, a mammal pump wherein the vacuum source -18-either from the outset vibration-free 'could be, as might be the case with a vacuum tank with a large capacity , or it is at least a correspondingly large, strongly attenuating equalizing vessel -19- or more ····················································································· . '· ··· ··· ··· • · ·.' · · · · ·
    Compensating vessels -19-, possibly in series * complete. · It may also be possible to find additional valves -20- between the elastic suction cups -15- and the equalizing vessel (s) -19- which only ever open. if the vacuum pump is not switched on. Thus, an absolutely vibration-free Unterduck can always be produced, whereby, for example, the signal quality of electrical and mechanical and optical customers could adapt the optimal negative feedback fed back coupled. In this case, the suppression can be set so that the signal quality and the signal-to-noise ratio of electrical, optical, mechanical and temperature sensors are -35-optimal in this case. A drain valve -21- for the rapid elimination of the vacuum may be present, which of course may be combined with the valve -20-.
    In order to ensure that the negative pressure is not lost in the electrodes not applied to the body, the suction electrodes are designed so that only in the applied state to the body in the suction chamber -15a, between the electrode body -11- and elastic suction cup - 15- arises when the electrode body -11- the human or animal skin is applied, an oppression can arise. For this purpose, it is necessary to press the electrode to the body, whereby a sealing lip -22- opens between the electrode body -11- and the elastic suction cup -15-. As soon as the electrode is removed from the body, the self-elasticity closes the sealing lip -22- around the electrode body -11- and in the suction line (s) -17- of the applied and non-applied electrode (s), the suppression remains upright.
    For example, if the conductive electrode -23- is silver chloride electrode, e.g. Asymmetrical opening -24- for the mechanical transducer -9-, for example, a microphone -9a- or an accelerometer -9b- has, this has the advantage that a larger, closed electrode surface for electrical contact with the skin is available. On the other hand, without altering the position of the electrode on the body, the mechanical transducer -9- can only be placed so that the mechanical transducer -9-lies between the ribs of the human body, even if the main part of the elastic suction cup-18- should come to rest over the ribs of the human body. By placing another mechanical transducer in another electrode on the thorax at a location where no heart sound or heart movement occurs, e.g. V4r to V6r, the background noise or the background movement at the thorax could also be registered and the useful signal for this disorder corrected.
    The electrode body leads -29- from the electrically conductive electrode -23- or the mechanical transducers -9- and / or the temperature sensors -35- either lead, for example, to a female connector -26- e.g. to a multi-pin connector -26- and via the corresponding contacts -30- to a plug -25-, eg multipole plug -25-, or directly to the combined ECG light - Mechäno-. and impedance and temperature analyzer, 12/33 11 abbreviated to ELMIT -27- or to the CPU -27-. For the sake of clarity, the filters are often only marked as simple lines, even if more than one electrical line is necessary for the function, and not all lines are marked with the -31-. since the electrical connection between the individual elements in the figure is obvious. In order not to allow residues from the skin, such as sweat, hair or dander, to enter the suction lines, an air-permeable sponge is provided which does not transmit biological residues and moisture and which is exchanged after the elastic suction cup has been removed can be. The contacting of e.g. Multipole plug -25- on the multipole plug female -26- to the electrode body leads -29- within the electrode body -11- represents a challenge because the elastic suction cup -15- and thus the Elekrodenkörper -11- and thus the Multipolstecker -25 - must be relatively small, so that a good oppression can be built. Nevertheless, the legally prescribed electrical safety distances between the contacts must be observed. It is therefore proposed, in order to mount the multipole plug an electrically conductive tube, which serves as an additional electrical contact and which at the same time serves as a transport medium for the suppression and which the suction lines -17- opposite the elastic suction cup -18- seals and thereby allows easy replacement of the elastic suction cup -15- and / or the electrode body -11. The electrically conductive tube -32- is separated from the multipole plug -25-, for example by an insulating body -33-. It must of course be ensured that the vacuum within the tube with the suction line -17- within the elastichen suction cup is in communication, which, for example, by a groove or hole - 34- in the insulating body -33- is possible. In the lower part of Figure 3, the electrode body - < 11- drawn rotated by 90 degrees, so that the shape of the suction line -17-, the Multpolstecker -25- and the multi-plug female -26- with the contacts -30- here better visible. The electrically conductive tube -32- is drawn by dashed lines, as it is not in the cutting plane of the figure. If the electrode is only designed as an electrically conductive electrode -23- without additional transducers on the electrode body -11-it does of course not require a multipole plug -25- but only a simply contacted plug -25-. The plug -25- or female plug -26- serve to allow the electric suction cup -15- can also be easily replaced. The plug -25- and the female plug -26- could be anywhere in the electrical line -31- to the electrical or electronic switch, eg multiplexer -2- lie. However, the plugs -25-have to be led out so slenderly that the electrical leads -31- are connected to the plug-25 or plug female -26- together with the electrode body -11- fixed in this case by the elastic suction bell threading, that is, that the suction cup then alone or the electrode body -11- alone with the attached cable gewelfgewifen VÖnrfdrt.'Dai It means * that the outer diameter of the plug -25- then may not be much larger, than the recess in the elastic suction bell -15-, in which in Figure 3, the electrically conductive tube -32- is inserted.
    It is intended to generate and store templates of all measured and calculated parameters during phases of unchanged cardiac activity. If the examination is then repeated at a later time, the changes in the parameters can be recorded numerically and graphically as a trend. In addition, the use of standard fields for the individual parameters is intended. If, in a single examination, several examination periods e.g. After physiological or pharmacological interventions are strung together and, for example, several templates of the same parameters are generated, the time course of the change in cardiovascular activity can be analyzed and the trend recorded. Then, if the study is repeated after some time, the trends of the individual examinations that took place at a different time could then be superimposed, graphically presented with dates, so as to easily detect changes in cardiac and circulatory activity between the individual times of the examinations , Again, the use of standard fields for the individual parameters is intended. As examples, changes in the ST distance or the dz / dt during a load test are given. The signals for the beginning and end of the periods can either be entered manually or from another device, eg an ergometer. In particular, it is also thought to analyze alternative heartbeats in separate templates, so as not only to generate and analyze the "electrical alternans" but also a "mechanical alternans", so as to be able to better recognize a malfunction of the heart muscle. The measurement of the change in volume not only in the thorax but also on at least one extremity (dZ or dZ / dt) also allows the determination of a concordant or discordant alternans of the right and left ventricles, since the change in volume in the thorax with the heartbeat mainly by the right ventricle, in the extremity, however, only by the left ventricle is effected. Accurate evaluation of mechanical alternans also allows for an identification of persistent or decaying alternans. Specifically, one will also use detected extrasystoles to discover a subsequent induced alternans. For the triggering of alternans and also for the general analysis of all signals, such as heart time intervals, pulse wave ventilation time, volume acceleration by dz / dt, etc. is also the use of stimulation methods of the circulation, such as increasing the heart rate by body work or pharmaceuticals or during the recovery phase thought of these loads, because it allows an even better assessment of the cycle. 14/33 13 Μ Μ ··· ·····························································································
    All data obtained can be permanently stored in a SpeTohei ** 3ST * * "HeTfi" pad. Thus, the patient can be examined in longitudinal studies over time and changes registered against the previous findings and detected or output in the report, for example by the printer -40- as numbers or graphically. Of course, this does not only concern the electrical activity, such as changes in the P-wave, R-wave and T-wave vector, anomalies of the p-wave, the chamber complex and the Nachschwankung, the PQ time, the duration of the chamber excitation, the T-wave height, QT duration, QT dispersion, and other changes to the ECG, plus changes in impedance with the heartbeat and all other parameters listed above, such as cardiac output, heart failure class (eg NYHA class), estimated atrial natriuretic Peptide, eg BNP, NT-proBNP, the soluble ST2 receptor (sST2), cardiotrophin, adrenomedullin and / or other estimated biochemical parameters for myocardial tension or biomechanical stress, systolic function, diastolic function, valve failure, extracellular water, intracellular water, Total body water, muscle mass,
    Fat mass, extracellular / intracellular water ratio or the distribution of body water and its components and their relationship to each other recognized in the individual body parts and output as numerical values and / or graphically as a trend over time, so at a glance a risk to the patient by change above parameter can be detected. The raw data obtained must then be partially combined by complexation in complex calculations, eg multiple
    Regression equations, are processed to calculate the desired parameters. Examples are only the combination of changes in the dZ / dt max in different body segments with a detection of an expanded extracellular water (ECW) eg increased ECW in relation to intracellular water (ICW) or in relation to Total Body Water (TBW), so one increased ECW / ICW or ECW / TBW ratio or a change in apexogram co-regularity with a change in the systolic and diastolic time intervals, eg the rapid relaxation time, namely the A20 time to detect a disturbed diastolic function as seen from the detection of heart sounds and the apexocardiogram. The changes in the apexocardiogram such as a "mid systolic bulge" can be used in addition to the ECG changes to diagnose a heart attack. Also disturbances of the Percards, eg Pericarditis and also flap errors, e.g. Aortic stenosis can also be detected via the relation of a to e-o wave in the apex cardiogram. The first derivative of the apexocardiogram also allows a particularly accurate assessment of cardiac function. But also the training condition and an improvement of the cardiovascular performance can be well calculated from the given parameters even without maximum load via regression equations, eg V02max, the maximum number of wattages and the body fatigue capacity in percent of the norm can be estimated from multiple regression equations or neuronal networks, which helps to train athletes and patients in training. Also, a change in muscle mass in individual body segments and in the whole body can be detected with the help of the data obtained.
    For the determination of overhydrogenation or underhydrogenation the calculation of the deviation from TBW or ECW or ICW or ECW / ICW ratio of the between the FM / kg body weight on the one hand and TBW / kg body weight or ECW / kg body weight or ECW / ICW in healthy persons proves particularly useful determined regression line. In order to optimize the signal quality of all signals, it is also intended, on the one hand to amplify the signals as close to the transducers, for example in a known manner with operational amplifiers to compensate for any interference or distortions, furthermore, where necessary, all lines should be equipped with altive screens In addition, where possible, early digitization of the signals close to the transducers is also intended, which would help eliminate any signal quality issues. 16/33 15
    权利要求:
    Claims (48)
    [1]
    1. An ECG device, comprising at least chest wall electrodes and limb electrodes, characterized in that at least one further electrode is attached to the body, which is suitable for the supply and / or measurement of an alternating current and that at least a portion of the conventional 12-lead ECG electrodes for an impedance measurement or measurement of the change in impedance with the heartbeat (eg dZ / dZ / dt max) is pronounced.
    [2]
    2. ECG device according to claim 1, characterized in that it is in the further electrode to a double electrode (1, 3) on a common carrier (37, 37 a) or electrode body (11).
    [3]
    3. ECG device according to claim 1 and 2, characterized in that at least one additional electrode positioned between the ECG electrodes, which are used for the derivative I to Einthoven, for example, a neck electrode (3), for measuring the impedance is present.
    [4]
    4. ECG device according to claim 1 to 3, characterized in that it is the at least one additional electrode to a double electrode (1,3), for feeding the current on the one hand and for measuring the impedance on the other hand.
    [5]
    5. ECG device according to claim 1 to 4, characterized in that the ground electrode of the ECG, usually the black electrode, is pronounced as Stromeinspeiselektrode for an alternating current.
    [6]
    6. ECG device according to the above claims, characterized in that a switching device (2), for example a multiplexer (2), is present, which can interconnect at least a portion of the ECG electrodes to a common impedance electrode or separate and / or the place the power supply can be changed.
    [7]
    7. ECG device according to the preceding claims, characterized in that at least two ECG electrodes, which are not interconnected for the central terminal Wilson, can be interconnected for the impedance measurement.
    [8]
    8. ECG device according to the preceding claims, characterized in that right ventricular chest wall leads, preferably V4r to V6r are pronounced. 17/33 16
    [9]
    9. ECG device according to claim 6 to 8, characterized in cfass the electrical switch, eg multiplexer (2) is so pronounced that the segments of the body, which are not flowed through by an alternating current, are pronounced as electrical conductors.
    [10]
    10. ECG device according to the preceding claims, characterized in that an alternating current at several frequencies, preferably at between about 1 and 10 kHz, at about 30 to 200 kHz and at about 200 to 800 kHz is fed.
    [11]
    11. ECG device according to claim 6 to 10, characterized in that the multiplexer (2) is so pronounced that the power supply to the distal extremity of the extremity carrying the ECG in the neutral electrode (in the conventional ECG black electrode), and the counterclockwise extremity, which carries the green electrode in the conventional ECG, and that the measurement of the impedance on the one hand to the distal leg electrode (5), which is used for the power supply and on the other hand to one of the electrodes on the upper half of the body are mounted, eg chest electrodes (V1-V6, V4r to V6r), or neck electrode (3) or arm electrodes (6) can be done.
    [12]
    12. ECG device according to claim 3 to 11, characterized in that the multiplexer (2) is so pronounced that the power supply on the one hand between the distal neck electrode (3) or the arm electrodes (6) and on the other hand optionally the distal ends of the limb, which carries the neutral electrode (in the conventional ECG black electrode) on the ECG and / or the extremity adjacent to the clock, which carries the green electrode in the conventional ECG, and in which the measurement of the impedance can optionally be between the proximal neck electrode (3) and the second the Armelektroden (6) and on the other hand optionally the chest wall electrodes (V1-V6, or V4r-V6r), if present, the proximal leg electrodes (4), or the respective distal leg electrode (5) which does not serve for power supply can take place.
    [13]
    13. ECG device according to the preceding claims, characterized in that the ground electrode (in the conventional ECG black electrode) and the central terminal Wilson used in the frontal view of the human body against the clock of the ground electrode adjacent electrode, green in the conventional ECG Electrode, in each case at least as a double electrode -1- are executed.
    [14]
    14. ECG device according to the preceding claims, characterized in that at least one, the ground electrode of the ECG in the frontal view of the human ······· ··············································· • Body can be connected to the ground electrode or an electrode adjacent to the extremity for impedance injection.
    [15]
    15. ECG device according to the preceding claims, characterized in that at least one electrode body (11), preferably a plurality of electrode body (11) as an additional transducer for physical measurements, eg mechanical (9) eg microphone (9a) eg Accelerometer (9b) For example, light sources (7) eg light sensors (8) eg temperature sensors (35) eg position sensors (36) are pronounced.
    [16]
    16. ECG device according to claim 15, characterized in that the mechanical sensors (9) are concealed within the electrode body (11) formed by the electrically conductive electrode (23).
    [17]
    17. ECG device according to claim 15 and 16, characterized in that within the ECG electrode body (11) has a recess is provided, in which the mechanical transducer (9), for example, the microphone (9a) or accelerometer (9b) asymetrically opposite the electrically conductive electrode (23) is housed.
    [18]
    18. ECG device according to claims 15 to 17, characterized in that the mechanical transducer (9), for example the accelerometer (9b) relative to the electrode body (11), e.g. is movably supported by a membrane (13).
    [19]
    19. ECG device according to claim 15 to 18, characterized in that a dome (12) is provided, in the upper part of the mechanical transducer (9), for example, the microphone (9a) is mounted.
    [20]
    20. The ECG device according to 15 and 17 to 19, characterized in that the electrically conductive electrode (23) by a soft ring (14), e.g. an O-ring, separated from the mechanical transducer (9).
    [21]
    21. ECG according to claims 19 and 20, characterized in that the microphone (9a) is separated by a microphone diaphragm (9c) from the dome (12).
    [22]
    22. ECG device according to claim 15 to 21, characterized in that for the evaluation of the signals from the mechanical transducer (9), eg Accelometer (9b) or microphone (9a), at least one, at least two filters are present, and at least a better both frequency ranges are analyzed separately.
    [23]
    23. ECG device according to claim 22, characterized in that it is in the filters for the evaluation of Accelerometersignale to a high-pass filter between about 50 to 18 19/33 ······· ··········· 70 Hz on the one hand to 1000 Hz on the other hand low-pass filter * ca between 0.1 on the one hand and 30 to 70 Hz on the other hand acts.
    [24]
    24. ECG device according to claim 15 to 23, characterized in that the mechanical pickup (9) in the electrodes, which are not interconnected to the terminal Wilson, that is, in the chest wall electrodes, in at least two chest wall electrodes housed.
    [25]
    25. ECG device according to claim 24, characterized in that the at least two mechanical transducers (9) are accommodated in the electrodes V1 or V2 and V4 or V5.
    [26]
    26. ECG device according to claim 15 to 25, characterized in that at least three mechanical transducer (9) are housed in at least three chest wall electrodes, that is not in the used for the central terminal Wilson electrodes, wherein the signal of the third electrode, eg V4r , V5r, V6r, for correcting the signal obtained from the electrodes V1 to V6.
    [27]
    27. ECG device according to claim 15 to 26, characterized in that in the limb, to which the ground electrode is mounted and in the counterclockwise adjacent extremity mechanical pickup (9) eg light sources (7) eg light sensors (9) eg temperature sensors (35) are pronounced.
    [28]
    28. ECG device according to the above claims, characterized in that in the limb, to which the ground electrode is mounted and proximal leg electrodes (4) are pronounced in the counterclockwise adjacent limb.
    [29]
    29. ECG device according to the preceding claims, characterized in that at least part of the electrodes are formed as vacuum electrodes.
    [30]
    30. ECG device according to claim 29, characterized in that a sealing lip (22) is present, which is so pronounced that it only on the electrode body (11) rests only when the electrode body (11) pressed against the body examined or is sucked.
    [31]
    31. An ECG apparatus according to claim 29 and 30, characterized in that within the electrode body (11) and / or within the electrical leads (31) a plug (25), and a plug female (26) is so pronounced that the elastic Suction cups can be easily replaced. 20/33 19 ·· ·· ·· ··················
    [32]
    32. ECG device according to claim 29 to 3f * dädurfth * # 9fek§tih2öifthnet, that a vacuum source (18), for example, a correspondingly large vacuum reservoir (19) is present, which provides a completely uniform Unterduck without pressure fluctuations.
    [33]
    33. ECG device according to claim 32, characterized in that the vacuum reservoir can be separated by at least one valve (20) from the suction lines (17) which is so pronounced that a rapid venting of the suction lines (17) can take place.
    [34]
    34. ECG device according to claim 29 to 33, characterized in that a device is provided which regulates the height of the negative pressure at the suction electrodes with respect to a determined physical signal, for example, mechanical, acoustic, electrical or optical signal and / or optimized.
    [35]
    35. ECG device according to the above claims, characterized in that a special evaluation of "steady state" periods is possible.
    [36]
    36. ECG device according to the above claims, characterized in that a special evaluation of alternative heartbeats with respect to a Altemans, eg electrical, eg mechanical Altemans takes place.
    [37]
    37. ECG device according to the above claims, characterized in that the change in impedance with the heartbeat is measured at least two segments and that and from a measure of the extracellular volume, eg the ratio of extracellular water to whole body water, for example, the ratio of extracellular water to intracellular water , the cardiac output and the degree of cardiac insufficiency eg also a biochemical parameter for the biomechanical stress of heart muscle cells and / or water accumulation, eg one of the atrial natriuretic peptides, eg BNP eg NT-proBNP, eg adrenomedullin is calculated.
    [38]
    38. ECG device according to claim 15 to 37, characterized in that from the simultaneously recorded phonocardiogram and apex cardiogram and / or the dz / dt at the thorax and / or the legs disorders of the diastolic function are calculated and output.
    [39]
    39. ECG device according to the above claims, characterized in that the physical performance, eg V02max, maximum wattage, performance in percent of the norm even without maximum load from the measured parameters eg PEP, 21/33 20 • · '• · • · · ········ LVET, dZ / dtmax, is estimated from the parameters of the acelerometer, eg A20, eg muscle mass, etc. by means of regression equations or neural networks.
    [40]
    40. ECG device according to the above claims, characterized in that a regression between body water, eg whole body water (TBW), eg intracellular water (ICW) eg extracellular water (ECW) expressed in percent body weight to the fat mass expressed in percent of the body weight is calculated.
    [41]
    41. ECG device according to claim 40, characterized in that the deviation from the determined in healthy persons regression line between the above parameters is calculated and output.
    [42]
    42. ECG device according to the preceding claims, characterized in that a memory (39) for all other data is present, and that the current values and the pre-values of the collected electrical and physical parameters over time as numbers or graphically represented with Normfeldem or printed by the printer (40).
    [43]
    43. ECG device according to the preceding claims, characterized in that the results of the measurement phases are graphically displayed as a trend in existing multiple measurement phases during the individual study and in a repeated examination at a later time, the measurement phases of the various studies stored superimposed with time designation graphically become.
    [44]
    44. ECG device according to the preceding claims, characterized in that the collected signals from additional transducers (9, 35, 36, 38), at least partially by radio to ELMIT (27) and CPU (27) are passed.
    [45]
    45. ECG device according to the preceding claims, characterized in that an additional pulse oximeter (38) is present.
    [46]
    46. ECG device according to the preceding claims, characterized in that at least one inflatable cuff (10) is present.
    [47]
    47. ECG device according to the preceding claims, characterized in that close to the transducers (9, 35, 36, 38) of the electrical or physical signals amplifiers, such as operational amplifiers are provided which amplify the signals or compensate for interference or distortions of the signal , 22/33 21 # ································································································ « IJ ··················································
    [48]
    48. ECG device according to the preceding claims, characterized in that, where necessary, the lines to the patient are equipped with active screens. 23/33 22
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    同族专利:
    公开号 | 公开日
    EP2958489A1|2015-12-30|
    WO2014128237A1|2014-08-28|
    US20150374256A1|2015-12-31|
    AT514017B1|2020-11-15|
    JP2016511032A|2016-04-14|
    US10517499B2|2019-12-31|
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    法律状态:
    优先权:
    申请号 | 申请日 | 专利标题
    ATA135/2013A|AT514017B1|2013-02-22|2013-02-22|Hemodynamic EKG|ATA135/2013A| AT514017B1|2013-02-22|2013-02-22|Hemodynamic EKG|
    EP14706294.7A| EP2958489A1|2013-02-22|2014-02-21|Ekg device|
    JP2015558456A| JP2016511032A|2013-02-22|2014-02-21|ECG equipment|
    US14/769,560| US10517499B2|2013-02-22|2014-02-21|ECG device|
    PCT/EP2014/053384| WO2014128237A1|2013-02-22|2014-02-21|Ekg device|
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