EP4188225A1

EP4188225A1 - Control for an extracorporeal circulatory support

Info

Publication number: EP4188225A1
Application number: EP21758625.4A
Authority: EP
Inventors: Matthias Heinke; Johannes Hörth; Steffen Eschinger; Ivo Simundic
Original assignee: Hochschule Offenburg; Xenios AG
Current assignee: Hochschule Offenburg; Xenios AG
Priority date: 2020-08-03
Filing date: 2021-08-03
Publication date: 2023-06-07
Also published as: CN116096455A; WO2022029139A1; WO2022029139A8; DE102020004698A1; US20230420123A1; JP2023538263A

Abstract

The present invention relates to open-loop and closed-loop control units for extracorporeal circulatory support, to systems comprising such an open-loop and closed-loop control unit, and to corresponding methods. An open-loop and closed-loop control unit (10) for extracorporeal circulatory support is proposed, which is configured to receive a measurement of an ECG signal (12) of a supported patient over a predefined period of time, wherein the ECG signal (12) comprises multiple data points for each time point within a heart cycle. The open-loop and closed-loop control unit (10) comprises an evaluation unit (100) which is configured to evaluate the data points for at least one time point in a spatial and/or temporal manner and to determine at least one amplitude change (14) within the heart cycle based on the evaluated data points. The open-loop and closed-loop control unit (10) is further configured to output an open-loop and/or closed-loop signal (16) for extracorporeal circulatory support at a predefined point in time after the at least one amplitude change (14).

Description

Control for extracorporeal circulatory support

technical field

The present invention relates to control and regulation units for extracorporeal circulatory support and systems comprising such a control and regulation unit and corresponding methods.

State of the art

When the heart fails to pump properly or function, cardiogenic shock can occur, which can result in hypoperfusion or hypoperfusion of end organs such as the brain, kidneys, and vasculature in general due to a reduction in cardiac output or cardiac output. This acute heart failure causes an acute undersupply of blood in the tissue and organs and thus an undersupply of oxygen, also known as hypoxia, which can lead to end-organ damage. In most cases, such cardiogenic shock occurs as a complication of an acute myocardial infarction (AMI) or heart attack. However, such life-threatening situations can also occur as a complication as a result of surgical treatment, such as a bypass, or as a result of insufficient or impaired lung function and finally also as a result of disturbances in the conduction system, structural heart disease or inflammatory processes in the myocardium. Although factors such as early revascularization, administration of inotropic drugs, and mechanical support can improve the patient's physiological status, the mortality rate from cardiogenic shock remains in excess of fifty percent.

In order to stabilize the patient's condition, circulatory support systems have been developed which provide mechanical support and speed with the circulatory system can be connected. They can improve blood flow and perfusion of organs, including the heart's own coronary vessels, and avoid a hypoxic state. For example, a blood pump can be connected to a venous access by means of a venous cannula and an arterial access by means of an arterial cannula for sucking or pumping the blood in order to allow blood to flow from one side with a low pressure, for example via an oxygenator, to one side to provide a higher pressure and thus to support the patient's circulation.

However, the complexity and the dynamics of the patient's own heart action require precise timing or coordination of the extracorporeal support. For example, the blood flow through the heart's own coronary arteries, which normally provide the heart muscle with sufficient oxygen, generally takes place in the diastole of the heart cycle - thus following a corresponding emptying of the left ventricle. Because if the filling pressure at the end of systole or at the beginning of diastole in the left ventricle is as low as possible, the coronary arteries can develop their lumen as much as possible in order to increase the blood flow rate and the oxygen supply. Accordingly, the extracorporeal circulatory support for perfusion of the coronary arteries should be controlled in such a way that perfusion preferably occurs at the beginning of diastole, with perfusion during systole being avoided.

Measurement signals from an electrocardiogram (ECG) can be recorded and used to control the extracorporeal support, with which corresponding characteristic amplitudes can be determined for different heart cycle phases. For example, an R-wave or R-wave that is characteristic of the systolic phase of the heart cycle can usually be easily distinguished from other phases of the heart cycle, for example in a QRS complex. The R-wave can thus, with a predetermined latency, serve to control a blood pump in a successive diastolic phase.

For the provision of an EKG signal, different EKG derivations can be provided, which are positioned at or introduced into different anatomical regions. This causes a certain variability in the measurement signal. Furthermore, disturbances caused by stimulation or pathophysiology can significantly worsen the ratio of useful signal to noise signal and thus make it more difficult to determine the amplitudes in the heart cycle, so that the desired amplitude may not be detected or determined. This not only results in an inconsistency with regard to the monitoring of the cardiac action and cardiac output. Rather, a control of the extracorporeal circulatory support, which uses the amplitude as a trigger signal, is controlled at the wrong point in time, so that support does not take place in the announced heart cycle phase. DE 102010 024 965 A1 discloses a method for determining an R-peak in an ECG signal in order to improve synchronization of the ECG signal with an MRT imaging method. In this case, the R-wave is determined by means of a time derivation of the ECG signal for a predetermined time instead of a threshold value check. The derivation of the ECG signal is based on individual data points per point in time and is subjected to a plausibility test, which takes into account interference signals and fluctuations that occur specifically due to the magnetic field. However, no pathophysiologically caused disorders or individual, spontaneous anomalies and in particular no stimulation-related disorders caused by an implanted cardiac pacemaker are taken into account. The method also always provides immediate synchronization with the R-wave, ie without a predetermined latency, which is essential for the control of extracorporeal circulatory support.

Accordingly, there is a need to optimize the ratio of the useful signal to the interference signal from an EKG in such a way that the stability of the trigger signal for the control/regulation of an extracorporeal circulatory support is improved under different physiological conditions.

Presentation of the invention

Proceeding from the known prior art, it is an object of the present invention to enable improved stability of a trigger signal for extracorporeal circulatory support.

The object is solved by the independent claims. Advantageous developments result from the dependent claims, the description and the figures.

Accordingly, a control and regulation unit for extracorporeal circulatory support is proposed, which is set up to receive a measurement of an ECG signal from a supported patient over a predetermined period of time, the ECG signal comprising a plurality of data points for each point in time within a cardiac cycle. The control and regulation unit comprises an evaluation unit which is set up to spatially and/or temporally evaluate the data points for at least one point in time and to determine at least one amplitude change within the heart cycle from the evaluated data points. Furthermore, the control and regulation unit is set up to output a control and/or regulation signal for the extracorporeal circulatory support at a predetermined point in time after the at least one amplitude change. Various heart cycles or heart actions can be recorded in the predetermined period of time, with each heart cycle being able to define specified points in time, for example from the beginning of the heart cycle to the end of the heart cycle. This simplifies the comparison between different heart cycles, for example compared to an evaluation using absolute points in time. The different cardiac cycle phases of successive cardiac cycles and in particular the course of these cardiac cycle phases of successive cardiac cycles can thus be compared with one another. Data points are thus collected at identical points in time—in successive cardiac cycles—so that the data points collected at identical points in time in the successive cardiac cycles can be compared with one another or offset. A useful signal can thus be displayed for each point in time of a cardiac cycle phase.

Furthermore, different ECG derivations can be provided for the same point in time of a single cardiac cycle to provide the ECG signal, so that a corresponding number of data points can be provided for each point in time. The various measurement signals thus enable selective data points from certain ECG derivations to be used for processing.

Accordingly, at least two data points are available for each point in time within the specified time period. However, depending on the number of cardiac cycles recorded and/or the existing ECG derivations, multiple data points can also be provided for each point in time. The specified period of time can be defined, for example, by the duration of the treatment or also by the specified number of cardiac cycles recorded.

The spatial and/or temporal evaluation thus enables individual interference signals to be corrected, so that the determination of the at least one amplitude change within the heart cycle is simplified and the accuracy is improved. In other words, such an improvement of the useful signal is made possible due to the presence of at least two data points for each point in time, specifically without a reference set of the ECG signal being required for this. In any case, this is not the case or even possible in the case of extracorporeal circulatory support and/or cardiac stimulation of the patient provided by a cardiac pacemaker.

Furthermore, the use of the data points for each point in time makes it possible to determine the change in amplitude in real time, so that, for example, disturbances caused by stimulation by an implanted cardiac pacemaker, pathophysiologically caused disturbances or individual, spontaneous anomalies can be taken into account and these do not make it more difficult to determine the change in amplitude. This means that exogenous interference signals that are not related to the cardiac stimulation are preferably not taken into account. In particular, exogenous interference signals, which are caused by imaging methods, for example in the course of MRT imaging or other magnetic field-induced interference signals, are preferably ruled out. The immediate utilization of the ECG signal recorded in real time makes it possible for the control and/or regulation signal to be based on the currently measured measurement signals and for the currently or currently received ECG signal to be used immediately or directly, i.e. in particular without a time delay, for the circulatory support of the patient , is taken into account. This is in contrast to methods that provide a prediction of the ECG signal, which is only based on previously acquired data (ie the data is first collected, stored and then finally evaluated, but not used directly) or is only used for virtual simulations. Furthermore, the amplitude change can be provided or expected at a specific point in time, so that the data points can be used to monitor for at least one point in time whether an amplitude change actually occurs at a given point in time.

The outputting of the control signal or regulation signal for the extracorporeal circulatory support can also bring about a direct setting of a corresponding parameter or operating parameter of a coupled extracorporeal circulatory support device. For example, one or more pump drives or pump heads for blood pumps, for example non-occlusive blood pumps, present in a system for extracorporeal circulatory support can thus be controlled or regulated. A desired blood flow rate for a corresponding heart cycle phase can thus be provided on the basis of the EKG signal.

The blood pump can be connected to a venous line by means of a venous cannula and an arterial line by means of an arterial cannula for sucking the blood to provide a blood flow from a side with a low pressure to a side with a higher pressure. The blood pump is preferably designed as a disposable or disposable item and is fluidically separated from the respective pump drive and can be easily coupled, for example via a magnetic coupling. By outputting the corresponding signal, the control and regulation unit actuates the motor of the pump drive and can thus bring about a change in the speed of the blood pump.

The EKG signal can also be fed into the control and regulation unit or received by it via an interface which is communicatively connected to at least one EKG device. However, the control and regulation unit is preferably designed as part of an EKG device or in such a way that the EKG device can be attached to the control and regulation unit. Thus, the control and regulation unit can be used independently of the presence of other components and can be of compact design. The ECG device is preferably integrated in a single housing of a system for extracorporeal circulatory support. for example in the sensor box in the form of an EKC card or an EKG module. Alternatively, however, the control and regulation unit can also be set up to receive an external ECG signal from the supported patient, for example from a heart monitor arranged outside of an extracorporeal circulatory support system. This allows the system to be made even more compact.

The at least one amplitude change is also preferably a characteristic ECG signal that enables the control and regulation unit to be synchronized with the blood pump, so that the control and regulation signal can be output regularly or periodically by the control and regulation unit. For example, the change in amplitude or the respective range in the electrical excitation line can be characteristic or indicative of the systolic or diastolic phase of the heart, so that a control and/or regulation signal can be output such that a blood pump is actuated at a predetermined point in time and can occur in a predetermined phase and not cause overlap with other phases.

The evaluation unit is preferably set up to evaluate the data points for a predefined time interval based on at least one cardiac cycle phase of the ECG signal and to determine the at least one amplitude change within the time interval. For example, a QRS complex can be detected or determined using the data points or the ECG signal, so that the at least one change in amplitude corresponds to one or more characteristic features.

Restricting the evaluation of the data points to a specific time interval not only facilitates the data processing and speeds up the processing, for example to ensure the determination of the amplitude change under different conditions, for example with a larger number of data points, in real time. This also enables greater accuracy of the determined amplitude change. For example, amplitude changes that are irrelevant for the control can be ignored or masked out and a computing capacity can be used for specific data points or one or more points in time and corresponding cardiac cycle phases. At the same time, this provides a high resolution of the amplitude change determination.

In order to be able to determine not only an absolute change in amplitude for a specific point in time within the heart cycle, but also a more precise course of the amplitude, the evaluation unit is preferably set up to determine the at least one change in amplitude based on data points for at least two points in time. The sampling of the ECG signal and the corresponding data points can take place, for example, at a frequency of 500 Hz, so that there are 2 ms between two respective points in time per second. Around To determine a course of the change in amplitude or a relative slope, two points in time, either successive points in time or points in time spaced apart from one another, can already be sufficient.

However, the at least one change in amplitude is preferably determined for a larger number of points in time of between 2 and 500 points in time, more preferably between 50 and 150 or of at least 50 or 100 or 150 points in time. For example, the evaluation unit can be set up to determine the at least one change in amplitude by evaluating all data points within a QRS complex. Correspondingly, the number of points in time can be selected as a function of the existing cardiac arrhythmia and/or cardiac stimulation. For example, 5 to 10 points in time can be selected in the event of an increased occurrence of ventricular extrasystoles, and 10 to 100 points in time, for example, can be selected in the case of irregular and/or rare ventricular and/or supraventricular extrasystoles. Furthermore, the number of time points can also be selected according to the duration of the examination and/or depending on the setup configurations, so that a higher number than 500 time points can also be selected. The number of points in time can also be between 10 and 10,000 points in time, for example in the case of pacemaker dependence and ventricular VVI pacing.

Furthermore, the cardiac output can be provided both by the patient's own cardiac activity and with stimulation, for example using a cardiac pacemaker. In these cases, pathophysiologically caused or stimulation-related disturbances can occur, which can be masked out by a specific selection of the points in time, for example by providing a corresponding time interval for determining the at least one amplitude change.

As described above, the provision of a control or regulation signal for the extracorporeal circulatory support should take place at a point in time and in a physiological state in order to provide maximum support of the cardiac output. Accordingly, an amplitude change should be determined, which can be used as a temporally stable trigger signal. The evaluation unit is therefore preferably set up to determine at least one selected change in amplitude which is characteristic of a cardiac cycle phase. More preferably, the at least one selected change in amplitude is characteristic of a P wave or, in particular, an R wave.

However, other changes in amplitude can also be determined, for example over a predetermined section of the EKG signal or from a prominent point of the EKG signal. However, at least one R-peak or R-wave is preferably determined from the data points, by means of which a trigger signal with a predetermined latency time is output will. For example, a control or regulation signal for an operating parameter of a blood pump can be output at a predetermined point in time after the R-wave has been detected, for example the detection of the maximum amplitude, and the blood pump can be adjusted accordingly, typically with a delay.

Correspondingly, by determining the at least one amplitude change, a temporally stable, electrocardiographically triggered and hemodynamically optimized, synchronized extracorporeal circulatory support is provided.

The data points can be evaluated both spatially and temporally. Accordingly, the ECG signal preferably comprises at least a first measurement signal from a first ECG derivation and a second measurement signal from a second ECG derivation, the first and second ECG derivations being spatially separated from one another and the evaluation unit being set up to calculate the data points evaluate spatially and to determine the at least one amplitude change based on an addition or averaging of the measurement signals.

The spatial separation of the leads and the corresponding signals, for example a spatial and/or anatomical separation, can ensure on the one hand that the distance between the useful signal and certain interference signals, for example from a stimulation of the heart, is improved and these interference signals are thus improved can be largely avoided and at least partially filtered out, so that they therefore do not impair the determination of the at least one amplitude change. On the other hand, this allows an ECG signal with the strongest possible useful signal to be detected due to the spatial separation of the ECG leads even in the case of modifications or variations of physiological signals, for example the excitation lines.

The addition or summation or averaging of the measurement signals or the respective spatially separated data points as part of signal averaging thus improves the ratio of the useful signal to the interference signal by a factor of at least 1.2 through the use of several ECG derivations or signal sources. for example 1.4, so that at least one change in amplitude can be clearly determined even with weaker measurement signals or fluctuations. In other words, the ratio of the useful signal to the interference signal can be improved by a factor of the square root of /7 for a number of n ECG derivations, so that at least one amplitude change can be clearly determined even with weaker measurement signals or fluctuations. With two ECG leads, an improvement of (n = 2) ~ 1.41 can be achieved. This improvement can be achieved, for example, in the presence of ideal noise with all frequencies, but can be reduced in the case of non-ideal noise signals, which can occur, for example, with biosignal interference.

A corresponding improvement in the ratio of the useful signal to the interference signal can also be achieved with time averaging or signal averaging, with the improvement resulting from the square root of the number /? of the averaged cardiac actions or cardiac cycles, for example from at least two averaged R-wave-triggered cardiac actions.

Accordingly, the control or regulation signal can be output as a trigger signal with high temporal stability.

The EKG signal preferably includes a measurement signal of a transthoracic EKG lead and/or a transesophageal EKG lead. The number of ECG leads is not limited to the number of the respective data points, so that there is always a choice of ECG leads for evaluating the data points. For example, a large number of transthoracic ECG leads (I, II, III, aVR, aVL, aVF, V1, V2, V3, V4, V5, V6) and (bipolar) transesophageal ECG leads (Oeso 12, Oeso 34, Oeso 56, Oeso 78), it being possible for one or two of the respective ECG derivation types to be used for the data points.

The trigger stability is usually relevant for the entire duration of the treatment and should therefore preferably be monitored over the specified period of time. Accordingly, the evaluation unit can be set up to determine an amplitude change and a time interval and/or a frequency of the amplitude changes for at least two heart cycles, with the control and regulation unit being set up in particular to determine a characteristic value for the time interval and/or the frequency output signal.

The characterizing signal can be, for example, a current time interval between the instantaneous amplitude change and the last determined amplitude change, for example an RR interval, and/or for example an average time interval, possibly with a current deviation. The signal can also cause a graphic representation on a display, for example, with the determined amplitude changes being marked or identified in the respective heart cycles. It is thus not only possible to detect whether the change in amplitude was determined at the same time or at a similar point in time, but also whether it was determined at the correct point in time, for example at a maximum value and not at the beginning or at the end of an amplitude. Correspondingly, the stability over time can easily be monitored visually using the markings. The evaluation unit is preferably set up to determine the at least one change in amplitude continuously for each successive heart cycle detected from the EKG signal. In this way, any instability of the trigger signal can be detected immediately and eliminated by adjusting the evaluation. For example, an alternative ECG derivation for providing the measurement signal and/or an alternative time interval for evaluating the data points can be selected, in which case the evaluation unit can advantageously be set up to be able to automatically adjust a setting in order to provide an improvement with regard to the determined amplitude change. For example, threshold values for the data points or the recorded measurement signals can be stored, optionally in relation to one or more points in time, with an alternative ECG derivation or an alternative time interval being selected automatically when a respective threshold value for determining the amplitude change is exceeded or not reached.

A temporal evaluation of the data points can be provided in addition to or as an alternative to the spatial evaluation. Accordingly, the evaluation unit can be set up to evaluate the respective data points of each heart cycle, in particular the data points that correspond to one another in time (i.e. those data points of consecutive heart cycles which are spaced at the same time from a reference point, e.g. the maximum of a signal in the heart cycle, in the heart cycle). to evaluate over time and to determine the at least one change in amplitude based on an averaging or addition of the corresponding data points collected for at least one point in time from at least two heart cycles.

As described above, different heart cycles or heart actions can be recorded in the predetermined time period, with each heart cycle being able to define points in time, for example from the beginning of the heart cycle to the end of the heart cycle. Thus, the different heart cycle phases of successive heart cycles and in particular the progression of these heart cycle phases can be compared with one another, so that data points for the same time (in relation to a defined reference point of the heart cycle) of different successive heart cycles, which are equally spaced in time, represent a useful signal for the same respective heart cycle phase. The data collection is preferably carried out in such a way that the data points for each heart cycle are determined at the same point in time before or after a defined reference point, which is chosen to be identical for all heart cycles, in the respective heart cycle, with the reference point preferably being morphologically and/or physiologically predetermined. The specification is typically a characteristic property in the ECG signal, i.e. the onset of one of the ECG signals (P, Q, R, S, T) or the point in time of the maximum of one of these signals, as they occur in each cardiac cycle. For example, the point in time of the maximum of the R-wave can be defined as a reference point in each cardiac cycle. The occurrence of this reference point, which is predetermined by the cardiac cycle, varies from cardiac cycle to cardiac cycle in terms of time, so that, for example, the R-wave or another characteristic of the cardiac cycle can occur somewhat earlier or later in one cardiac cycle than in the following cardiac cycle. Nevertheless, this feature of the EKG remains the reference point in each of the heart cycles recorded according to the invention. The measurement of the data points per heart cycle is therefore carried out individually for each heart cycle, but in a temporally constant dependence on this predetermined reference point. In each heart cycle, data points are measured according to a predetermined frequency before and after the reference point over the course of the heart cycle, i.e., for example, a data point is recorded in each of the recorded heart cycles consistently per ps or per 2 ps before and after the occurrence of the reference point.

The time averaging, i. H. averaging or addition of the data points thus make it possible for individual outliers, which, for example, are not in a relevant heart cycle range and are therefore not characteristic of a specific heart cycle phase, to still not affect the determination of the amplitude change, especially since the height of the corresponding data point for other heart cycles in the ratio is low. In this way, it can be monitored in real time whether the determined amplitude change is within the intended range and whether a trigger signal is stable.

Although the averaging or addition already brings about an improvement in the useful signal compared to the interference signal with data points from two heart cycles, an averaging or addition over more than two heart cycles is preferably provided. Accordingly, the evaluation unit can be set up to determine the at least one change in amplitude based on an averaging or addition of the data points from at least 10, e.g. 10 to 100 or 10 to 40 or 10 to 35 heart cycles, preferably at least 40, e.g. between 40 and 80 cardiac cycles. As described above, a (theoretical) improvement in the useful signal given a number of n heart cycles or heart actions can be increased by a factor which corresponds to the square root, ie Vn. With an averaging of 25 cardiac cycles, the useful signal or the signal-to-noise ratio can be improved by a (theoretical) factor of 5.

However, the number of cardiac cycles is not limited to the numbers. Correspondingly, more than 100 heart cycles can also be provided, for example in order to compensate for relatively prominent outliers. However, data points from 10 to 40 heart cycles can also be evaluated, for example to enable rapid adaptation to a changed physiological state.

The determination of the at least one change in amplitude can also be adjusted manually, for example to extend or restrict a specified time period or a time interval. The control and regulation unit is therefore preferably in the coupled state with a display is set up to output a signal for displaying successive heart cycles detected from the ECG signal for corresponding points in time of the determined at least one amplitude change, and a manipulable time range specification, which characterizes the range of the evaluated data points, to the display. The evaluation unit can then also advantageously be set up to receive an adjustment signal from the coupled display and to determine the at least one amplitude change when adjusting the time range for successive cardiac cycles in the adjusted relative time range.

As a result, an overlap of the respective heart cycles or a chronologically determined selection of the respective heart cycles with the currently determined at least one amplitude change can be shown on a display in a graphical representation, for example, with a time window comprising the current time interval for evaluating the corresponding data points. By adjusting the time window, for example by shifting the limit values on a horizontal axis, the time interval can be shifted and/or lengthened or shortened, depending on how the displayed heart cycles with regard to a heart cycle phase - relevant for the at least one amplitude change - require it. A certain flexibility and, as a result, even intuitive operability for optimizing the at least one amplitude change is thus provided for the user.

For the temporal evaluation of the data points, the ECG signal can also include at least a first measurement signal from a first ECG derivation and a second measurement signal from a second ECG derivation, with the first and second ECG derivations being spatially separated from one another and with the evaluation unit is set up to determine the at least one amplitude change based on averaging or adding the data points for the at least two measurement signals.

The data points from the two measurement signals can form a value together, for example, so that the data points are averaged both in terms of time and space. For example, at least one of the ECG leads can be designed as a transesophageal EKG lead and as a corresponding probe. This has the advantage that the distance to a possible interference signal, for example in the case of a stimulation of the heart, and thus the useful signal are improved accordingly.

Temporal averaging and spatial addition of the data points can also be provided. In this case, for example, data points from at least two measurement signals from spatially separate ECG derivations can be added for the respective point in time and the added data points can then be averaged for two or more cardiac cycles or an average can be formed. In this way, the relationship between the useful signal and the Interference signal and the stability of a trigger signal are further improved. Although temporal averaging or spatial addition alone enable a considerable improvement in the useful signal, the combination of spatial and temporal evaluation is therefore particularly advantageous in order to further reduce any interference signals and to enable more precise, signal-optimized circulatory support for the patient.

The evaluation unit is preferably also set up to multiply the respective data points or the evaluated data points, but in particular to raise them to a power, preferably with a factor or exponent of greater than 1.3. The factor is particularly preferably from 1.3 to about 5.0 or from 1.3 to 3.0 or from 1.3 to 2.0.

In this way, the data points or the individual measurement signals are further improved, with higher measurement values being more prominent than lower measurement values due to the exponentiation, and a potential interference signal can thus be reduced. The factor or exponent can depend both on a detection frequency and on a number of detected and evaluated heart cycles. In combination with the spatial and/or temporal evaluation, the potentiation can thus bring about a further improvement in the useful signal and consequently further support the determination of the amplitude change in order to provide more stable extracorporeal circulatory support for the patient.

The underlying object set above is also achieved by a system for extracorporeal circulatory support of a patient. Accordingly, the system comprises a device for extracorporeal circulatory support, comprising a blood pump which can be fluidically connected to a venous patient access and an arterial patient access and is designed to provide a blood flow from the venous patient access to the arterial patient access, an interface for receiving an ECG signal from the patient, and a control and regulation unit as described above, which is communicatively coupled to the device and wherein the control and regulation signal is a control and regulation signal for adjusting the blood pump.

The system preferably also includes an EKG device which is communicatively connected to the interface.

The control and regulation unit can, for example, be designed as part of an EKG device or be integrated therein and thus be coupled to the system as an independent unit. The ECG device can thus be communicatively connected to the interface of the system. As a result, the system can also be used independently of the presence of other components. The ECG device is preferably integrated in a single housing of the system, for example in a sensor box in the form of an ECG card or an ECG module. Alternatively, however, the control and regulation unit can also be set up to receive an external ECG signal of the assisted patient, for example from a cardiac monitor external to the system. As a result, the system can be made even more compact.

The control and regulation unit can also be accommodated in a console that has a user interface for entering and reading out system settings, in particular parameters of the blood pump and/or the EKG device. For example, the console can include a touch screen and/or a display with a keyboard that can be operated by a user. The control and regulation unit operates, actuates, controls, regulates and monitors the blood pump and enables the blood pump to be synchronized with the heart cycle of the respective patient.

For example, the control and regulation unit can record the received ECG signal and the heart rate, with the display showing the current ECG signal graphically and the current or average trigger frequency and/or trigger stability numerically. Furthermore, characteristic properties of the ECG signal or the respective heart cycle can be emphasized or marked in the graphic representation, so that in a QRS signal, for example, a trigger signal determined as an amplitude change in the form of an R-peak in the ECG signal or in the current heart cycle can be marked. Furthermore, other settings such as the time interval between several amplitude changes or trigger signals or the heart rate can be mapped in the ECG signal, so that a user can monitor the control and regulation of the blood pump with regard to the patient's physiological condition.

The interface can be designed, for example, as a sensor box, which can be connected via connections to various sensors, such as pressure sensors of an extracorporeal circulatory support device, and an EKG device.

The object set above is also achieved by a method for controlling/regulating an extracorporeal circulatory support. The procedure comprises at least the following steps:

receiving a measurement of an assisted patient's ECG signal over a predetermined period of time, the ECG signal including multiple data points for each time point within a cardiac cycle,

Evaluation of the data points for at least one point in time, the evaluation being spatially and/or temporally resolved and at least one amplitude change within the heart cycle being determined from the evaluated data points, and Setting a control and/or regulation signal for the extracorporeal circulatory support at a predetermined point in time after the at least one amplitude change.

The at least one specific change in amplitude is preferably characteristic of a P wave or R wave. Thus, for example, a trigger signal can be output based on a specific R-wave, with the stability of the trigger signal being significantly improved by evaluating the data points in terms of space and/or time.

Provision can accordingly be made in the method for the EKC signal to comprise at least a first measurement signal from a first ECG derivation and a second measurement signal from a second ECG derivation, the first and second ECG derivations being spatially separated from one another and the data points are evaluated spatially and the at least one amplitude change is determined based on an addition or averaging of the measurement signals. The ECG signal preferably includes a measurement signal from a transthoracic ECG lead and/or a transesophageal lead.

At least one amplitude change for at least two cardiac cycles and a time interval and/or a frequency of the amplitude changes can be determined for improved monitoring of the temporal trigger stability, with a signal characterizing the time interval and/or the frequency being output. For example, the signal may include a graphical representation, wherein trigger signals are marked based on the determined changes in amplitude in the heart cycles or at the corresponding respective point in time.

Provision can furthermore be made for the at least one change in amplitude to be determined continuously for each successive cardiac cycle detected from the ECG signal. Thus, the determination of the at least one change in amplitude can be adapted directly to a current change in the physiological state of the patient.

Finally, a chronological evaluation of the data points can be provided. Correspondingly, each point in time of each cardiac cycle can be used, with the temporally corresponding data points of consecutive cardiac cycles being evaluated in terms of time and the at least one change in amplitude based on an averaging or addition of the data points collected for at least one point in time (equally spaced in relation to the reference point) from at least two heart cycles.

The at least one change in amplitude is preferably determined based on an averaging of the data points from at least 10, for example 10 to 100 heart cycles, preferably at least 40, for example between 40 and 80 heart cycles or 10 to 40 heart cycles. By averaging or adding over time, for example, individual outliers that are not in a relevant heart cycle range and are therefore not characteristic of a specific heart cycle phase do not affect the determination of the amplitude change, especially since the height of the corresponding data point for other heart cycles is comparatively low. In this way, it can be monitored in real time whether the determined amplitude change is within the intended range and whether a trigger signal is stable.

The determination of the at least one change in amplitude can also be adjusted manually, for example to extend or restrict a specified time period or a time interval. The successive heart cycles recorded from the ECG signal are then shown on a display for corresponding points in time, each related to the same reference point, which have at least one change in amplitude, and a manipulable time range specification that characterizes the range of the evaluated data points, with one of the coupled display received adjustment signal determining the at least one amplitude change in the adjusted, related to the same reference point, relative time range for successive heart cycles is determined.

In addition to averaging over time, it can also be provided that the ECG signal comprises at least a first measurement signal from a first ECG lead and a second measurement signal from a second ECG lead, with the first and second ECG leads being spatially separated from one another and with the at least one change in amplitude is determined based on an averaging or addition of the data points for the at least two measurement signals.

Further advantages as well as possible versions and developments of the methods have already been described in detail with regard to the control and regulation unit described above, so that the corresponding aspects will not be described again in order to avoid redundancies. However, the corresponding disclosure content continues to apply to this subject matter.

The object set above is also achieved by a method for monitoring a temporal trigger stability of an extracorporeal circulatory support. The procedure comprises at least the following steps:

Evaluation of the data points for at least one point in time, the evaluation being spatially and/or temporally resolved and being based on the evaluated data points at least one change in amplitude within the heart cycle is determined, wherein the at least one change in amplitude determined is preferably characteristic of a P wave or R wave, and wherein at least one change in amplitude is determined for at least two heart cycles,

determining a time interval and/or a frequency of the amplitude changes, and

Outputting a signal when the time interval and/or the frequency of the amplitude changes exceeds a predetermined threshold value.

Determining the time spacing and/or frequency of the amplitude changes allows for stability over time, i. H. whether a trigger signal is issued with similar time intervals and at the correct times with regard to the respective heart cycle phases based on the determined amplitude changes. For example, a slight deviation can be ignored, but a deviation over a predetermined percentage of the time interval, for example exceeding a tolerance range of between 10 and 15 percent of the average time interval, can lead to the output of a signal.

The signal may include both an audible warning signal and a visual marker or warning on a display, for example in a portion of a timeline of the output trigger signals.

Brief description of the figures

Preferred further embodiments of the invention are explained in more detail by the following description of the figures. show:

FIG. 1 shows the course of an electrocardiogram in a sinus rhythm for a large number of transthoracic ECG leads and two transesophageal ECG leads;

FIGS. 2A to 2E show an electrocardiographic curve of spatially separated ECG leads without stimulation and with stimulation of the heart by an implanted cardiac pacemaker;

Figure 3 is a schematic representation of a control and regulation unit according to the invention;

FIG. 4 shows an electrocardiographic curve of two spatially separate ECG leads for a specific period of time; FIG. 5 shows the determination of several amplitude changes based on a spatial evaluation of the data points shown in FIG. 4 according to the invention;

FIG. 6 shows the output of control and regulation signals based on the amplitude changes determined in FIG. 5 according to the invention;

Figures 7A and 7B show alternative spatial interpretations and plots of the data points according to the invention;

FIGS. 8A to 8C show the determination of amplitude changes based on a time evaluation according to the invention for a different number of cardiac cycles and a predetermined time interval; and

FIG. 9 shows a monitoring and graphical adjustment possibility of the time interval for determining the amplitude change according to the invention.

Detailed description of preferred embodiments

Preferred exemplary embodiments are described below with reference to the figures. Elements that are the same, similar or have the same effect are provided with identical reference symbols in the different figures, and a repeated description of these elements is sometimes dispensed with in order to avoid redundancies.

FIG. 1 shows the course of an electrocardiogram in a sinus rhythm for a large number of transthoracic (T) ECG leads and two transesophageal (O) ECG leads, in this example the ECG signals of a patient with an AV block III. Grades and right atrial synchronous bipolar right ventricular pacing in DDD mode of an implanted cardioverter/defibrillator (ICD). However, the course shown in this figure is to be regarded as merely an example. Other aspects that are determined in the course of recording the EKG signal and are characteristic of other heart diseases or therapies can also be correspondingly recorded or recorded. In other words, the example shown here is not limited to the specific pathophysiological condition and/or therapy.

The measurement signals of the ECG leads, which are recorded and shown in FIG. 1 for a predetermined period of time, include measurement signals from the transthoracic ECG leads I, II, III, aVR, aVL, aVF, V1, V2, V3, V4, V5 , and V6 and from Oeso 12 and Oeso 34 bipolar transesophageal ECG leads. However, the number and type of leads should not be considered limiting. This is because, in principle, any selection of the ECG leads can be made to determine at least one change in amplitude. Therewith a spatially separate acquisition of measurement signals can take place, both within an anatomical region and for different anatomical regions.

Accordingly, the measurement signals can be processed and evaluated in order, for example, to enable a spatial and/or temporal evaluation or evaluation according to the invention.

The spatial and/or temporal evaluation of data points of an EKG signal has the advantage that the ratio of the useful signal to the interference signal can be improved. As a result, an amplitude change within a heart cycle can be determined more precisely. Interfering signals can occur, for example, as a result of a stimulation of the heart or due to pathophysiology or spontaneously, so that the regularity or stability of the ECG signal is reduced and the determination of an amplitude change, for example an R-wave or R-wave, is made more difficult.

An example of a corresponding ECG signal with various complex heart actions is shown in Figures 2A to 2E in an unpaced state and a paced state.

FIG. 2A accordingly shows an electrocardiographic profile of a first 12A and second 12B measurement signal from two spatially separate ECG leads and a corresponding sum signal 12C, with ECG leads II and III being transthoracic ECG leads. In the course, six amplitude changes are determined based on a detection of R-waves 16 or R-waves, with the course depicting the corresponding measurement signals in the case of atrial-triggered ventricular stimulation from left to right. In this course, a relatively stable determination of the R-peak 16 is possible and the measurement signals 12A, 12B have no significant fluctuations or anomalies. In FIG -Derivations II and III transthoracic ECG derivations and ECG derivation Oeso 5/6 is a left atrial bipolar transesophageal ECG derivation. In the course, two amplitude changes are determined based on the detection of R-waves, with the course depicting the corresponding measurement signals for inhibition of bipolar right-ventricular stimulation, for ventricular extrasystole and for a narrow QRS complex from left to right. Correspondingly, there are fluctuations due to different cardiac arrhythmias, which make it difficult to determine an amplitude change, as in the case of an R-wave.

Corresponding successive amplitude changes are also determined in FIG stimulation from left to right. It can thus also be seen here that a variation of the measurement signals can occur, which can lead to instability of a trigger signal if the amplitude change cannot be determined with sufficient accuracy over time.

In FIG. 2D two right ventricular stimulated heart actions followed by a ventricular extrasystole and two spontaneous heart actions are shown from left to right, while two QRS morphologies are shown in FIG. 2E. As a result, different fluctuations can be recorded from the measurement signals depending on the patient, heart disease and stimulation.

A schematic representation of a control and regulation unit 10 according to the present invention is shown in FIG. In this embodiment, the control and regulation unit 10 is set up to receive an ECG signal 12 for two different ECG leads, with an evaluation unit 100 present in the control and regulation unit 10 evaluating the corresponding data points for two different measurement signals 12A, 12B . Thus, for example, a spatial evaluation can be carried out in order to facilitate the determination of an amplitude change 14 and to improve the ratio of the useful signal to the interference signal.

In the present case, the control and regulation unit 10 is designed as an EKG module, so that no special coupling is required to receive the EKG signal. However, the EKG module can include an interface (not shown) which enables communicative coupling to an extracorporeal circulatory support system or an extracorporeal circulatory support device, so that it can be controlled or regulated accordingly by the control and regulation unit 10 .

The control and regulation unit 10 is also set up to output a control and regulation signal 16 based on the determined change in amplitude. For example, one or more amplitude changes 14 can be determined, which are characteristic of an R-wave in the respective heart cycle. The control and regulation signal 16 can accordingly be output as an R trigger signal and, for example, operate or control/regulate a blood pump with a latency period, so that improved perfusion of the patient's coronary arteries can be provided.

An example of a spatial evaluation is shown in FIGS. In Figure 4 (top) an ECG signal 12 is recorded and shown, with first measurement signals 12A from a first ECG derivation (middle) and second measurement signals 12B from a second ECG derivation (bottom) being recorded and from the Control and regulation unit or the evaluation unit were received. In this example, the ECG leads are spatial separated from each other and correspond to the ECG leads II (middle) and III (bottom) of Figures 1 and 2.

This example is an ECG signal 12 from a patient with coronary artery disease with a left ventricular ejection fraction of 65%, with sinus rhythm, high-grade AV block and intermittent bipolar right ventricular stimulation in a WIR mode of an implanted cardiac pacemaker. In Figure 4, a total of seven heart actions of the ECG leads II and III are shown in the specified period, with the amplitude of the measurement signal 12A, 12B on the y-axis and the time curve of the ECG signal 12 on the x-axis with a sampling frequency of 500 Hz are shown, so an interval of "500" corresponds to 1000 ms.

The measurement signals 12A and 12B shown show that the useful signals are different between the different heart actions and for the different anatomical regions and can vary accordingly, not only in terms of amplitude size, but also in terms of their distribution over time. In the evaluation unit of the control and regulation unit, however, the measurement signals can be evaluated in a spatially resolved manner and added, for example, as is shown in FIG. The addition of the measurement signals 12A, 12B can thus improve the ratio of the useful signal to the interference signal by a factor of 1.4, so that the amplitude change 14 can be determined in a considerably simplified and more precise manner. This is shown, for example, using the amplitude improvement for the third and fourth heart action in FIG. 5 with regard to the corresponding amplitudes in FIG.

The improvement in the amplitudes enables an improvement in the output of the control and regulation signal 16, especially since the change in amplitude can be precisely determined and thus, for example, a maximum gradient or a maximum of the amplitude can be determined more precisely. Correspondingly, the change in amplitude can serve as a trigger signal 16 for extracorporeal circulatory support, with a temporal stability of the trigger signal 16 being ensured.

This can be seen, for example, in FIG. 6, in which the time interval between two respective trigger signals 16 does not show any serious irregularities and trigger signals 16 can therefore be provided or output for control/regulation of extracorporeal circulatory support in corresponding cardiac cycle phases. In the present example, the control and regulation signals 16 or trigger signals 16 are output on the basis of specific R peaks. However, these signals 16 can also be output with a corresponding latency period based on specific P waves or other characteristic changes in the amplitude of the EKG signal. The improved temporal trigger stability based on the spatial evaluation of the data points can thus be advantageous in particular for the precise control of extracorporeal circulatory support, with interference signals being able to be masked out or corrected. For example, interference signals as a result of intermittent stimulation, for example bipolar right-ventricular stimulation, can be blanked out or corrected in a patient with an implanted heart pacemaker with cardiac insufficiency and coronary artery disease, but with a normal left-ventricular pump function.

Alternative spatial evaluations and graphical representations of the data points according to the invention are shown in FIGS. 7A and 7B. Accordingly, the data points for the entire period, as shown in Figure 7A, can be evaluated spatially and displayed by means of an overlap and color coding on a display coupled to the control and regulation unit, so that the useful signal is improved and the amplitude changes determined are also stable over time can be easily monitored.

However, the data points can also be evaluated only for a specific time interval or also for a specific time range of a cardiac cycle phase, as is shown, for example, in FIG. 7B for an alternative data set.

Correspondingly, a spatial evaluation or addition of the measurement signals is carried out, for example, only for the R-wave, which can be detected using a slope of a first measurement signal. The spatially evaluated data points can be represented as an extension of the data points of the first measurement signal for a specific time range of a cardiac cycle phase, this range being defined, for example, by a threshold value of the evaluated data points being exceeded.

According to the invention, the data points can be evaluated over time to determine changes in amplitude, as shown in FIGS. 8A to 8C. In this exemplary embodiment, each point in time forms a relative point in time of each cardiac cycle. The evaluation unit is set up to evaluate the data points over time and the at least one amplitude change, based on an averaging of the data points for at least one corresponding, identical in time from the same reference point in the at least two heart cycles, for example always the maximum of a signal for the at least two heart cycles, e.g. the R-wave, to determine a point in time from at least two heart cycles, as shown in FIG. 8A.

The data points are averaged accordingly for each of the time points corresponding in time in the heart cycles. Alternatively, however, an addition can also be provided. The change in amplitude is determined on the basis of the course within a specific time interval, in the present case a detected QRS complex, where P denotes the start of the P wave, Q denotes the beginning of the Q wave and S denotes the end of the S wave in Figures 8A to 8C. For example, the data points can be evaluated over time using the following formula: where there is a summation of n points and where j is a single data point within the time period for a particular time corresponding in each of the n heart cycles and i is a respective heart cycle. Accordingly, an average value is calculated or formed for the corresponding n data points. A correspondingly spaced point in time in the n cardiac cycles is, for example, in each cardiac cycle after a period of yi (ps) before or after the occurrence of the reference point (e.g. the maximum of a signal in the ECG, e.g. the R-wave) in respective heart cycle. For each heart cycle, a data point is determined at time y 1 , and an average value is formed for these data points at time y 1 in all heart cycles. The same procedure is used at time y ₂ to y _n .

The change in amplitude is also used to output a corresponding control and regulation signal 16 or a trigger signal 16 and is correspondingly marked within the QRS complex.

The different heart cycle phases of successive heart cycles and, in particular, the course of these heart cycle phases can be compared with one another by temporal averaging between several heart cycles for each corresponding point in time in the heart cycles, so that data points for the same point in time that is correspondingly spaced apart in time from the selected reference point, but for different successive heart cycles, represent a useful signal for the same respective cardiac cycle phase. The averaging over time thus makes it possible for individual outliers, which, for example, are not in a relevant heart cycle range and are therefore not characteristic of a specific heart cycle phase, to nevertheless not affect the determination of the amplitude change, especially since the height of the corresponding data point for other heart cycles is relatively low.

An increase in the number of heart cycles compared can further improve the temporal stability of the trigger signal 16, for example with a regular heart rhythm, as can be seen, for example, from FIGS. 8B with ten heart cycles and 8C with 65 heart cycles. In addition to a different number of cardiac cycles, the data points or the measurement signals were also exponentiated in the present case, so that the data points with a low measurement signal value are less pronounced. This is illustrated by the fact that the respective curves run even less jaggedly, ie with fewer deflections, with a simultaneous increase in the number of cardiac cycles, and thus interference signals at least can be partially hidden. FIG. 9 shows a monitoring and graphic adjustment possibility of the time interval 18 for determining the amplitude change according to the invention.

In the case of averaging over time, a specific or predetermined trigger point for the number n of heart cycles or heart actions can be required, which is preferably an R trigger 16 . The determination of the at least one change in amplitude can also be adjusted manually, for example to extend or restrict a specified time period or a time interval. In the coupled state with a display, the control and regulation unit is preferably set up to display a signal for displaying successive heart cycles detected from the ECG signal for the corresponding points in time, the at least one amplitude change determined, and a manipulable time range specification which shows the Area of the evaluated data points indicates to be output to the display. The evaluation unit is also advantageously set up to receive an adjustment signal from the coupled display and to determine the at least one amplitude change when adjusting the time range for successive heart cycles in the adjusted relative time range.

Correspondingly, according to this example, an overlap of the current heart cycle with the two most recent heart cycles is shown in a graphical representation by way of example. The graphical representation also shows the currently determined at least one amplitude change and a time marker for the current output of the control and regulation signal 16 or the trigger signal 16 on a display coupled to the control and regulation unit, with a time window showing the current time interval 18 for evaluating the corresponding data points. In other words, the time window forms a monitoring period for a sampling complex, with the heart cycles preferably being completely within the time window in order to acquire a complete data set within the time interval 18 . FIG. 9 is a schematic representation of the heart cycles, which accordingly have any morphology.

The time intervals shown are also only examples, but can also be preset as predefined values. The time window is preferably selected or set in such a way that at least the current heart cycle is displayed starting from a morphologically and/or physiologically specified reference point and more preferably also up to a corresponding reference point. For example, the time window can thus represent a time interval 18 which represents at least the current heart cycle from the end of the previous T wave to the end of the current T wave. By adjusting the time window, for example by shifting the limit values on a horizontal axis, the time interval 18 can be shifted and/or lengthened or shortened, depending on how the displayed heart cycles require it with regard to a heart cycle phase relevant to the at least one amplitude change. A certain flexibility and even intuitive usability for optimizing the at least one amplitude change is thus provided for the user. Thus, when the time window is adjusted or shifted, the position of the trigger signal in the window can also be shifted (not shown). In the present case, three successive heart cycles, ie the current and the last two heart cycles, are shown overlapping, but only two or more heart cycles can be provided for determining the amplitude change, for example 10 or 65, as described above.

As far as applicable, all the individual features that are presented in the exemplary embodiments can be combined with one another and/or exchanged without departing from the subject matter of the invention.

Reference List

10 control and regulation unit

12 ECG signal 12A First measurement signal

12B Second measurement signal

12C sum signal

14 amplitude change

16 Control and/or regulation signal or trigger signal 18 Time interval

100 evaluation unit

O Transesophageal ECG lead

P Start of P wave

Q Beginning of Q wave S End of S wave

T Transthoracic ECG lead

Claims

27

Claims Control and regulation unit (10) for extracorporeal circulatory support, which is set up to receive a measurement of an ECG signal (12) of a supported patient over a predetermined period of time, the ECG signal (12) for each point in time within a cardiac cycle comprises a plurality of data points, wherein the control and regulation unit (10) comprises an evaluation unit (100) which is set up to spatially and/or temporally evaluate the data points for at least one point in time and from the evaluated data points at least one amplitude change (14) within the determine the heart cycle, and wherein the control and regulation unit (10) is further set up to output a control and/or regulation signal (16) for the extracorporeal circulatory support at a predetermined point in time after the at least one amplitude change (14). Control and regulation unit (10) according to claim 1, wherein the evaluation unit (100) is set up to evaluate the data points for a predetermined time interval (18) based on at least one heart cycle phase of the ECG signal (12) and the at least one amplitude change (14 ) within the time interval (18). Control and regulation unit (10) according to claim 1 or 2, wherein the evaluation unit (100) is set up to determine the at least one amplitude change (14) based on data points for at least two points in time. Control and regulation unit (10) according to one of the preceding claims, wherein the evaluation unit (100) is set up to determine at least one specific amplitude change (14) which is characteristic of a heart cycle phase. Control and regulation unit (10) according to claim 4, wherein the evaluation unit (100) is set up to determine at least one specific amplitude change (14) which is characteristic of a P wave or R wave.

. Control and regulation unit (10) according to one of the preceding claims, wherein the EKG signal (12) at least a first measurement signal (12A) from a first EKG derivation (O, T) and a second measurement signal (12B) from a second EKG - derivation (O, T), wherein the first and second ECG derivations (O, T) are spatially separated from one another and wherein the evaluation unit (100) is set up to spatially evaluate the data points and the at least one amplitude change (14) based to be determined by adding or averaging the measurement signals 12A, 12B). . Control and regulation unit (10) according to one of the preceding claims, wherein the EKG signal (12) comprises a measurement signal (12A, 12B) of a transthoracic EKG lead (T) and/or a transesophageal EKG lead (O) and/ or wherein the ECG signal (12) is an ECG signal (12) of a cardiac paced patient. . Control and regulation unit (10) according to one of the preceding claims, wherein the evaluation unit (100) is set up to determine an amplitude change (14) and a time interval and/or a frequency of the amplitude changes (14) for at least two heart cycles, wherein the control and regulation unit (10) is set up to output a signal characterizing the time interval and/or the frequency. . Control and regulation unit (10) according to one of the preceding claims, wherein the evaluation unit (100) is set up to continuously, preferably in real time, the at least one amplitude change (14) with each successive heart cycle detected from the ECG signal (12). determine. 0. Control and regulation unit (10) according to one of the preceding claims, wherein the evaluation unit (100) is set up to evaluate the data points over time and the at least one amplitude change (14), based on an addition or averaging of the data points, for at least one to determine the corresponding point in time in the at least two cardiac cycles. 1 . Control and regulation unit (10) according to claim 10, wherein the evaluation unit (100) is set up to determine the at least one amplitude change (14) based on averaging or adding the data points from 10 to 40 cardiac cycles or 10 to 100 cardiac cycles, preferably between 40 and 80 cardiac cycles. 2. Control and regulation unit (10) according to claim 10 or 11, wherein the corresponding point in time in the at least two heart cycles is identical in time to the reference point occurring in the at least two heart cycles, the reference point preferably being morphological and/or is physiologically predetermined by a signal in the ECG, in particular by a maximum in the ECG signal. Control and regulation unit (10) according to any one of claims 10 to 12, which is set up in the coupled state with a display to a signal for displaying from the ECG signal (12) detected successive heart cycles for respective temporally corresponding points in time; the determined at least one amplitude change (14); and to output to the display a manipulable time range specification that characterizes the range of the evaluated data points, the evaluation unit (100) also being set up to receive an adjustment signal from the coupled display and the at least one amplitude change (14) when the time range for successive cardiac cycles in the adjusted relative time domain. Control and regulation unit (10) according to any one of claims 10 to 13, wherein the EKG signal (12) at least a first measurement signal (12 A) from a first EKG derivation (O, T) and a second measurement signal (12B). a second ECG derivation (O, T), wherein the first and second ECG derivations (O, T) are spatially separated from one another and wherein the evaluation unit (100) is set up to calculate the at least one amplitude change (14) based on a averaging or adding the data points for the at least two measurement signals (12A, 12B). Control and regulation unit (10) according to one of the preceding claims, wherein the evaluation unit (100) is set up to raise the respective data points or the evaluated data points to a power, preferably with an exponent of greater than 1.3. Control and regulation unit (10) according to claim 15, wherein the exponent is 1.3 to 5.0 or 1.3 to 2.0. A system for extracorporeal circulatory support of a patient, comprising:

- A device for extracorporeal circulatory support, comprising a blood pump which is fluidly connected to a venous patient access and a arterial patient access can be connected and is designed to provide a blood flow from the venous patient access to the arterial patient access,

- an interface for receiving an ECG signal from the patient, and

- A control and regulation unit according to one of the preceding claims, which is communicatively coupled to the device and wherein the control and regulation signal is a control and regulation signal for adjusting the blood pump. 18. The system of claim 17, further comprising an EKG machine communicatively coupled to the interface. Method for controlling/regulating an extracorporeal circulatory support, comprising the steps:

Evaluation of the data points for at least one point in time, the evaluation taking place spatially and/or temporally and at least one amplitude change within the heart cycle being determined from the evaluated data points, and

Setting a control and/or regulation signal for the extracorporeal circulatory support at a predetermined point in time after the at least one amplitude change. 20. The method of claim 19, wherein the at least one determined amplitude change is characteristic of a P-wave or R-wave. The method according to claim 19 or 20, wherein the ECG signal comprises at least a first measurement signal from a first ECG derivation and a second measurement signal from a second ECG derivation, the first and second ECG derivations being spatially separated from one another and the data points are evaluated spatially and the at least one amplitude change is determined based on an addition and/or averaging of the measurement signals. Method according to one of claims 19 to 21, wherein the EKG signal comprises a measurement signal of a transthoracic EKG derivation and/or a transesophageal derivation. 31 Method according to one of claims 19 to 22, wherein at least one amplitude change for at least two heart cycles and a time interval and/or a frequency of the amplitude changes are determined, with a signal characterizing the time interval and/or the frequency being output. Method according to one of Claims 19 to 23, in which the at least one change in amplitude is determined continuously for each successive heart cycle detected from the ECG signal. The method according to any one of claims 19 to 24, wherein each point in time at a time interval from the reference point is chosen to be the same for each heart cycle and the data points are evaluated over time and the at least one amplitude change is based on an averaging or addition of the data points for at least one corresponding in time to a reference point Time can be determined from at least two heart cycles. Method according to claim 25, wherein the at least one change in amplitude is determined based on an averaging or addition of the data points from 10 to 100 heart cycles or 10 to 40 heart cycles, preferably between 40 and 80 heart cycles. Method according to Claim 25 or 26, in which the point in time for each cardiac cycle remains the same in terms of time in relation to a reference point, the reference point preferably being predetermined morphologically and/or physiologically by an EKG signal. The method according to any one of claims 25 to 27, wherein successive heart cycles recorded from the ECG signal for times corresponding in time to a reference point, the at least one amplitude change and a manipulable time range specification, which characterizes the range of the evaluated data points, are shown on a display and wherein an adjustment signal received from the coupled display is used to determine the at least one amplitude change in the adjusted relative time domain for successive cardiac cycles. The method according to any one of claims 19 to 28, wherein the ECG signal comprises at least a first measurement signal from a first ECG derivation and a second measurement signal from a second ECG derivation, the first and second ECG derivations being spatially separated from one another and wherein the at least one change in amplitude is determined based on an averaging or addition of the data points for the at least two measurement signals. 32 Method according to one of claims 19 to 29, wherein the respective data points or the evaluated data points are raised to a power, preferably with an exponent of greater than 1.3. The method according to claim 30, wherein the exponent is 1.3 to 5.0 or 1.3 to 2.0. Method for monitoring a temporal trigger stability of an extracorporeal circulatory support, comprising the steps:

Evaluation of the data points for at least one point in time, the evaluation being spatial and/or temporal and at least one amplitude change within the heart cycle being determined from the evaluated data points, the at least one determined amplitude change preferably being characteristic of a P wave or R wave , and wherein at least one change in amplitude is determined for at least two heart cycles,

determining a time interval and/or a frequency of the amplitude changes, and

Outputting a signal when the time interval and/or the frequency of the amplitude changes exceeds a predetermined threshold.