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    • 专利摘要:

    公开号:AT510252A1
    申请号:T19832010
    申请日:2010-03-29
    公开日:2012-02-15
    发明作者:
    申请人:Miracor Medical Systems Gmbh；
    IPC主号:
    专利说明:

    - 1 • * *
    ♦ Φ · «« VI
    The invention relates to a device for the intermittent occlusion of a blood vessel, in particular a vein draining the organ system, comprising an occlusion controllable occlusion, a control device connected to the occlusion device, at least one sensor for continuous or periodically detected detection of at least one physiological measurement value and one of Sensor-fed measured value memory for saving a series of measured values.
    Arterial blood that supplies the heart muscle can pass through and sustain healthy heart tissue but has difficulty reaching the ischemic tissue. This obstructs the supply of nutrients to the ischemic tissue as well as the removal of degradation products of the metabolism of the ischemic tissue. In this connection, it has already been proposed to provide the ischemic tissue with blood by retrograde perfusion. The retroinfusion of blood in coronary veins plays an important role in the field of myocardial protection during open heart surgery. A typical such procedure is, for example, the balloon dilatation of an atherosclerotic narrowed coronary artery. In this method, also known as percutaneous transluminal coronary angioplasty (PTCA), a balloon catheter is guided under X-ray control into the area of the stenosis of the coronary artery and the arteriosclerotic plaque is compressed by inflating the balloon located at the end of the catheter. During dilation of the balloon downstream of the artery there is no oxygen supply to the tissue, and functional changes in the ischemic area of the myocardium can be detected even in dilatations lasting longer than 30 seconds. Corresponding problems of ischemic protection of the myocardium are also present in other coronary vascularization interventions, e.g. in atherectomy, coronary arthroplasty and laryngoplasty * * * * * * * * * * * * * * * * * * * ♦ «* * * * * ** * * t * * * * Μ »« ··· - 2 - ser applications. Even in acute myocardial infarction there is a shortage of myocardium.
    In connection with the short-term ischemic protection, a retroinfusion of arterial blood or other nutritive fluids into a vein of the relevant ischemic area of the myocardium has been carried out for some time. The blood is pumped via the corresponding vein into the nutritive capillaries of the ischemic area and supplies the myocardium in this region with oxygen and substrates.
    A device for retroinfusion of coronary veins has become known from US 4,934,996, with which a pressure-controlled intermittent coronary sinusocclusion can be made. The device comprises means for occluding the sinus, e.g. an inflatable balloon catheter, a pressure gauge for measuring the fluid pressure within the coronary sinus, and a controller that generates trigger signals for the occluder to trigger or cancel an occlusion. In this case, the control unit is designed such that the pressure maximum in the coronary sinus is measured during each heartbeat, a plateau value of the pressure maxima of successive heartbeats is calculated and the occlusion of the coronary sinus is canceled on the basis of the plateau value of the pressure maxima.
    The occlusion of the coronary sinus causes a pressure increase and subsequently a retroperfusion of blood via the corresponding vein into the nutritive capillaries of the ischemic area, so that these areas can be supplied with nutrients. When the occlusion is removed, the retroperfused blood is flushed out, at the same time removing the waste products of the metabolism. Thus, in the method according to US Pat. No. 4,934,996, a systolic pressure curve is calculated on the basis of the measurement of the maximum pressure in the coronary sinus during each heartbeat, the intermittent occlusion being dependent on the plateau value of the systolic
    Pressure curve is controlled. The course of the estimated systolic pressure curve also allows a conclusion on the performance of the heart, for example, the slope of the curve reflects the contractility of the heart. The slope of the curve naturally also has an influence on the height of the plateau value, whereby a lower plateau value is achieved with a flatter curve, the plateau moreover being achieved after a longer period of time after the introduction of the occlusion, compared to a healthy heart. A shift in the curve also occurs when a coronary vessel is occluded temporarily or through a complication for an interventional procedure such as PTCA or stenting, so that the pressure curve increases more slowly and takes longer to reach the plateau.
    Methods for the intermittent occlusion of a blood vessel and in particular of the coronary sinus have also become known from WO 03/008018 A2, WO 2005/120602 A1 and WO 2005/120601 A1. Such methods are also applicable to acute myocardial infarction, and it has been demonstrated that periodontal occlusion of the venous outflow may result in a reduction of the infarct area.
    It has also been proposed to divert blood from the coronary veins of well perfused areas into the poorly supplied vascular districts.
    The previously known devices are suitable exclusively for the temporary treatment of a patient during an operative procedure. Such an intervention is usually associated with considerable effort and requires not only for the placement of the occlusion device in the occluding blood vessel a doctor. The operation of the occlusion device requires constant monitoring by a doctor. During intermittent occlusion, critical parameters must be monitored, such as pressure in the occluded blood vessel, and physiological ···················································································.
    Measurements are constantly analyzed to see whether due to the treatment, the desired improvement of the condition and in particular an increase in the performance of the heart has occurred. Furthermore, it must be decided on the basis of the measured values when the treatment, i. the process of intermittent occlusion can be terminated.
    A disadvantage associated with the methods and devices for intermittent occlusion of a blood vessel known from the prior art is also that the treatment can usually only be carried out when the patient has serious complaints, i. at a time when irreparable damage may have occurred. A preventive application of the intermittent occlusion of the blood vessel even with a small deviation of certain physiological parameters from the patient-specific desired values is generally not possible.
    The present invention now aims to improve the known from the prior art device for intermittent occlusion of a blood vessel in that the treatment cost is reduced and can be dispensed with a permanent medical control during treatment.
    The invention further aims to automate the control of the intermittent occlusion as far as possible, the control should be such that an optimal treatment result can be achieved.
    The underlying object of the present invention is achieved by a device for intermittent occlusion of a blood vessel, in particular a vein draining the organ system, comprising - an occlusion medium controllable for intermittent occlusion, 5 - a control device connected to the occlusion device, - at least one sensor for continuous or Recording of at least one physiological measured value carried out at intervals and - a measured value memory fed by the sensor for storing a measured value series which is characterized in that the measured value series is supplied to the control device which is designed for computational, in particular statistical evaluation of the measured value series and with the occlusion device for starting or cooperating to terminate the intermittent occlusion in response to the result of the evaluation.
    With the device according to the invention, a method for the treatment of the heart or circulatory disorders can be carried out, which comprises the intermittent occlusion of a blood vessel, in particular a vein draining the organ system, and in which the blood vessel is alternately occluded and released. The method is characterized in that the size of at least one physiological value of the patient is determined at intervals or continuously, that the respective measured values are stored and a measured value series is obtained, that a mathematical, in particular statistical evaluation of the measured value series is made and that in dependence from the result of the evaluation, the intermittent occlusion is started or terminated.
    With the method and the device a completely automated operation is possible, whereby on the basis of the arithmetic and in particular statistical evaluation of the measured value series the optimal time can be determined at which the treatment in which the blood vessel is intermittently occluded is started and when the treatment ends shall be. Such an automated operation is particularly necessary when the occlusion device is permanently implanted in the blood vessel, since in this case exposure by the doctor is generally no longer possible. It is therefore necessary for the control device, on the basis of the measured values determined, to decide whether and how long a treatment should be carried out with the aid of the intermittent occlusion. For this purpose, according to the invention a mathematical and in particular statistical evaluation of the measured value series is provided, wherein the process of the intermittent occlusion is started or terminated depending on the result of the evaluation. As already mentioned, the process of intermittent occlusion comprises a sequence of alternating occlusion phases in which the blood vessel is occluded and release phases in which the blood vessel is released.
    In order to enable as precise a determination as possible of the time of commencement or termination of the treatment, it is provided according to a preferred development that the arithmetic evaluation is carried out after each measurement value determination. The arithmetical evaluation thus always takes into account the most recent measured value, so that a constant updating of the evaluation results is carried out.
    The arithmetic evaluation itself can be made in various ways. According to a first preferred method, it is provided that the mathematical evaluation of the measured value series comprises the conversion of the individual measured values of the measured value series into derived measured values, a derived measured value series being obtained. The conversion is necessary, for example, if the physiological value to be used for the evaluation can not be measured directly. In the context of the present invention, measurable quantities are preferably the blood pressure in the region of the blood vessel, the blood mass or volume flow in the region of the blood vessel, the electrical resistance, the conductivity, the electrical impedance in the region of the blood vessel, in particular of the heart and / or the lung, the ECG and / or a metabolic parameter, such as, for example, the O 2 saturation and / or the lactate content or the pH of the blood.
    According to a further preferred procedure, it is provided that the arithmetic evaluation of the measured value series comprises the determination of the difference between the respectively last two measured values of the measured value series or the difference of the respectively last two derived measured values of the derived measured value series, a difference value series being obtained. The evaluation can be made in this context such that when a predetermined difference occurs, the intermittent occlusion is started or terminated. Such a jump behavior of the measured value can be an indicator for a critical condition of the blood vessel or the heart, so that the treatment must be started immediately. Occasional jumps in the measured values can also be regarded as outliers, which can be attributed, for example, to errors in the measured value determination. In order to disregard such outliers in the evaluation, the arithmetic evaluation may preferably include a statistical evaluation, in which a trend detection is performed and short-term outliers are suppressed.
    The arithmetic evaluation of the measured value series can include the comparison of the individual measured values with a predetermined absolute limit value in order to detect an impermissible or critical condition of the blood vessel or heart when the limit value is exceeded or undershot. Alternatively, however, a relative limit value may also be of interest, and in this context the training is preferably carried out in such a way that the mathematical evaluation of the measured value series comprises the determination of the cumulative differences of the difference value series. The cumulated difference represents the difference between the last measured value and the first measured value of the measured value series. - 8 - «f - 8 -« f * * * * «· ·« · I · · «· · · ·» I f · · · · · ff ff * · «» · f * ·· * · «
    According to a further preferred method, it is provided that the arithmetic evaluation of the measured value series comprises the determination of the change in the measured values of the measured value series or the derived measured values of the derived measured value series per time unit, with a derivation series being obtained. The change in the measured values per time unit reflects the speed of the change and thus corresponds to the first derivative of the measured value curve over time.
    A series of measured values changes with the cycle of the heartbeat, for example the blood pressure, the volume or mass flow of the blood or the like, wherein as a rule only the respective maximum or minimum value during a heartbeat is of interest for the evaluation. A further preferred development therefore provides that the arithmetic evaluation of the measured value series comprises the determination of local maxima and / or local minima of the values of the measured value series, the converted measured value series, the difference value series and / or the derivative series and that from the local maxima or minima an extreme value series is formed.
    In addition, it is often the case that a measured value or the local maxima and / or local minima occurring during the respective heartbeats increase or decrease during the occlusion phase with each heartbeat. In this context, it may be advantageous to use only the maximum value for the evaluation occurring during an occlusion phase. A further preferred procedure therefore provides that the maximum b2w occurring in each case during an occlusion as a local maximum or minimum. Minimum of said values is selected.
    The control device, in which the arithmetic evaluation of the measured values or measured value series is undertaken, can interact in different ways with the occlusion device, and accordingly the time of commencement or termination of the intermittent occlusion can be reduced to •••••• »» · 9 * ······················································. According to a preferred embodiment, it is provided in the context of the present invention that the arithmetic evaluation of the measured value series comprises the comparison of the values of the measured value series, the derived measured value series, the difference value series, the derivative series and / or the extreme value series and / or the cumulative differences with a predetermined limit value , wherein the intermittent occlusion is started upon reaching the threshold. In the idle state, in which no intermittent occlusion is performed, it is thus respectively monitored in the mathematical evaluation of the measured values whether a predetermined limit value is reached. For example, the contractility of the heart can be monitored on the basis of measured values. Furthermore, on the basis of characteristic changes of the ECG, for example on the basis of the so-called " ST elevation " an ischemia can be detected. When contractility or STM elevation reaches or falls below a threshold that may be patient dependent, the occlusion device is directed to perform an intermittent occlusion. The beginning of the intermittent occlusion can also be determined, for example, by reference to the 02 saturation of the blood or by means of the pH and in particular by means of the lactate content.
    Another way to determine the optimal timing of the onset of intermittent occlusion is to measure the electrical impedance of the thorax or areas of the thorax, such as the thorax. to determine the lung. The electrical impedance is indirectly proportional to the fluid content of the detected area, so that, for example, a left heart failure, in which blood accumulates in the lungs, can be detected on the basis of the electrical impedance. In this context, reference is made to WO 2008/070818 A2. During the intermittent occlusion, the readings are also evaluated as described, with the optimal time to terminate the intermittent occlusion fixed. "....... Μ · · · must be made. In this context, a preferred development provides that the arithmetic evaluation of the measured value series comprises the detection or estimation of a plateau value of the values of the measured value series, the derived measured value series, the difference value series, the derivative series and / or the extreme value series, the intermittent occlusion at the plateau value or at a predetermined percentage of the plateau value is terminated. The achievement of a plateau value indicates that a characteristic measured value has changed and reached a stable final value. Upon reaching such a steady state. For example, once the physiological parameter has dropped below a critical value or has risen above a critical value, it has again reached a stable normal value, so that the process of intermittent occlusion can be ended.
    In a preferred refinement, a new series of measurements is started when starting and / or stopping the intermittent occlusion, so that the evaluation can only be based on the measured value determined in each case after the last starting or ending of the intermittent occlusion.
    The measured values determined can not only be used to determine the beginning and the end of the intermittent occlusion, but can also be used to control the individual occlusion and release phases during the intermittent occlusion. In this context, it is preferably provided that the measured values ascertained during the occlusion of the blood vessel are each subjected to a separate computational evaluation and that the individual occlusion phases of the intermittent occlusion are ended as a function of the result of the evaluation. The same applies to the release phases, wherein it is preferably provided here that the measured values determined during the release of the blood vessel are each subjected to a separate computational evaluation and that the individual release phases of the intermittent occlusion depending on the result of the evaluation.
    The device according to the invention is particularly advantageous in an implanted occlusion device, as will be described in more detail below. The implantable device for intermittent occlusion of a blood vessel, particularly a vein draining the organ system, such as e.g. of the coronary sinus, comprises an occlusion device which can be controlled for intermittent occlusion and positioned in the blood vessel, at least one sensor for continuous or intermittent detection of at least one physiological measured value, a preferably implantable control device to which the at least one physiological measured value is supplied and which with the occlusion means for controlling the intermittent occlusion in function of the measured value cooperates, and an implantable anchoring means separate from the occlusion means for positioning the occlusion means relative to the blood vessel, which can be brought into operative connection with the blood vessel. The occlusive means is fixed for positioning the same relative to the blood vessel, in particular on the anchoring means.
    The implantable device includes all components required for autonomous operation. In addition to the occlusion device, which can be controlled to intermittent occlusion and positioned in the blood vessel, the implantable device comprises at least one sensor and a control device so that the occlusion device can be controlled in dependence on the measured values detected by the at least one sensor. In this case, for example, a pressure-dependent control is possible, as described in the documents US 4,934,996, WO 03/008018 A2, WO 2005/120602 Al and WO 2005/120601 Al. In this case, the control comprises, in particular, the following: "··········································· The determination of the optimum times at which the blood vessel is occluded by the occlusive means and those times at which the blood vessel is in turn released. The intermittent occlusion here comprises a plurality of alternately performed occlusion and release phases. Furthermore, the device according to the invention comprises an anchoring means separate from the occlusion means with the aid of which the occlusive means can be positioned in the blood vessel or relative to the blood vessel. With the aid of the anchoring means, a permanent fixation of the occlusive means and possibly of the at least one sensor can be pre-established so that the occlusion means remain in the blood vessel for a long time and can be operated completely automatically. The treatment of a patient requires only a single surgical operation by the physician, namely the implantation of the device according to the invention into a blood vessel of the patient, whereby not only the occlusive device is implanted, but also the at least one sensor, the control device and the anchoring means. After implantation, the patient may leave the hospital with the intermittent occlusion of the blood vessel as needed. It is conceivable that the starting of the intermittent occlusion is triggered externally, for example by the patient himself or by a doctor, or that an automatic triggering takes place on the basis of the measured values detected by the at least one sensor.
    In the intermittent occlusion devices according to the prior art, the intermittent occlusion was performed with the aid of a balloon introduced into the blood vessel, which was expanded to occlude the blood vessel and emptied again to release the occlusion. The expansion and contraction of the balloon took place with the aid of a gaseous or liquid medium, which was pumped into the balloon and again sucked off. Such a occlusive agent is not necessarily suitable for permanent implantation, since on the one hand a corresponding reservoir for the liquid or 13
    gaseous medium would have to be provided in the body of the patient and on the other hand, the risk of bursting of the balloon and thus leakage of the medium is too high. According to a preferred embodiment of the device according to the invention, the occlusion means is therefore not driven hydraulically or pneumatically, but as a mechanically or electrically driven occlusion means, wherein the drive is preferably electrically actuated. Such a mechanical or electrical drive for the occlusive means can be easily implanted, wherein only an electrical power supply is to be provided for the electrical control of the drive. In this case, the electrical energy supply can similarly be implanted at a suitable position in the body of the patient, as is also the case with pacemakers, whereby the electrical connection lines to the occlusive means or to the drive of the occlusion device are guided in the body. In this case, the electrical energy supply can be integrated, for example, with the control device into a single component, so that the outlay for the surgical procedure can be reduced.
    Mechanically or electrically driven occlusion means are conceivable in a large number of embodiments. For example, according to a preferred embodiment, the occlusion means comprise an electrically controllable valve. The occlusion means may preferably have an electrically controllable actuator, which may be formed for example by an electromagnet. The actuator may cooperate with at least one component which is movable in response to the actuation of the actuator or the electromagnet between a position occluding the blood vessel and a position releasing the blood vessel. For example, the actuator can interact with a foldable membrane. According to another embodiment, the actuator may cooperate with a snap-on and collapsible closure member in the manner of a screen.
    Also conceivable is an embodiment in which the actuator is formed by a shape memory material ("shape memory material"). The shape of such a material changes, for example, depending on an applied voltage or on the temperature. Also, electroactive polymers are conceivable in this context.
    In another embodiment, at least one flap may be provided, for example made of conductive plastic, wherein the flap can repel depending on the electrical state of charge of a counter member, such as another flap, whereby the flap between a closed and an open position is movable. Such mechanisms have become known, for example, in connection with heart valves.
    In those embodiments in which the occlusion means has at least one movable part between a closed position in which the blood vessel is occluded and an open position in which the blood vessel is not occluded, a preferred embodiment provides that the actuator is electrically energized the movable part cooperates to apply a force acting in the closing direction. This has the consequence that the movable part is acted upon in the closing direction and the movable part is accordingly brought against the resistance of the blood flow within the blood vessel in the closed position, so that in a possible failure of the actuator due to the upcoming pressure of the pent-up blood an automatic reset of the movable part, so that the blood can flow undisturbed through the blood vessel in the sequence. As a result, the reliability of the device according to the invention is substantially increased.
    In order to achieve a suitable anchoring of the occlusive means, the anchoring means is preferably designed as a vascular implant and in particular as a radially expandable stent. Such stents are generally used in vascular surgery. * »%» · »« ** ** ** ** Φ Φ · · * -i * * Ji · «I * · · t · * · t • ** *« · «* * # "" * * T * "- 15 - commonly known and usually designed so that they can be introduced into the corresponding blood vessel in compressed form, in which they have a reduced outer diameter, and after reaching the desired position in a expanded form in which they have an enlarged outer diameter, can be brought. In the expanded state, the stent exerts a controlled radial contact pressure on the inner wall of the blood vessel, so that the fixation of the assumed position is ensured. The holding force can be increased by a special structure of the stent jacket, such as by a helical structure or by friction-increasing measures on the outer jacket.
    At least part of the actuator can be accommodated in the stent.
    According to an alternative embodiment it is provided that the anchoring means is formed by an artificial vessel. In this case, the implantation of the device according to the invention comprises the replacement of a section of the blood vessel with the artificial vessel, which connects to the adjacent region of the natural vessel and in this way enables anchoring of the occlusion device connected to the artificial vessel.
    Preferably, the embodiment is developed in such a way that the anchoring means has or forms a receiving space for the occlusive means. In this case, the occlusive means is arranged directly in the anchoring means, for example in the stent or in the artificial vessel, which has the advantage that the implant can be implanted as a prefabricated unit.
    As already mentioned, the control of the occlusion means takes place as a function of at least one physiological measured value. In this context, the training is preferably developed in such a way that a timer is provided in order to be able to: • * • * • ·
    ♦ · · · «i * ·« · · · · · · «· · · · · · ············································································································································································································· The smaller the predefined time intervals, the more precise the control can be, since in each case the most recent measured value can be used for the control.
    Preferably, a memory for the physiological measured values and / or the occlusion processes is provided, which is connected to a sensor for the wireless transmission of the memory contents. In this case, for example, an external evaluation device can be provided which reads out the data contained in the memory wirelessly and allows the patient and / or the attending physician to analyze and evaluate the data. This makes it possible in a simple manner to check the functioning of the implantable device and to make regular diagnoses.
    The control of the occlusion device can be done in a variety of ways. It is preferably provided that the sensor be used to detect a fluid pressure, a fluid volume, a flow, an electrical resistance, an electrical impedance, cardiac currents for establishing an electrocardiogram (ECG) and / or a metabolic parameter, such as e.g. the 02 saturation or the pH or the lactate content of the blood is formed. Only one of these parameters can be measured or a majority. Usually, the corresponding measured values have to be fed to a mathematical or statistical evaluation in order to generate suitable control signals for the occlusive means. The sensor can be arranged either in the blood vessel to be occluded, in particular at or in the vicinity of the occlusion device, or else in a separate unit not arranged in the blood vessel but also implantable, which houses the power supply and / or the control device. If several sensors are provided, at least one sensor in the blood vessel and at least one other sensor in the separate unit can be arranged. 17 »« ·
    The invention will be explained in more detail with reference to embodiments shown schematically in the drawing. 2 shows an implanted occlusion device in cross section, FIG. 3 shows a representation of the pressure curve delivered by a pressure sensor, FIG. 4 shows the first derivative of the pressure curve, FIG FIG. 6 shows the curves according to FIGS. 3 and 4 over a plurality of occlusion and release phases.
    FIG. 1 schematically shows a human heart 1. Arranged in the coronary sinus 2 is an occlusion device 3, which can be activated for intermittent occlusion of the coronary sinus 2. The control device for the control of the occlusive means is denoted by 4. The control device 4 is supplied with the measured values of a sensor 5 via a line. The sensor 5 is designed for example as a blood pressure sensor and measures the pressure in the coronary sinus. To the control device 4, an electrode 6 is further connected, via which a current pulse can be emitted. With the aid of the sensor 7, which is arranged diametrically opposite to the electrode 6 with respect to the heart 1 or the unrepresented lung, the electrical impedance of the thorax or of the heart 1 and of the lung can be determined, which in turn determines a Conclusion on the contractility of the heart 1 allowed. Furthermore, a sensor 22 may be provided which serves to measure the conductivity of the blood in the coronary sinus, and studies have shown that the conductivity of the blood is a measure of the contractility of the heart. In the control device 4, the measured values of the sensors 5 and 7 are evaluated, wherein the occlusion means 3 is controlled as a function of the result of the evaluation. In particular, the length of the individual occlusion and release phases is determined during the intermittent occlusion. Furthermore, based on the measured values, the optimum time for the beginning and the termination
    ♦ ♦ * • der der der der der der der der der der der der der der der der der der der der der der. The exact control algorithm will be explained with reference to Figs.
    The power supply of the control device 4 and possibly of the occlusion means 3 is denoted by 8.
    2, the coronary sinus is shown in more detail and it can be seen that an anchoring means 9 designed as a stent has been inserted into the coronary sinus 2. The stent 9 cooperates with the inner wall of the coronary sinus 2 so that the stent 9 is fixed in position. The flow direction of the blood with open occlusion means 3 is designated by 10. The stent 9 carries a pressure sensor 5, which measures the pressure in the coronary sinus 2. The occlusion means is formed by at least two flap-like components 11 which can be moved between a closed position in which the coronary sinus 2 is occluded and an open position in which the coronary sinus is opened, that is, not occluded. The movement of the flap-like components can be done by pivoting. 2, the flap-like components 11 are shown in an intermediate position. For occluding the flap-like components 11 are pivoted against the direction of the arrow 10 in the closed position and held by applying force in this position. Once the application of force ceases, i. as soon as the actuation of the occlusion device is stopped, the flap-like components 11 are automatically pressed by the blood pressure applied, so that an automatic opening of the coronary sinus is effected. Such a configuration has the consequence that the coronary sinus 2 is automatically opened even in the event of a malfunction, for example when the power source is dry, so that the malfunction can not lead to damage to the organism.
    When the occlusive device closes the coronary sinus 2 during an occlusion phase, the blood accumulates in the coronary sinus 2 and retroperfused into the surrounding tissue. When the occlusion agent is opened during the subsequent release phase, the accumulated blood is shaken out. The alternating occlusion and release phases are repeated until an improvement in the situation is established on the basis of the measured values.
    The stent 9 is connected to two electrical lines 12, one line serving to transmit the measured values of the sensor 5 to the control device 4 and the other line 12 to electrically actuate the occlusion device.
    3 shows the measured values determined by the pressure sensor 5. The pressure curve shows the course of the pressure in mm Hg over time. It can be seen that the pressure maximum occurring during each heartbeat increases during the occlusion phase 13 with each heartbeat until the pressure maxima reach an upper plateau value, the pressure maxima being designated 15. During the release phase 14, the pressure drops abruptly, the pressure maxima reach a lower plateau value. The pressure maxima 15 in this case form an extreme value series. The pressure maxima 15 can be approximated by a curve 16 (occlusion phase) and a curve 17 (release phase). The approach is preferably carried out according to the method of least squares. The choice of the duration of the individual occlusion and release phases can be made on the basis of the approximated curves 16, 17.
    However, the choice of the duration of the individual occlusion and release phases can also be based on the time derivative dp / dt of the pressure curve. The first derivative dp / dt of the pressure curve is shown in FIG. The graph shows that during each heartbeat again a local maximum and a local minimum of the first derivative occur. The location of the local maximum indicates the time at which the pressure increase is fastest. The location of the local minimum indicates the time at which the pressure drop is fastest. FIG. 4 shows the curve 18 approximating the local maxima of the first derivative and the curve 19 approximating the local minimums of the first derivative for the occlusion phase. It can be seen that the maxima of the first derivative occurring in successive heartbeats initially become higher until they reach the maximum at the point 20 during the occlusion phase and then sink again. The same applies to the point 21 of the minima of the first derivative occurring in successive heart beats. The points 20 and 21 can be computationally determined by setting the derivative of the approximate curves 18 and 19 equal to zero.
    The positive values of the time derivative dp / dt of the pressure curve (see curve 18) are an indicator of the contractility of the heart, whereby the occlusion phase 13 is terminated when the contractility reaches a maximum. However, the contractility of the heart can be determined not only on the basis of the time derivative dp / dt of the pressure curve, but instead on the basis of the conductivity of the blood in the coronary sinus determined with the sensor 22.
    In the illustration according to FIG. 5, the curve 16 approximating the local maxima of the pressure curve and the curve 18 approximating the local maxima of the first derivative dp / dt of the pressure curve are shown above one another. It can be seen that the maximum 20 of the curve 18 offers a significantly better recognizable and clearer indication of the end of the occlusion phase than the plateau value of the curve 16.
    The negative values of the time derivative dp / dt can also be used to determine the optimal time of completion of the respective occlusion phase. The negative values of the time derivative dp / dt are an indicator of the relaxation phase of the heart. The time of the maximum pressure drop rate (the time of each local minimum of the first during each heartbeat - 21 * ♦ * 9 *
    Derivation) represents the beginning of the isovolumic relaxation phase of the heart. If the occlusion phase now takes too long, the isovolumic relaxation phase is shortened. To avoid this shortening, the occlusion phase must be ended in time. This is achieved by the continuous evaluation of the first derivative of the pressure curve with respect to the local minima, in combination with the determination of the cardiac currents (ECG), the duration of the relaxation phase can be calculated and a trend detection can be performed.
    FIG. 6 shows the pressure curve and the corresponding first derivative dp / dt for a plurality of successive occlusion and release phases. Likewise, the approximated curves 18 and 19 are shown, and the maximum occurring during the individual occlusion phases 20 and the minimum 21 drawn. From the maxima 2 0 and the minima 21, an extremal series can now be formed, which can each be evaluated with regard to the development of the maximum or minimum in order to determine the optimal time of termination of the intermittent occlusion on the basis of the result of this evaluation. In a successful course of intermittent occlusion treatment, the value of the point 20 may increase from one occlusion phase to the next occlusion phase, or at least one trend toward increasing the value over a plurality of occlusion phases. The increase in the value of point 20 suggests an increase in myocardial contractility. If the value of the point 20 now reaches a predetermined target value or a plateau value, the intermittent occlusion and thus the treatment can be terminated. More often, however, during intermittent occlusion treatment, it is observed that the value of the point 21 becomes lower. The value of point 21 is representative of the diastolic phase of heart relaxation. The value is the lower, the greater the left ventricular - 22
    Pressure drop rate is, i. the faster the pressure in the occluded coronary sinus decreases during diastole. The determination of the time of the end of the intermittent occlusion can therefore also take place as a function of the value of the point 21. The intermittent occlusion and thus the treatment can be terminated, for example, when the value of the point 21 reaches a predetermined desired value or a plateau value.
    A combination of the evaluation of the change in the value of the point 20 and the change in the value of the point 21 can also be expedient.
    Further treatment may subsequently become necessary again if the constant monitoring of defined physiological parameters shows that the performance of the heart is deteriorating, for example if a measurement of the electrical impedance or the electrical conductivity of the thorax, in particular of the heart and / or the heart Lung, reveals an increase in fluid content in this area.
    权利要求:
    Claims (19)
    [1]
    - 23 • »

    1. A device for the intermittent occlusion of a blood vessel, in particular a vein draining the organ system, comprising - an occlusion (3) controllable for intermittent occlusion, a control device (4) connected to the occlusion means (3), at least one sensor {5,6 , 7) for the continuous or periodically recorded acquisition of at least one physiological measured value and a measured value memory fed by the sensor for storing a measured value series, characterized in that the measured value series of the control device {4) is supplied, which is designed for mathematical, in particular statistical evaluation of the measured value series and cooperating with the occlusion device (3) to begin or terminate the intermittent occlusion in response to the result of the evaluation.
    [2]
    2. Apparatus according to claim 1, characterized in that the control device (4) is designed to carry out the arithmetic evaluation after each measured value determination.
    [3]
    3. Apparatus according to claim 1 or 2, characterized in that the control device (4) has a conversion circuit for converting the individual measured values of the measured value series into derived measured values, wherein a derived measured value series is obtained.
    [4]
    4. Apparatus according to claim 1, 2 or 3, characterized in that the control device (4) for determining the difference between the last two measured values of the measured value series or the difference of the last two derived measuring

    * · * * · «···« - 24 - «* ····· ····················································································································································································
    [5]
    5. Apparatus according to claim 4, characterized in that the control device (4) is designed to determine the cumulative differences of the difference value series.
    [6]
    6. Device according to one of claims 1 to 5, characterized in that the control device (4) is designed to determine the change in the measured values of the measured value series or the derived measured values of the derived measured value series per time unit, wherein a derivative series is obtained.
    [7]
    7. Device according to one of claims 1 to 6, characterized in that the control device (4) for determining local maxima (15) and / or local minima of the values of the measured value series, the converted measured value series, the difference value series and / or the derivative series and to form an extreme value series (16,17,18,19) from the local maxima (15) or minima is formed.
    [8]
    8. The device according to claim 7, characterized in that the control device (4) is designed such that is selected as a local maximum or minimum occurring during an occlusion maximum (20) or minimum (21) of said values.
    [9]
    9. Device according to one of claims 1 to 8, characterized in that the control device (4) comparison circuit for comparing the values of the measured value series, the derived measured value series, the difference value series, the derivative series and / or the extreme value series and / or the cumulative differences with a predetermined threshold and cooperates with the occlusive means such that the intermittent occlusion is started upon reaching the threshold.
    [10]
    10. Device according to one of claims 1 to 9, characterized in that the control device (4) for detecting or estimating a plateau value of the values of the measured value series, the derived measured value series, the difference value series, the derivative series and / or the extreme value series is formed and so with the occlusive agent cooperates to terminate the intermittent occlusion at the plateau value or at a predetermined percentage of the plateau value.
    [11]
    11. The device according to one of claims 1 to 10, characterized in that the control device (4) cooperates with the occlusion means such that when starting and / or when terminating the intermittent occlusion in each case a new series of measurements is started.
    [12]
    12. Device according to one of claims 1 to 11, characterized in that the sensor (5,6,7) for detecting the blood pressure in the region of the blood vessel (2), the blood mass or volume flow in the region of the blood vessel (2), the electrical Resistance, the conductivity, the electrical impedance in the region of the blood vessel (2), in particular the heart (1) and / or the lung, the ECG and / or a metabolic parameter, such as the 02 saturation and / or the lactate content or the pH of the blood is formed.
    [13]
    13. Device according to one of claims 1 to 12, characterized in that the sensor comprises an electrode (6) for emitting a current pulse.
    [14]
    14. Device according to one of claims 1 to 13, characterized in that an evaluation circuit for evaluating the ECG, in particular for detecting an ST elevation, is provided.
    [15]
    15. Device according to one of claims 1 to 14, characterized in that the control device (4) for each separate arithmetic evaluation, in particular for each 26 • ···· · · separate evaluation on the nature of at least one of claims 32 to 36, the measured values determined during the occlusion of the blood vessel (2) and cooperating with the occlusion means (3) in such a way that the occlusion is ended as a function of the result of the evaluation.
    [16]
    16. Device according to one of claims 1 to 15, characterized in that the control device (4) for each separate arithmetic evaluation, in particular for each separate evaluation of the type at least one of claims 32 to 36, during the release of the blood vessel (2). measured values is formed and with the occlusion means (3) cooperates such that the occlusion is initiated in dependence on the result of the evaluation.
    [17]
    17. The device according to one of claims 1 to 16, characterized in that the sensor is designed as a blood pressure sensor (5) and can be positioned in the occluded blood vessel, wherein the control means cooperates with the occlusive means such that the occlusion is released upon reaching a limit value.
    [18]
    18. Device according to one of claims 1 to 17, characterized in that the blood vessel (2) is the coronary sinus.
    [19]
    19. Device according to one of claims 1 to 18, characterized in that the device is designed as an implantable device according to one of claims 1 to 13. Vienna, 26 November 2010 Applicant rlnr-r, h

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    引用文献:
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    法律状态:
    优先权:
    申请号 | 申请日 | 专利标题
    AT18562008A|AT507578B1|2008-11-27|2008-11-27|IMPLANTABLE DEVICE FOR THE INTERMITTENT OCCLUSION OF A BLOOD VESSEL|
    AT19832010A|AT510252B1|2008-11-27|2010-03-29|IMPLANTABLE DEVICE FOR THE INTERMITTENT OCCLUSION OF A BLOOD VESSEL|AT19832010A| AT510252B1|2008-11-27|2010-03-29|IMPLANTABLE DEVICE FOR THE INTERMITTENT OCCLUSION OF A BLOOD VESSEL|
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