FLOW-OPTIMIZED SUPPLY TO AN ORGAN-SYNCHRONOUS, DYNAMIC SEALING BALLOON ELEMENT

Description

[0001] The invention is directed to devices for organ-synchronous, dynamic occlusion, sealing and / or tamponade of a hollow organ by means of a balloon-like element, in particular to the dynamically adapting, aspiration-preventive secretion seal of the intubated trachea in independently breathing patients as well as in patients who are mechanically ventilated in a supportive spontaneous breathing mode.In particular, the invention is directed to a device for the dynamically adapting sealing of an organ or a body cavity, for example the trachea of an intubated and ventilated patient, in particular by means of a sealing balloon element, wherein in the exemplary case of the dynamic sealing of the trachea, a balloon-like film body, preferably of a residual diameter, i.e. exceeding the tracheal diameter, rests in a sealing manner against the inner wall of the trachea with a pressure that is as constant as possible; fluctuations in the balloon volume, which are caused by fluctuations in the intrathoracic pressure due to breathing mechanics, are to be compensated with the smallest possible time latency by supplying volume from an extracorporeal reservoir or an extracorporeal source, so that the tracheal secretion seal of the balloon is continuously maintained.

[0002] In particular, the invention is directed to a device for the organ-synchronous volume-compensating sealing of a hollow organ or an anatomical space with a predetermined anatomical dimension, comprising (i) an intracorporeal, balloon-like film body with sealing surfaces for contact with the wall of the respective hollow organ or space, while the film-like balloon body itself is filled with a filling medium under a target pressure of at most 50 mbar, preferably under a target pressure of at most 40 mbar, in particular under a target pressure of at most 30 mbar, (ii) a tube or other shaft on which the balloon-like shaped body sits, (iii) an extracorporeal control device with a volume reservoir and / or a pressure source for the filling medium, and (iv) a flow connection between the intracorporeal balloon-like film body and the extracorporeal control device,which runs at least partially in or along the tube or other shaft, wherein a connector is provided extracorporeally in the flow connection.

[0003] A fundamental problem with organ-compatible, efficient sealing or space-filling tamponade of organs or cavities with an extracorporeally filled, balloon-like element is the continuous, more or less pronounced motility of the organ itself. Organs or body cavities bounded by muscular connective tissue often exhibit characteristic movement dynamics or are typically exposed to the dynamics of adjacent organs or structures. Such intrinsically motile or correspondingly motile organs require a special control mechanism for continuously effective closure of the organ lumen that rapidly reacts to and compensates for fluctuations in organ diameter and / or changes in the tone of the organ wall.The mechanism must act as synchronously as possible with the respective diameter or tone change in the organ and maintain the closing or sealing properties of the balloon by optimally rapid supply or discharge of filling medium into the balloon.

[0004] The problem of a dynamically adapting seal in a hollow organ can be illustrated using the example of the human trachea. The trachea is a tube-like structure composed of cartilaginous, connective tissue, and muscular-connective tissue sections. It extends from the lower end of the larynx to the branching into the two main bronchi. The anterior and lateral sections of the trachea are stabilized by brace-like, roughly horseshoe-shaped structures, which in turn are connected longitudinally by layers of connective tissue. On the posterior side, the tracheal lumen is closed off by the so-called pars membranacea, which consists of continuous layers of muscular-connective tissue without any integrated stiffening elements. The muscular-connective tissue esophagus lies dorsally adjacent to this.

[0005] The upper third of the trachea is usually located outside the rib cage (thorax), while the two lower thirds lie within the thoracic cavity defined by the rib cage and diaphragm. The lower, thoracic portion of the trachea is thus particularly exposed to pressure fluctuations in the thoracic cavity that occur during the "thoracic work of breathing" of a patient breathing spontaneously without support or receiving mechanical ventilation.

[0006] During the patient's inspiration, the thoracic volume increases due to the elevation of the ribs and the simultaneous lowering of the diaphragm, which reduces the intra-thoracic pressure in the thorax. This drop in pressure in the thorax leads to the flow of air into the elastically expanding lungs, which follow the thorax.

[0007] The decrease in intra-thoracic pressure associated with the increase in thoracic volume causes pressure fluctuations in sealing and / or tamponing balloon elements positioned within the thoracic cavity and pressurized to a specific inflation pressure, corresponding to the patient's thoracic breathing. This is observed, for example, in the sealing balloon elements (cuffs) of tracheal tubes and tracheostomy tubes, which seal the deep airways against incoming pharyngeal secretions and enable positive pressure ventilation (PPV) of the patient's lungs.

[0008] The cyclical intra-thoracic pressure fluctuations generated by the patient during thoracic breathing can shift the effective pressure in the balloons of ventilation catheters to levels where a sufficient seal against secretions from the pharynx and digestive tract is no longer guaranteed. During the patient's thoracic breathing, the cuff pressure can sometimes reach subatmospheric values that almost correspond to the prevailing thoracic pressure. See Badenhorst CH, "Changes in tracheal cuff pressure in respiratory support," CritCareMed, 1987; 15 / 4: 300-302.

[0009] While the sealing performance of conventional tracheal tube cuffs made of PVC is closely correlated with the current filling pressure in the cuff and results in a corresponding decrease in sealing performance in the pressure range from 30 mbar down to 15 mbar, particularly thin-walled tracheal tube cuffs made of polyurethane have a significantly more stable sealing efficiency when the filling pressure in the cuff drops from 30 to 15 mbar, see Bassi GL, CritCareMed, 2013; 41: 518-526.

[0010] Of significantly greater importance for the secretion sealing efficiency of tracheal cuffs, however, is the filling pressure range of 15 to 5 mbar, which can be achieved virtually from breath to breath, even with moderately forced breathing. While seal-optimized, micro-thin-walled PUR cuffs offer good sealing performance even at approximately 10 mbar filling pressure, they cannot protect against inflowing subglottic secretions when pressure drops below 10 mbar or to subatmospheric, intra-thoracic pressure values.

[0011] A cost-effective, tracheal closure technique using a cuff-like sealing balloon that synchronizes with the patient's spontaneous breathing and provides efficient, atraumatic sealing over sufficiently wide filling pressure ranges is not yet available. While various designs of extracorporeal, filling pressure-regulating devices for tracheal ventilation catheters have been described in the state of the art, a truly synchronous, stroke-to-stroke adjustment of the sealing pressure to alternating thoracic pressures, such as those encountered during the patient's spontaneous breathing, does not currently exist.

[0012] In conventional ventilation catheters, the tracheal sealing cuff is usually filled through small-lumen, channel-like supply lines extruded into the wall of the catheter shaft. The small cross-sections of the filling lines, approximately 0.5 mm, generally do not ensure a sufficiently large volume flow of the filling medium pressurizing the cuff to maintain the tracheal seal of the cuff throughout a complete respiratory cycle of the patient. Even technically complex, electronically controlled control mechanisms, such as the CDR 2000 device from Logomed GmbH (no longer commercially available), also offer only inadequate sealing efficiency due to the traditional small-lumen supply line between the sealing balloon element and the regulator located outside the body.

[0013] The present invention is based on an arrangement wherein an extracorporeal connector is provided in the flow connection of the filling hose, via which a reservoir or a source can be connected to the filling hose.

[0014] In contrast, DE 30 28 568 A1 is directed to an endotracheal tube for ventilating a patient. However, an extracorporeal connector is not disclosed, so this endotracheal tube does not provide for a detachable connection of a reservoir or source to the filling tube.

[0015] In a similar form, US 4,856,510 also discloses a tracheal tube, but also without an extracorporeal connector, so that here too no detachable connection of a reservoir or a source or any other control device to the filling tube is possible.

[0016] The same applies to US Pat. No. 5,247,927. This discloses a tracheal tube with a cuff or balloon, but without any connector, so that neither a reservoir nor a source nor any other control device can be detachably connected to the filling tube.

[0017] In WO 2014 / 090680 A1, such a connector is present, at best, in a form integrated with a damping valve. However, this damping valve does not incorporate any measures to prevent tubulent flow in the relevant area.

[0018] US 4,159,722 discloses a pressure regulator for the cuff or balloon of an endotracheal tube. Fig.2However, it can be seen that the balloon rests against the wall of the hollow organ in question without any folds, meaning it is not residually dimensioned. Furthermore, no measures have been taken to prevent turbulent flow in the area of a tube between the balloon and the tube on the one hand and the control device itself. In particular, there are edges and protrusions in the area of these connectors that impede laminar flow and thus prevent rapid pressure equalization within the cuff or balloon.

[0019] The same applies to US Pat. No. 6,647,984 B1, which concerns a device for controlling the pressure within the cuff or balloon of an endotracheal tube. There, too, no folds are visible between the balloon body and the surrounding trachea, so that there is no residual dimensioning of the cuff and, consequently, an increased pressure exists within it, which does not require rapid pressure equalization.

[0020] The same is true for US 3 794 043 in Fig. 1 can be seen; there too, the unfolded balloon body within the hollow organ does not show any folds, which is an unmistakable indication that there is increased pressure within the balloon and therefore rapid pressure equalization is not necessary.

[0021] US Pat. No. 5,235,973 describes a relatively complex, electronically controlled control technology designed for particularly rapid pressure regulation in a sealing catheter balloon element. It describes, among other things, preferred cross-sections of the supply line connecting the catheter balloon to the pressure-regulating device. The specified diameters are in the range of approximately 2 to 3 mm. To reduce the flow resistance within the supply line to the tracheally sealing cuff, which is essentially determined by the diameter of the supply lumen integrated or extruded into the catheter shaft, WO 2016 / 087930 A1 and WO 2017 / 085540 A1 propose appropriately dimensioned supply line cross-sections.

[0022] However, it has been shown that the supply line cross-sections alone do not guarantee the fastest possible pressure equalization in an intracorporeal sealing balloon. Rather, the entire structural design of the flow channel between an intracorporeal sealing balloon and an extracorporeal control device influences the achievable flow velocity and thus the temporarily adjustable filling pressure volume. Neither US 5,235,973 nor WO 2016 / 087930 A1 nor WO 2017 / 085540 A1 address this issue.

[0023] These disadvantages of the described prior art give rise to the problem initiating the invention, namely to design the flow channel between an intracorporeal sealing balloon on the one hand and an extracorporeal control device on the other hand in such a way that, on the one hand, the extracorporeal control device can be connected to the filling tube and detached from it again, while, on the other hand, the fastest possible pressure equalization in an intracorporeal sealing balloon should be achievable.

[0024] This problem is solved within the framework of a device for organ-synchronous volume-compensating sealing of a hollow organ or an anatomical space, comprising (i) an intracorporeal, balloon-like film body shaped to a residual dimension, i.e., exceeding the anatomical dimension of the organ or the respective space, with sealing surfaces which, when the balloon-like film body is tensionlessly unstretched, at least partially abut the wall of the respective hollow organ or space, forming folds, while the film-like balloon body itself is filled with a filling medium at a target pressure of at most 50 mbar, preferably at a target pressure of at most 40 mbar, in particular at a target pressure of at most 30 mbar, (ii) a tube or other shaft onto which the balloon-like shaped body sits, (iii) an extracorporeal control device with a volume reservoir and / or a pressure source for the filling medium,and (iv) a flow connection between the intracorporeal balloon-like film body and the extracorporeal control device, which runs at least partially in or along the tube or other shaft, wherein a connector is provided extracorporeally in the flow connection, in that, a) the balloon-like shaped body is shaped to a residual size exceeding the anatomical size of the organ or the respective space, such that the sealing surfaces of the balloon-like film body rest against the wall of the respective hollow organ or space when the balloon-like film body is unstretched without tension, at least in some areas, forming folds, and that b) the flow connection b1) between the intracorporeal balloon-like film body and the extracorporeal control device is free of right-angled deflections in the region of its run in or along the tube or other shaft, including a transition region from the tube or other shaft to a run detached therefrom, so that a laminar flow can develop there and within a latency time of 200 ms or less, for example of 100 ms or less, preferably of 50 ms or less, in particular of 25 ms or less,the additional filling quantity of the filling medium required in the balloon-like film body can be supplemented in order to compensate for fluctuations in the balloon inflation pressure and / or the balloon volume and / or the pressures and forces acting on the balloon-like film body, so that the seal or the space-filling tamponade of the hollow organ or space is maintained under dynamically alternating fluctuations in the balloon inflation pressure with a pressure drop in the balloon-like film body of 30 mbar, and b2) in the region of the transition between different components, in particular in the region of the connector, is free of kinks and edges and steps and gaps and ridges and other abrupt elevations or depressions in order not to impair the laminar flow.

[0025] The invention thus takes into account the special requirement of avoiding transitions and obstacles within the supply line leading to the balloon that reduce flow or hinder the optimal rapid pressure equalization between the sealing balloon and the regulator.

[0026] The inventor recognized that, in particular, the specific structural design of the transition from the shaft-integrated supply line to a tubular supply line connected to the shaft, or the specific structural design in the area where the filling medium exits the shaft-integrated supply line into the cuff, can reduce the volume flow and delay the seal. Flow-restricting transitions are particularly problematic during pressure equalization from an extracorporeal reservoir pressurized isobarically to the sealing cuff due to the generally small pressure differences that drive the volume flow. The resulting delay in pressure equalization between the two communicating compartments, reservoir and cuff, precludes a continuously reliable seal.The cyclically occurring pressure gradients range from a few millibars, typically within a pressure range of approximately 5 to 30 mbar. The pressure gradient driving the volume flow from the reservoir or volume source to the cuff therefore requires the particularly flow-optimized design of all components, as described below, as well as all transitions between the components that make up the supply line between the reservoir and the cuff as a whole.

[0027] It has proven advantageous for the tube or other shaft to be made of a material with such limited flexibility that it is bendable but not kinkable. This allows the tube or other shaft to optimally adapt to the patient's anatomy without compromising its functionality. In particular, a kink could significantly delay or even prevent volume displacement.

[0028] Since, for example, steps, ridges, uneven surfaces or other unsmoothed structures interrupt the laminar flow of the filling medium in a turbulent manner, the invention provides that the flow connection in the region of the tube or other shaft and / or in the region of a transition between different components is free of kinks and / or free of edges and / or free of steps and / or free of gaps and / or free of ridges and / or free of other abrupt elevations or depressions in order not to impair the laminar flow.

[0029] The invention is advantageously further developed in that the flow connection in the region of the tube or other shaft is free of bends whose bending radius in the longitudinal direction of the flow is less than 0.5 cm, for example, less than 1 cm, preferably less than 2 cm, in particular less than 5 cm. Like kinks, tight changes in the direction of flow in the flow channel can also have a negative impact on the achievable flow velocity, particularly because they would increase the tendency toward vortex formation, and for this reason, such tight bends should be avoided.

[0030] It is within the scope of the invention that the cross-sectional area of the flow connection does not decrease from the area of the tube or other shaft to the extracorporeal control device. Any backflow within the flow channel reduces the achievable flow velocity and should therefore be avoided.

[0031] Particular advantages arise from the fact that the cross-sectional area of the flow connection is increased in the transition area from the tube or other shaft to a separate section. This allows a potentially higher pressure within the control device to spread almost unrestrictedly up to the transition area into the tube, so that a maximum pressure difference is available there to drive a maximum volume shift within the limited flow cross-section there.

[0032] It has proven effective for the cross-section of the flow connection in or along the tube or other shaft to have an arcuate shape, which preferably fits approximately tangentially to a functional lumen within the tube or other shaft or surrounds it coaxially. On the one hand, such a design makes it possible to maintain a relatively circular overall cross-section of the tube, corresponding to the lumens of the human body, which are usually also approximately circular in cross-section. On the other hand, an arcuate, elongated cross-sectional shape of the flow connection has the advantage that any fluid that has penetrated cannot close off the flow channel across its entire cross-sectional area, which would significantly impair pressure equalization.

[0033] Only with the largest possible lumen and shortest possible supply components, in conjunction with turbulence-minimizing transitions between the components, can an optimally delay-free, as laminar as possible flow of the sealing medium from a volume reservoir or from an electronically / electro-mechanically regulated volume source to the sealing balloon be achieved, and thus a sufficiently rapid, dynamic seal of the trachea, from breath to breath, be maintained.

[0034] The invention also allows for implementation in such a way that the flow connection in the region of the tube or other shaft is designed as a line or hose line that can be attached to its outside, so that the number of transitions between different components of the flow channel - where vortices could be triggered - can be reduced.

[0035] To accommodate such an attachable line or tubing, a trough-shaped groove or recess can be formed in the outside of the tube or other shaft. This would have the advantage that the flow channel, which is important for sealing the balloon, is not exposed in the area of the tube and therefore could be crushed, but is protected in a recess in the tube.

[0036] Within the scope of a preferred development of the invention, the trough-shaped groove or depression can have lateral undercuts so that a cable or hose line that can be pressed or inserted therein is held and cannot come loose on its own, thereby facilitating handling.

[0037] It is also possible for the line or tubing to be attached to the outside of the tube or other shaft to be preformed in such a way that it fills the trough-shaped groove or depression, thereby complementing the adjacent outer contours of the tube or other shaft in a contour-preserving manner. In this case, the tube or shaft in question can also be placed atraumatically in a lumen of the human body in the area of the tubing.

[0038] The invention allows for a further development in that a component with a ramp-shaped or curved profile is provided, in particular inserted, in the transition region of the flow connection from a flow channel section integrated or molded into the tube or other shaft to a separate flow channel section. The function of such a component is to gently and smoothly redirect the flow of the filling medium, e.g., air, in this transition region so as not to impair the laminar flow.

[0039] Further following this inventive concept, it can be provided that a detachable component is inserted by means of a rearward, preferably spike-like extension arranged on a side facing away from the ramp, into a recess aligned with the flow channel section integrated or molded into the tube or other shaft. This ensures that such a component is always optimally aligned and that no gaps or edges arise due to inclination or similar factors that could impair the flow. Of course, such a component can also be additionally fixed in position using adhesive.

[0040] Furthermore, it can be provided that a component with a tubular shape and a gently curved profile made of a kink-resistant material is inserted in the transition region of the flow connection from a flow channel section integrated or molded into the tube or other shaft to a separate flow channel section. The primary function of such a component is also to ensure a smooth change in the flow direction in the transition region and to counteract the development of turbulent flow there.

[0041] If the outer cross-section of the tubular component is larger than the inner cross-section of the flow channel section integrated or molded into the tube or other shaft, it can be fixed there by frictional engagement with local expansion of the flow channel section and thus experiences a leading alignment in the longitudinal direction of the flow channel molded into the tube or other shaft.

[0042] A preferred embodiment of the invention is characterized in that, in the transition region of the flow connection from a flow channel section integrated or molded into the tube or other shaft to a separate flow channel section, a component made of a thin-walled material that conforms to the opening of the flow channel in the tube or other shaft is inserted. One function of such a component is to serve as reinforcement in the area of the cut in the tube or other shaft, thereby structurally weakening it in certain areas, in order to prevent the formation of an undesirable kink there.

[0043] A special embodiment of the invention is provided in that, in the transition region of the flow connection from a flow channel section integrated or molded into the tube or other shaft to a separate flow channel section, a hood-shaped component with lateral, saddle-like, flat extensions is attached or inserted. These extensions can preferably be connected in a stabilizing manner, for example, adhesively, to the tube shaft covered thereby. These lateral, saddle-like, flat extensions also serve both to align the tube or shaft casing and to secure it to this tube or shaft casing.

[0044] In a particularly preferred embodiment of the invention, a component with a ramp-shaped or curved profile is covered by a hood-shaped component. According to the invention, several such components can be combined with one another, in particular one transition component inserted into the flow channel inside the tube or its extension and one transition component adjacent to the outside of the tube or other shaft.

[0045] Geometries designed in a manner comparable to all previously described transition elements can also be provided at the transition area between the distal end of the tube- or shaft-integrated flow channel and the sealing balloon applied there on the tube or shaft.

[0046] In general, a component arranged in the transition region of the flow connection from a flow channel section integrated or molded into the tube or other shaft to a separate flow channel section can be provided with a sleeve in the region of its proximal end for attaching or inserting a tube. If the tube has a radial expansion on its inner side, steps in this area can be avoided.

[0047] In the segments or components of the supply line that lie outside the body and whose structural design or dimensions are not limited by anatomical specifications, the design of the supply line can usually be adapted to the requirements of flow maximization. In particular, larger supply line cross-sections can be realized there. In the described example of a tracheal tube or a tracheostomy cannula, anatomically determined limitations exist in the supply lines to the tracheally sealing cuff, primarily in the area of the tube-like or tubular shaft component that supports the cuff. The plane of the vocal cords (glottis) in particular limits the dimensions of the tube shaft. This is the narrowest point in the airways and determines the possible dimensions of the respective outer tube diameters, and thus essentially also the diameter of the inner tube lumina extruded into the shaft.The cross-sectional area of the tube lumen used for lung ventilation must be maximized in order to keep breathing resistance as low as possible during ventilation. In the intubated vocal cord plane, a certain residual space usually remains in the dorsal region towards the tube shaft, whereby the vocal cords open out in a triangular manner from ventral to dorsal, tent-like, and at the bottom of the tent-like curtain or glottis, a gusset-shaped area is created between the outer wall of the tube shaft and the floor of the glottis. This can be used for additional and / or enlarged shaft-integrated lumens, in the sense of a flow-optimized supply or drainage of a filling medium to the cuff. The invention proposes, among other things,an approximately dumbbell-shaped profile of a supply line in the dorsally positioned back wall of the tubal shaft, whose special, lateral extensions of the dumbbell-shaped cross-section fill or use this remaining space.

[0048] The length of the shaft-integrated supply line to the sealing balloon element is ideally designed to be as short as possible for the respective tube or cannula, extending from the opening of the supply line in the cuff to a point immediately above, for example, 2 to 3 cm from the glottis. Even in the supra-glottic hypopharynx, a tube or other conduit lumen that is significantly larger than the shaft-integrated lumen can be connected, with a correspondingly reduced flow resistance.

[0049] A filter and / or vapor barrier can be arranged, preferably extracorporeally, in the flow connection. A vapor barrier can, for example, protect the extracorporeal control device from moisture ingress.

[0050] If a connector with an inner lumen is provided in the extracorporeal flow connection, its inner lumen should preferably have a constant cross-sectional area over the entire length of the connector in the connected state of its subcomponents.

[0051] It has proven useful for the minimum clear internal cross-sectional area in the extracorporeal flow connection to be larger than the minimum clear internal cross-sectional area of the intracorporeal flow channel section integrated or molded into the tube or other shaft, for example, at least 1.1 times the minimum clear internal cross-sectional area of the intracorporeal flow channel section, preferably at least 1.2 times the minimum clear internal cross-sectional area of the intracorporeal flow channel section, in particular at least 1.3 times the minimum clear internal cross-sectional area of the intracorporeal flow channel section. Such a cross-sectional expansion can further optimize the flow velocity.

[0052] The invention aims to achieve continuous pressure stabilization in the tracheal cuff at a target value that can be variably adjusted by the user or fixed by the specific design of the device in the range of 20 to 40 mbar, preferably 30 mbar, with a maximum time delay of approximately 10 to 20 milliseconds, starting from the time of the initial deflection of the thoracic pressure during the patient's active inspiration, from a mechanically resting position to a pressure level below this resting position. After a maximum of 20 milliseconds (ms), the respective deflections of the balloon seal pressure occurring from breath to breath should be returned to the target value.

[0053] A structurally simple arrangement is achieved by setting the pressure in a volume reservoir of the extracorporeal control device to the pressure setpoint for the balloon-like foil body. This ensures that the pressure in the sealing balloon cannot rise to excessive levels, even without active control.

[0054] In such a case, an element with a valve function and / or a flow-directing function can be provided in the flow connection, which element is preferably oriented in such a way that it opens when there is a negative pressure in the balloon-like film body compared to the pressure in a volume reservoir of the extracorporeal control device and allows a rapid volume flow into the balloon-like film body, in particular even without active control.

[0055] In order to allow an overpressure in the balloon-like foil body to gradually reduce compared to the pressure in a volume reservoir of the extracorporeal control device, a throttle element should be connected in parallel to the element with a valve function and / or a flow-directing function.

[0056] The volume shifts required for pressure stabilization to the sealing balloon component are driven, in the inventive composite of a sealing balloon with a flow-optimized supply line to the sealing balloon integrated into the shaft tube of the catheter carrying the balloon, by an extracorporeal volume reservoir pressurized with constant pressure, or by a reservoir- and / or pump-like, permanently acting mechanism that otherwise provides volume at constant pressure.

[0057] The respective sealing pressure in the pressurized connection between balloon and supply line can be generated and maintained, for example, by a gravity- or spring-based mechanism that acts on a balloon- or bellows-like reservoir component, compressing or pressurizing the filling medium contained therein by exerting force on the outer shell of the reservoir component. The balloon, supply line, and reservoir are connected to form a closed system. The system is filled and emptied via a filling valve, preferably integrated into the reservoir.

[0058] The application of pressure to a reservoir component can also be achieved by a pump-like or electromechanical, for example piezo-electrically driven valve mechanism that is permanently connected to the reservoir.

[0059] Alternatively, the filling pressure prevailing in the system can also be generated by a reservoir bladder that expands elastically in a specific manner. When filled with a certain initial volume, the shell of the bladder-like component enters a state of expansion, which places the volume contained in the bladder under a structurally determined, specifically determined pressure that corresponds to the desired sealing target pressure in the system. As the filling volume of the bladder increases, it expands further in a characteristic "isobaric" manner, whereby the excess pressure established in the reservoir bladder does not increase over a certain volume range, or the respective target pressure is maintained. The reservoir bladder thus holds volume in "reserve," while the pressure of the filling medium remains constant in the "isobaric reserve range."An external force acting on the reservoir shell can be dispensed with in such volume-expandable reservoir bladders, for example, made of polyisoprene. A corresponding technique is described, for example, in WO 2013 / 139986 A1.

[0060] Furthermore, electronically or electromechanically controlled components connected to the balloon and the supply line to form a communicating closed system are conceivable, which deliver the volume required for the control of the balloon seal into the system or provide it to the system at a constant pressure (isobaric) without the interposition of a quasi "buffering", reservoir-like component, in the manner of a "source".

[0061] In addition to such constant-pressure sources, which generate a pressure corresponding to the required sealing pressure in the tracheal cuff, regulating, reservoir-like, or source-like systems can also be connected to the balloon and balloon supply line. These systems operate with pressure gradients or exceed the pressure range of 20 to 40 mbar. Such systems, for example, maintain a pressure of 100 mbar and displace the filling medium in a correspondingly accelerated manner, driven by gradients high relative to the sealing target pressure. The accelerated volume flow directed to the cuff can be adjusted, for example, by an electronically controlled proportional valve. Precise, piezoelectrically driven valves are particularly suitable for this purpose. The valves are small, silent, and have low energy consumption.Piezo-electrically driven pumps can also be connected upstream of the valves, which also silently build up a reservoir pressure of up to 100 mbar.

[0062] The pressure of a pressure source for the filling medium in the extracorporeal control device, in particular upstream of a regulating valve, can be set to a pressure value above the target value for the balloon-like film body, for example to a pressure value of 100 mbar or more, preferably to a pressure value of 200 mbar or more, preferably to a pressure value of 500 mbar or more, in particular to a pressure value of 1 bar or more, or even to a pressure value of 2 bar or more. The differential pressure to the significantly lower pressure in the sealing balloon then drops largely via a regulating valve, which, depending on the embodiment, either opens only slightly when needed or is operated in a cycle such that the pressure downstream of the valve is regulated.

[0063] To detect the actual pressure value in the balloon-like film body, a pressure sensor can be arranged in the balloon-like film body.

[0064] Such a pressure sensor in the balloon-like foil body should be connected or connectable to the extracorporeal control device via a cable, preferably with the connecting cable routed within the tube or other shaft in a possibly additional lumen or within the flow connection. A wireless connection, for example, via Bluetooth, would also be conceivable, but this is considerably more complex and more susceptible to interference than a wired connection.

[0065] The invention further provides that the extracorporeal control device has an active controller, preferably an electronic controller, in particular a two-point controller, which is designed in particular to regulate the pressure detected as an actual value within the balloon-shaped film body to a predetermined or predeterminable target value as constantly as possible.

[0066] In conjunction with active, electronically controlled regulators, particularly optimized, closed control loops can be created. Pressure-sensing sensors are integrated within the sealing balloon component and are preferably connected to the controller unit via a cable connection. Such feedback systems can also be designed for the active removal of volume from a balloon. The regulator generates a negative pressure gradient parallel to a positive pressure gradient, allowing volume to flow from the sealing balloon toward the regulator in an accelerated manner.

[0067] An electronic two-point controller used within the scope of the invention can be operated with a fixed clock frequency of, for example, between 100 Hz and 1000 Hz, wherein a valve, for example a piezo valve, is alternately opened and closed between a pressure source for the filling medium at a corresponding frequency, wherein the pulse ratio between the opening and closing phases can preferably be influenced by the controller, in particular as a reaction to the difference between a predetermined or predeterminable pressure setpoint on the one hand and the actual pressure value measured within the balloon-like shaped body on the other. Due to the control valve used, there can be a considerable pressure difference between a possible high pressure upstream of such a valve and the low pressure downstream of the valve, which is regulated by the pulsation.

[0068] Preferably, the hollow organ or anatomical space is the patient's trachea or esophagus. The described principle of flow-optimized, latency-minimized volume compensation or stabilization in a tracheally placed, sealing balloon can, however, also be applied analogously to the sealing tamponade of the esophagus in a spontaneously breathing patient. The pressure fluctuations in an esophageally placed, tampon-sealing balloon, which also correspond to the patient's own breathing, are generally even more pronounced than in a tracheally placed balloon. They correspond closely to the prevailing intra-thoracic pressure. To create the most efficient balloon tamponade in the esophagus, the invention proposes, as a structural variant, a segmentation of the sealing balloon.While the distal segment of the balloon, which seals the esophagus, extends over the section of the esophagus between the upper and lower sphincters, a tapered balloon segment follows proximally, optionally extending to the proximal end of the catheter carrying the balloon. The resulting gap between the shaft and the proximal balloon segment can be generously dimensioned. It allows the distal balloon segment to be filled virtually around the catheter shaft and enables flow-optimized, rapid volume shifts, even at small differential pressures that drive volume flow from extracorporeal to intracorporeal. Such dynamically pressure-regulated balloon tamponades are particularly applicable to transesophageally placed tubes for gastric nutrition and / or gastric decompression.The connection to an isobaric volume reservoir or to a volume source regulated by a differential pressure can be carried out in a design analogous to the sealing of the trachea.

[0069] The invention further provides that the sealing balloon element consists of a thin-walled balloon film made of polyurethane, which has a wall thickness of 5 to 30 µm, preferably 10 to 20 µm, in the segment facing the respective surface to be sealed. Furthermore, the sealing balloon element can be made of PUR with a Shore hardness of 70 A to 95 A, and / or with a Shore hardness of 54 D to 60 D. Such a material can be easily preformed, so that it does not need to be converted into an elastically stretched state for sealing.

[0070] Finally, it is in accordance with the teaching of the invention that the sealing balloon element has a multi-layer wall structure, with at least one material layer having special barrier properties for water vapor and / or air, the barrier layer being made of EVOH, for example. This can prevent, for example, the penetration of moisture that could condense in the supply line and hinder rapid volume transfer there.

[0071] The following figures illustrate the described inventive content using concrete structural designs. Here, they show: Fig. 1 shows an exemplary design of a tracheal tube according to the invention, which integrates a selection of flow-optimizing components and features that enable a rapid displacement of the filling medium to the sealing balloon even with a small pressure difference driving the volume flow from extracorporeal to intracorporeal, or enable a dynamically adapting seal of the trachea that is synchronous to the patient's respiratory effort; Fig. 2a shows a transverse section through the shaft of a tracheal tube, with a special design of the lumens integrated into the shaft, wherein the total cross-sectional area of the supply line to the tracheally sealing cuff, which is integrated into the wall of the tube, is optimally designed, and wherein a special, dumbbell-shaped profile prevents temporary, lumen-closing obstructions of the supply line due to condensation that has penetrated into the supply line; Fig. 2b shows a structural variation of the Fig. 2ashown embodiment, wherein the supply to the cuff is carried out through a separately manufactured tube which Fig. 2adescribed dumbbell-shaped cross-section, but is inserted into a shape-congruent recess in the dorsal tube shaft and fixed there; Fig. 3a a representation of the distal, balloon-carrying section of a tracheal tube shaft according to the invention, comprising a flow-optimized transition by a ramp-like component from a filling line integrated into the wall of the tracheal tube shaft into the interior space enclosed by the balloon component; Fig. 3b a further embodiment of a flow-optimized transition from the shaft-integrated, channel-like supply line to the sealing balloon, wherein the transition is designed in the form of a shell-like supporting component that hugs the outer circumference of the tube shaft around the opening area of the shaft-integrated supply line and thus stabilizes the shaft wall in the opening area and prevents kinking of the shaft; Fig. 4a an embodiment of the invention with a flow- orFlow-optimized transition from a filling hose to the shaft-integrated, channel-like supply lumen; Fig. 4b shows a further embodiment of the transition from the filling hose to the shaft-integrated supply lumen, comprising a hood-like component connecting the supply line and the filling hose, which creates a continuous, flow-optimized transition to both connected lumens; Fig. 5 shows a vapor barrier and / or microbial barrier integrated into the filling hose in a longitudinal section; Fig. 6 shows a design of a flow-optimized connector between the proximal end of the filling hose and the regulator; Fig. 7 shows a longitudinal section through a smooth-running valve element with optional retrograde volume compensation function; Fig. 8 shows an extracorporeal volume reservoir with isobaric volume expansion characteristics; Fig.9An electronic / electromechanical regulator system with direct feedback to a tracheally sealing cuff, which accelerates the inflow of the filling medium, and optionally also its outflow, via the hose and channel supply line extending from the regulator to the sealed cuff, by means of a differential pressure that compensates for flow resistance, or wherein the pressure generated by the regulator exceeds the target pressure in the tracheally sealing cuff, and wherein the pressure in the cuff is recorded by an electronic sensor positioned within the cuff and fed to the regulator unit; Fig. 10An alternative electronic / electromechanical regulator system, wherein the electronic sensor component recording the cuff pressure is integrated into the regulator unit.

[0072] Fig. 1describes, by way of example, a catheter according to the invention using a tracheal tube 1, consisting of a shaft element 2 which carries a tracheally sealing cuff 3 at the distal end, said cuff being connected to an extracorporeal volume reservoir 5a via a shaft-integrated, channel-like supply line 4a which merges outside the shaft into a filling tube 4b. The extracorporeal volume reservoir 5a keeps the cuff pressurized or stores a gaseous filling medium with a tracheally sealing target pressure, or connects it to an electronically controlled volume source 5b which sets the tracheally sealing target pressure through a pressure difference generated by the volume source or the pressure generated by the volume source exceeds the tracheally sealing target pressure. The reservoir or source is connected to the filling tube 4b by a connector 6.In addition to a leg 7, which terminates with the connector 6, the filling tube 4b has a further leg 8, which merges into a pilot balloon 9 equipped with a filling valve 10. A manually operable closure mechanism 11 is optionally integrated into the leg 7, which enables the reservoir or source unit to be connected to a tube already intubated in the patient and pressurized, without a pressure drop in the tracheally sealing cuff. To prevent condensate from the supply system from passing into the respective pressure-regulating unit, a gas-permeable element 12, which has water-repellent properties, can optionally be integrated into the leg 7. Alternatively or in addition to the water-repellent function, the element 12 can also act as a microbial filter.The total cross-sectional area of the shaft-integrated channel 4b corresponds to a circular cross-section of at least 2 mm, preferably 3 to 4 mm. The cross-sectional area of the inner lumen of the filling tube 4b, as well as of the leg 7 and the hose line adjoining the leg to the reservoir, corresponds to a circular diameter that preferably exceeds 2.0 mm, preferably more than 3.0 mm, and particularly preferably more than 3.5 mm.

[0073] Fig. 2ashows a design of the shaft element 2, wherein the supply line 4a integrated into the shaft wall has a special, dumbbell-shaped profile 13 in transverse section, which optimally maximizes the overall cross-section of the supply line, which determines the flow resistance. The supply line is extruded into the dorsal portion 2a of the tube shaft, thus, in the usual design of a tracheal tube according to Magill, lies in the so-called greater curvature of the shaft, which rests on the broad base of the vocal cord trigone. The overall profile of the shaft SQ resulting from the dumbbell-shaped filling line has a corresponding widening of the dorsal "base" of the tube profile. The broad base of the greater curvature allows the ventilation lumen 14 of the tracheal tube, integrated ventrally into the shaft, to be retained in its round or slightly oval shape and cross-sectional area.The terminal extensions 13a of the filling line are each located at the outer angles of the dorsally directed base of the shaft profile. When the tube is properly intubated, its widened posterior wall rests approximately congruently against the broad base of the glottis. The lateral extensions of the profile are connected by a tapered, bridge-like, central segment 13b. The communication of the extensions through the central bridge prevents condensate penetrating the filling line from causing a capillary-induced closure of the lumen leading to the cuff, which could impair the continuous connection of the regulating unit to the cuff. A fluid level forming in the dumbbell-shaped profile usually disperses due to the bridge-like connection between one profile extension and the parallel extension, thus largely eliminating a flow-effective closure of the filling line.In the preferred embodiment, the extensions 13a each have a diameter of 1.5 to 2.5 mm, preferably 1.5 to 2.0 mm. The bridge 13b connecting the lumina has a height of approximately 0.5 to 1.0 mm.

[0074] Fig. 2b shows a structurally modified version of the Fig. 2adescribed profile 13, wherein the dumbbell-shaped supply line is inserted as a separately manufactured tube 15 into a shape-congruent recess 15a in the dorsal wall of the tube or in its greater curvature and fixed there. The advantage of this design is that the tube can be led out of the shaft of the tube above the vocal cord level and can be continued as a filling tube without structural interruption. The tube element 15 thus connects the cuff of the tube with the extracorporeally integrated elements of the supply line in a continuous, flow-optimized manner, whereby flow-inhibiting transitions are avoided. To maximize the inner diameter, the tube element 15 can be made of a thin-walled material that spontaneously elastically straightens, such as polyurethane, whereby material hardnesses in the range of 90A to 95A or 55D to 60D are preferably used.The tube shaft itself is preferably made of non-elastic, plastically deforming PVC.

[0075] Fig. 3a represents the transition from the shaft-integrated filling line 4a to the tracheally sealing cuff 3, whereby flow-inhibiting effects caused by turbulence during the transfer of the filling medium from the supplying lumen into the cuff are minimized by deflecting the medium at as flat an angle as possible or by avoiding a transfer at a steep or right angle, as is typically caused in the conventional design of tracheal tubes by a simple tangential cut in the wall of the filling line.

[0076] The inlet 16 of the filling line 4a is therefore extended in its axial extent, from 1 to 2 mm for conventional tubes, to 4 to 10 mm, preferably 5 to 8 mm. Inserted into the distally extending opening of the inlet 4a inlet is a component 17 that closes the inlet. This component forms a ramp 17a that descends from distal to proximal into the opening, directing the medium flowing toward the cuff into the cuff without turbulence. The ramp extends over an axial length of 4 to 6 mm.

[0077] Fig. 3b shows a component 18, which is in addition to the Fig. 3aThe described component 17 is integrated in the area of the opening 16 of the supply line for axial stabilization of the tube shaft in the area of the extended gate. Component 18 is made of a particularly thin-walled, high-hardness material and fits snugly around the outer contour of the gate, in a saddle-like manner, on its lateral surfaces 18a. The component is preferably manufactured by injection molding. The previously described lumen-closing and flow-directing component 17 can be structurally connected to or integrated into component 18.

[0078] Fig. 4ashows a special transition element 19, which leads the shaft-integrated supply line 4a into the filling tube 4b or connects the lumen of the supply line to the lumen of the filling tube. The supply line 4a is cut tangentially in the transition area and is open over a length of approximately 5 mm. The transition element 19 is preferably made of kink-resistant, thin-walled, solvent-bondable material and has a distally directed extension 19a, the outer dimensions of which are enlarged in relation to the diameter of the filling line integrated into the shaft of the tube, and is thus inserted with a certain tension into the supply line 4a opened by the tangential cut. The inner lumen of the thorn-like extension corresponds to that of the supply line, whereby the formation of step-like structures or turbulent flow occurring in the transition area can be avoided.

[0079] In the proximal region of the transition element 19, this optionally has a sleeve-like receptacle for the filling tube 4b, whereby the tube is inserted into the receptacle and fixed by adhesive such that the inner lumen of the element 19 corresponds to the inner lumen of the filling tube 4b. The element 19 thus also ensures, in the area of the proximal connection, that caliber transitions from the shaft-integrated supply line to the filling tube are avoided, and flow-reducing step formations are excluded. In this particularly flow-critical region, the element enables a laminar flow of the filling medium from the reservoir or source to the tracheally sealing cuff. Furthermore, the element 19 can be used to smooth transitions from circular cross-sections of the filling tube 4b to flattened, oval, flat-oval, or even dumbbell-shaped cross-sections of the distal portion 19a of the transition element, thus optimizing flow.

[0080] The cross-sectional area of the filling hose 4b corresponds at least to the total cross-sectional area of the shaft-integrated supply line 4a, but exceeds this in the preferred embodiments.

[0081] Fig. 4b shows a hood-like component 18a, which fits snugly against the dorsal circumference of the tracheal tube and tightly covers the incision of the supply line 4a. The component has lateral, saddle-like extensions 18b, which connect to the lateral wall of the tube shaft in a manner that stabilizes the tube shaft in the area of the incision. The hood-like component has a nozzle 18c, which extends proximally at a shallow angle and receives the filling tube 4b. The figure also shows a component 17, which is inserted proximally into the supply line channel 4a and closes it. Analogous to the ramp-like design in Fig. 3a, the nozzle 18 forms a flow-optimizing ramp 17a, which extends from proximal to distal into the cut of the supply line and is accordingly beveled.

[0082] Fig. 5shows an optional vapor barrier 20 integrated into the filling hose 4b or the leg 7. The surface area of the respective separating layer 21 is selected to be large enough to compensate for the flow resistance caused by the barrier function and to avoid delays in pressure equalization in the cuff. The barrier layer has a diameter of at least 10 to a maximum of 25 mm, preferably 15 mm. The housing 22 is flat and discoid in design, thus reducing the residual space around the separating layer. The function of the vapor barrier ensures that water vapor and condensate do not penetrate into the area of the regulating unit and impair the opening and closing behavior of the valves installed there. Alternatively, or in addition to the vapor barrier 20, a microbe-tight barrier layer can also be installed in the housing 22.

[0083] Fig. 6shows a special connector 6 that has a constant cross-sectional area across its entire inner lumen. The insertion of the male part 6a into the female part 6b enables a seamless, gapless, and burr-free transition. The cross-sections of the connected lumens are identical in the connection area.

[0084] Fig. 7shows a unit 23 with a valve function, wherein the flow-directing function is preferably provided by a flap-like, film-like thin valve plate 24. When the valve is open, the cross-sectional area of the valve opening is at least equal to, but preferably exceeds, the diameter of the line arranged distal to the valve. The valve plate preferably has a hole-like perforation 25, which, even when the valve is closed, allows a reduced volume flow from the cuff to the regulating unit, directed counter to the main flow, so that temporary overpressure situations in the cuff can be compensated by a correspondingly delayed volume outflow from the cuff.

[0085] A correspondingly effective backflow function can alternatively be achieved by a channel-like connection arranged parallel to the valve plate, which allows a certain, throttled outflow of medium from the cuff to the reservoir or source.

[0086] Fig. 8shows a volume reservoir 26 which has a specifically volume-expandable reservoir bladder 27 which, across a specific radial expansion area 27a of the bladder shell, absorbs the filling medium at a constant, isobaric pressure. The plateau pressure which arises when the bladder shell expands is defined by the specific design or the material used and the geometry of the bladder. The respective plateau pressure in the reservoir corresponds to the target pressure prevailing in the balloon, for example 30 mbar. The pressure generated by the expanded reservoir bladder drives the volume flow to the sealing balloon element at the moment of a pressure drop in the balloon. The reservoir can be filled through a filling valve 28, preferably with air as the filling medium.

[0087] Fig. 9shows a feedback control system 29 which is connected to a flow-optimized catheter 1 of the type according to the invention. The catheter has an electronic pressure sensor 30 permanently integrated within the sealing balloon, which is connected to the control system via a cable connection 31. The controller itself consists of a pump module 32 with an optionally integrated reservoir 33 and at least one regulating valve module 34 with an integrated control unit. Setpoint and alarm values can be entered into the control system by the user. Optionally, the controller can also have two pump systems, each with a connected reservoir, with one reservoir maintaining an overpressure and the other a negative pressure. The gradients orThe differential pressure stored in the regulator relative to the setpoint in the cuff is automatically adjusted by the regulator in an optional version using a learning algorithm such that the latency until the setpoint is reached in the cuff is in the range of 10 to 20 ms. Both the pump functions and the valve functions are preferably based on piezoelectric components, which can be operated precisely and quickly, as well as quietly and energy-efficiently.

[0088] The supply line 35 to leg 7 of the catheter preferably has an inner diameter that exceeds the diameter of the leg, ideally by 30%, in order to minimize resistance-related flow losses. As an alternative to the cuff-integrated pressure sensor, a peripheral pressure-transforming sensor 36 can be integrated into the supply line, positioned in close proximity to connector 6. In this design, a sensor integrated into the cuff can be omitted, although a certain delay in the control time is accepted.

[0089] Fig. 10describes a further regulator unit 37 for continuously maintaining a sealing balloon inflation pressure. The cuff of the tracheal tube is formed to its required working dimension during production. The balloon is filled in the previously described, flow-optimized and resistance-minimized manner. The balloon is filled with a gaseous medium. The hose supply line 35 from the regulator to the connector 6 should have a circular lumen of at least 5 mm in diameter to avoid flow-related pressure losses and damping effects between the balloon and the regulator. The regulator unit consists of a single piezoelectric valve Voi, which both directs volume to the tamponing balloon and releases volume from it. Upstream of the valve on the patient side is an electronic pressure-measuring component 38, which continuously records the pressure in the balloon body and feeds it to the control unit C.The regulator unit does not have a measuring function for a pressure electronically measured directly in the balloon. A pressure reservoir R integrated in the device or an external pressure source Qi is connected upstream of the valve on the side facing away from the patient, which keeps a supply of filling medium in the pressure range, for example, from 1 to 2 bar. The piezo valve Voi reduces this supply pressure to a sealing pressure in the balloon of approximately 10 to 30 mbar. If the target pressure in the balloon set by the user is exceeded, this is detected by component 38. The control unit C then opens the valve Voi and releases filling medium to the atmosphere via an opening 39 following the respective gradient. The unit has an adjustment option for the tracheal sealing target pressure 40 and an option for adjusting the respective volume flow 41 to or from the balloon. List of reference symbols 1 Tracheal tube 17 component 2 Shaft element 17a ramp 2a rear wall portion 18 component 3 Cuff 18a lateral surface 4a channel-like supply line 18b flat runner 4b filling hose 19 transition element 5a Volume reservoir 19a distal part 5b Volume source 20 vapor barrier 6 connector 21 Separating layer 6a male part 22 Housing 6b female part 23 Unit 7 leg 24 valve plate 8 leg 25 hole-like perforation 9 pilot balloon 26 Volume reservoir 10 Filling valve 27 reservoir bladder 11 locking mechanism 27a Filling area 12 gas-permeable element 28 Filling valve 13 dumbbell-shaped profile 29 Control system 13a terminal extension 30 pressure sensor 13b central segment 31 Cable connection 14 ventilating lumen 32 Pump module 15 Hose 33 reservoir 15a shape-congruent recess 34 Valve module 16 Cut 35 supply line 16a distal opening 36 sensor 37 Control unit 38 component 39 opening 40 Target pressure 41 Volume flow C Control unit Qi external pressure source R pressure reservoir SQ Shaft profile Voi valve

Claims

1. A device for the volume-compensating sealing of a hollow organ or an anatomical space in sync with organs, comprising (i) an intracorporeal balloon-type foil body (3) formed to a specified dimension, having sealing surfaces, which contact the wall of the respective hollow organ or space, while the balloon-type foil body is itself filled with a filling medium under a maximum target pressure of 50 mbar, preferably under a maximum target pressure of 40 mbar, in particular under a maximum target pressure of 30 mbar, (ii) a tube (1) or other shaft, on which rests the balloon-type foil body (3), (iii) an extracorporeal regulating device (29) with a volume reservoir (26, R) and / or a pressure source (Qi) for the filling medium, as well as (iv) a flow connection (4a, 4b, 7, 13, 15, 35) between the intracorporeal balloon-type foil body (3) and the extracorporeal regulating device (29), which extends at least in regions in or along the tube (1) or other shaft, whereby a connector (6) is provided extracorporeally in the flow connection (4a, 4b, 7, 13, 15, 35), characterized in that a) a balloon-type foil body (3) is formed to a residual dimension, exceeding the anatomical dimension of the organ or the respective space so that the sealing surfaces of the balloon-type foil body (3) contact the wall of the respective hollow organ or space at least in regions while forming folds, when the unexpanded balloon-type foil body (3) is free of tension; and that b) the flow connection (4a, 4b, 7, 13, 15, 35) b1) between the intracorporeal balloon-type foil body (3) and the extracorporeal regulating device (29) is free of right-angled deflections in the region of its extension in or along the tube (1) or other shaft including a transition region from the tube (1) or other shaft to an extension that is detached therefrom, so that a laminar flow can form there, and the additional filling quantity of the filling medium needed in the balloon-type foil body (3) can be supplemented within a latency period of 200 ms or less, for example of 100 ms or less, preferably of 50 ms or less, in particular of 25 ms or less, in order to compensate for fluctuations of the balloon filling pressure and / or of the balloon volume and / or of the pressures and forces bearing on the balloon-type foil body (3), so that the sealing or the space-filling tamponade of the hollow organ or of the space is maintained under dynamically alternating fluctuations of the balloon filling pressure with a pressure drop in the balloon-type foil body (3) of 30 mbar, and b2) is free of kinks and / or free of edges and / or free of steps and / or free of gaps and / or free of ridges and / or free of other abrupt elevations or depressions in the region of a transition between different components (4a, 4b, 7, 13, 15, 35), especially in the region of connector (6), so as not to impair the laminar flow.

2. The device according to claim 1, characterized in that the flow connection (4a, 4b, 7, 13, 15, 35) in the region of the tube (1) or of the other shaft a) is free of kinks and / or free of edges and / or free of steps and / or free of gaps and / or free of ridges and / or free of other abrupt elevations or depressions, so as not to impair the laminar flow, and / or b) is free of bends, whose bending radius in the longitudinal direction of the flow is less than 0,5 cm, for example less than 1 cm, preferably less than 2 cm, in particular less than 5 cm.

3. The device according to one of the preceding claims, characterized in that the cross-sectional area of the flow connection (4a, 4b, 7, 13, 15, 35) a) does not decrease starting from the region of the tube (1) or of the other shaft up till the extracorporeal regulating device (29); and / or b) increases in the transition region from the tube (1) or other shaft to a progression that is detached therefrom; and / or c) in that the minimum clear inside cross-sectional area in the extracorporeal flow connection (4b, 7, 13, 15, 35) is larger than the minimum clear inside cross-sectional area of the intracorporeal flow channel section (4a) formed in or integrated into the tube (1) or in another shaft, for example at least 1.1 times as large as the minimum clear inside cross-sectional area of the intracorporeal flow channel section (4a), preferably at least 1.2 times as large as the minimum clear inside cross-sectional area of the intracorporeal flow channel section (4a), in particular at least 1.3 times as large as the minimum clear inside cross-sectional area of the intracorporeal flow channel section (4a).

4. The device according to one of the preceding claims, characterized in that the cross section of the flow connection (4a, 4b, 7, 13, 15, 35) in or along the tube (1) or other shaft comprises an arch-shaped form, which preferably tangentially nestles a functional lumen inside the tube (1) or other shaft, or coaxially surrounds it.

5. The device according to one of the preceding claims, characterized in that the flow connection (4a, 4b, 7, 13, 15, 35) in the region of the tube (1) or other shaft is configured as one on whose outer side a line or hose line can be attached, preferably whereby a trough-shaped groove or depression is formed in the outer side of the tube (1) or other shaft for accommodating an attachable line or hose line, especially whereby the trough-shaped groove or depression comprises lateral undercuts, so that a line or hose line, which can be pressed in or inserted there, is fixed and cannot detach spontaneously, and / or whereby the line or hose line that can be attached to the outer side of the tube (1) or of the other shaft is preformed in such a way that it fills the trough-shaped groove or depression and thereby supplements the adjacent outer contours of the tube (1) or the other shaft in a manner than maintains the contour.

6. The device according to one of the preceding claims, characterized in that in the transition region of the flow connection (4a, 4b, 7, 13, 15, 35) from a flow channel section (4a) formed in or integrated into the tube (1) or in another shaft to a progression of the flow channel (4b, 7, 13, 15, 35) that is detached therefrom a) a component (17, 17a) with a ramp-shaped or arch-shaped progression is provided, in particular inserted, preferably whereby a detachable component (17, 17a) is inserted, by means of a rearward, preferably mandrel-like prolongation (17) arranged on a side facing away from the ramp (17a), into a depression aligning with the flow channel section (4a) formed in or integrated into the tube (1) or in another shaft; and / or b) a component (18) made of a thin-walled material that nestles the outlet of the flow channel (4a) in the tube (1) or other shaft; and / or c) a component (19) with a tubular form and a gently bent progression made of a kink-resistant material is inserted, preferably whereby the outer cross section of the component (19) with a tubular form is larger than the inner cross section of the flow channel section (4a) formed in or integrated into the tube (1) or in another shaft, preferably in such a way that it can be frictionally fixed there under local widening of the flow channel section (4a); and / or d) a hood-shaped component (18a) with lateral, saddle-like planar extensions (18b) is attached or inserted, wherein the extensions (18b) can preferably be connected in a stabilizing manner, for example adhesively, to the tube shaft covered therewith, whereby a component (17, 17a) with a ramp-shaped or arch-shaped progression is covered by a hood-shaped component (18a), preferably whereby a component (17, 17a, 18, 18a, 19) arranged in the transition region of the flow connection (4a, 4b, 7, 13, 15, 35) from a flow channel section (4a) formed in or integrated into the tube (1) or in another shaft to a progression of the flow channel (4b, 7, 13, 15, 35) that is detached therefrom, is provided in the region of the proximal end of said component with a socket for attaching or inserting a hose.

7. The device according to one of the preceding claims, characterized in that a) a filter and / or a vapor barrier (20) is preferably provided extracorporeally in the flow connection (4a, 4b, 7, 13, 15, 35), and / or b) the inner lumen in the connector (6) preferably comprises a constant cross-sectional area over the entire length of the connector (6) in a connected state of the subcomponents thereof.

8. The device according to one of the preceding claims, characterized in that the pressure in a volume reservoir (26, R) of the extracorporeal regulating device (29) is set to the target pressure value for the balloon-type foil body (3).

9. The device according to one of the preceding claims, characterized in that an element (23) with a valve function and / or a flow-directing function is provided in the flow connection (4a, 4b, 7, 13, 15, 35), which element is preferably oriented in such a way that it opens in the case of a negative pressure in the balloon-type foil body (3) as compared to the pressure in a volume reservoir (26, R) of the extracorporeal regulating device (29) and allows a rapid volume flow into the balloon-type foil body (3), in particular even without an active regulation, preferably whereby a throttling element is connected in parallel with the element (23) with a valve function and / or a flow-directing function, in particular in such a way that an excess pressure in the balloon-type foil body (3) as compared to the pressure in a volume reservoir (26, R) of the extracorporeal regulating device (29) can gradually dissipate.

10. The device according to one of the preceding claims, characterized in that the pressure of a pressure source (Qi) for the filling medium in the extracorporeal regulating device (29), in particular upstream of a regulating valve, is set to a pressure value above the target value for the balloon-type foil body (3), for example to a pressure value of 100 mbar or more, preferably to a pressure value of 200 mbar or more, preferentially to a pressure value of 500 mbar or more, in particular to a pressure value of 1 bar or more, or even to a pressure value of 2 bar or more11. The device according to one of the preceding claims, characterized in that a pressure sensor is arranged in the balloon-type foil body (3) so that the actual pressure value in the balloon-type foil body (3) can be detected, preferably whereby the pressure sensor in the balloon-type foil body (3) is connected or can be connected via cable to the extracorporeal regulating device (29), preferably wherein the connecting cable is laid inside the tube (1) or other shaft in a possibly additional lumen or inside the flow connection (4a).

12. The device according to one of the preceding claims, characterized in that the extracorporeal regulating device (29) comprises an active regulator, preferably an electronic regulator, in particular a two-point regulator, which in particular is designed in such a way that, in order to adjust the pressure inside the balloon-type foil body (3) that was detected as an actual value as constantly as possible to a predetermined or predeterminable target value, preferably whereby the two-point regulator is operated with a fixed timing frequency of for example between 100 Hz and 1000 Hz, wherein respectively a valve, for example a piezo valve, is alternatingly opened and closed between a pressure source (Qi) for the filling medium with an appropriate frequency, wherein preferably the pulsation ratio between the opening phase and the closing phase can be influenced by the regulator, in particular as a reaction to the difference between a predetermined or predeterminable target pressure value, on the one hand, and the actual pressure value measured inside the balloon-type foil body (3), on the other hand.

13. The device according to one of the preceding claims, characterized in that the sealing surfaces of the balloon-type foil body (3) fit closely on the wall of the respective organ or space with a sealing pressure of the balloon-type foil body (3) that acts as constantly as possible, in a sealing manner on all sides and / or in a manner that minimizes as much as possible a remaining residual space between the balloon-type foil body (3) and an adjacent structure.

14. The device according to one of the preceding claims, characterized in that in the case of a tracheal tube (1) a) a defined high-volume, flow-optimized supply of the filling medium to the tracheal tube cuff (3) is provided, and / or b) the length of a shaft-integrated supply line (4a) to the sealing balloon-type foil body (3) is reduced to a minimum, preferably such that the structural transition region from the tube (1) or shaft to the filling hose (4b) is approximately 1 to 2 cm above the level of the vocal folds (glottis), and / or c) a turbulent flow is prevented when moving the filling medium between the reservoir or regulator (35) and the cuff (3), and / or d) in the region of the transition from the shaft-integrated lumen (4b) in the tracheal sealing cuff (3), and / or in the region of the transition from the shaft-integrated supply lumen (4a) in the supply hose (4b) that extends extracorporeally, as well as between the connector parts (6), the flow properties are optimized to the extent that a sealing-pressure-maintaining extracorporeal volume compensation that acts in a synchronous manner can be achieved in the sealing balloon element (3), and / or e) between connector parts (6), and / or in the region of integrated filter components or valve components (20, 23), the flow properties are optimized to the extent that a sealing-pressure-maintaining extracorporeal volume compensation that acts in a synchronous manner can be achieved in the sealing balloon element (3).

15. The device according to one of the preceding claims, characterized in that the sealing balloon element or the balloon-type foil body (3) a) consist of a thin-walled balloon foil made of polyurethane, which in the segment directed towards the respective surface to be sealed has a wall thickness of 5 to 30 µm, preferably of 10 to 20 µm, and / or b) consists of PUR with a material durometer according to Shore of 70 A to 95 A, and / or with a material durometer according to Shore of 54D to 60D, and / or c) comprises a multilayer wall structure, wherein at least one material layer has special barrier properties for water vapor and / or air, wherein the barrier layer consists for example of EVOH