Device for a dynamically sealing occlusion or a space-filling tamponade of a hollow organ

Abstract

The invention is directed to a device for the sealing occlusion and/or for the space-filling tamponade of hollow organs or other cavities in the human body, comprising a preferably fully and residually formed balloon (2) which applies a sealing pressure that is as constant as possible to the wall of the organ to be occluded or tamponaded. The device comprises an isobarically acting regulator (3) for the filling pressure within the interior of the balloon, the regulator having a volume reservoir (3) situated extracorporeally outside of the body, and a feed line (6) for communicatively connecting the extracorporeal volume reservoir of the regulator to the interior of the balloon. The connecting feed line between the balloon and the regulator has a flow-directing one-way valve (26) that prevents backflow from the balloon to the volume reservoir of the regulator, while a nonflow-directing throttle element (27) is provided which allows a slow volume compensation between the balloon and the volume reservoir.

Claims

1. A device for the sealing occlusion and/or for the space-filling tamponade of a hollow organ or a cavity in a human body, comprising a fully and residually formed balloon (2) which is configured to apply an appreciably constant sealing pressure to a wall of the hollow organ or cavity to be occluded or tamponaded in use, characterized by an appreciably isobarically acting regulator for a filling pressure within the interior of the balloon (2), the regulator having an extracorporeal volume reservoir which is configured to be situated extracorporeally outside of the human body in use and a feed line (6) for communicatively connecting the extracorporeal volume reservoir of the regulator to the interior of the balloon (2), wherein the connecting feed line (6) between the balloon (2) and the regulator comprises: a) a supply channel with a cross-sectional area corresponding to a circular cross-sectional area with a diameter of at least 2 mm, b) a flow-directing one-way valve (26) that prevents backflow from the balloon (2) to the extracorporeal volume reservoir of the regulator, and c) a nonflow-directing throttle element (27) which allows a slow volume compensation between the balloon (2) and the extracorporeal volume reservoir, wherein the nonflow-directing throttle element (27) is arranged in parallel to the flow-directing one-way valve (26) as a bypass thereto.

2. The device according to claim 1, including a tube that is insertable into the hollow organ, with a primary lumen as access which is configured to be provided through or to the hollow organ or cavity in use, wherein the balloon has the shape of a cuff and encloses this tube for the purpose of sealing off with respect to the hollow organ or cavity, with at least one or multiple secondary lumen(s) for filling the balloon.

3. The device according to claim 2, characterized in that the balloon or a proximal area of the balloon ends at an end-face side of a hose-shaped element in which the primary lumen continues radially within a hose casing as a clear opening, while the at least one secondary lumen or the multiple secondary lumen(s) continues or continue in the form of one or more channels that are molded into the hose casing itself.

4. The device according to claim 3, characterized in that the minimum total cross section of all channels molded into the hose casing as the at least one secondary lumen or the multiple secondary lumens is greater than or equal to the maximum cross section of a ring-shaped secondary lumen in the proximal area of the balloon.

5. The device according to claim 2, characterized in that a ring-shaped collecting channel is present in the area of a proximal tube end, with which all channels of the secondary lumen communicate, in particular all channels that are molded into a hose casing as secondary lumens.

6. The device according to claim 5, characterized in that a connection for a filling hose that communicates with all secondary lumens is provided at the proximal tube end, in particular at the ring-shaped collecting channel.

7. The device according to claim 1, characterized by an apparatus for actively controlling or regulating the pressure in the extracorporeal volume reservoir.

8. The device according to claim 7, characterized in that the apparatus for actively controlling or regulating the pressure in the extracorporeal volume reservoir is designed in such a way that the pressure in the balloon (2) is held constant.

9. The device according to claim 8, characterized by an apparatus for measuring the pressure in the balloon (2), for the purpose of specifying an actual value for a control loop that acts on the pressure in the extracorporeal volume reservoir.

10. The device according to claim 2, characterized in that the balloon has a radially expanded distal area for sealing, and a proximal area adjacent thereto that is tapered radially with respect to same, as a covering of the secondary lumen(s) for filling the distal area.

11. The device according to claim 2, characterized in that a single secondary lumen is provided in a proximal area of the balloon which concentrically encloses the primary lumen on the outside.

12. The device according to claim 2, characterized in that a proximal area of the balloon does not extend to a proximal end of the tube, and instead ends prior to same.

13. The device according to claim 2, characterized in that the extracorporeal volume reservoir (9) in the freely unfolded state has a larger volume than the balloon (2), or has a larger volume than the balloon, in the distal area of the tube.

14. The device according to claim 1, characterized by a noncollapsible profile (41) inside the balloon (2) or inside a shaft which is configured to draw, in the event of a peristaltic contraction of the hollow organ, a portion of a filling medium from the balloon segments that are distal with respect to the contraction wave, preferably through the profile (41) or beneath the profile (41), in areas that are proximal with respect to the contraction wave.

15. The device according to claim 14, characterized in that the noncollapsible profile (41) communicates with the balloon (2) and/or its feed line and/or filling lumen of the balloon (2), in particular via one or more openings.

16. The device according to claim 1, characterized in that the balloon is pre-formed with different outer diameters in its distal and proximal areas.

17. The device according to claim 1, characterized in that a radially tapered area which is configured for the glottis in use is molded into the balloon or into a distal area of the balloon.

18. The device according to claim 1, characterized in that the extracorporeal volume reservoir (9) is acted on with a constant pressure or an appreciably constant pressure, for example by a weight or a spring element.

19. The device according to claim 1, characterized in that the balloon (2) is closed in a ring shape, and in particular has a toroidal design.

20. The device according to claim 1, characterized in that the balloon (2) is designed as a larynx mask, in particular for placing on the hypopharynx.

21. The device according to claim 1, characterized in that the flow-directing one-way valve (26) and/or the nonflow-directing throttle element (27) are/is extracorporeally situated.

22. A device for the sealing occlusion and/or for the space-filling tamponade of a hollow organ or a cavity in a human body, comprising a prcfcrably fully and residually formed balloon (2) which is intended to be configured to apply an appreciably constant sealing pressure to a wall of the hollow organ or cavity to be occluded or tamponaded in use, comprising a regulating unit for a filling pressure within the interior of the balloon (2), which regulating unit is intended to be configured to be situated extracorporeally outside of the human body during use and comprises an extracorporeal volume reservoir (9) which is intended to be configured to be situated extracorporeally outside of the human body in use, and a feed line (6) for communicatively connecting the extracorporeal volume reservoir (9) to the interior of the balloon (2), wherein the connecting feed line (6) between the balloon (2) and the extracorporeal volume reservoir (9) comprises (i) a supply channel with a cross-sectional area corresponding to a circular cross-sectional area with a diameter of at least 2 mm, (ii) a flow-directing one-way valve (26) that prevents backflow from the balloon (2) to the extracorporeal volume reservoir (9), and (iii) a nonflow-directing bypass throttle element (27) which allows a slow volume compensation between the balloon (2) and the extracorporeal volume reservoir (9), wherein the nonflow-directing throttle element (27) is arranged in parallel to the flow-directing one-way valve (26) as a bypass thereto, and wherein the regulating unit is implemented a) as a combined regulator and volume reservoir unit (3), where the extracorporeal volume reservoir (9) comprises a volume-expandable balloon bladder (28) made of a material with an elasticity sufficient to increase the volume due to an increasing pressure in order to provide a constant pressure or an appreciably constant pressure inside the extracorporeal volume reservoir (9), or b) as a weight or a spring element acting on the extracorporeal volume reservoir (9) with a constant pressure or an appreciably constant pressure.

23. A device for the sealing occlusion and/or for the space-filling tamponade of a hollow organ or a cavity in a human body, comprising a preferably fully and residually formed balloon (2) which is intended to be configured to apply an appreciably constant sealing pressure to a wall of the hollow organ or cavity to be occluded or tamponaded in use, comprising a regulating unit for a filling pressure within the interior of the balloon (2), which regulating unit is intended to be configured to be situated extracorporeally outside of the human body in use and comprises an extracorporeal volume reservoir (9) which is intended to be configured to be situated extracorporeally outside of the human body in use, and a feed line (6) for communicatively connecting the extracorporeal regulating unit to the interior of the balloon (2), wherein the connecting feed line (6) between the balloon (2) and the extracorporeal volume reservoir (9) comprises: a) a supply channel with a cross-sectional area corresponding to a circular cross-sectional area with a diameter of at least 2 mm, b) a flow-directing one-way valve (26) that prevents backflow from the balloon (2) to the extracorporeal volume reservoir of the regulator, c) a nonflow-directing throttle element (27) which allows a slow volume compensation between the balloon (2) and the extracorporeal volume reservoir, d) wherein the nonflow-directing throttle element (27) is arranged in parallel to the flow-directing one-way valve (26) as a bypass thereto, and wherein the regulating unit comprises: e) either a control apparatus for actively controlling the pressure in the extracorporeal volume reservoir (9) which is designed in such a way that the pressure in the balloon (2) is held constant, or f) a regulating apparatus for actively regulating the pressure in the extracorporeal volume reservoir (9) as a result of the pressure measured in the balloon (2) by a measuring sensor arranged inside of the balloon (2) for the purpose of specifying an actual value for a control loop that acts on the pressure in the extracorporeal volume reservoir (9).

Description

BRIEF DESCRIPTION OF THE DRAWINGS

(1) Further features, particulars, advantages, and effects based on the invention result from the subclaims and from the following description of preferred exemplary embodiments of the invention, and with reference to the drawings, which show the following:

(2) FIG. 1 shows a tracheal tube according to the invention with a continuous feed line integrated into the shaft in combination with an external volume- or pressure-regulating device and a flow-directing device;

(3) FIG. 1a shows an example of a shaft profile in cross section, corresponding to FIG. 1;

(4) FIG. 2 shows a tracheal tube with a gap-forming, extended proximal balloon end, which in the subglottal area transitions into the shaft body;

(5) FIG. 2a shows a design corresponding to FIG. 2, but with the extended proximal balloon end in the supraglottal area connected to the shaft body;

(6) FIG. 2b shows an atraumatic transition between the shaft body and the proximal balloon end;

(7) FIG. 2c shows advantageous proportions of the gap space relative to the diameters of the tube shaft;

(8) FIG. 2d shows a grooved pre-formation of the shaft body for shifting the volume;

(9) FIG. 2e shows a cross section of the pre-formation shown in FIG. 2d;

(10) FIG. 3 shows a single-chamber balloon that is tracheal sealed as well as subglottally tamponaded;

(11) FIG. 3a shows a double-chamber arrangement with a tracheal sealing and a subglottally to supraglottally tamponading balloon;

(12) FIG. 4 shows a tracheal tube having a two-part shaft body whose supraglottal section is designed as a particularly stable bite protector, and whose shaft adjoining in the distal direction has a single-lumen segment with a maximized inner diameter;

(13) FIG. 4a shows a triangular shaft segment for positioning in the glottis;

(14) FIG. 5 shows a tracheal cannula having a proximal balloon that is extracorporeally extended;

(15) FIG. 6 shows a combined valve/throttle mechanism;

(16) FIG. 7 shows an example of a regulator or reservoir component;

(17) FIG. 7a shows a pressure-volume curve associated with the component described for FIG. 7;

(18) FIG. 7b shows a reservoir balloon or regulator balloon designed for double-chamber systems;

(19) FIG. 8 shows a supply line-optimized tracheal tube according to the invention, with a sensor element in the area of the trachea-sealing balloon segment, and a regulator unit which together with the sensor is situated in a control loop;

(20) FIG. 9 shows a larynx mask with a connected regulator unit; and

(21) FIG. 10 shows a transesophageal probe with a connected regulator unit.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

(22) FIG. 1 describes, in an illustrative total overview, various function-optimizing components of a tracheal ventilation catheter 1 (tracheal tube) for dynamic tracheal sealing, with cyclically alternating thoracic pressures, by flow-optimized shifting of a filling medium that is acted on by pressure, between a tracheal positioned sealing balloon 2 (cuff) and an extracorporeal regulator or reservoir element 3.

(23) The shape and dimensions of the device according to the invention largely correspond to a conventional tracheal tube. At the distal end of the tube, the trachea-sealing balloon at both its ends is connected with a tight seal to the catheter shaft bearing the balloon. The shaft body 4 preferably has a large-bore or multi-lumen feed line, integrated into the shaft, for the cuff. The respective supply lumens are combined at the proximal shaft end 5, and from there are attached via a large-bore feed line 6 to the regulator element 3. To avoid rapid retrograde emptying toward the reservoir, and also for delayed pressure or volume compensation between the compartments on the end, a combined valve-throttle function 7 is integrated into the feed line. The combination of the communicating volumes of the balloon, feed line, valve-throttle, and reservoir or regulator element results in a shared interior in which a constant pressure, defined by the reservoir or the regulator, is maintained. Within the scope of the invention, air is used as a preferred medium for filling the communicating interior.

(24) The technology described within the scope of the invention, for optimal quick volume shifting with the lowest possible resistance, and at the same time, the lowest possible pressure gradients between a tracheal positioned balloon and an extracorporeal regulator unit, is intended to allow pressure-stabilizing volume compensation within the trachea-sealing balloon, which in the optimal case is terminated after no more than 10 to 20 milliseconds after the onset of a pressure drop that is triggered by respiration mechanics.

(25) FIG. 1a shows an example of a multi-lumen shaft profile 8 in cross section. The feed line lumens 9 integrated into the shaft wall, in the sense of the smallest possible enlargement of the shaft outer diameter, are preferably flat or designed with the smallest possible radial height. In the base design shown in FIGS. 1 and 1a, PVC is a preferred shaft material for the Shore durometer range of 80 A to 90 A.

(26) FIG. 2 shows a tracheal tube according to the invention, having a trachea-sealing balloon 2 at the distal tube end; the tapered proximal end 10 of the balloon is extended further into the subglottal area SB, where it is accommodated by the proximal shaft portion 4a or is connected to same with a tight seal. The distal shaft portion 4b has a single-lumen design, whereas the proximal portion preferably has a multi-lumen profile corresponding to FIG. 1a. The same as in FIG. 1, the filling medium is thus supplied to the proximal balloon end in a flow-optimized manner. The hose-like tapered balloon end 10 creates a large-bore gap space SR between the hose sleeve and the shaft which freely communicates with the sealing body, thus allowing very advantageous flow resistances that are low according to the invention.

(27) FIG. 2a shows a tracheal tube corresponding to FIG. 2, in which the transition or the connection of the proximally extended end of the balloon 10 which forms a gap space relative to the shaft takes place in the supraglottal area SP, i.e., above the vocal folds. The flow-effective cross section of the gap space SR that results with this design should at least correspond to the flow-effective cross section of the sum of the supply lumens integrated into the shaft, and in turn should at least correspond to the flow-effective cross section of the hose connection between the tube shaft and the regulator unit.

(28) The hose-like balloon end 10 that is extended in the proximal direction may be created directly from the trachea-sealing balloon body when it is formed, or, as a separately manufactured hose-like element, may be attached to the proximal end of the sealing body, for example by gluing. The balloon end is likewise preferably made of polyurethane having a small wall thickness of 10 to 50 μm, particularly preferably 10 to 30 μm.

(29) FIG. 2b shows the subglottal or supraglottal transition from the proximal balloon end 10 to the proximal shaft end 4a in a design by way of example. The transition 11 of the proximal shaft end 4a to the distal shaft end 4b preferably has an atraumatic conical design. The lumens 9 integrated into the shaft open into the gap space SR via the conical taper.

(30) For the dimensioning of the gap space in the area of the proximal balloon extension 10, FIG. 2c shows the preferred dimensional ratios of the volume-shifting cross-sectional area of the gap space SR to the cross-sectional area of the ventilation lumen ID, and to the total cross-sectional area OD of the catheter. The gap surface S illustrated in FIGS. 2 and 2a results from the difference between the diameter of the cross-sectional area G specified by the sleeve wall in the area 10 and the cross-sectional area OD of the shaft body delimited by the outer surface of the shaft. The gap surface S should be 1/10 to 5/10 of the cross-sectional area G, particularly preferably 2/10 to 3/10 of the cross-sectional area G. Relative to the cross-sectional area ID of the inner lumen of the shaft body, the gap surface S should be 2/10 to 6/10 of the cross-sectional area ID, particularly preferably 3/10 to 4/10 of the cross-sectional area ID.

(31) FIG. 2d shows a particular design detail of the shaft body 4, which ensures an unhindered volume flow across the anatomically narrow vocal fold plane, in particular for the design of the device according to FIG. 2a. The illustrated recess 13 may be made up, for example, of one or more grooved indentations extending in the shaft longitudinal axis. The recess is intended to ensure that a sufficiently rapid volume flow is able to communicate between the regulator and the sealing balloon, even in the event of a transient or permanent closure of the volume-shifting gap space. For example, a tubing network 14 or a corresponding hose element having a sieve-like perforation may be inserted into the recess, which keeps the recess open. The recess may contribute to stabilization of the tube shaft against buckling and twisting in a preferred positioning at the apex of the large curvature.

(32) FIG. 2e shows the recess in the shaft body 4 in cross section.

(33) The following place-holder values should be used for an exemplary quantitative calculation of the flow conditions in a cylindrical shell-shaped gap space SR defined in FIGS. 2 and 2a, in particular [based] on the pressure ratios in the distal trachea-sealing balloon section 2:

(34) V.sub.1 volume of the trachea-sealing balloon 2

(35) P.sub.1 pressure in the trachea-sealing balloon 2

(36) ρ.sub.1 filling density in the trachea-sealing balloon 2

(37) M.sub.1 air mass in the trachea-sealing balloon 2

(38) V.sub.2 volume of the extracorporeal reservoir 3

(39) P.sub.2 pressure in the extracorporeal reservoir 3

(40) ρ.sub.2 filling density in the extracorporeal reservoir 3

(41) m.sub.2 air mass in the extracorporeal reservoir 3

(42) The following applies for the air masses m.sub.1, m.sub.2:

(43) $\begin{array}{cc}{m}_1\left(t\right)=m_{1,0}{\int }_{T=0}^{T=t}{S}_{m,1}\left(T\right)\mathrm{dT}& \left(1\right)\\ m_2\left(t\right)=m_{2,0}-{\int }_{T=0}^{T=t}{S}_{m,2}\left(T\right)\mathrm{dT}& \left(2\right)\end{array}$
S.sub.m,v stands for the air flow to the respective balloon 2, 3 as an air mass flow.

(44) According to the Hagen-Poiseuille law, the following is true for the mass fluid flow through a line having an inner radius R and a length l:

(45) $\begin{array}{cc}{S}_{m,1}=\frac{{\rho }_1.Math.\pi \left(p_2-p_1\right).Math.R^4}{8\eta .Math.l}& \left(3\right)\\ S_{m,2}=\frac{{\rho }_2.Math.\pi \left(p_1-p_2\right).Math.R^4}{8\eta .Math.l}& \left(4\right)\end{array}$
η stands for the dynamic viscosity of the flowing gas. For air:
η is 17.1 μPa.Math.s at 273 K

(46) Furthermore, based on the thermal equation of state of ideal gases, the following applies in the balloon 2:
η.sub.1=ρ.sub.1.Math.R.sub.S.Math.T.sub.1  (5)
and in the reservoir 3:
η.sub.2=ρ.sub.2.Math.R.sub.S.Math.T.sub.2  (6)
R.sub.S is the individual or specific gas constant, which for air has the value 287.058 J/(kg.Math.K).
T.sub.v is the temperature in the balloon 2 and in the reservoir 3.

(47) For a temperature of 23° C. or 296 K, the factor is
k=R.sub.S,air.Math.T.sub.23° C.=85.Math.10.sup.3 J(kg.Math.K)  (7)

(48) It should be assumed below that the temperature in the balloon 2 and also in the reservoir 3 is constant at 23° C.
T.sub.1=T.sub.2=296 K

(49) The following then applies:
ρ.sub.1=ρ.sub.1.Math.k  (8)
ρ.sub.2=ρ.sub.2.Math.k  (9)

(50) Thus, by inserting equation (3) into equation (1), the result is:

(51) $\begin{array}{cc}{m}_1\left(t\right)=m_{1.0}+{\int }_{\tau =0}^{\tau =t}\frac{{\rho }_1.Math.\pi .Math.R^4}{8\eta .Math.l}\left(p_2-p_1\right)d\tau & \left(10\right)\end{array}$

(52) With equation (8), it follows that:

(53) $\begin{array}{cc}{m}_1\left(t\right)=m_{1.0}+{\int }_{\tau =0}^{\tau =t}\frac{{\rho }_1.Math.\pi .Math.R^4}{8\eta .Math.l.Math.k}{p}_1\left(p_2-p_1\right)d\tau & \left(11\right)\end{array}$

(54) In addition, in the balloon (2) the following applies:

(55) $\begin{array}{cc}\frac{m_1}{V_1}={\rho }_1=\frac{p_1}{k}& \left(12\right)\end{array}$

(56) Therefore, the following can be written in equation (11) for the mass m.sub.1:

(57) $\begin{array}{cc}{m}_1=\frac{V_1.Math.p_1}{k}& \left(13\right)\end{array}$

(58) The result is:

(59) $\begin{array}{cc}\frac{V_1}{k}.Math.p_1\left(t\right)=\frac{V_1}{k}.Math.p_{1.0}-{\int }_{\tau =0}^{\tau =t}\frac{\pi .Math.R^4}{8\eta .Math.l.Math.k}.Math.\left[p_1^2-p_1{p}_2\right]d\tau & \left(14\right)\end{array}$

(60) The entire equation can be shortened to V.sub.1/k. Differentiation on both sides results in:

(61) $\begin{array}{cc}\frac{{\mathrm{dp}}_1}{\mathrm{dt}}=-\frac{\pi .Math.R^4}{V_{1}8\eta l}.Math.\left[p_1^2-p_1{p}_2\right]& \left(15\right)\end{array}$

(62) This is a Bernoulli differential equation of the form:

(63) $\begin{array}{cc}{x}^{\prime }=-a.Math.x.Math.\left(x-b\right),\mathrm{where}& \left(16\right)\\ a=\frac{\pi .Math.R^4}{V_{1}8\eta l}& \left(17\right)\\ b=p_2& \left(18\right)\end{array}$

(64) It should be assumed below that the reservoir 3 is significantly larger than the balloon 2:
V.sub.2>>V.sub.1

(65) From this it follows that the pressure ρ.sub.2 in the reservoir 3 remains essentially constant, even when the pressure p.sub.1 in the balloon 2 briefly changes. Under this assumption, the coefficients a and b from the Bernoulli differential equation (16) are constant, and the solution to the Bernoulli differential equation is:

(66) 0$\begin{array}{cc}x\left(t\right)=\frac{b}{1-e^{-\mathrm{abt}-{\mathrm{bc}}_1}}& \left(19\right)\end{array}$

(67) The integration constant c.sub.1 may be determined as follows:

(68) $\begin{array}{cc}{p}_1\left(t\right)=\frac{p_2}{1-e^{-{\mathrm{ap}}_{2}t-p_2{c}_1}}& \left(20\right)\end{array}$

(69) For t=0, the following must apply:

(70) $\begin{array}{cc}{p}_1\left(t\right)=p_{1.0}\mathrm{The}\mathrm{result}\mathrm{is}\text{:}& \left(21\right)\\ p_{1.0}=\frac{p_2}{1-e^{-p_2{c}_1}}& \left(22\right)\\ \frac{p_2}{p_{1.0}}=1-e^{-p_2{c}_1}& \left(23\right)\\ e^{-p_2{c}_1}=\frac{p_{1.0}-p_2}{p_{1.0}}& \left(24\right)\\ -p_2{c}_1=\ln \frac{p_{1.0}-p_2}{p_{1.0}}& \left(25\right)\\ c_1=-\frac{1}{p_2}.Math.\ln \frac{p_{1.0}-p_2}{p_{1.0}}=\frac{1}{p_2}.Math.\ln \frac{p_{1.0}}{p_{1.0}-p_2}& \left(26\right)\end{array}$

(71) Inserted into equation (2), this provides:

(72) $\begin{array}{cc}\frac{p_1\left(t\right)}{p_{1.0}}=\frac{p_2}{p_{1.0}-\left[p_{1.0}-p_2\right].Math.e^{-\left(\pi R^4{p}_{2}t\right)/\left(8V_1\eta l\right)}}& \left(27\right)\end{array}$

(73) This equation is of the form:

(74) $\begin{array}{cc}\frac{p_1\left(t\right)}{p_{1.0}}=\frac{p_2}{p_{1.0}-\left[p_{1.0}-p_2\right].Math.e^{-t/\tau }}\mathrm{where}& \left(28\right)\\ \tau =\left(8V_1\eta l\right)/\left(\pi R^4{p}_2\right)& \left(29\right)\end{array}$

(75) The following, for example, applies for minor pressure fluctuations in the balloon 2:
P.sub.1.0≈0.99ρ.sub.2

(76) Moreover, for t=τ:
e.sup.−t/τ=e.sup.−1≈0.37

(77) And for t=4τ:
e.sup.−t/τ=e.sup.−4≈0.018

(78) In equation (28) this yields:

(79) $\frac{p_1\left(t=4\tau \right)}{0.99p_2}=\frac{p_2}{0.99p_2-\left(0.99p_2-p_2\right).Math.0.018}\mathrm{or}\text{:}$$p_1\left(t=4\tau \right)=p_2.Math.\frac{0.99}{0.99+0.018+0.01}=0.9998.Math.p_2,$
respectively.

(80) This is only 2% of the initial deviation.

(81) When applied within the framework of respiration, it should be noted that a breathing cycle lasts about 3 sec. So that the cuff does not develop leaks during this period, this compensation time should be t=4 τ≈8 ms.

(82) This results in:

(83) $\tau =2.Math.{10}^{-3}s=\frac{8.Math.5.Math.{10}^{-6}{m}^3.Math.0.2m.Math.17.1.Math.{10}^{-6}\mathrm{Pas}}{\pi .Math.R^4.Math.{10}^5\mathrm{Pa}}$
for which it was assumed:
V.sub.1=5 cm.sup.3
I=20 cm
p.sub.2=10.sup.5 Pa

(84) This results in:
R.sup.4=0.7.Math.10.sup.−12 m.sup.4,
that is,
R=0.91.Math.10.sup.−3 m≈1 mm.

(85) Since the flow conditions in a cylindrical shell-shaped cavity are much poorer than in a cylindrical cavity, the radial cross section of cylindrical shell-shaped cavity should be significantly larger. In addition, the feed lines 6 and 9 were likewise disregarded in the above calculation, which, however, represents a flow resistance that is not insignificant. Therefore, the radial height of the cylindrical shell-shaped gap space 10 should be at least 2 mm, or even better, 3 to 4 mm.

(86) FIG. 3 shows a tracheal tube having a balloon element 2 that is extended beyond the plane of the vocal folds. The balloon element, corresponding to the other embodiments described within the scope of the invention, should preferably be made of molded film material, whose diameter has a residual dimension such that the balloon element does not have to be stretched in order to seal the tracheal lumen, and the mucosa of the organ make close contact, largely without tension, when the excess portion of the balloon sleeve is folded in. Polyurethane-based balloon films having a wall thickness of preferably 5 to 20 μm, less preferably 20 to 50 μm, in the area of the trachea-sealing balloon segment are preferred in the invention.

(87) Polyurethanes having Shore hardnesses of 70 A to 95 A or 55 D to 65 D are preferably used according to the invention for the trachea-sealing balloon element. Shore hardnesses in the range of 85 A to 95 A are particularly preferably used.

(88) Although in the simple case the balloon element is dimensioned for sealing in the area of the transition from the lower third to the middle third of the trachea, as is common in conventional tracheal tubes or tracheal cannulas, within the scope of the invention the trachea-sealing balloon segment may also be extended in the proximal direction, reaching beyond the vocal folds into the area of the supraglottal lower throat. The body of the balloon element 2 preferably has a cylindrical shape, and in the area of the vocal fold plane may be provided with a circular taper 12 for accommodating the vocal folds.

(89) The design of the trachea-sealing balloon extended in the proximal direction allows a particularly large balloon volume that is capable of developing a certain pressure-maintaining buffer effect when enlargements of the tracheal cross section caused by respiratory mechanics, or a reduction in transmural force acting on the trachea-sealing balloon, occurs in the tracheal section of the balloon body. If the proximal balloon end extends out of the thorax, this extra-thoracic segment of the thoracic respiratory mechanics is not exposed, which correspondingly assists with the damping effect of the extracorporeal volume reserve, and the dynamically acting, seal-maintaining function of the device according to the invention is further improved.

(90) In addition, due to the large contact surface of a trachea-sealing balloon extended in the proximal direction, the largest possible migration path for secretions and pathogens contained therein is made possible.

(91) FIG. 3a shows a tube corresponding to FIG. 3, containing two internested cuffs, and which, in addition to the tracheal sealing by an inner balloon 2a at a relatively higher sealing pressure, also allows tamponading of the subglottal space by an outer balloon 2b at a relatively lower tamponade pressure. In addition to the concentric arrangement, a sequential arrangement of the trachea-sealing cuff (distal) and subglottal tamponade balloon (proximal), without a space in between, is conceivable.

(92) In the design illustrated in FIG. 4, the catheter shaft 4 used for the tracheal ventilation device is likewise made of polyurethane (PUR), since PUR, with an appropriate combination of material hardness and machining, such as profiling of the surface of the shaft, provides the option for manufacturing very thin-walled shafts which still have good anti-kink stability. In comparison to alternative materials such as silicone or PVC, this allows larger inner lumens that improve the flow resistance of the respiratory gas. Since the shaft has no filling line integrated into the shaft wall for the sealing cuff, as is common in conventional tube shafts, the inner lumen of the shaft that is active in ventilation may be correspondingly enlarged, and thus, the flow resistance during respiration or ventilation of the patient may be optimally reduced to a great extent.

(93) For stabilizing the shaft lumen and for allowing essentially tension-free axial bending of the shaft during placement in the airways, the particularly thin-walled shaft body 15 with a single-lumen design is provided with an undulating corrugation 16 on its surface. In the preferred case, it should be possible to axially bend the shaft from 90 to 180 degrees without relevant lumen constriction, and without elastic restoring forces, which are typical for polyurethane, acting on the tissue, which could potentially be traumatic. The shaft may thus optimally follow movements of the patient or relative movements between the shaft and the patient.

(94) For inner shaft diameters of 7-10 mm, with a combination of a wall thickness of approximately 0.3 to 0.5 mm, a Shore hardness value of 95 A to 75 D, a peak-to-peak corrugation spacing of 0.3 to 0.8 mm, and a corrugation amplitude of 0.5 to 1 mm, it is possible to produce a correspondingly kink-resistant, lumen-optimized shaft.

(95) The corrugation may be limited to the tracheal section of the tube shaft, but may also extend to the subglottal area or across the entire length of the shaft to the proximal end of the shaft and the connector 17 mounted at that location.

(96) In the case of the corrugated design of the shaft 4, when an exchangeable inner cannula is used, such as those common in tracheostomy cannulas, it is possible to use an inner cannula with a congruently corrugated profile, whose corrugation optimally conforms to the corrugation of the outer cannula and advantageously reinforces and stabilizes the outer cannula with a small combined wall thickness of the outer and inner cannulas, and thus allows partial wall thicknesses, for example, of 0.3 to 0.5 mm for the outer cannula and 0.1 to 0.3 mm for the inner cannula.

(97) The illustration shows a combined design of the shaft body, which has tracheal and glottal segments made of a single-layer, inner diameter-optimized shaft material, and which in the supraglottal segment transitions into a solid, for example injection-molded, PVC portion which, as illustrated in FIG. 1a, may be provided with multiple lumens 9 for the feed line to the balloon element. In particular, the subglottal portion may be strengthened by a possible reinforcing or multilayer design, so that it is used as a bite protector and thus, in particular for vigilant patients, avoids lumen closure of the tube when the jaws are closed.

(98) FIG. 4a shows a cross section of the embodiment in FIG. 5 in its glottal segment 18. The profile of the shaft may have a triangular design here, so that it rests with its base 19 on the dorsal surface of the vocal fold plane, and with its apex 20 points in the ventral direction, thus optimally adapting to the triangular opening of the vocal folds.

(99) FIG. 5 shows an example of an application of the invention for a tracheostomy cannula 21. Similar to the design for tracheal tubes, the proximal balloon end 10 here is guided through the stoma to the trachea. The balloon end may form a ridge-like widening 22 in front of the stoma. The proximal widening may be designed as a ridge-like widening, upon which connector 23 rests, which via a ring-like sealing lip 23 allows free movability of the connector on the shaft. The proximal widening may thus be pushed toward the stoma, and the device may thus be adapted to the particular neck anatomy.

(100) To ensure the sufficiently rapid volume flow of the filling medium between all intracorporeal portions of the cannula resting on the balloon 2, the balloon is preferably provided with a grooved, optionally reinforced recess, as described for FIG. 2c.

(101) In terms of the largest possible inner diameter, and thus, the lowest possible respiration or ventilation resistance, the shaft body 4 of the cannula is likewise preferably made of thin-walled PUR having a corrugated profile, as described for FIG. 4.

(102) With reference to FIG. 6, to avoid sudden, retrograde, potentially seal-critical emptying of the balloon volume toward the regulator or the reservoir, which may occur, for example, when the patient coughs several times in quick succession, the connecting feed line 6 between the shaft and the regulating reservoir unit may be equipped with a flow-directing valve 26 that prevents the rapid backflow of filling medium. The valve should be designed in such a way that it impairs the open anterograde volume flow from the regulator toward the balloon as little as possible.

(103) To avoid pooling effects of medium in the balloon caused by the valve 26, the valve is preferably equipped with a nonflow-directed bypass throttle 27 that is open on both sides, and which allows a slow, delayed pressure or volume compensation between the two end-side compartments of the balloon 2 and the regulator 3. In the simplest embodiment, the sealing valve surface in question is provided with a small borehole or opening that allows an appropriate throttled volume flow.

(104) FIG. 7 describes an example of a design of a combined regulator and reservoir unit 3. The unit has some design features of a so-called Lanz regulator (see US . . . ). The essential functional component of the unit 3, the same as for the unit according to Lanz, comprises a special volume-expandable balloon bladder 28 made of highly elastic material, and which due to filling, transitions from a certain preformed, for example spherical, base or resting shape 29 into a stretched working shape 30. When suitable materials are used, a certain expansion behavior of the balloon bladder may be achieved, in which the volume increases with isobaric pressure development in the balloon. The associated conceptually desired pressure-volume curve is illustrated in FIG. 7a. The balloon bladder is preferably made of a natural latex-like material or a synthetic material, such as an isoprene-related material. The balloon bladder rests on a pedestal housing 31 in which a one-way valve 32 for filling with air is preferably installed.

(105) FIG. 7a shows a pressure-volume curve as an example of FIG. 7, and which provides a constant pressure over a specified volume range VP. Thus, a volume of the balloon 2 may flow out of the expanded balloon 30, without a pressure loss resulting due to the volume outflow in the reservoir, i.e., leaving the pressure plateau DP. For applications of this regulator technology with ventilation tubes, the isobaric volume range IBV which is settable in this way should correspond approximately to the freely formed volume of the trachea-sealing balloon.

(106) FIG. 7b shows a special double-chamber reservoir balloon arrangement DR, in which two balloon-based reservoirs according to FIGS. 7 and 7a are mounted on a single, shared based housing 33. One chamber allows a trachea-sealing pressure of 25 to 30 mbar, while the other chamber allows the setting of a tamponade pressure of 5 to 15 mbar, for example for the subglottal tamponade as described for FIG. 3a.

(107) FIG. 8 shows a tracheal tube which is provided with a pressure-sensitive or pressure-measuring sensor element 34 inside the trachea-sealing balloon segment 2. In one preferred embodiment, the pressure sensor is an electronic component that relays its measuring signal to an electronically controlled regulator 36 via a cable line 35. The sensor element preferably comprises an absolute pressure sensor. Sensors based on strain gauges or piezoelectric sensors may preferably be used. The regulator 36 has a bellows-like or piston-like reservoir 37, for example, that is actuated by a drive 38 and either shifts volume to the balloon 2 or removes volume from the balloon 2; the drive may, for example, comprise a step motor or may be designed as a linear magnetic drive. The control of the regulator is designed in such a way that deviations in the filling pressure in the area of the sealing balloon segment 2 may be immediately compensated for by a corresponding volume shift, or the filling pressure may be held constant at a setpoint value SW that is settable with the regulator. With this method, the sealing balloon pressure is stabilized at a point in time that is optimally before the mechanical ventilation stroke begins, and before the actual volume flow of respiratory gas into the patient's lungs. This is particularly relevant for patients who must expend increased breathing effort after a long period of controlled machine-assisted ventilation in order to stretch an insufficiently volume-expandable lung to a point that triggers an effective volume flow into the lung. In this phase of the isometric tensioning of the lung within the thorax and the decrease in pressure within the thorax that accompanies the tensioning of the reinforced lung, drops in the filling pressure of the balloon may occur due to aspiration.

(108) In contrast to a mechanical regulator 3 having a simple design, which provides an isobaric reserve volume of preferably 20 to 35 mbar, with the described electronic regulation a pressure may be built up which briefly exceeds the tracheal uncritical sealing pressure of 20 to 35 mbar, and may thus sealingly counteract pressure peaks in the tracheal balloon possibly caused by the patient.

(109) FIG. 9 shows a so-called larynx mask 39, which on a regulating reservoir unit 3 is equipped with flow-optimized feed lines 6, 9 as well as an optional valve-throttle combination 7 according to the invention. The closed balloon element 2, which is generally toroidal or ring-shaped, seals the larynx in the area of the hypopharynx, and is preferably made of a micro thin-walled PUR material corresponding to the materials proposed here for manufacturing the sealing balloon of tracheal ventilation catheters. For use in the hypopharynx, the regulator component is designed in such a way that a sealing pressure plateau DP of approximately 50 to 60 mbar develops within the communicating interior.

(110) FIG. 10 shows a transesophageal probe 40 for supplying or discharging substances or media into the stomach or through the stomach, and which is equipped with an esophagus-sealing balloon element 2. The proximal balloon end 10 may be extended to the area of the extracorporeal connector 17. At this location it may be sealingly connected to a sealing closure element 23 that is freely movable on the shaft, and which in turn transitions into a large-bore feed line 6 that is connected to a regulation mechanism 3 according to the invention. For the esophageal sealing, the regulator component sets a sealing pressure plateau DP of approximately 20 to 30 mbar within the communicating interior.

(111) To assist the tamponading sealing balloon segment in remaining stationary in the esophagus, the balloon segment may be provided with a noncollapsible profile 41 in the esophageal area, which, in the event of a peristaltic contraction of the esophagus, draws volume from the balloon segments in front of the peristaltic contraction, and through or underneath the profile in areas that have already been released from the contraction. Mushrooming of filling medium in front of the peristaltic contraction, which would result in transport of the entire device toward the stomach, may thus be prevented. Corresponding profiles have already been described in EP 0929339 B1, and within the scope of the present invention may be used to the full extent as disclosed therein.