Valve arrangement, ventilation device, method of operating a valve arrangement, computer program

Abstract

Embodiments relate to a valve arrangement, a ventilation device, a method for operating a valve arrangement and a computer program. A valve arrangement for a ventilation device comprises an inlet configured for inflow of ventilation gas, an outlet configured for outflow of ventilation gas, and a device for regulating a volume flow of ventilation gas between the inlet and the outlet. The device for regulating a volume flow is configured to adjust the volume flow of ventilation gas in a range between a blockage and a maximum volume flow. The device for regulating a volume flow is configured such that the attenuation of a volume flow change when the volume flow of ventilation gas increases is different from the attenuation of a volume flow change when the volume flow of ventilation gas decreases.

Description

Technical Field

[0001] The present invention relates to a valve device, a ventilation device, a method for operating the valve device, and a computer program, and particularly, but not exclusively, to a concept for more robustly regulating volumetric flow in a ventilation device. Background Technology

[0002] When controlling mechanical ventilation or respiratory support, rapid proportional valves are typically used to control and / or regulate volumetric flow toward the patient (inspiration) and away from the patient (expiration).

[0003] Alternatively, a rapidly modulated gas source can be used. These gas sources are mostly found in respiratory support and CPAP (continuous positive airway pressure) devices.

[0004] Volumetric flow control during ventilation requires a high level of dynamics. Electromagnetic actuators are typically used in this context. These components are large and heavy, and require high power input. The faster these components need to be regulated, the more pronounced these drawbacks become. These drawbacks are a significant factor for cost-effective and / or mobile applications.

[0005] Alternatively, the valve can be pneumatically actuated. This largely eliminates the aforementioned drawbacks. However, this often results in a pronounced tendency to vibrate, thus requiring strong limitation of the frequency range or very precise adjustment of the valve regulator depending on the circumstances, including patient characteristics. Summary of the Invention

[0006] Starting from this point, the objective of this invention is to create an improved concept for volumetric flow regulation during patient ventilation.

[0007] This task is addressed in accordance with the subject matter of the parallel independent claims.

[0008] The embodiments are based on the understanding that, during patient ventilation, a rapid change in volumetric flow is desired when the valve is open at the start of the respiratory phase. At the onset of inspiration, the volumetric flow should increase dramatically. Conversely, during or at the end of inspiration, the change in volumetric flow is slower. The same applies to expiration, where the volumetric flow should also increase rapidly at the beginning, with slower changes occurring in subsequent stages. Based on this understanding, the valve device can be designed such that the decay of the volumetric flow change when open differs from the decay when closed. This allows for the desired dynamics of the volumetric flow throughout the respiratory phase while effectively attenuating unwanted disturbance variables. These disturbance variables often exhibit harmonic progressions, thus requiring harmonic changes in the volumetric flow, i.e., changes that are equally rapid both during increase and decrease. However, since the decay in the embodiments differs between open and closed states, the disturbance variables generally experience decay.

[0009] An embodiment provides a valve device for a ventilation apparatus, the valve device having an inlet configured to allow ventilation gas to flow in and an outlet configured to allow the ventilation gas to flow out. The valve device further includes means for regulating the volumetric flow of the ventilation gas between the inlet and the outlet. The means for regulating the volumetric flow is configured to adjust the volumetric flow of the ventilation gas within a range between blockage and maximum volumetric flow. The means for regulating the volumetric flow is configured such that the volumetric flow change attenuates when the valve is open, when the volumetric flow of the ventilation gas increases, unlike the attenuation when the valve is closed, when the volumetric flow of the ventilation gas decreases. Thus, in this embodiment, the valve device can suppress disturbance variables while maintaining desired dynamics, thereby reducing other costs associated with these disturbance variables, particularly reducing complexity in the case of a regulator.

[0010] In an embodiment, the attenuation can limit the rate of change of volumetric flow, thereby limiting the maximum change in volumetric flow per unit time differently when the circuit is on and off. This allows for the attenuation or reduction of disturbance variables that are above the limit, at least within the frequency range.

[0011] For example, a device for regulating volumetric flow can be configured such that the shortest opening time period differs from the shortest closing time period, during which the flow is regulated from blocked to maximum volumetric flow, and during the closing time period, it is regulated from maximum volumetric flow to blocked. The opening and closing speeds may differ. This may be the case when fully open and closed, but it may also be the case when varying within a moderate range of volumetric flow. Accordingly, the device for regulating volumetric flow can also be configured such that the attenuation during opening differs from the attenuation during closing, regulating from blocked to maximum volumetric flow during opening, and regulating from maximum volumetric flow to blocked during closing.

[0012] For example, a device used to regulate volumetric flow may have a lower attenuation when open than when closed. Thus, during ventilation, this could mean that the volumetric flow can be rapidly changed at the start of the corresponding respiratory phase, but the closing process is slower. In other words, a device used to regulate volumetric flow may have a greater attenuation, for example, when closed than when open.

[0013] Therefore, when performing ventilation, the following advantages can be achieved in particular: for a regulating design of a device for regulating volumetric flow, the parameters of the regulator, i.e., the analog or digital regulator, can be designed to have increased robustness relative to disturbance variables due to the intentionally slow design of the closing process during the exhalation phase, because the dynamic requirements of regulating the valve during the exhalation phase can be reduced through the structural design of the valve compared to the dynamic requirements of regulating the valve during the inhalation phase.

[0014] In an alternative implementation, it is also possible that, to achieve this effect, the valve is manipulated in exactly the opposite manner and closed at the start of the breathing phase. Thus, the device for regulating volumetric flow can, for example, have higher inertia (lower attenuation) when open than when closed. Different circuit variations are conceivable in the embodiments, particularly parallel circuits, series circuits, and bypass circuits, which can be implemented correspondingly using valve devices with different attenuation centers (when open or closed).

[0015] In some embodiments, the device for regulating volumetric flow may have a pneumatic control element for controlling the volumetric flow by controlling the pressure volume, wherein the limitation on the rate of change of the pressure volume when open is different from the limitation on the rate of change of the pressure volume when closed. Generally, pneumatic control / regulation can provide less inertia than, for example, electromagnetic control. For example, the pneumatic control element may include a pilot valve (pneumatically / electrically operable) or a pneumatic pump (electrically operable) that can be adjusted by controlling the pressure volume.

[0016] The device for regulating volumetric flow can have a diaphragm valve controllable by the pneumatic control element. This allows for efficient setting and regulation of the volumetric flow. The diaphragm valve can be operated via a loading connection and an unloading connection, wherein the loading connection and the unloading connection can have different constraints. Different constraints represent effective measures to achieve different attenuations.

[0017] Different constraints can be set, thereby allowing for further adaptation to specific situations, such as patient conditions. The device for regulating volumetric flow may also include control mechanisms for dynamically controlling the constraints, thereby enabling adaptation of these constraints during the ventilation process.

[0018] In some embodiments, the loading connection and the unloading connection may also share common constraints. Therefore, a basic attenuation can be defined for both directions.

[0019] The pneumatic control element may include, for example, an electrically operable pneumatic pump. The device for regulating volumetric flow may have a diaphragm valve, which can be operated by the pneumatic control element and via a control connection. The device for regulating volumetric flow may include an electrical control element for operating the pneumatic pump. Thus, the pneumatic pump can be effectively integrated into a regulating or control loop and function as a regulating element.

[0020] The valve device can be designed to incorporate constraints in the control connection, such constraints being configured to limit a basic attenuation. These constraints in the control connection are also adjustable, thereby adapting to specific situations.

[0021] Furthermore, the embodiments create a ventilation device having the valve device described herein for performing intake.

[0022] Furthermore, the embodiments create a ventilation device having the valve device described herein for performing exhalation.

[0023] Devices used to regulate volumetric flow for inspiration and expiration can have lower attenuation when open than when closed. This allows for the alteration of volumetric flow at the desired rate at the onset of the respiratory phase without sacrificing attenuation of disturbance variables with similar rates of change in volumetric flow.

[0024] At least one of the devices for regulating volumetric flow for inhalation and exhalation can be configured to allow the volumetric flow change when open to be at least 2, 4, or 8 times that when closed, within the same unit of time. This allows for the selection of an appropriate ratio of the rate of change to the attenuation.

[0025] At least one of the devices used to regulate volumetric flow for inspiration and expiration can be configured to allow the change in patient pressure when open to be at least 2, 4, or 8 times the change in patient pressure when closed, within the same unit of time. An appropriate ratio between the rate of change and the attenuation can also be selected based on the change in patient pressure.

[0026] Another embodiment is a ventilation system having the ventilation device described herein.

[0027] The embodiment also creates a method for operating a valve device in a ventilation device. The valve device includes an inlet for allowing ventilation gas to flow in, an outlet for allowing the ventilation gas to flow out, and means for regulating the volumetric flow of the ventilation gas between the inlet and the outlet. The method includes adjusting the volumetric flow of the ventilation gas within a range between blockage and a maximum flow rate. The valve device is opened with a first attenuation, wherein the volumetric flow of the ventilation gas increases, and the valve device is closed with a second attenuation, wherein the volumetric flow of the ventilation gas decreases. The first attenuation differs from the second attenuation.

[0028] Another embodiment is a computer program having program code for performing one of the methods described herein when the program code is executed on a computer, processor, or programmable hardware component. Attached Figure Description

[0029] Some examples of devices and / or methods are explained in more detail below with reference to the accompanying drawings.

[0030] Figure 1 Embodiments of valve devices and ventilation equipment are shown;

[0031] Figure 2 A block diagram illustrating an embodiment of a method for operating a valve device in a ventilation system is shown;

[0032] Figure 3 An embodiment of a ventilation system with typical components is shown;

[0033] Figure 4 An embodiment of a ventilation system with a pneumatic pilot valve is shown;

[0034] Figure 5 A diagram illustrating a typical gas exchange process with respiratory phases is shown.

[0035] Figure 6 An illustration of a respiratory system with a pilot valve and specific attenuation is shown in an embodiment;

[0036] Figure 7 The illustration shows different frequency responses on a Bode plot of a low-pass characteristic in the embodiment;

[0037] Figure 8 Another embodiment is shown;

[0038] Figure 9 It shows Figure 8 Bode plot of an embodiment;

[0039] Figure 10 Another embodiment is shown;

[0040] Figure 11 It shows Figure 10 Bode plot of an embodiment;

[0041] Figure 12 Another embodiment with single attenuation is shown;

[0042] Figure 13 An embodiment with separate attenuation for loading / unloading is shown; and

[0043] Figure 14 An embodiment with adjustable attenuation is shown. Detailed Implementation

[0044] Various examples will now be described in more detail with reference to the accompanying drawings. In the drawings, the thickness of lines, layers, and / or regions may be exaggerated for clarity.

[0045] Other examples may cover modifications, equivalents, and alternatives that fall within the scope of this disclosure. Identical or similar reference numerals throughout the description of the drawings refer to identical or similar elements that, when compared with each other, may be implemented in the same or modified form while providing the same or similar function.

[0046] It should be understood that when one element is referred to as "connected" or "coupled" to another element, these elements can be directly connected or coupled, or connected or coupled via one or more intermediate elements. When "or" is used to combine two elements A and B, it should be understood that all possible combinations are disclosed, i.e., only A, only B, and A and B, unless otherwise expressly or implicitly defined. Alternative wording for the same combination is "at least one of A and B" or "A and / or B". This also applies to combinations of more than two elements, with necessary modifications.

[0047] Figure 1 An embodiment of the valve device 10 and an embodiment of the ventilation device 100 are shown.

[0048] The valve device 10 for the ventilation device 100 (shown in dashed lines because it is optional from the perspective of the valve device) includes an inlet 12 configured to allow ventilation gas to flow in. Furthermore, the valve device 10 includes an outlet 14 configured to allow ventilation gas to flow out. Additionally, the valve device 10 includes a means 16 for regulating the volumetric flow of the ventilation gas between the inlet 12 and the outlet 14. The means 16 for regulating the volumetric flow is configured to adjust the volumetric flow of the ventilation gas within a range between blockage and maximum volumetric flow. The means 16 for regulating the volumetric flow is configured such that the attenuation of the volumetric flow change when open, where the volumetric flow of the ventilation gas increases, differs from the attenuation when closed, where the volumetric flow of the ventilation gas decreases.

[0049] like Figure 1As shown in the dashed line, as an optional embodiment, a ventilation device 100 (or ventilation system 100) having a valve device 10 for inhalation and / or a valve device 10 for exhalation is another embodiment.

[0050] Figure 2 A block diagram of an embodiment of a method 20 for operating a valve device 10 in a ventilation device 100 is shown. The method 20 for operating the valve device 10 in the ventilation device 100 includes adjusting the volumetric flow of ventilation gas 22 within a range between blockage and maximum flow. The method 20 also includes opening valve device 24 with a first attenuation, wherein the volumetric flow of ventilation gas increases, and closing valve device 26 with a second attenuation, wherein the volumetric flow of ventilation gas decreases. The first attenuation differs from the second attenuation.

[0051] In some embodiments, the adaptation of the pneumatic regulation section can be achieved using a damping element. This damping element draws energy from the system once the output variable changes rapidly. Therefore, the excited deflection of the output variable no longer readily leads to sustained or even increased vibration amplitude. However, this damping element primarily operates in the presence of undesirable excitations (disturbing variables) so as not to affect, or only minimally affect, the actual ventilation performance in the sense of a rapid increase in pressure.

[0052] In principle, digital regulators can also selectively amplify known frequencies within the regulator band weakly, thereby reducing or suppressing oscillations. However, this requires corresponding computing power.

[0053] Some embodiments use a fixed attenuation setting integrated into the regulating section. This reduces the load on the regulator and allows for more operation while reducing certain resonant overshoots.

[0054] Thus, the device 16 for regulating volumetric flow can have lower attenuation when open than when closed, or vice versa, depending on which direction greater dynamics (faster change) is desired. This can vary depending on interconnection and application, as rapid change is desired at the beginning of each respiratory phase during ventilation, as will be explained in more detail below. This rapid change can be achieved using circuitry techniques via rapid opening or closing. Therefore, the device 16 for regulating volumetric flow can also have higher inertia when open than when closed, depending on the application and circuitry variations.

[0055] Several embodiments are explained in more detail below, wherein the device 16 for regulating volumetric flow has a pneumatic control element for controlling the volumetric flow by controlling the pressure volume. The limitation on the rate of change of pressure volume when open differs from the limitation on the rate of change of pressure volume when closed.

[0056] This can be achieved through corresponding integrated attenuation. The attenuation is integrated in a specific way such that the desired rapid response of the regulation segment is unrestricted or only slightly restricted, and that the highest possible attenuation is applied to undesirable rapid disturbance variables.

[0057] For example, if the vibration produces a signal that is too steep, the attenuation element should draw energy from the system.

[0058] Therefore, it is meaningful to establish the equations of motion for the mechanical oscillation model, which will be done below—as explained based on Equation 1—using a diaphragm valve as an example.

[0059] Formula 1

[0060] Where E is the total force.

[0061] M is the mass.

[0062] D represents the decay or friction with an associated decay constant.

[0063] F is a spring with an associated spring constant.

[0064] It refers to distance in a time-dependent representation, such as the movement of the diaphragm;

[0065] Here is the first derivative with respect to time, i.e., the velocity of the diaphragm; and

[0066] It is the second derivative with respect to time, i.e., the acceleration of the diaphragm.

[0067] In this example, mass is the mass of the diaphragm and all moving parts.

[0068] Here, damping is represented, for example, by the viscosity of the diaphragm suspension or other forces generated when the diaphragm should change at a certain velocity. Specifically, damping can be used to effectively suppress resonant hyperextension caused by the combination of multiple vibrating components, which will also be discussed below based on... Figure 7 To explain in more detail.

[0069] The force related to the spring adjustment path. Typically, this is a control variable used to adjust the diaphragm position. The system itself also includes a spring characteristic curve in combination with said control variable.

[0070] In a pneumatic system, as exemplified in a ventilation system, there are many components, each exhibiting specific, independent behavior in response to stimuli or generating its own stimuli.

[0071] Figure 3 An embodiment of a ventilation system with typical components is shown. Figure 3 The patient is shown on the right, represented schematically by a lung 30. The lung 30 is coupled to the expiratory path 40 and the inspiratory path 50 via a Y-shaped connection through a ventilation tube. An expiratory valve 42 and a check valve 44 are present in the expiratory path 40, with the check valve 44 preventing volumetric flow towards the patient. Similarly, an inspiratory valve 52 and a check valve 54 are present in the inspiratory path 50, with the check valve 54 preventing volumetric flow away from the patient. The expiratory valve 42 and the inspiratory valve 52 are here coupled to a sensor 60 that detects pressure or volumetric flow. The system may also include additional sensors 62 at different locations that detect corresponding measurement variables for regulation. The inspiratory valve 52 is coupled on the input side to a gas source 70 for providing respiratory gas. These components also appear in the embodiments explained below and will not be described further.

[0072] The excitation occurring during normal operation is caused by changes in the nominal variable resulting from ventilation control, for example, during the switching between the inhalation-to-exhalation and exhalation-to-inhalation ventilation phases. This excitation should be transmitted as quickly as possible and should reach the system in the asymptotic limit. Additional excitations from other influences of the system or other components should be attenuated as much as possible. This means that the sum of the responses from all components must be less than the gain of 1.

[0073] Ideally, this means that excitation caused, for example, by a mechanical shock through a ventilation duct, will not produce pressure oscillations. Through a system with poor attenuation, this excitation (rapid pressure wave) can propagate to all components in the system with low loss. If the response of another component is 1 (resistance jumps are echoed accordingly) or even higher, the excitation at the next oscillation amplitude is at least as high as or even higher than the first excitation. The system then begins to oscillate.

[0074] Furthermore, each component of the system is equipped with its own frequency response. This frequency response can be represented as a Bode plot. Because vibration involves the exchange of energy and mass, a strongly nonlinear frequency progression is also derived. This results in a resonant range with respect to frequency. The resonant frequency, quality (width of the resonant range), and amplitude are only partially constant. Some components are, for example, strongly temperature-dependent (diaphragms made of elastomers) or are also individual and variable (patient compliance (scalability) and resistance changing over time).

[0075] Exceeding the resonant frequency will also cause a phase change, thereby shifting the system's response by, for example, 180°, and turning the hypothetical negative feedback from the regulator into positive feedback to the disturbance variable.

[0076] This can be offset by attempting to integrate as many low-pass components as possible into the system, thus effectively suppressing the rapid response. Unfortunately, this results in a slower overall system behavior, where the pressure rise time is insufficient for ventilation.

[0077] At least some embodiments generate high attenuation through constraints, i.e., resistance or contraction in the pneumatic system. Passing volumetric flow through this constraint results in high pressure loss, which in turn leads to energy loss.

[0078] When these components are examined in more detail, the beginning of each respiratory phase is the timeframe within which a high pressure gradient is required and desired. For inspiratory valve 42, this marks the start of inspiration. For the remainder of the ventilation process, a more decaying behavior is desired. While this may result in slower compensation for disturbance variables, excessively high system response amplitudes are no longer observed.

[0079] In this embodiment, the regulating section for pneumatic pressure / volume flow regulation in the ventilation technology can be designed to enable operation over a wide frequency range while maintaining reasonable regulator costs. Passive components can be used to suppress vibration excitation. This results in a lower computational burden, for example, for software regulators. Thus, in this embodiment, basic attenuation can be achieved via pneumatic components and coordination can be achieved through regulator parameterization.

[0080] In some embodiments, the pneumatic control element is, for example, a pneumatic pump or a pilot valve that can be adjusted by controlling the pressure volume.

[0081] Figure 4 An embodiment of a ventilation system or ventilation device 100 with pneumatic pilot valves 17a, 17b is shown. Based on Figure 3 The illustrated ventilation device 100 includes valve devices 10a and 10b in the exhalation path 40 and inhalation path 50, respectively. Valve device 10a includes an inlet 12a, an outlet 14a, and a device 16a for regulating volumetric flow. Similarly, valve device 10b includes an inlet 12b, an outlet 14b, and a device 16b for regulating volumetric flow. The devices 16a and 16b for regulating volumetric flow each have diaphragm valves 42 and 52 (exhalation valve 42, inhalation valve 52), which can be controlled by pneumatic control elements (pilot valves 17a and 17b), wherein diaphragm valves 42 and 52 can be operated via loading connections 18a and 18b and unloading connections 19a and 19b (discharge to the atmosphere), respectively. In various embodiments, various implementations of the valves are conceivable regarding their normal state (the static state without power). Thus, for example, it is possible to distinguish between a valve in its normally open (NO) state and a valve in its normally closed (NC) state. Figure 4In the illustrated embodiment, the pilot valve 17a in the exhalation path 40 is implemented as NC, and the exhalation valve 42 is implemented as NO. In the inhalation path 50, the pilot valve 17b is NO, and the inhalation valve 52 is NC. Other implementations, particularly the opposite implementations, are conceivable in other embodiments. These components also appear in the embodiments explained below and will not be described further.

[0082] Figure 5 A diagram illustrating a typical gas exchange process with respiratory phases is shown. Figure 5 A time flow chart is shown, where time is plotted to the right and pressure P... AW Alternatively, the position of the diaphragm can be drawn qualitatively upwards. The upper part shows a schematic progression of the respiratory phases with an inspiratory phase 56 and an expiratory phase 46. During the inspiratory phase 56, the pressure is qualitatively high to induce a volumetric flow toward the patient during inspiration, and during the expiratory phase 46, the pressure is low to induce a volumetric flow away from the patient during expiration. Figure 5 The process of setting or positioning the diaphragm of the inspiratory valve 52 is shown in the middle section, and the process of setting or positioning the diaphragm of the expiratory valve 42 is shown in the lower section. In the upper process 501, the valves are closed, while in the lower process 502, the valves are correspondingly opened.

[0083] from Figure 5 It can be seen that the inhalation valve 52 opens suddenly (rapidly) at the beginning of the inhalation phase 56, and then closes slowly again during the process of the inhalation phase 56. Similarly, the exhalation valve 42 opens suddenly (rapidly) at the beginning of the exhalation phase 46, and then closes slowly again during the process of the exhalation phase 46. The rapid opening of valves 42 and 52... Figure 5 The text is highlighted by arrow 503. (Example) Figure 5 It is also shown that during the closing process of valves 42 and 52, adjustment processes occur in stages 46 and 56, which represent small fluctuations in the diaphragm position (dynamic adjustment) and... Figure 5 The arrow 504 is highlighted in the middle.

[0084] Figure 6 A diagram of a respiratory system with pilot valves 17a, 17b and a specific attenuation is shown in one embodiment. Figure 6 It shows Figure 4 The apparatus has identical components, wherein loading connections 18a, 18b and unloading connections 19a, 19b have different constraints R1, R2, R3, R4 as limits. For example, constraints R1 and R3 in loading connections 18a, 18b are each selected as 40 mbar / (L / min), while constraints R2 and R4 in unloading connections 19a, 19b are each selected as 5 mbar / (L / min).

[0085] Therefore, in some embodiments, constraints R1, R2, R3, and R4 are integrated into the operation of the valve with a pilot valve. Inhalation and exhalation are performed separately on sides 18a and 18b, and rapid pressure changes do not require loading of connections 18a and 18b. Specifically, attenuation here should reduce the transmission of disturbance variables as positive feedback to the regulator system. The attenuation of the respiratory system itself is unaffected. This has the advantage of having no other moving parts in the system.

[0086] As mentioned earlier, attenuation for confounding variables is integrated here. The rapid changes expected at the start of respiration phases 46 and 56 should be attenuated as little as possible or as minimally attenuated as possible.

[0087] In the case of intake valve 42, the valve is designed as NC (normally closed). This embodiment has already been implemented. Figure 4 Overview. Pilot valve 17b is therefore configured as NO (normally open) to keep inspiratory valve 42 closed. At the onset of inspiration 46, inspiratory valve 42 should be able to open as quickly and wide as possible. During the rest of inspiration 46, only compensation / correction (here, particularly for patient) for compliance strain and possible interference variables is made. During expiration 56, inspiratory valve 42 remains almost completely closed and only compensation for leakage and possible interference variables is made. This valve device, including constraints R1, R2, R3, and R4, is... Figure 6 Overview. These constraints are used to dampen the system and are designed to unload with a small resistance value R2. Higher pressures are loaded by constraints with higher resistance values. This results in damping that primarily acts on the closing of the intake valve 42, but produces little or no damping on its opening.

[0088] As mentioned above, for disturbance variables and vibration excitation, energy needs to be extracted from the system, where the attenuation distributed on opening / closing has no effect on the overall attenuation. A similar requirement applies to the exhalation valve 52. Here, the exhalation valve 52 is implemented as a NO (normally open) type, thereby the pilot valve 17a is implemented as an NC (normally closed) type. Exhalation of the exhalation valve 52 must proceed rapidly at the start of exhalation 56, while closing can occur attenuatedly. Here, the constraint R4 for unloading is also small, while the constraint R3 for loading is large. According to general technical teachings, the difference between the above valve types NC and NO is as follows:

[0089] A NO valve is in the "OPEN" state without external activation, meaning gas can flow through the valve. An NC valve is in the "CLOSED" state without external activation, meaning no gas can flow through the valve.

[0090] For example, when controlling the pressure volume at 5 ml, the following values ​​are used as constraint values:

[0091] Inhale:

[0092] Loading R1 = 40 mbar / (L / min) Unloading R2 = 5 mbar / (L / min)

[0093] Exhale:

[0094] Load R3 = 40 mbar / (L / min) Unload R4 = 5 mbar / (L / min).

[0095] Figure 7 Illustrations of some frequency responses with Bode plots and low-pass characteristics in the embodiments are shown. Figure 7 The Bode plot is shown, which shows the magnitude logA plotted upwards logarithmically and the frequency logf / Hz plotted to the right logarithmically in Hertz. Figure 7 The upper part illustrates a classic low-pass process 701, where the attenuation increases steadily from the threshold frequency and the amplitude decreases accordingly. Conversely, in one embodiment, Figure 7 The middle section shows process 702 with resonance, i.e., amplitude super-high (magnified) without attenuation, and process 703 with resonance with adaptive attenuation. Figure 7 The lower section also shows a comparison between a frequency response 704 with strong attenuation (lower threshold frequency) and a frequency response 705 with small attenuation (higher threshold frequency).

[0096] Figure 8 Another embodiment is shown, in which constraints R5 and R6 are introduced in the control circuit / control connection, respectively. Figure 9 Showing from Figure 8 The Bode plot of an example.

[0097] This embodiment involves introducing additional energy harvesting systems that can or must be adjusted individually. For this purpose, an implementation with constraints and volumes located behind the constraints is shown. The two valves 42, 52 to be controlled have control pressure volumes 48, 58 respectively located behind the diaphragm.

[0098] Here, according to Formula 2, the limiting frequency can be set using the size of the volume (C is the volume capacity) and constraints R5 and R6:

[0099] ω=1⁄(2π*R*C) Formula 2.

[0100] For example, constraints R5 and R6 are chosen to be 10 mbar / (L / min). Lowering the threshold frequency also helps suppress the transmission of higher frequency components. Here, maintaining volume under adapted constraints may be particularly advantageous because energy extraction can be modulated in particular. The volumes of the inspiratory valve 48 and expiratory valve 58 used to control pressure can be used here for volume control (see...). Figure 8 ). Figure 9 Frequency responses 901 with strong attenuation (e.g., according to R1, R3 as described above), 902 with moderate attenuation (e.g., according to R5, R6 as described above), and 903 with small attenuation (e.g., according to R2, R4 as described above) are shown.

[0101] In another embodiment, one or more constraints can be fixed, variable, or dynamic, and can be adjusted, for example, by a control device. This allows for dynamic adjustment of these elements to achieve a sufficiently fast system response and adequate suppression of disturbance variables under desired pressure switching conditions.

[0102] Figure 10 Another embodiment is shown in which the attenuation in the control line / control connection is adjustable. Figure 11 It shows Figure 10 The Bode plot of the embodiments. In these embodiments, constraints R7 and R8 can be adjusted, for example, in the range of 1 to 40 mbar / (L / min). Then, the device 16 for regulating the volumetric flow can also include a control device for dynamically controlling constraints R7 and R8. Furthermore, the loading connection and the unloading connection can also have common constraints. Figure 11 Based on the corresponding Bode plots, the frequency response 1101 with strong attenuation (high R7 and R8) and the frequency response 1102 with weak attenuation (low R7 and R8) are shown.

[0103] In other embodiments, the pneumatic control element may include pneumatic pumps 49 and 59. Figure 12 Another embodiment with a single attenuation R10 is shown, similar to Figure 8 Examples are shown in the text. Figure 12 As shown, constraints R9 and R10, for example, with a size of 10 mbar / (L / min), are located in the control connection between pumps 49 and 59 and valves 42 and 52, respectively. In this embodiment, the means for regulating volumetric flow includes diaphragm valves 42 and 52, which can be controlled by pneumatic control elements 49 and 59. Diaphragm valves 42 and 52 can be manipulated via control connections. The means for regulating volumetric flow may also include electrical control elements for controlling the pneumatic pumps, such as controllers, processors, or programmable hardware. In the same manner, in other embodiments, adjustable constraints can also be electronically controlled or regulated. Therefore, another embodiment is also a computer program having program code for performing one of the methods described herein when the program code is executed on a computer, processor, or programmable hardware component.

[0104] Figure 13One embodiment is shown, featuring separate attenuations R11 and R14 (e.g., 5 mbar / (L / min)) for loading and attenuations R12 and R13 (e.g., 40 mbar / (L / min)) for unloading. For this purpose, in the control connection, downstream of pneumatic pumps 49 and 59, respectively, a (anti)parallel circuit consisting of constraints (R11, R12, R13, R14) and check valves (R11r, R12r, R13r, R14r) is connected. The check valves (R11r, R12r, R13r, R14r) ensure that breathing gas flows in only one direction in the corresponding branch. This allows for different attenuations when open and closed. Thus, in Figure 13 In this configuration, inspiratory valve 42 can only be opened via constraint R12 and check valve R12r, and similarly, expiratory valve 52 can only be opened via constraint R13 and check valve R13r. Likewise, inspiratory valve 42 can only be closed via constraint R11, and expiratory valve 52 can only be closed via constraint R14. The opening and closing dynamics can therefore be affected by appropriately selecting the constraints.

[0105] Similar to the embodiments described above, adjustable attenuation can also be used in embodiments with micropumps 49 and 59. Figure 14 An embodiment with adjustable attenuation is shown. Similar to the embodiments described above, the attenuation in embodiments with pumps 49 and 59 can also be constructed separately for loading and unloading (see...). Figure 13 And / or these attenuations can also be adjustable, such as Figure 14 As shown. The two constraints R13 and R14 in the control connection between pumps 49 and 59 and valves 42 and 52 are implemented here as adjustable, for example in the range of 1 to 40 mbar / (L / min).

[0106] In the embodiments of the ventilation device explained herein, the means for regulating volumetric flow for inhalation and exhalation are configured such that the attenuation when open is lower than the attenuation when closed. Typically, other embodiments or implementations are also conceivable.

[0107] For example, at least one of the devices for regulating volumetric flow for inhalation and exhalation is configured to allow the volumetric flow change when open to be at least 2, 4, or 8 times greater than the volumetric flow change when closed, within the same time unit. In a specific implementation, the volumetric flow change may be limited to 100 L / min over 30 ms during the rise and 100 L / min over 240 ms during the fall.

[0108] At least one of the devices for regulating volumetric flow for inspiration and expiration can be configured to allow patient pressure changes when open to be at least 2, 4, or 8 times greater than patient pressure changes when closed, within the same time unit. Thus, in one implementation, patient pressure changes can be limited to 40 mbar over 30 ms during the rise and to 40 mbar over 240 ms during the fall.

[0109] With one or more previously detailed examples and appendices Figure 1 The aspects and features described therein can also be combined with one or more other examples to replace the same features of the other examples or to additionally introduce features into the other examples.

[0110] Examples may also be or relate to computer programs having program code for performing one or more of the methods described above when the computer program is executed on a computer or processor. The steps, operations, or processes of the various methods described above may be performed by a programmed computer or processor. Examples may also cover program storage devices, such as machine, processor, or computer-readable digital data storage media that encode machine-executable, processor-executable, or computer-executable instructions. These instructions execute or cause some or all of the steps of the methods described above to be performed. Program storage devices may include, for example, digital memory, magnetic storage media (e.g., disks and tapes), hard disk drives, or optically readable digital data storage media. Other examples may also cover computers, processors, or control units programmed to perform the steps of the methods described above, or (field)programmable logic arrays ((F)PLAs) or (field)programmable gate arrays ((F)PGAs) programmed to perform the steps of the methods described above.

[0111] The specification and accompanying drawings represent only the principles of this disclosure. Furthermore, all examples implemented herein are intended, in principle, explicitly for illustrative purposes only, to aid the reader in understanding the principles of this disclosure and the concepts contributed by the inventors to advance the technology. All statements herein relating to the principles, aspects, and examples of this disclosure, and their specific examples, include their equivalents.

[0112] A function block that performs a specific function and is referred to as a “device for…” can involve a circuit that is constructed to perform a specific function. Therefore, a “device for…” can be implemented as “a device constructed for or suitable for…”, such as a component or circuit constructed for or suitable for a corresponding task.

[0113] The functions of the various components shown in the diagram, including each functional block referred to as a "device," "device for providing a signal," "device for generating a signal," etc., can be implemented as dedicated hardware, such as a "signal provider," "signal processing unit," "processor," "controller," etc., and as hardware implemented to execute software in conjunction with associated software. When provided by a processor, the functionality can be provided by a single dedicated processor, a single shared processor, or multiple separate processors, some or all of which may be shared. However, the terms "processor" or "controller" are not limited to hardware that can only execute software; they can also include digital signal processor (DSP) hardware, network processors, application-specific integrated circuits (ASICs), field-programmable logic arrays (FPGAs), read-only memory (ROM) for storing software, direct-access memory (RAM), and non-volatile storage devices. Other hardware, conventional and / or customer-specific, may also be included.

[0114] For example, a block diagram can represent a rough circuit diagram implementing the principles of this disclosure. Similarly, flowcharts, operation diagrams, state transition diagrams, pseudocode, etc., can represent various processes, operations, or steps that are substantially embodied in a computer-readable medium and thus executed by a computer or processor, whether or not such a computer or processor is explicitly shown. The methods disclosed in the specification or claims can be implemented by components having means for performing each of the corresponding steps of these methods.

[0115] It should be understood that the disclosure of multiple steps, processes, operations, or functions in the specification or claims should not be construed as being in a particular order, unless otherwise expressly or implied, for example, for technical reasons. Therefore, the disclosure of multiple steps or functions is not limited to a specific order unless these steps or functions are not interchangeable for technical reasons. Furthermore, in some examples, a single step, function, process, or operation may include and / or be divided into multiple sub-steps, sub-functions, sub-processes, or sub-operations. Unless expressly excluded, such sub-steps may be included and form part of the disclosure of that single step.

[0116] Furthermore, the following claims are incorporated herein by reference in the detailed description, wherein each claim may exist independently as a separate example. While each claim may exist independently as a separate example, it should be noted that although dependent claims in the claim set may relate to a particular combination with one or more other claims, other examples may also include combinations of dependent claims with the subject matter of each of the other dependent or independent claims. Such combinations are explicitly stated herein, unless otherwise stated that a particular combination is not intended to be used. Furthermore, the features of a claim should also be included in any other independent claim, even if the claim does not directly depend on that independent claim.

[0117] List of reference numerals

[0118] Valve devices 10, 10a, and 10b

[0119] Entrances 12, 12a, and 12b

[0120] Exports of 14, 14a, and 14b

[0121] 16, 16a, 16b: Devices for adjusting volume

[0122] 17a, 17b pilot valves

[0123] 18a, 18b Loading Connections

[0124] Uninstall links 19a and 19b

[0125] 20 Methods for operating valve devices

[0126] 22. Adjust the volumetric flow rate of the ventilation gas within the range between blockage and maximum flow rate.

[0127] 24. The valve device is opened with a first attenuation, wherein the volumetric flow of the ventilated gas increases.

[0128] 26. A second attenuation is used to close the valve device, wherein the volumetric flow of the ventilated gas is reduced, wherein the first attenuation differs from the second attenuation.

[0129] 30 patients / lung

[0130] 40. Expiratory Pathway

[0131] 42 Exhalation valve

[0132] 44 Check valve

[0133] 46. ​​Exhalation phase

[0134] 48. Controlling volume

[0135] 49 Pumps, micro pumps, pneumatic pumps

[0136] 50 Inhalation Path

[0137] 52 Intake valve

[0138] 54 Check valve

[0139] 56. Inhalation phase

[0140] 58. Controlling volume

[0141] 59 Pumps, Miniature Pumps, Pneumatic Pumps

[0142] 60 sensors

[0143] 62 sensors

[0144] 70 Gas Source

[0145] 100 ventilation equipment

[0146] 501 Closed

[0147] 502 Open

[0148] 503 Quick Open

[0149] 504 Dynamic Adjustment

[0150] 701 Low-pass process

[0151] 702 Resonant Process

[0152] 703 features a process with resonance and adaptive decay.

[0153] 704 Strong Attenuation Process

[0154] 705 The process of weak decay

[0155] 901 Strong decay process

[0156] 902 Moderate decay process

[0157] 903 The process of weak decay

[0158] 1101 Strong decay process

[0159] 1102 Weak decay process

[0160] R1-R14 constraints

[0161] R11r-R14r check valve

Claims

1. A valve device (10; 10a; 10b) for a ventilation device (100), said valve device having Inlets (12; 12a; 12b) are constructed to allow ventilation gas to flow in. The outlets (14; 14a; 14b) are configured to allow the ventilation gas to flow out; and Devices (16; 16a; 16b) for regulating the volumetric flow of the ventilation gas between the inlet (12; 12a; 12b) and the outlet (14; 14a; 14b). The means (16; 16a; 16b) for regulating the volumetric flow are configured to adjust the volumetric flow of the ventilated gas within a range between blockage and maximum volumetric flow. The means (16; 16a; 16b) for regulating the volume flow are configured such that the volume flow change decreases when the gas is turned on, unlike the decrease when the gas is turned off, which causes a sharp increase in volume flow when the gas is turned on and a slower change in volume flow when the gas is turned off. The device (16; 16a; 16b) for regulating volumetric flow has pneumatic control elements (17a; 17b; 49; 59) for controlling the volumetric flow by controlling the pressure volume (48; 58), wherein the limitation on the rate of change of the control pressure volume when open is different from the limitation on the rate of change of the control pressure volume when closed. The device (16; 16a; 16b) for regulating volumetric flow has a diaphragm valve (42; 52) controllable by the pneumatic control element (17a; 17b; 49; 59), wherein the diaphragm valve (42; 52) can be operated via a loading connection (18a; 18b) and an unloading connection (19a; 19b), wherein the loading connection (18a; 18b) and the unloading connection (19a; 19b) have different constraints as limitations.

2. The valve device (10; 10a; 10b) according to claim 1. in, The device (16; 16a; 16b) for regulating volumetric flow has a lower attenuation when it is turned on than when it is turned off.

3. The valve device (10; 10a; 10b) according to claim 1. in, The device (16; 16a; 16b) for regulating volumetric flow has a greater attenuation when closed than when open.

4. The valve device (10; 10a; 10b) according to any one of claims 1 to 3. in, The device (16; 16a; 16b) for regulating volumetric flow has higher inertia when it is open than when it is closed.

5. The valve device (10; 10a; 10b) according to claim 1. in, The pneumatic control elements (17a; 17b; 49; 59) include pilot valves that can be adjusted by controlling the pressure volume (48; 58) or include a pneumatic pump.

6. The valve device (10; 10a; 10b) according to claim 1. Different constraints can be set.

7. The valve device (10; 10a; 10b) according to claim 6. in, The device (16; 16a; 16b) for regulating volumetric flow also includes a control device for dynamically controlling the constraint.

8. The valve device (10; 10a; 10b) according to any one of claims 1 to 3, wherein, The loading connection (18a; 18b) and the unloading connection (19a; 19b) share common constraints.

9. The valve device (10; 10a; 10b) according to claim 1. in, The pneumatic control element (17a; 17b; 49; 59) includes a pneumatic pump, wherein the diaphragm valve (42; 52) is operable via a control connection, and wherein the device for regulating volumetric flow (16; 16a; 16b) includes an electrical control element for operating the pneumatic pump.

10. The valve device (10; 10a; 10b) according to claim 9. in, Constraints are arranged in the control connection.

11. The valve device (10; 10a; 10b) according to claim 10. in, The constraints in the control connection are adjustable.

12. A ventilation device having a valve device (10; 10a; 10b) for performing an intake phase according to any one of claims 1 to 11.

13. A ventilation device having a valve device (10; 10a; 10b) for performing an exhalation phase according to any one of claims 1 to 11.

14. The ventilation device according to claim 13, in, The devices (16; 16a; 16b) for regulating volumetric flow for inhalation and / or for regulating volumetric flow for exhalation have lower attenuation when open than when closed.

15. The ventilation device according to claim 14, in, At least one of the devices (16; 16a; 16b) for regulating volume flow for inhalation and exhalation is configured to allow the volume flow change when open to be at least 2, 4, or 8 times the volume flow change when closed in the same unit of time.

16. The ventilation device according to any one of claims 14 or 15, in, At least one of the devices (16; 16a; 16b) for regulating volumetric flow for inspiration and expiration is configured to allow the patient pressure change when open to be at least 2, 4, or 8 times the patient pressure change when closed in the same unit of time.

17. A method for operating a valve device (10; 10a; 10b) in a ventilation system. The valve device (10; 10a; 10b) includes an inlet (12; 12a; 12b) for allowing ventilation gas to flow in, an outlet (14; 14a; 14b) for allowing the ventilation gas to flow out, and a means (16; 16a; 16b) for regulating the volumetric flow of the ventilation gas between the inlet (12; 12a; 12b) and the outlet (14; 14a; 14b), the method comprising Adjust the volumetric flow of the ventilation gas (22) within the range between blockage and maximum flow. The valve device (10; 10a; 10b) is opened with a first attenuation (24), wherein the volumetric flow of the ventilated gas increases, and The valve device (10; 10a; 10b) is closed with a second attenuation (26), wherein the volumetric flow of the ventilated gas is reduced. The first attenuation differs from the second attenuation, causing a sharp increase in volumetric flow when the device is turned on, while the volumetric flow changes more slowly when the device is turned off. The device (16; 16a; 16b) for regulating the volumetric flow has pneumatic control elements (17a; 17b; 49; 59) for controlling the volumetric flow by controlling the pressure volume (48; 58), wherein the limitation on the rate of change of the control pressure volume when open is different from the limitation on the rate of change of the control pressure volume when closed. The device (16; 16a; 16b) for regulating volumetric flow has a diaphragm valve (42; 52) controllable by the pneumatic control element (17a; 17b; 49; 59), wherein the diaphragm valve (42; 52) can be operated via a loading connection (18a; 18b) and an unloading connection (19a; 19b), wherein the loading connection (18a; 18b) and the unloading connection (19a; 19b) have different constraints as limitations.

18. A computer program having program code, the program code being configured to perform the method (20) of claim 17 when executed on a computer, processor or programmable hardware component.

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